diff --git a/scripts/dev/compare_figure_inventory_legacy_vs_vnext.py b/scripts/dev/compare_figure_inventory_legacy_vs_vnext.py
index e03d740b..a149ebee 100644
--- a/scripts/dev/compare_figure_inventory_legacy_vs_vnext.py
+++ b/scripts/dev/compare_figure_inventory_legacy_vs_vnext.py
@@ -31,6 +31,14 @@ def compare_inventories(legacy: dict[str, object], vnext: dict[str, object]) ->
),
}
+def compare_blocks_file(blocks_path: Path) -> dict[str, object]:
+ blocks = [json.loads(line) for line in blocks_path.read_text(encoding="utf-8").splitlines() if line.strip()]
+ legacy = build_figure_inventory_legacy(blocks)
+ vnext = build_figure_inventory_vnext(blocks)
+ diff = compare_inventories(legacy, vnext)
+ diff["paper"] = blocks_path.parent.name
+ return diff
+
def main(blocks_path: str) -> int:
blocks = [json.loads(line) for line in Path(blocks_path).read_text(encoding="utf-8").splitlines() if line.strip()]
diff --git a/tests/fixtures/ocr_vnext_real_papers/2HEUD5P9/blocks.structured.jsonl b/tests/fixtures/ocr_vnext_real_papers/2HEUD5P9/blocks.structured.jsonl
new file mode 100644
index 00000000..34be0c77
--- /dev/null
+++ b/tests/fixtures/ocr_vnext_real_papers/2HEUD5P9/blocks.structured.jsonl
@@ -0,0 +1,670 @@
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 0, "raw_label": "header", "raw_order": null, "bbox": [98, 53, 210, 81], "text": "REVIEW", "page_width": 1191, "page_height": 1565, "role": "noise", "role_confidence": 0.9, "evidence": ["header label"], "seed_role": "noise", "seed_confidence": 0.9, "seed_evidence": ["header label"], "span_metadata": [{"size": 11.955100059509277, "font": "FuturaStd-ExtraBold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 0, "page": 1, "raw_label": "header", "text": "REVIEW", "bbox": [98, 53, 210, 81], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "short_fragment", "raw_marker": "REVIEW", "number": null, "kind": "short_fragment", "normalized_text": "REVIEW"}, "layout_signature": {"width": 112, "width_bucket": 100, "height": 28, "left": 98, "top": 53, "right": 210, "bottom": 81, "x_center": 154.0, "x_center_bucket": 150, "y_center": 67.0, "x_ratio": 0.1293, "y_ratio": 0.0428, "width_ratio": 0.094, "height_ratio": 0.0179, "line_count": 1}, "span_signature": {"font_size": 11.96, "font_size_median": 11.96, "font_size_bucket": 12.0, "font_family_norm": "FuturaStd-ExtraBold", "bold": true, "italic": true, "span_count": 1}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": false, "index_default": false, "zone": "frontmatter_main_zone", "style_family": "support_like", "style_family_authority": "zone_context", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 1, "raw_label": "header_image", "raw_order": null, "bbox": [1037, 2, 1190, 27], "text": "", "page_width": 1191, "page_height": 1565, "role": "unknown_structural", "role_confidence": 0.2, "evidence": ["unrecognized label 'header_image'"], "seed_role": "unknown_structural", "seed_confidence": 0.2, "seed_evidence": ["unrecognized label 'header_image'"], "span_metadata": null, "raw_observation": {"block_id": 1, "page": 1, "raw_label": "header_image", "text": "", "bbox": [1037, 2, 1190, 27], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "empty", "raw_marker": null, "number": null, "kind": null, "normalized_text": ""}, "layout_signature": {"width": 153, "width_bucket": 150, "height": 25, "left": 1037, "top": 2, "right": 1190, "bottom": 27, "x_center": 1113.5, "x_center_bucket": 1125, "y_center": 14.5, "x_ratio": 0.9349, "y_ratio": 0.0093, "width_ratio": 0.1285, "height_ratio": 0.016, "line_count": 1}, "span_signature": {"font_size": null, "font_size_median": null, "font_size_bucket": null, "font_family_norm": null, "bold": false, "italic": false, "span_count": 0}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": false, "index_default": true, "zone": "frontmatter_main_zone", "style_family": "support_like", "style_family_authority": "zone_context", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["non-structural role accepted"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 2, "raw_label": "header", "raw_order": null, "bbox": [901, 38, 1097, 117], "text": "small methods\nwww.small-methods.com", "page_width": 1191, "page_height": 1565, "role": "noise", "role_confidence": 0.9, "evidence": ["header label"], "seed_role": "noise", "seed_confidence": 0.9, "seed_evidence": ["header label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaSansPro-Bold", "flags": 20, "color": 255, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 2, "page": 1, "raw_label": "header", "text": "small methods\nwww.small-methods.com", "bbox": [901, 38, 1097, 117], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "small methods\nwww.small-methods.com"}, "layout_signature": {"width": 196, "width_bucket": 200, "height": 79, "left": 901, "top": 38, "right": 1097, "bottom": 117, "x_center": 999.0, "x_center_bucket": 1000, "y_center": 77.5, "x_ratio": 0.8388, "y_ratio": 0.0495, "width_ratio": 0.1646, "height_ratio": 0.0505, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaSansPro-Bold", "bold": true, "italic": true, "span_count": 1}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": false, "index_default": false, "zone": "frontmatter_main_zone", "style_family": "support_like", "style_family_authority": "zone_context", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 3, "raw_label": "doc_title", "raw_order": 1, "bbox": [96, 147, 1065, 238], "text": "Application of Bioactive Materials for Osteogenic Function in Bone Tissue Engineering", "page_width": 1191, "page_height": 1565, "role": "paper_title", "role_confidence": 0.8, "evidence": ["page-1 zone title_zone: Application of Bioactive Materials for Osteogenic Function i"], "seed_role": "paper_title", "seed_confidence": 0.8, "seed_evidence": ["page-1 zone title_zone: Application of Bioactive Materials for Osteogenic Function i"], "span_metadata": [{"size": 19.92530059814453, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 19.92530059814453, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 3, "page": 1, "raw_label": "doc_title", "text": "Application of Bioactive Materials for Osteogenic Function in Bone Tissue Engineering", "bbox": [96, 147, 1065, 238], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Application of Bioactive Materials for Osteogenic Function in Bone Tissue Engineering"}, "layout_signature": {"width": 969, "width_bucket": 975, "height": 91, "left": 96, "top": 147, "right": 1065, "bottom": 238, "x_center": 580.5, "x_center_bucket": 575, "y_center": 192.5, "x_ratio": 0.4874, "y_ratio": 0.123, "width_ratio": 0.8136, "height_ratio": 0.0581, "line_count": 1}, "span_signature": {"font_size": 19.93, "font_size_median": 19.93, "font_size_bucket": 20.0, "font_family_norm": "ScalaSansPro-Bold", "bold": true, "italic": true, "span_count": 2}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "frontmatter_main_zone", "style_family": "support_like", "style_family_authority": "zone_context", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.0, "decision": "body", "evidence": []}, "role_verification_status": "ACCEPT", "role_source": "source_frontmatter_title_anchor", "role_evidence": ["matched source title anchor"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 4, "raw_label": "text", "raw_order": 2, "bbox": [96, 268, 1035, 340], "text": "Yuxin Bai, Zhaojie Wang, Xiaolie He, Yanjing Zhu, Xu Xu, Huiyi Yang, Guangyu Mei, Shengguang Chen,* Bei Ma,* and Rongrong Zhu*", "page_width": 1191, "page_height": 1565, "role": "authors", "role_confidence": 0.8, "evidence": ["page-1 zone author_zone: Yuxin Bai, Zhaojie Wang, Xiaolie He, Yanjing Zhu, Xu Xu, Hui"], "seed_role": "authors", "seed_confidence": 0.8, "seed_evidence": ["page-1 zone author_zone: Yuxin Bai, Zhaojie Wang, Xiaolie He, Yanjing Zhu, Xu Xu, Hui"], "span_metadata": [{"size": 13.947699546813965, "font": "ScalaSansPro-Italic", "flags": 6, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 13.947699546813965, "font": "ScalaSansPro-Italic", "flags": 6, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 4, "page": 1, "raw_label": "text", "text": "Yuxin Bai, Zhaojie Wang, Xiaolie He, Yanjing Zhu, Xu Xu, Huiyi Yang, Guangyu Mei, Shengguang Chen,* Bei Ma,* and Rongrong Zhu*", "bbox": [96, 268, 1035, 340], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Yuxin Bai, Zhaojie Wang, Xiaolie He, Yanjing Zhu, Xu Xu, Huiyi Yang, Guangyu Mei, Shengguang Chen,* Bei Ma,* and Rongrong Zhu*"}, "layout_signature": {"width": 939, "width_bucket": 950, "height": 72, "left": 96, "top": 268, "right": 1035, "bottom": 340, "x_center": 565.5, "x_center_bucket": 575, "y_center": 304.0, "x_ratio": 0.4748, "y_ratio": 0.1942, "width_ratio": 0.7884, "height_ratio": 0.046, "line_count": 1}, "span_signature": {"font_size": 13.95, "font_size_median": 13.95, "font_size_bucket": 14.0, "font_family_norm": "ScalaSansPro-Italic", "bold": false, "italic": true, "span_count": 2}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "frontmatter_main_zone", "style_family": "support_like", "style_family_authority": "zone_context", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.0, "decision": "body", "evidence": []}, "role_verification_status": "ACCEPT", "role_source": "source_frontmatter_authors_anchor", "role_evidence": ["matched source authors anchor"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 5, "raw_label": "abstract", "raw_order": 3, "bbox": [114, 403, 761, 821], "text": "Bone tissue defects present a major challenge in orthopedic surgery. Bone tissue engineering using multiple versatile bioactive materials is a potential strategy for bone-defect repair and regeneration. Due to their unique physicochemical and mechanical properties, biofunctional materials can enhance cellular adhesion, proliferation, and osteogenic differentiation, thereby supporting and stimulating the formation of new bone tissue. 3D bioprinting and physical stimuli-responsive strategies have been employed in various studies on bone regeneration for the fabrication of desired multifunctional biomaterials with integrated bone tissue repair and regeneration properties. In this review, biomaterials applied to bone tissue engineering, emerging 3D bioprinting techniques, and physical stimuli-responsive strategies for the rational manufacturing of novel biomaterials with bone therapeutic and regenerative functions are summarized. Furthermore, the impact of biomaterials on the osteogenic differentiation of stem cells and the potential pathways associated with biomaterial-induced osteogenesis are discussed.", "page_width": 1191, "page_height": 1565, "role": "abstract_body", "role_confidence": 0.85, "evidence": ["abstract label from Paddle OCR"], "seed_role": "abstract_body", "seed_confidence": 0.85, "seed_evidence": ["abstract label from Paddle OCR"], "span_metadata": [{"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 9.713600158691406, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 5, "page": 1, "raw_label": "abstract", "text": "Bone tissue defects present a major challenge in orthopedic surgery. Bone tissue engineering using multiple versatile bioactive materials is a potential strategy for bone-defect repair and regeneration. Due to their unique physicochemical and mechanical properties, biofunctional materials can enhance cellular adhesion, proliferation, and osteogenic differentiation, thereby supporting and stimulating the formation of new bone tissue. 3D bioprinting and physical stimuli-responsive strategies have been employed in various studies on bone regeneration for the fabrication of desired multifunctional biomaterials with integrated bone tissue repair and regeneration properties. In this review, biomaterials applied to bone tissue engineering, emerging 3D bioprinting techniques, and physical stimuli-responsive strategies for the rational manufacturing of novel biomaterials with bone therapeutic and regenerative functions are summarized. Furthermore, the impact of biomaterials on the osteogenic differentiation of stem cells and the potential pathways associated with biomaterial-induced osteogenesis are discussed.", "bbox": [114, 403, 761, 821], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Bone tissue defects present a major challenge in orthopedic surgery. Bone tissue engineering using multiple versatile bioactive materials is a potential strategy for bone-defect repair and regeneration. Due to their unique physicochemical and mechanical properties, biofunctional materials can enhance cellular adhesion, proliferation, and osteogenic differentiation, thereby supporting and stimulating the formation of new bone tissue. 3D bioprinting and physical stimuli-responsive strategies have been employed in various studies on bone regeneration for the fabrication of desired multifunctional biomaterials with integrated bone tissue repair and regeneration properties. In this review, biomaterials applied to bone tissue engineering, emerging 3D bioprinting techniques, and physical stimuli-responsive strategies for the rational manufacturing of novel biomaterials with bone therapeutic and regenerative functions are summarized. Furthermore, the impact of biomaterials on the osteogenic differentiation of stem cells and the potential pathways associated with biomaterial-induced osteogenesis are discussed."}, "layout_signature": {"width": 647, "width_bucket": 650, "height": 418, "left": 114, "top": 403, "right": 761, "bottom": 821, "x_center": 437.5, "x_center_bucket": 450, "y_center": 612.0, "x_ratio": 0.3673, "y_ratio": 0.3911, "width_ratio": 0.5432, "height_ratio": 0.2671, "line_count": 1}, "span_signature": {"font_size": 9.71, "font_size_median": 9.71, "font_size_bucket": 9.5, "font_family_norm": "ScalaSansPro-Bold", "bold": true, "italic": true, "span_count": 16}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.0, "decision": "body", "evidence": []}, "role_verification_status": "ACCEPT", "role_source": "abstract_span_missing_fallback", "role_evidence": ["abstract body accepted from seed (no span to verify)"]}
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Bone tissue defects, infections, illnesses, and dislocations can impair the quality of life of a patient.[1] Autograft and allograft techniques are often used to treat bone-related diseases. Autografting involves the transfer of healthy tissue from the same individual to an injury site. Although this treatment has achieved outstanding therapeutic effects in recent years, it has significant limitations, such as scarcity of donor sites, the need for additional surgeries, and morbidity of the donor site. In contrast, allografts have the drawbacks of potential immune rejection, infection, and infectious disease transmission from the donor to the recipient.[2] These challenges can be overcome by emerging tissue engineering techniques, which aim to repair or regenerate native tissue using bioactive material composites that incorporate suitable cell sources and growth factors.[3,4]", "bbox": [781, 389, 1099, 870], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "component. Bone tissue defects, infections, illnesses, and dislocations can impair the quality of life of a patient.[1] Autograft and allograft techniques are often used to treat bone-related diseases. Autografting involves the transfer of healthy tissue from the same individual to an injury site. Although this treatment has achieved outstanding therapeutic effects in recent years, it has significant limitations, such as scarcity of donor sites, the need for additional surgeries, and morbidity of the donor site. In contrast, allografts have the drawbacks of potential immune rejection, infection, and infectious disease transmission from the donor to the recipient.[2] These challenges can be overcome by emerging tissue engineering techniques, which aim to repair or regenerate native tissue using bioactive material composites that incorporate suitable cell sources and growth factors.[3,4]"}, "layout_signature": {"width": 318, "width_bucket": 325, "height": 481, "left": 781, "top": 389, "right": 1099, "bottom": 870, "x_center": 940.0, "x_center_bucket": 950, "y_center": 629.5, "x_ratio": 0.7893, "y_ratio": 0.4022, "width_ratio": 0.267, "height_ratio": 0.3073, "line_count": 1}, "span_signature": {"font_size": 8.77, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 137}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 1, "block_id": 9, "raw_label": "footnote", "raw_order": null, "bbox": [96, 993, 584, 1365], "text": "Y. Bai, Z. Wang, X. He, Y. Zhu, X. Xu, H. Yang, G. Mei, S. Chen, B. Ma, R. Zhu\nKey Laboratory of Spine and Spinal Cord Injury Repair and Regeneration of Ministry of Education\nDepartment of Orthopedics\nTongji Hospital affiliated to Tongji University\nSchool of Life Science and Technology\nSchool of Medicine\nTongji University\nShanghai 200065, China\nE-mail: 1711119@tongji.edu.cn; 2000002@tongji.edu.cn; rrzhu@tongji.edu.cn\nR. Zhu\nFrontier Science Center for Stem Cell Research\nTongji University\nShanghai 200065, China\nS. Chen\nDepartment of Endocrinology and Metabolism\nGongli Hospital of Shanghai Pudong New Area\nShanghai 200135, China", "page_width": 1191, "page_height": 1565, "role": "footnote", "role_confidence": 0.7, "evidence": ["footnote label: Y. Bai, Z. Wang, X. He, Y. Zhu, X. Xu, H. Yang, G. Mei, S. 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Bai, Z. Wang, X. He, Y. Zhu, X. Xu, H. Yang, G. Mei, S. Chen, B. Ma, R. Zhu\nKey Laboratory of Spine and Spinal Cord Injury Repair and Regeneration of Ministry of Education\nDepartment of Orthopedics\nTongji Hospital affiliated to Tongji University\nSchool of Life Science and Technology\nSchool of Medicine\nTongji University\nShanghai 200065, China\nE-mail: 1711119@tongji.edu.cn; 2000002@tongji.edu.cn; rrzhu@tongji.edu.cn\nR. Zhu\nFrontier Science Center for Stem Cell Research\nTongji University\nShanghai 200065, China\nS. Chen\nDepartment of Endocrinology and Metabolism\nGongli Hospital of Shanghai Pudong New Area\nShanghai 200135, China", "bbox": [96, 993, 584, 1365], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Y. Bai, Z. Wang, X. He, Y. Zhu, X. Xu, H. Yang, G. Mei, S. Chen, B. Ma, R. Zhu\nKey Laboratory of Spine and Spinal Cord Injury Repair and Regeneration of Ministry of Education\nDepartment of Orthopedics\nTongji Hospital affiliated to Tongji University\nSchool of Life Science and Technology\nSchool of Medicine\nTongji University\nShanghai 200065, China\nE-mail: 1711119@tongji.edu.cn; 2000002@tongji.edu.cn; rrzhu@tongji.edu.cn\nR. Zhu\nFrontier Science Center for Stem Cell Research\nTongji University\nShanghai 200065, China\nS. Chen\nDepartment of Endocrinology and Metabolism\nGongli Hospital of Shanghai Pudong New Area\nShanghai 200135, China"}, "layout_signature": {"width": 488, "width_bucket": 500, "height": 372, "left": 96, "top": 993, "right": 584, "bottom": 1365, "x_center": 340.0, "x_center_bucket": 350, "y_center": 1179.0, "x_ratio": 0.2855, "y_ratio": 0.7534, "width_ratio": 0.4097, "height_ratio": 0.2377, "line_count": 1}, "span_signature": {"font_size": 7.97, "font_size_median": 7.97, "font_size_bucket": 8.0, "font_family_norm": "ScalaSansPro-Regular", "bold": false, "italic": true, "span_count": 24}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_138", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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Bone tissue engineering and regeneration offer a promising approach that utilizes several entities for bone tissue formation, such as biomaterials, stem cells, growth and differentiation factors, and scaffolds. $ ^{[5,6]} $ Bone tissue engineering scaffolds aim to mimic the features and properties of the natural bone extracellular matrix (ECM). $ ^{[7]} $ However, creating an intricate 3D environment may not be feasible with a single biomaterial and may necessitate the integration of the biofactors associated with the bone regeneration process. $ ^{[4]} $ Biomaterial-based scaffolds should ideally exhibit both osteoconductive and osteoinductive capabilities and establish a favorable niche for stem cells. $ ^{[8]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], 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Bone tissue engineering and regeneration offer a promising approach that utilizes several entities for bone tissue formation, such as biomaterials, stem cells, growth and differentiation factors, and scaffolds. $ ^{[5,6]} $ Bone tissue engineering scaffolds aim to mimic the features and properties of the natural bone extracellular matrix (ECM). $ ^{[7]} $ However, creating an intricate 3D environment may not be feasible with a single biomaterial and may necessitate the integration of the biofactors associated with the bone regeneration process. $ ^{[4]} $ Biomaterial-based scaffolds should ideally exhibit both osteoconductive and osteoinductive capabilities and establish a favorable niche for stem cells. $ ^{[8]} $", "bbox": [605, 871, 1099, 1177], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Bone regeneration requires effective solutions for bone loss and defects, which are prominent clinical challenges in orthopedic surgery. Bone tissue engineering and regeneration offer a promising approach that utilizes several entities for bone tissue formation, such as biomaterials, stem cells, growth and differentiation factors, and scaffolds. $ ^{[5,6]} $ Bone tissue engineering scaffolds aim to mimic the features and properties of the natural bone extracellular matrix (ECM). $ ^{[7]} $ However, creating an intricate 3D environment may not be feasible with a single biomaterial and may necessitate the integration of the biofactors associated with the bone regeneration process. $ ^{[4]} $ Biomaterial-based scaffolds should ideally exhibit both osteoconductive and osteoinductive capabilities and establish a favorable niche for stem cells. $ ^{[8]} $"}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 306, "left": 605, "top": 871, "right": 1099, "bottom": 1177, "x_center": 852.0, "x_center_bucket": 850, "y_center": 1024.0, "x_ratio": 0.7154, "y_ratio": 0.6543, "width_ratio": 0.4148, "height_ratio": 0.1955, "line_count": 1}, "span_signature": {"font_size": 8.73, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 154}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_141", "display_cluster_candidate_id": "", "layout_region": "reference_candidate", "boundary_before": "hard", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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While facilitating cell growth and differentiation to complete bone regeneration, scaffolds should exhibit high biocompatibility and biodegradability during the formation of new bone tissue.[10,11] Previous studies have indicated that some factors involved in osteogenic and chondrogenic differentiation, such as bone morphogenetic proteins (BMPs), transforming growth factor-β (TGF-β), and vascular endothelial growth factors (VEGFs), can trigger", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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In addition, advanced techniques such as 3D bioprinting and physical stimuli-responsive strategies have attracted increasing attention in the orthopedic field. $ ^{[13]} $", "bbox": [89, 148, 582, 281], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "specific differentiation pathways, thereby improving bone healing and osteogenesis. $ ^{[12]} $ Therefore, scaffolds should possess a considerable capacity for the delivery of these factors. In addition, advanced techniques such as 3D bioprinting and physical stimuli-responsive strategies have attracted increasing attention in the orthopedic field. $ ^{[13]} $"}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 133, "left": 89, "top": 148, "right": 582, "bottom": 281, "x_center": 335.5, "x_center_bucket": 325, "y_center": 214.5, "x_ratio": 0.2817, "y_ratio": 0.1371, "width_ratio": 0.4139, "height_ratio": 0.085, "line_count": 1}, "span_signature": {"font_size": 8.72, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 72}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 2, "block_id": 3, "raw_label": "text", "raw_order": 2, "bbox": [89, 281, 582, 676], "text": "Bioactive composite 3D porous scaffolds can improve the outcomes of bone-defect repair, including osteoconduction (bone cell infiltration into scaffolds), osseointegration (firm attachment of scaffolds to host bone tissue), osteoinduction (differentiation of host cells into osteogenic cells), and vascularization. $ ^{[14]} $ Bone cells can respond to physical stimuli such as light, electrical, and magnetic fields, ultrasound, and mechanical forces, which can induce cell adhesion, proliferation, and differentiation in scaffolds and ultimately enhance bone healing and regeneration. Many therapeutic biomaterials are composed of nanomaterials with therapeutic functions, such as photothermal nanoagents for photonic therapy, magnetic nanoparticles for magnetothermal therapy, and drug nanocarriers for chemotherapy. $ ^{[15-17]} $ Therefore, incorporating nanoparticles into bone scaffolds to develop physical stimuli-responsive scaffolds for bone-defect repair is an attractive strategy. 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"wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 3, "page": 2, "raw_label": "text", "text": "Bioactive composite 3D porous scaffolds can improve the outcomes of bone-defect repair, including osteoconduction (bone cell infiltration into scaffolds), osseointegration (firm attachment of scaffolds to host bone tissue), osteoinduction (differentiation of host cells into osteogenic cells), and vascularization. $ ^{[14]} $ Bone cells can respond to physical stimuli such as light, electrical, and magnetic fields, ultrasound, and mechanical forces, which can induce cell adhesion, proliferation, and differentiation in scaffolds and ultimately enhance bone healing and regeneration. Many therapeutic biomaterials are composed of nanomaterials with therapeutic functions, such as photothermal nanoagents for photonic therapy, magnetic nanoparticles for magnetothermal therapy, and drug nanocarriers for chemotherapy. $ ^{[15-17]} $ Therefore, incorporating nanoparticles into bone scaffolds to develop physical stimuli-responsive scaffolds for bone-defect repair is an attractive strategy. Several novel physical stimuli-responsive biomaterials have been developed using these strategies.", "bbox": [89, 281, 582, 676], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Bioactive composite 3D porous scaffolds can improve the outcomes of bone-defect repair, including osteoconduction (bone cell infiltration into scaffolds), osseointegration (firm attachment of scaffolds to host bone tissue), osteoinduction (differentiation of host cells into osteogenic cells), and vascularization. $ ^{[14]} $ Bone cells can respond to physical stimuli such as light, electrical, and magnetic fields, ultrasound, and mechanical forces, which can induce cell adhesion, proliferation, and differentiation in scaffolds and ultimately enhance bone healing and regeneration. Many therapeutic biomaterials are composed of nanomaterials with therapeutic functions, such as photothermal nanoagents for photonic therapy, magnetic nanoparticles for magnetothermal therapy, and drug nanocarriers for chemotherapy. $ ^{[15-17]} $ Therefore, incorporating nanoparticles into bone scaffolds to develop physical stimuli-responsive scaffolds for bone-defect repair is an attractive strategy. Several novel physical stimuli-responsive biomaterials have been developed using these strategies."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 395, "left": 89, "top": 281, "right": 582, "bottom": 676, "x_center": 335.5, "x_center_bucket": 325, "y_center": 478.5, "x_ratio": 0.2817, "y_ratio": 0.3058, "width_ratio": 0.4139, "height_ratio": 0.2524, "line_count": 1}, "span_signature": {"font_size": 8.87, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 194}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 2, "block_id": 4, "raw_label": "text", "raw_order": 3, "bbox": [90, 675, 582, 1158], "text": "Osteoconductivity and osteoinductivity of biomaterials has significant importance in clinical applications. The design of bone tissue engineering materials requires an understanding of the composition and structure of natural bone tissue, as well as the appropriate selection of biomimetic natural or tunable synthetic materials, such as polymers, bioceramics, metals, and composite materials. Scalable manufacturing techniques can be used to achieve control over the structural hierarchy at multiple length scales, including 3D printing technology, which can be used to process these biomaterials into forms suitable for bone tissue engineering. $ ^{[18]} $ Furthermore, Wang et al. reported that macrophages play a key role in the process of bone tissue injury repair and healing. Biomaterials regulate macrophage polarization and improve bone immune microenvironment, thereby accelerating bone regeneration. Bone biomaterials should have the ability of “bone immune regulation” to regulate local immune response to form a bone microenvironment that is conducive to bone regeneration. $ ^{[19]} $ Currently, the modification strategies of bone biomaterials mainly include changing the physicochemical properties of materials and constructing scaffold materials to deliver different bioactive substances.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], 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osteoinductivity of biomaterials has significant importance in clinical applications. The design of bone tissue engineering materials requires an understanding of the composition and structure of natural bone tissue, as well as the appropriate selection of biomimetic natural or tunable synthetic materials, such as polymers, bioceramics, metals, and composite materials. Scalable manufacturing techniques can be used to achieve control over the structural hierarchy at multiple length scales, including 3D printing technology, which can be used to process these biomaterials into forms suitable for bone tissue engineering. $ ^{[18]} $ Furthermore, Wang et al. reported that macrophages play a key role in the process of bone tissue injury repair and healing. Biomaterials regulate macrophage polarization and improve bone immune microenvironment, thereby accelerating bone regeneration. Bone biomaterials should have the ability of “bone immune regulation” to regulate local immune response to form a bone microenvironment that is conducive to bone regeneration. $ ^{[19]} $ Currently, the modification strategies of bone biomaterials mainly include changing the physicochemical properties of materials and constructing scaffold materials to deliver different bioactive substances.", "bbox": [90, 675, 582, 1158], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Osteoconductivity and osteoinductivity of biomaterials has significant importance in clinical applications. The design of bone tissue engineering materials requires an understanding of the composition and structure of natural bone tissue, as well as the appropriate selection of biomimetic natural or tunable synthetic materials, such as polymers, bioceramics, metals, and composite materials. Scalable manufacturing techniques can be used to achieve control over the structural hierarchy at multiple length scales, including 3D printing technology, which can be used to process these biomaterials into forms suitable for bone tissue engineering. $ ^{[18]} $ Furthermore, Wang et al. reported that macrophages play a key role in the process of bone tissue injury repair and healing. Biomaterials regulate macrophage polarization and improve bone immune microenvironment, thereby accelerating bone regeneration. Bone biomaterials should have the ability of “bone immune regulation” to regulate local immune response to form a bone microenvironment that is conducive to bone regeneration. $ ^{[19]} $ Currently, the modification strategies of bone biomaterials mainly include changing the physicochemical properties of materials and constructing scaffold materials to deliver different bioactive substances."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 483, "left": 90, "top": 675, "right": 582, "bottom": 1158, "x_center": 336.0, "x_center_bucket": 325, "y_center": 916.5, "x_ratio": 0.2821, "y_ratio": 0.5856, "width_ratio": 0.4131, "height_ratio": 0.3086, "line_count": 1}, "span_signature": {"font_size": 8.91, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 304}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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We also evaluated the advantages and disadvantages of these biomaterials and explored the current challenges and prospects of 3D bioprinting and physical stimuli-responsive strategies for the design of versatile bone biomaterials to satisfy the need for bone regeneration in diverse microenvironments (Figure 1).", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, 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This review summarizes several biomaterials and advanced techniques and illustrates the canonical biomedical applications for bone therapy and regeneration in recent literature. We also evaluated the advantages and disadvantages of these biomaterials and explored the current challenges and prospects of 3D bioprinting and physical stimuli-responsive strategies for the design of versatile bone biomaterials to satisfy the need for bone regeneration in diverse microenvironments (Figure 1).", "bbox": [89, 1157, 583, 1402], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Multiple biomaterials have been used in bone tissue repair and regeneration to date, largely owing to their unique properties. This review summarizes several biomaterials and advanced techniques and illustrates the canonical biomedical applications for bone therapy and regeneration in recent literature. We also evaluated the advantages and disadvantages of these biomaterials and explored the current challenges and prospects of 3D bioprinting and physical stimuli-responsive strategies for the design of versatile bone biomaterials to satisfy the need for bone regeneration in diverse microenvironments (Figure 1)."}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 245, "left": 89, "top": 1157, "right": 583, "bottom": 1402, "x_center": 336.0, "x_center_bucket": 325, "y_center": 1279.5, "x_ratio": 0.2821, "y_ratio": 0.8176, "width_ratio": 0.4148, "height_ratio": 0.1565, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 148}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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CaP-based ceramic biomaterials, including tricalcium phosphate (TCP), and biphasic calcium phosphate (BCP), hydroxyapatite (HAP), possess osteoconductive and osteoinductive characteristics and promote the osteogenic differentiation of mesenchymal stem cells (MSCs).[24] BGs that are capable of firmly bonding to bone and soft tissues mainly consist of silicate, borate, phosphorus, and calcium oxide.[25] Based on their different compositions and proportions, BGs can be divided into 45S5, 58S, and 1393 categories.[26] Many researchers have focused on bioactive ceramics, which are presented in the following sections.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], 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differentiation and bone regeneration.[20] Bioactive ceramics, such as CaP ceramics and bioactive glasses (BGs), possess osteoconductivity and excellent biocompatibility and have been used as bone substitutes for several decades.[21] Greater osteoinductivity derived from the mimicry of the mineral phase of bone makes bioactive ceramics a common bone-grafting material.[22] CaP is the main inorganic material in ≈70% of human bones.[23] CaP ceramics are extensively used for bone repair and regeneration, and some are commercially available for clinical use. CaP-based ceramic biomaterials, including tricalcium phosphate (TCP), and biphasic calcium phosphate (BCP), hydroxyapatite (HAP), possess osteoconductive and osteoinductive characteristics and promote the osteogenic differentiation of mesenchymal stem cells (MSCs).[24] BGs that are capable of firmly bonding to bone and soft tissues mainly consist of silicate, borate, phosphorus, and calcium oxide.[25] Based on their different compositions and proportions, BGs can be divided into 45S5, 58S, and 1393 categories.[26] Many researchers have focused on bioactive ceramics, which are presented in the following sections.", "bbox": [600, 231, 1092, 695], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Ceramics, which are non-metallic inorganic biomaterials, have been widely proposed for cell osteogenic differentiation and bone regeneration.[20] Bioactive ceramics, such as CaP ceramics and bioactive glasses (BGs), possess osteoconductivity and excellent biocompatibility and have been used as bone substitutes for several decades.[21] Greater osteoinductivity derived from the mimicry of the mineral phase of bone makes bioactive ceramics a common bone-grafting material.[22] CaP is the main inorganic material in ≈70% of human bones.[23] CaP ceramics are extensively used for bone repair and regeneration, and some are commercially available for clinical use. CaP-based ceramic biomaterials, including tricalcium phosphate (TCP), and biphasic calcium phosphate (BCP), hydroxyapatite (HAP), possess osteoconductive and osteoinductive characteristics and promote the osteogenic differentiation of mesenchymal stem cells (MSCs).[24] BGs that are capable of firmly bonding to bone and soft tissues mainly consist of silicate, borate, phosphorus, and calcium oxide.[25] Based on their different compositions and proportions, BGs can be divided into 45S5, 58S, and 1393 categories.[26] Many researchers have focused on bioactive ceramics, which are presented in the following sections."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 464, "left": 600, "top": 231, "right": 1092, "bottom": 695, "x_center": 846.0, "x_center_bucket": 850, "y_center": 463.0, "x_ratio": 0.7103, "y_ratio": 0.2958, "width_ratio": 0.4131, "height_ratio": 0.2965, "line_count": 1}, "span_signature": {"font_size": 8.68, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 221}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 2, "block_id": 10, "raw_label": "text", "raw_order": 9, "bbox": [600, 759, 1093, 1177], "text": "HAP is one of the most extensively used CaP ceramics in bone repair and regeneration because of its similarity to the components of human bone minerals.[27,28] HAP with the capability of osteoconductivity and osteoinductivity, can promote bone growth on the surface of biomaterials, and induce the differentiation of progenitor cells into osteoblasts.[29,30] The synthetic whitlockite (WH: Ca $ _{18} $Mg $ _{2} $(HPO $ _{4} $) $ _2 $(PO $ _{4} $) $ _12 $) nanoparticles can recapitulate early-stage of bone regeneration through stimulating osteogenic differentiation, prohibiting osteoclastic activity, and transforming into mechanically enhanced HAP-neo bone tissues (Figure 2A–D). The release of calcium and phosphate ions from HAP scaffolds promotes osteoblast differentiation, accelerate bone formation through calcification, and upregulate the expression of osteoblastic differentiation-related genes. Ion doping is a modification method that can alter the structure of HAP and make it more widely applicable in biological performance. For example, doping elements such as calcium ions, zinc ions, and magnesium ions can improve the biological activity and biodegradability of HAP.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 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"text": "HAP is one of the most extensively used CaP ceramics in bone repair and regeneration because of its similarity to the components of human bone minerals.[27,28] HAP with the capability of osteoconductivity and osteoinductivity, can promote bone growth on the surface of biomaterials, and induce the differentiation of progenitor cells into osteoblasts.[29,30] The synthetic whitlockite (WH: Ca $ _{18} $Mg $ _{2} $(HPO $ _{4} $) $ _2 $(PO $ _{4} $) $ _12 $) nanoparticles can recapitulate early-stage of bone regeneration through stimulating osteogenic differentiation, prohibiting osteoclastic activity, and transforming into mechanically enhanced HAP-neo bone tissues (Figure 2A–D). The release of calcium and phosphate ions from HAP scaffolds promotes osteoblast differentiation, accelerate bone formation through calcification, and upregulate the expression of osteoblastic differentiation-related genes. Ion doping is a modification method that can alter the structure of HAP and make it more widely applicable in biological performance. For example, doping elements such as calcium ions, zinc ions, and magnesium ions can improve the biological activity and biodegradability of HAP.", "bbox": [600, 759, 1093, 1177], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "HAP is one of the most extensively used CaP ceramics in bone repair and regeneration because of its similarity to the components of human bone minerals.[27,28] HAP with the capability of osteoconductivity and osteoinductivity, can promote bone growth on the surface of biomaterials, and induce the differentiation of progenitor cells into osteoblasts.[29,30] The synthetic whitlockite (WH: Ca $ _{18} $Mg $ _{2} $(HPO $ _{4} $) $ _2 $(PO $ _{4} $) $ _12 $) nanoparticles can recapitulate early-stage of bone regeneration through stimulating osteogenic differentiation, prohibiting osteoclastic activity, and transforming into mechanically enhanced HAP-neo bone tissues (Figure 2A–D). The release of calcium and phosphate ions from HAP scaffolds promotes osteoblast differentiation, accelerate bone formation through calcification, and upregulate the expression of osteoblastic differentiation-related genes. Ion doping is a modification method that can alter the structure of HAP and make it more widely applicable in biological performance. For example, doping elements such as calcium ions, zinc ions, and magnesium ions can improve the biological activity and biodegradability of HAP."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 418, "left": 600, "top": 759, "right": 1093, "bottom": 1177, "x_center": 846.5, "x_center_bucket": 850, "y_center": 968.0, "x_ratio": 0.7107, "y_ratio": 0.6185, "width_ratio": 0.4139, "height_ratio": 0.2671, "line_count": 1}, "span_signature": {"font_size": 8.82, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 253}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_141", "display_cluster_candidate_id": "", "layout_region": "reference_candidate", "boundary_before": "hard", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 2, "block_id": 11, "raw_label": "text", "raw_order": 10, "bbox": [599, 1176, 1093, 1399], "text": "HAP has some drawbacks compared with other CaP ceramics, including poor mechanical properties and low degradability. Therefore, HAP is often mixed with polymers to yield composite scaffolds with improved mechanical properties and biodegradability. Porous bone scaffolds comprising HAP were recently manufactured, and demonstrated enhanced compressive strength and biodegradation properties. Wu et al. embedded HAP and nano-magnesium oxide (MgO) in cocoon fibers (F) and silk fibroin (SF), and this composite scaffold with irregular porous and interconnected architecture exhibited good", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 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"text": "β-TCP can be prepared using two methods: high-temperature solid-phase reaction and room-temperature wet method. The high-temperature solid-phase reaction method typically involves mixing CaHPO₄·2H₂O and CaCO₃ in a 2:1 molar ratio and heating the mixture at 800—1000 °C for 10 hours to produce β-TCP powder. The room-temperature wet method, also known as the aqueous solution reaction method, involves mixing calcium hydroxide or soluble calcium salt with phosphate salt in a certain proportion, allowing the precipitate to react and then drying and calcining it to obtain β-TCP ceramic powder. The advantages of high-temperature solid-phase reaction method include simple preparation process, short reaction time, good crystal quality, and controllable crystal size. However, this method also has some disadvantages such as requiring high-temperature heat treatment, easy impurity generation, and high cost. The advantages of room temperature wet method include simple preparation process, convenient operation, low cost, uniform particle size, and high", "bbox": [604, 1071, 1099, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "β-TCP can be prepared using two methods: high-temperature solid-phase reaction and room-temperature wet method. The high-temperature solid-phase reaction method typically involves mixing CaHPO₄·2H₂O and CaCO₃ in a 2:1 molar ratio and heating the mixture at 800—1000 °C for 10 hours to produce β-TCP powder. The room-temperature wet method, also known as the aqueous solution reaction method, involves mixing calcium hydroxide or soluble calcium salt with phosphate salt in a certain proportion, allowing the precipitate to react and then drying and calcining it to obtain β-TCP ceramic powder. The advantages of high-temperature solid-phase reaction method include simple preparation process, short reaction time, good crystal quality, and controllable crystal size. However, this method also has some disadvantages such as requiring high-temperature heat treatment, easy impurity generation, and high cost. The advantages of room temperature wet method include simple preparation process, convenient operation, low cost, uniform particle size, and high"}, "layout_signature": {"width": 495, "width_bucket": 500, "height": 374, "left": 604, "top": 1071, "right": 1099, "bottom": 1445, "x_center": 851.5, "x_center_bucket": 850, "y_center": 1258.0, "x_ratio": 0.7149, "y_ratio": 0.8038, "width_ratio": 0.4156, "height_ratio": 0.239, "line_count": 1}, "span_signature": {"font_size": 8.9, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "STIXMath-Italic", "bold": false, "italic": true, "span_count": 129}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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G) Percentage changes of density and porosity in the three kinds of samples after implantation for 90 days. $ ^{[39]} $ Copyright 2019, American Chemical Society. H) Incorporation of Cu-containing bioactive glass nanoparticles in gelatin-coated scaffolds enhances bioactivity and osteogenic activity. I) Digital photographs of uncoated and coated scaffolds before (inserted) and after compressive strength test showing different mechanical failure behaviors. $ ^{[45]} $ Copyright 2018, American Chemical Society.", "page_width": 1191, "page_height": 1565, "role": "figure_caption", "role_confidence": 0.92, "evidence": ["figure_title label: Figure 2. A) In vivo bone regeneration efficacy of whitlocki"], "seed_role": "figure_caption", "seed_confidence": 0.92, "seed_evidence": ["figure_title label: Figure 2. 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A) In vivo bone regeneration efficacy of whitlockite (WH: Ca $ _{18} $Mg $ _{2} $(HPO $ _{4} $) $ _{2} $(PO $ _{4} $) $ _{12} $) embedded 3D cryogel implants after 6 weeks of subcutaneous injection, each group of cryogels rendered by the micro-CT program as grey areas indicated the amount of mineralization. B) Young's modulus of subcutaneously injected cryogels for each group. C) Bone formations were examined via subcutaneous implantation and critical sized calvarial defect models. D) In vivo bone regeneration of the calvarial defects by ARS staining. $ ^{[30]} $ Copyright 2017, Elsevier. E) Sketch map illustrating the fabrication process of the spherical BCP ceramic spheres with nanocrystalline. F) 3D visualizations of BCP-G, BCP-N, and BCP-I before and after implantation. G) Percentage changes of density and porosity in the three kinds of samples after implantation for 90 days. $ ^{[39]} $ Copyright 2019, American Chemical Society. H) Incorporation of Cu-containing bioactive glass nanoparticles in gelatin-coated scaffolds enhances bioactivity and osteogenic activity. I) Digital photographs of uncoated and coated scaffolds before (inserted) and after compressive strength test showing different mechanical failure behaviors. $ ^{[45]} $ Copyright 2018, American Chemical Society.", "bbox": [90, 1187, 1094, 1361], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "figure_number", "raw_marker": "Figure 2", "number": 2, "kind": "figure", "normalized_text": "Figure 2. A) In vivo bone regeneration efficacy of whitlockite (WH: Ca $ _{18} $Mg $ _{2} $(HPO $ _{4} $) $ _{2} $(PO $ _{4} $) $ _{12} $) embedded 3D cryogel implants after 6 weeks of subcutaneous injection, each group of cryogels rendered by the micro-CT program as grey areas indicated the amount of mineralization. B) Young's modulus of subcutaneously injected cryogels for each group. C) Bone formations were examined via subcutaneous implantation and critical sized calvarial defect models. D) In vivo bone regeneration of the calvarial defects by ARS staining. $ ^{[30]} $ Copyright 2017, Elsevier. E) Sketch map illustrating the fabrication process of the spherical BCP ceramic spheres with nanocrystalline. F) 3D visualizations of BCP-G, BCP-N, and BCP-I before and after implantation. G) Percentage changes of density and porosity in the three kinds of samples after implantation for 90 days. $ ^{[39]} $ Copyright 2019, American Chemical Society. H) Incorporation of Cu-containing bioactive glass nanoparticles in gelatin-coated scaffolds enhances bioactivity and osteogenic activity. 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"raw_observation": {"block_id": 4, "page": 5, "raw_label": "text", "text": "However, $ \\beta $-TCP scaffolds are brittle and are often mixed with other biomaterials to counteract the drawback of low tensile strength. The use of porous $ \\beta $-TCP scaffolds in bone regeneration could increase cell proliferation and adhesion. Kumar et al. synthesized a biocompatible and biodegradable PCL-PGA- $ \\beta $-TCP scaffold that was both porous and mechanically strong. During the degradation of PGA, the architecture of scaffold would develop porosity, and the corresponding decreased mechanical strength was compensated by new bone formation and ingrowth. $ ^{[35]} $", "bbox": [95, 281, 587, 501], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "However, $ \\beta $-TCP scaffolds are brittle and are often mixed with other biomaterials to counteract the drawback of low tensile strength. The use of porous $ \\beta $-TCP scaffolds in bone regeneration could increase cell proliferation and adhesion. Kumar et al. synthesized a biocompatible and biodegradable PCL-PGA- $ \\beta $-TCP scaffold that was both porous and mechanically strong. During the degradation of PGA, the architecture of scaffold would develop porosity, and the corresponding decreased mechanical strength was compensated by new bone formation and ingrowth. $ ^{[35]} $"}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 220, "left": 95, "top": 281, "right": 587, "bottom": 501, "x_center": 341.0, "x_center_bucket": 350, "y_center": 391.0, "x_ratio": 0.2863, "y_ratio": 0.2498, "width_ratio": 0.4131, "height_ratio": 0.1406, "line_count": 1}, "span_signature": {"font_size": 8.89, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 111}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 5, "block_id": 6, "raw_label": "text", "raw_order": 4, "bbox": [95, 587, 588, 917], "text": "BCP is a combination of HAP and $ \\beta $-TCP, and, as a result, combines the advantages of two calcium phosphates, including the good biocompatibility, osteoconductivity, and osteoinductivity of both, and the biodegradability of $ \\beta $-TCP. $ ^{[36]} $ The characteristics of BCP are determined by the HAP: $ \\beta $-TCP ratio, and BCP with a high $ \\beta $-TCP content exhibits a faster degradation rate and better osteoinductivity. $ ^{[37]} $ BCP with a particle size ranging from 40 to 1500 $ \\mu $m possess superior osteoconductivity, and promotes osteogenesis in vivo. $ ^{[38]} $ Li et al. fabricated porous BCP ceramic spheres with nanocrystalline (BCP-N) by combining alginate gelatinizing with microwave hybrid sintering methods, and their results showed the obtained BCP-N with specific nanotopography could well initiate and regulate in vitro biological response, such as degradation, protein adsorption, bone-like apatite formation, cell behaviors, and osteogenic differentiation (Figure 2E–G). $ ^{[39]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "STIXMath-Italic", "flags": 6, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 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osteoconductivity, and osteoinductivity of both, and the biodegradability of $ \\beta $-TCP. $ ^{[36]} $ The characteristics of BCP are determined by the HAP: $ \\beta $-TCP ratio, and BCP with a high $ \\beta $-TCP content exhibits a faster degradation rate and better osteoinductivity. $ ^{[37]} $ BCP with a particle size ranging from 40 to 1500 $ \\mu $m possess superior osteoconductivity, and promotes osteogenesis in vivo. $ ^{[38]} $ Li et al. fabricated porous BCP ceramic spheres with nanocrystalline (BCP-N) by combining alginate gelatinizing with microwave hybrid sintering methods, and their results showed the obtained BCP-N with specific nanotopography could well initiate and regulate in vitro biological response, such as degradation, protein adsorption, bone-like apatite formation, cell behaviors, and osteogenic differentiation (Figure 2E–G). $ ^{[39]} $", "bbox": [95, 587, 588, 917], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "BCP is a combination of HAP and $ \\beta $-TCP, and, as a result, combines the advantages of two calcium phosphates, including the good biocompatibility, osteoconductivity, and osteoinductivity of both, and the biodegradability of $ \\beta $-TCP. $ ^{[36]} $ The characteristics of BCP are determined by the HAP: $ \\beta $-TCP ratio, and BCP with a high $ \\beta $-TCP content exhibits a faster degradation rate and better osteoinductivity. $ ^{[37]} $ BCP with a particle size ranging from 40 to 1500 $ \\mu $m possess superior osteoconductivity, and promotes osteogenesis in vivo. $ ^{[38]} $ Li et al. fabricated porous BCP ceramic spheres with nanocrystalline (BCP-N) by combining alginate gelatinizing with microwave hybrid sintering methods, and their results showed the obtained BCP-N with specific nanotopography could well initiate and regulate in vitro biological response, such as degradation, protein adsorption, bone-like apatite formation, cell behaviors, and osteogenic differentiation (Figure 2E–G). $ ^{[39]} $"}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 330, "left": 95, "top": 587, "right": 588, "bottom": 917, "x_center": 341.5, "x_center_bucket": 350, "y_center": 752.0, "x_ratio": 0.2867, "y_ratio": 0.4805, "width_ratio": 0.4139, "height_ratio": 0.2109, "line_count": 1}, "span_signature": {"font_size": 8.68, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 127}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 5, "block_id": 7, "raw_label": "text", "raw_order": 5, "bbox": [96, 918, 587, 1203], "text": "Nevertheless, BCP has low biological activity, which is not conducive to the proliferation and differentiation of bone cells. In addition, the slow degradation rate of BCP may affect the regeneration and repair of bone tissue. To address these issues, researchers have been developing new BCP composite materials that can enhance its biological activity and degradability. For example, some studies have shown that incorporating bioactive agents such as growth factors or extracellular matrix proteins into BCP can improve its biological activity and promote bone regeneration. In addition, 3D printing technology has emerged as a promising approach for fabricating BCP scaffolds with complex geometries and tailored mechanical properties for personalized treatment.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, 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In addition, the slow degradation rate of BCP may affect the regeneration and repair of bone tissue. To address these issues, researchers have been developing new BCP composite materials that can enhance its biological activity and degradability. For example, some studies have shown that incorporating bioactive agents such as growth factors or extracellular matrix proteins into BCP can improve its biological activity and promote bone regeneration. 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+{"paper_id": "2HEUD5P9", "page": 5, "block_id": 11, "raw_label": "text", "raw_order": 9, "bbox": [605, 303, 1098, 632], "text": "Mesoporous BGs doped with manganese and silver have been proposed to exhibit antibacterial activity and facilitate wound healing by preventing infection. $ ^{[49,50]} $ Nanostructured BGs with highly ordered mesopores and surface area can also be an excellent delivery system for drugs, proteins, and growth factors to further promote bone repair and regeneration. Furthermore, BGs with osteoconductive and osteoinductive properties can firmly bind to living bone and aid in bone repair and regeneration. BGs scaffolds with good biocompatibility could stimulate the proliferation and differentiation of osteoblasts and the formation of mature bone at the bone-BG interface. The Cu-BGN/gelatin nanocomposite coated BGS exhibiting high bioactivity, appropriate mechanical properties, and osteogenic potential are candidate biomaterials for bone tissue engineering/regeneration (Figure 2H,I). $ ^{[45]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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system for drugs, proteins, and growth factors to further promote bone repair and regeneration. Furthermore, BGs with osteoconductive and osteoinductive properties can firmly bind to living bone and aid in bone repair and regeneration. BGs scaffolds with good biocompatibility could stimulate the proliferation and differentiation of osteoblasts and the formation of mature bone at the bone-BG interface. The Cu-BGN/gelatin nanocomposite coated BGS exhibiting high bioactivity, appropriate mechanical properties, and osteogenic potential are candidate biomaterials for bone tissue engineering/regeneration (Figure 2H,I). $ ^{[45]} $", "bbox": [605, 303, 1098, 632], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Mesoporous BGs doped with manganese and silver have been proposed to exhibit antibacterial activity and facilitate wound healing by preventing infection. $ ^{[49,50]} $ Nanostructured BGs with highly ordered mesopores and surface area can also be an excellent delivery system for drugs, proteins, and growth factors to further promote bone repair and regeneration. Furthermore, BGs with osteoconductive and osteoinductive properties can firmly bind to living bone and aid in bone repair and regeneration. BGs scaffolds with good biocompatibility could stimulate the proliferation and differentiation of osteoblasts and the formation of mature bone at the bone-BG interface. The Cu-BGN/gelatin nanocomposite coated BGS exhibiting high bioactivity, appropriate mechanical properties, and osteogenic potential are candidate biomaterials for bone tissue engineering/regeneration (Figure 2H,I). $ ^{[45]} $"}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 329, "left": 605, "top": 303, "right": 1098, "bottom": 632, "x_center": 851.5, "x_center_bucket": 850, "y_center": 467.5, "x_ratio": 0.7149, "y_ratio": 0.2987, "width_ratio": 0.4139, "height_ratio": 0.2102, "line_count": 1}, "span_signature": {"font_size": 8.86, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 161}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 5, "block_id": 12, "raw_label": "text", "raw_order": 10, "bbox": [605, 633, 1098, 1004], "text": "Among various preparation methods, sol-gel method is a common one, which involves preparing sol, gel, drying, and heat treatment. BGs has good biocompatibility and biodegradability, which can promote bone tissue regeneration and repair by closely bonding with bone tissue through the formation of hydroxyapatite when in contact with body fluid. However, BGs also have some drawbacks in bone regeneration and repair. For example, BGs has a slow degradation rate, which may affect bone tissue regeneration and repair. In addition, BGs have low strength and high brittleness, which are not suitable for complex mechanical environments such as load-bearing bones. In the future, new methods need to be explored to improve the performance of BGs and enhance its application prospects in bone regeneration and repair. For instance, developing new BGs composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using 3D printing technology to manufacture BGs scaffolds for personalized treatment.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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BGs has good biocompatibility and biodegradability, which can promote bone tissue regeneration and repair by closely bonding with bone tissue through the formation of hydroxyapatite when in contact with body fluid. However, BGs also have some drawbacks in bone regeneration and repair. For example, BGs has a slow degradation rate, which may affect bone tissue regeneration and repair. In addition, BGs have low strength and high brittleness, which are not suitable for complex mechanical environments such as load-bearing bones. In the future, new methods need to be explored to improve the performance of BGs and enhance its application prospects in bone regeneration and repair. For instance, developing new BGs composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using 3D printing technology to manufacture BGs scaffolds for personalized treatment.", "bbox": [605, 633, 1098, 1004], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Among various preparation methods, sol-gel method is a common one, which involves preparing sol, gel, drying, and heat treatment. BGs has good biocompatibility and biodegradability, which can promote bone tissue regeneration and repair by closely bonding with bone tissue through the formation of hydroxyapatite when in contact with body fluid. However, BGs also have some drawbacks in bone regeneration and repair. For example, BGs has a slow degradation rate, which may affect bone tissue regeneration and repair. In addition, BGs have low strength and high brittleness, which are not suitable for complex mechanical environments such as load-bearing bones. In the future, new methods need to be explored to improve the performance of BGs and enhance its application prospects in bone regeneration and repair. For instance, developing new BGs composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using 3D printing technology to manufacture BGs scaffolds for personalized treatment."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 371, "left": 605, "top": 633, "right": 1098, "bottom": 1004, "x_center": 851.5, "x_center_bucket": 850, "y_center": 818.5, "x_ratio": 0.7149, "y_ratio": 0.523, "width_ratio": 0.4139, "height_ratio": 0.2371, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 131}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 5, "block_id": 13, "raw_label": "text", "raw_order": 11, "bbox": [604, 1004, 1099, 1313], "text": "In recent years, ceramics has been utilized in various forms, such as coating and scaffold, for bone regeneration due to its unique bioactive properties and effectiveness in promoting bone regeneration. The activation of osteoblasts and stem cells to facilitate bone regeneration could be regulated by the released bioactive ions from ceramics. The surface properties and porosity of ceramics play a crucial role in regulating cell/protein adhesion and growth, as well as bone mineral formation. Different types of ceramics can be applied in multiple applications due to differences in mechanical strength, stability, ion release and solubility. The advantages and disadvantages of the above-mentioned ceramics were listed as follows (Table 1). To make the utmost of their properties, ceramics have been combined with other materials to complement their drawbacks and highlight their strengths.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 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The activation of osteoblasts and stem cells to facilitate bone regeneration could be regulated by the released bioactive ions from ceramics. The surface properties and porosity of ceramics play a crucial role in regulating cell/protein adhesion and growth, as well as bone mineral formation. Different types of ceramics can be applied in multiple applications due to differences in mechanical strength, stability, ion release and solubility. The advantages and disadvantages of the above-mentioned ceramics were listed as follows (Table 1). To make the utmost of their properties, ceramics have been combined with other materials to complement their drawbacks and highlight their strengths.", "bbox": [604, 1004, 1099, 1313], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "In recent years, ceramics has been utilized in various forms, such as coating and scaffold, for bone regeneration due to its unique bioactive properties and effectiveness in promoting bone regeneration. The activation of osteoblasts and stem cells to facilitate bone regeneration could be regulated by the released bioactive ions from ceramics. The surface properties and porosity of ceramics play a crucial role in regulating cell/protein adhesion and growth, as well as bone mineral formation. Different types of ceramics can be applied in multiple applications due to differences in mechanical strength, stability, ion release and solubility. The advantages and disadvantages of the above-mentioned ceramics were listed as follows (Table 1). 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| Type of ceramics | Advantages | Disadvantages | References |
| HAP | Resembles mineral phase of bone | Poor mechanical properties | [27,29] |
| Can be doped with multiple ions to closely mimic bone mineral | Slow degradation rates in vivo |
| High biocompatibility can be used in a plethora of formulations |
| Osteoconductivity and osteoinductivity |
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| Osteoconductivity | Higher biodegradability |
| Can be doped with multiple ions to tune bioactivity and degradation |
| High biocompatibility |
| BCP | Bioresorbability | Low mechanical property | [36-38] |
| Osteoconductivity and osteoinductivity | Rapid degradability |
| High biocompatibility |
| BGs | Biocompatible | Suboptimal biodegradation | [40,41] |
| Enhanced bone integration | Poor mechanical properties |
| Improved biodegradation | Lower biodegradability |
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| HAP | Resembles mineral phase of bone | Poor mechanical properties | [27,29] |
| Can be doped with multiple ions to closely mimic bone mineral | Slow degradation rates in vivo |
| High biocompatibility can be used in a plethora of formulations |
| Osteoconductivity and osteoinductivity |
| TCP | Faster in vivo degradation | Poor mechanical properties | [33,34] |
| Osteoconductivity | Higher biodegradability |
| Can be doped with multiple ions to tune bioactivity and degradation |
| High biocompatibility |
| BCP | Bioresorbability | Low mechanical property | [36-38] |
| Osteoconductivity and osteoinductivity | Rapid degradability |
| High biocompatibility |
| BGs | Biocompatible | Suboptimal biodegradation | [40,41] |
| Enhanced bone integration | Poor mechanical properties |
| Improved biodegradation | Lower biodegradability |
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| Can be doped with multiple ions to closely mimic bone mineral | Slow degradation rates in vivo |
| High biocompatibility can be used in a plethora of formulations |
| Osteoconductivity and osteoinductivity |
| TCP | Faster in vivo degradation | Poor mechanical properties | [33,34] |
| Osteoconductivity | Higher biodegradability |
| Can be doped with multiple ions to tune bioactivity and degradation |
| High biocompatibility |
| BCP | Bioresorbability | Low mechanical property | [36-38] |
| Osteoconductivity and osteoinductivity | Rapid degradability |
| High biocompatibility |
| BGs | Biocompatible | Suboptimal biodegradation | [40,41] |
| Enhanced bone integration | Poor mechanical properties |
| Improved biodegradation | Lower biodegradability |
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+{"paper_id": "2HEUD5P9", "page": 6, "block_id": 5, "raw_label": "text", "raw_order": 1, "bbox": [89, 609, 582, 1073], "text": "classified as natural or synthetic polymers. Natural polymers such as polysaccharides (chitosan, hyaluronic acid, cellulose, alginate, starch, carrageenan, and gellan gum) and proteins (collagen, gelatin, fibrin, and silk fibroin) are suitable for bone tissue regeneration because of their natural origin, good biocompatibility and biodegradability, and similarity to the structural native ECM of tissues. $ ^{[51,52]} $ Chitosan, alginate, hyaluronic acid, collagen, gelatin, and silk fibroin are commonly used in bone tissue engineering. Although bioactive natural polymers can interact with host tissues, they have drawbacks such as insufficient mechanical properties, batch variation, high degradation rates, and immunogenicity. $ ^{[53]} $ Synthetic polymers exhibit tailored structures and characteristics owing to the appropriate design of their functional groups. Polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), polylactic-coglycolic acid (PLGA), and other synthetic polymers can be fabricated with different pore sizes, porosities, degradation rates, morphologies, and mechanical properties. However, synthetic polymers lack bioactivity and cell interactions and exhibit reduced osteoconductivity. Hence, synthetic polymers are often mixed with biomaterials for bone repair and regeneration.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 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Natural polymers such as polysaccharides (chitosan, hyaluronic acid, cellulose, alginate, starch, carrageenan, and gellan gum) and proteins (collagen, gelatin, fibrin, and silk fibroin) are suitable for bone tissue regeneration because of their natural origin, good biocompatibility and biodegradability, and similarity to the structural native ECM of tissues. $ ^{[51,52]} $ Chitosan, alginate, hyaluronic acid, collagen, gelatin, and silk fibroin are commonly used in bone tissue engineering. Although bioactive natural polymers can interact with host tissues, they have drawbacks such as insufficient mechanical properties, batch variation, high degradation rates, and immunogenicity. $ ^{[53]} $ Synthetic polymers exhibit tailored structures and characteristics owing to the appropriate design of their functional groups. Polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), polylactic-coglycolic acid (PLGA), and other synthetic polymers can be fabricated with different pore sizes, porosities, degradation rates, morphologies, and mechanical properties. However, synthetic polymers lack bioactivity and cell interactions and exhibit reduced osteoconductivity. Hence, synthetic polymers are often mixed with biomaterials for bone repair and regeneration.", "bbox": [89, 609, 582, 1073], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "classified as natural or synthetic polymers. Natural polymers such as polysaccharides (chitosan, hyaluronic acid, cellulose, alginate, starch, carrageenan, and gellan gum) and proteins (collagen, gelatin, fibrin, and silk fibroin) are suitable for bone tissue regeneration because of their natural origin, good biocompatibility and biodegradability, and similarity to the structural native ECM of tissues. $ ^{[51,52]} $ Chitosan, alginate, hyaluronic acid, collagen, gelatin, and silk fibroin are commonly used in bone tissue engineering. Although bioactive natural polymers can interact with host tissues, they have drawbacks such as insufficient mechanical properties, batch variation, high degradation rates, and immunogenicity. $ ^{[53]} $ Synthetic polymers exhibit tailored structures and characteristics owing to the appropriate design of their functional groups. Polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), polylactic-coglycolic acid (PLGA), and other synthetic polymers can be fabricated with different pore sizes, porosities, degradation rates, morphologies, and mechanical properties. However, synthetic polymers lack bioactivity and cell interactions and exhibit reduced osteoconductivity. Hence, synthetic polymers are often mixed with biomaterials for bone repair and regeneration."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 464, "left": 89, "top": 609, "right": 582, "bottom": 1073, "x_center": 335.5, "x_center_bucket": 325, "y_center": 841.0, "x_ratio": 0.2817, "y_ratio": 0.5374, "width_ratio": 0.4139, "height_ratio": 0.2965, "line_count": 1}, "span_signature": {"font_size": 8.86, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 161}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 6, "block_id": 7, "raw_label": "text", "raw_order": 3, "bbox": [89, 1157, 583, 1445], "text": "Chitosan is made up of glucosamine and N-acetyl glucosamine units that are linked together by $ \\beta(1-4) $ glycosidic bonds. Chitosan is a versatile natural polymer derived from the partial deacetylation of chitin. It has good biocompatibility and biodegradability, low toxicity, and antibacterial properties, and is extensively used in bone scaffolds. Chitosan can be degraded into absorbable, nontoxic, small-molecule polysaccharides and amino acids by chitosanolytic enzymes. $ ^{[54]} $ Considering its formulation and structure, chitosan can promote cell adhesion and proliferation of osteoblasts and MSCs, and enhance the formation of mineralized bone matrix. $ ^{[55,56]} $ Lei et al. fabricated strontium hydroxypatite (SrHAP)/chitosan nanohybrid scaffolds with interconnected macropores by a freeze-drying protocol. This composite with high stem cell affinity could promote cell proliferation, adhesion, and osteogenesis in vitro and upregulate the expression of osteogenic markers and alkaline phosphatase (ALP) activity. $ ^{[57]} $ Polycaprolactone/chitosan nanofibrous membrane by electrospinning could promote cell proliferation and adhesion, upregulate the expression of osteogenic genes, and induce ALP activity and calcium deposition in stem cells. $ ^{[58]} $ Jahan et al. developed chitosan-apatite hydrogels with an interconnected porous structure, and this scaffold could improve cell behavior and showed potential application for bone repair. $ ^{[59]} $ However, low mechanical strength and solubility, and allergic reactions are the main drawbacks of chitosan. Therefore, biopolymers, ceramics, and metals are often combined with chitosan for bone repair and regeneration. Furthermore, research on how to improve the bioactivity and biodegradability of chitosan by changing its physicochemical properties and constructing scaffold materials that deliver different bioactive substances is needed to be investigated.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, 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+{"paper_id": "2HEUD5P9", "page": 6, "block_id": 9, "raw_label": "text", "raw_order": 5, "bbox": [598, 982, 1093, 1445], "text": "Alginate is a linear polysaccharide that contains β-D-mannuronate (M) and α-L-guluronate (G) residues, which are linked together in a (1, 4) configuration. Alginate extracted from brown seaweed possesses attractive properties, including high abundance, low cost, biocompatibility, biodegradability, non-toxicity, and non-immunity.[60] The mechanical strength, cell affinity, biodegradability, and gel-forming properties of alginate can be finely tuned through various physicochemical modifications. Moreover, various hydrogels, microcapsules, microspheres, fibers, foams, and sponges can be fabricated using alginate.[61] A variety of crosslinking protocols have been applied to obtain alginate and its composites for bone repair and regeneration.[61] It has been reported that alginate-based scaffolds with bone regeneration properties have the potential for use in bone tissue engineering applications. HAP combined with alginate enhanced the mechanical strength of the scaffold, and the composite significantly promoted osteogenic differentiation.[62] Luo et al. developed 3D porous alginate scaffolds composited with bone-forming peptide-1, and the data revealed that the scaffold promoted bioactivity and osteogenic differentiation in vitro and bone regenerative capability in vivo, and could sustainably", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": 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"dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 3, "page": 7, "raw_label": "text", "text": "deliver bone-forming peptide-1. $ ^{[63]} $ A thermo-sensitive alginate/ $ \\beta $-TCP/aspirin hydrogel with an interconnected porous microstructure fabricated by Fang et al. was implanted into the periosteum of rat cranial bone, and the results suggested that the formation of new bone was promoted. $ ^{[64]} $ Furthermore, alginate has been combined with other polymers and ceramics, such as collagen, gelatin, and BGs, to enhance its osteogenic differentiation ability, cell adhesion, and mechanical strength. Nevertheless, current research indicates that Alginate has some drawbacks in bone regeneration and repair. For example, alginate has low bioactivity, which is not conducive to the proliferation and differentiation of bone cells. In addition, alginate has a slow degradation rate, which may affect bone tissue regeneration and repair. Modifying alginate's physicochemical properties and constructing scaffold materials that deliver different bioactive substances can improve its performance and enhance its application prospects in clinical settings. For instance, adjusting alginate's molecular weight, structure, and chemical modification can enhance its bioactivity and biodegradability; blending alginate with other biomaterials or combining alginate with drugs or other bioactive substances also can improve its bioactivity and biodegradability.", "bbox": [95, 149, 588, 633], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "deliver bone-forming peptide-1. $ ^{[63]} $ A thermo-sensitive alginate/ $ \\beta $-TCP/aspirin hydrogel with an interconnected porous microstructure fabricated by Fang et al. was implanted into the periosteum of rat cranial bone, and the results suggested that the formation of new bone was promoted. $ ^{[64]} $ Furthermore, alginate has been combined with other polymers and ceramics, such as collagen, gelatin, and BGs, to enhance its osteogenic differentiation ability, cell adhesion, and mechanical strength. Nevertheless, current research indicates that Alginate has some drawbacks in bone regeneration and repair. For example, alginate has low bioactivity, which is not conducive to the proliferation and differentiation of bone cells. In addition, alginate has a slow degradation rate, which may affect bone tissue regeneration and repair. Modifying alginate's physicochemical properties and constructing scaffold materials that deliver different bioactive substances can improve its performance and enhance its application prospects in clinical settings. For instance, adjusting alginate's molecular weight, structure, and chemical modification can enhance its bioactivity and biodegradability; blending alginate with other biomaterials or combining alginate with drugs or other bioactive substances also can improve its bioactivity and biodegradability."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 484, "left": 95, "top": 149, "right": 588, "bottom": 633, "x_center": 341.5, "x_center_bucket": 350, "y_center": 391.0, "x_ratio": 0.2867, "y_ratio": 0.2498, "width_ratio": 0.4139, "height_ratio": 0.3093, "line_count": 1}, "span_signature": {"font_size": 8.89, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 228}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 7, "block_id": 4, "raw_label": "text", "raw_order": 2, "bbox": [96, 633, 587, 1268], "text": "Hyaluronic acid (HA) is an important component of the ECM in the human body, and its interaction with cluster of differentiation 44 (CD44) may regulate cell motility and adhesion. $ ^{[65]} $ Bioactive proteins or drugs can bind to HA through covalent binding or reverse-charged interactions, and HA can be used as a coating material on metal surfaces. $ ^{[66]} $ Various HA-based scaffolds have been investigated to improve stem cell proliferation, adhesion, viability, vascularization, and osteogenic differentiation, indicating that HA plays an important role in bone repair and regeneration. Although HA has a limited role in promoting bone formation, its synergy with other biomaterials or bioactive factors is widely employed in bone tissue engineering. For instance, 3D-printed gelatin/HA/HAP composite scaffold could facilitate cell proliferation and osteogenic differentiation, and the biomineralized composite scaffolds significantly affected cell biological activity. $ ^{[67]} $ The combination of CaP cement with HA also improved the viability and growth rate of human bone marrow MSCs suitable for bone substitution. $ ^{[68]} $ HAP/HA hydrogels loaded with BMP-2 could sustainably deliver osteogenic factors, further facilitating the formation of the bone matrix and inducing bone maturation. $ ^{[69]} $ Low bioactivity and slow degradation rate influence its role in bone repair. Novel strategies need to be explored to improve the performance of HA and enhance its application prospects in bone regeneration and repair. For instance, developing novel HA-based composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using HA-based hydrogels as exosome delivery systems for osteogenic differentiation; in addition, investigating the use of HA-based hydrogels as scaffolds for bone tissue engineering.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 5.97760009765625, "font": "ScalaPro-Regular", 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have been investigated to improve stem cell proliferation, adhesion, viability, vascularization, and osteogenic differentiation, indicating that HA plays an important role in bone repair and regeneration. Although HA has a limited role in promoting bone formation, its synergy with other biomaterials or bioactive factors is widely employed in bone tissue engineering. For instance, 3D-printed gelatin/HA/HAP composite scaffold could facilitate cell proliferation and osteogenic differentiation, and the biomineralized composite scaffolds significantly affected cell biological activity. $ ^{[67]} $ The combination of CaP cement with HA also improved the viability and growth rate of human bone marrow MSCs suitable for bone substitution. $ ^{[68]} $ HAP/HA hydrogels loaded with BMP-2 could sustainably deliver osteogenic factors, further facilitating the formation of the bone matrix and inducing bone maturation. $ ^{[69]} $ Low bioactivity and slow degradation rate influence its role in bone repair. Novel strategies need to be explored to improve the performance of HA and enhance its application prospects in bone regeneration and repair. For instance, developing novel HA-based composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using HA-based hydrogels as exosome delivery systems for osteogenic differentiation; in addition, investigating the use of HA-based hydrogels as scaffolds for bone tissue engineering.", "bbox": [96, 633, 587, 1268], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Hyaluronic acid (HA) is an important component of the ECM in the human body, and its interaction with cluster of differentiation 44 (CD44) may regulate cell motility and adhesion. $ ^{[65]} $ Bioactive proteins or drugs can bind to HA through covalent binding or reverse-charged interactions, and HA can be used as a coating material on metal surfaces. $ ^{[66]} $ Various HA-based scaffolds have been investigated to improve stem cell proliferation, adhesion, viability, vascularization, and osteogenic differentiation, indicating that HA plays an important role in bone repair and regeneration. Although HA has a limited role in promoting bone formation, its synergy with other biomaterials or bioactive factors is widely employed in bone tissue engineering. For instance, 3D-printed gelatin/HA/HAP composite scaffold could facilitate cell proliferation and osteogenic differentiation, and the biomineralized composite scaffolds significantly affected cell biological activity. $ ^{[67]} $ The combination of CaP cement with HA also improved the viability and growth rate of human bone marrow MSCs suitable for bone substitution. $ ^{[68]} $ HAP/HA hydrogels loaded with BMP-2 could sustainably deliver osteogenic factors, further facilitating the formation of the bone matrix and inducing bone maturation. $ ^{[69]} $ Low bioactivity and slow degradation rate influence its role in bone repair. Novel strategies need to be explored to improve the performance of HA and enhance its application prospects in bone regeneration and repair. For instance, developing novel HA-based composite materials to enhance their bioactivity and biodegradability; exploring the possibility of using HA-based hydrogels as exosome delivery systems for osteogenic differentiation; in addition, investigating the use of HA-based hydrogels as scaffolds for bone tissue engineering."}, "layout_signature": {"width": 491, "width_bucket": 500, "height": 635, "left": 96, "top": 633, "right": 587, "bottom": 1268, "x_center": 341.5, "x_center_bucket": 350, "y_center": 950.5, "x_ratio": 0.2867, "y_ratio": 0.6073, "width_ratio": 0.4123, "height_ratio": 0.4058, "line_count": 1}, "span_signature": {"font_size": 8.79, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 248}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 7, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [95, 1266, 588, 1445], "text": "Collagen is the most abundant protein in bone ECM, and type I collagen is the most ubiquitous among $ \\approx $29 types of collagen, especially in bone tissues. $ ^{[70]} $ Collagen is a fibrous protein that is the main component of connective tissue in mammals. Collagen is the most extensively used bone biomaterial owing to its inferior antigenicity and excellent physicochemical properties. Collagen can be modified by crosslinking its functional groups with biomolecules to fabricate various bone materials with specific mechanical and biological properties. Collagen can be applied to bone tissue engineering in different physical forms, such as scaffolds, hydrogels, sponges, films, micro-and nanospheres, and composites, to promote stem cell attachment, proliferation, motility, differentiation, and osteogenesis. Heo et al. found that MSC/human umbilical vein endothelial cell spheroids encapsulated in a collagen/fibrin hydrogel significantly improved cell viability and proliferation, promoted osteogenic differentiation, induced pre-vascular formation, and increased bone mineral deposition compared with an MSC-suspension. $ ^{[71]} $ Chen et al. reported that dexamethasone incorporated into collagen/BCP scaffolds was released sustainably, and the composite exhibited enhanced osteogenic differentiation of MSCs in vitro and promoted the formation of new bone tissue in vivo. $ ^{[72]} $ Furthermore, However, weak mechanical strength, high costs of manufacturing, rapid degradability, and risk of infection limit the clinical applications of collagen. Although collagen has some disadvantages, it is still an indispensable part of bone regeneration and repair. Researchers are working hard to find ways to solve these problems so that the advantages of collagen can be better utilized while minimizing the impact of its disadvantages. Degradation rate of collagen can be adjusted by changing its physical and chemical properties to improve its effect in bone repair. In addition, collagen can be used in combination with other biomaterials to further improve its effect in bone repair. 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the most abundant protein in bone ECM, and type I collagen is the most ubiquitous among $ \\approx $29 types of collagen, especially in bone tissues. $ ^{[70]} $ Collagen is a fibrous protein that is the main component of connective tissue in mammals. Collagen is the most extensively used bone biomaterial owing to its inferior antigenicity and excellent physicochemical properties. Collagen can be modified by crosslinking its functional groups with biomolecules to fabricate various bone materials with specific mechanical and biological properties. Collagen can be applied to bone tissue engineering in different physical forms, such as scaffolds, hydrogels, sponges, films, micro-and nanospheres, and composites, to promote stem cell attachment, proliferation, motility, differentiation, and osteogenesis. Heo et al. found that MSC/human umbilical vein endothelial cell spheroids encapsulated in a collagen/fibrin hydrogel significantly improved cell viability and proliferation, promoted osteogenic differentiation, induced pre-vascular formation, and increased bone mineral deposition compared with an MSC-suspension. $ ^{[71]} $ Chen et al. reported that dexamethasone incorporated into collagen/BCP scaffolds was released sustainably, and the composite exhibited enhanced osteogenic differentiation of MSCs in vitro and promoted the formation of new bone tissue in vivo. $ ^{[72]} $ Furthermore, However, weak mechanical strength, high costs of manufacturing, rapid degradability, and risk of infection limit the clinical applications of collagen. Although collagen has some disadvantages, it is still an indispensable part of bone regeneration and repair. Researchers are working hard to find ways to solve these problems so that the advantages of collagen can be better utilized while minimizing the impact of its disadvantages. Degradation rate of collagen can be adjusted by changing its physical and chemical properties to improve its effect in bone repair. In addition, collagen can be used in combination with other biomaterials to further improve its effect in bone repair. For example, collagen can be combined with inorganic substances such as HAP to manufacture bone repair materials with better mechanical properties.", "bbox": [95, 1266, 588, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Collagen is the most abundant protein in bone ECM, and type I collagen is the most ubiquitous among $ \\approx $29 types of collagen, especially in bone tissues. $ ^{[70]} $ Collagen is a fibrous protein that is the main component of connective tissue in mammals. Collagen is the most extensively used bone biomaterial owing to its inferior antigenicity and excellent physicochemical properties. Collagen can be modified by crosslinking its functional groups with biomolecules to fabricate various bone materials with specific mechanical and biological properties. Collagen can be applied to bone tissue engineering in different physical forms, such as scaffolds, hydrogels, sponges, films, micro-and nanospheres, and composites, to promote stem cell attachment, proliferation, motility, differentiation, and osteogenesis. Heo et al. found that MSC/human umbilical vein endothelial cell spheroids encapsulated in a collagen/fibrin hydrogel significantly improved cell viability and proliferation, promoted osteogenic differentiation, induced pre-vascular formation, and increased bone mineral deposition compared with an MSC-suspension. $ ^{[71]} $ Chen et al. reported that dexamethasone incorporated into collagen/BCP scaffolds was released sustainably, and the composite exhibited enhanced osteogenic differentiation of MSCs in vitro and promoted the formation of new bone tissue in vivo. $ ^{[72]} $ Furthermore, However, weak mechanical strength, high costs of manufacturing, rapid degradability, and risk of infection limit the clinical applications of collagen. Although collagen has some disadvantages, it is still an indispensable part of bone regeneration and repair. Researchers are working hard to find ways to solve these problems so that the advantages of collagen can be better utilized while minimizing the impact of its disadvantages. Degradation rate of collagen can be adjusted by changing its physical and chemical properties to improve its effect in bone repair. In addition, collagen can be used in combination with other biomaterials to further improve its effect in bone repair. 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+{"paper_id": "2HEUD5P9", "page": 7, "block_id": 7, "raw_label": "text", "raw_order": 5, "bbox": [604, 742, 1098, 1311], "text": "Gelatin is derived from the degradation of type I collagen. Gelatin has biologically functional arginine–glycine–aspartate-binding sequences that improve cell adhesion, differentiation, and proliferation. $ ^{[73,74]} $ The porous surface of the HA-loaded gelatin/alginate hydrogel with high order, homogeneity, and size restriction provided an osteogenic platform for the interaction and cooperation between bone marrow-derived stem cells and macrophages. Effective communication between the macrophages and bone marrow-derived stem cells accounted for the remarkable performance of the composite in healing critical-sized skull bone defects. $ ^{[75]} $ Gelatin–chitosan–BG composite scaffolds prepared by Dasgupta et al. could promote the proliferation and osteogenic differentiation of MSCs and accelerate new bone formation in a rabbit tibia model. $ ^{[76]} $ A macroporous composite scaffold comprising of gelatin and BGs fabricated by Thomas et al. displayed a good apatite-forming capability, cell adhesion properties, and enhanced compressive strength and osteogenesis. $ ^{[77]} $ While gelatin possesses good biocompatibility, biodegradability, and low antigenicity, its poor mechanical properties and high degradability limit its application in bone tissue engineering. However, gelatin can be chemically modified to achieve better therapeutic effects in bone repair. It has been reported that gelatin hydrogels loaded with growth factors could promote bone repair and regeneration. $ ^{[78]} $ Physical and chemical properties of collagen can be changed to adjust its degradation rate, thereby improving its effect in bone repair.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, 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Gelatin has biologically functional arginine–glycine–aspartate-binding sequences that improve cell adhesion, differentiation, and proliferation. $ ^{[73,74]} $ The porous surface of the HA-loaded gelatin/alginate hydrogel with high order, homogeneity, and size restriction provided an osteogenic platform for the interaction and cooperation between bone marrow-derived stem cells and macrophages. Effective communication between the macrophages and bone marrow-derived stem cells accounted for the remarkable performance of the composite in healing critical-sized skull bone defects. $ ^{[75]} $ Gelatin–chitosan–BG composite scaffolds prepared by Dasgupta et al. could promote the proliferation and osteogenic differentiation of MSCs and accelerate new bone formation in a rabbit tibia model. $ ^{[76]} $ A macroporous composite scaffold comprising of gelatin and BGs fabricated by Thomas et al. displayed a good apatite-forming capability, cell adhesion properties, and enhanced compressive strength and osteogenesis. $ ^{[77]} $ While gelatin possesses good biocompatibility, biodegradability, and low antigenicity, its poor mechanical properties and high degradability limit its application in bone tissue engineering. However, gelatin can be chemically modified to achieve better therapeutic effects in bone repair. It has been reported that gelatin hydrogels loaded with growth factors could promote bone repair and regeneration. $ ^{[78]} $ Physical and chemical properties of collagen can be changed to adjust its degradation rate, thereby improving its effect in bone repair.", "bbox": [604, 742, 1098, 1311], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Gelatin is derived from the degradation of type I collagen. Gelatin has biologically functional arginine–glycine–aspartate-binding sequences that improve cell adhesion, differentiation, and proliferation. $ ^{[73,74]} $ The porous surface of the HA-loaded gelatin/alginate hydrogel with high order, homogeneity, and size restriction provided an osteogenic platform for the interaction and cooperation between bone marrow-derived stem cells and macrophages. Effective communication between the macrophages and bone marrow-derived stem cells accounted for the remarkable performance of the composite in healing critical-sized skull bone defects. $ ^{[75]} $ Gelatin–chitosan–BG composite scaffolds prepared by Dasgupta et al. could promote the proliferation and osteogenic differentiation of MSCs and accelerate new bone formation in a rabbit tibia model. $ ^{[76]} $ A macroporous composite scaffold comprising of gelatin and BGs fabricated by Thomas et al. displayed a good apatite-forming capability, cell adhesion properties, and enhanced compressive strength and osteogenesis. $ ^{[77]} $ While gelatin possesses good biocompatibility, biodegradability, and low antigenicity, its poor mechanical properties and high degradability limit its application in bone tissue engineering. However, gelatin can be chemically modified to achieve better therapeutic effects in bone repair. 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For instance, researchers can compound silk fibroin with other materials such as hydroxyapatite and nanocarbon fibers to prepare composite materials with excellent mechanical properties and bioactivity for bone regeneration and repair. Additionally, researchers can regulate silk fibroin's mechanical properties and bioactivity by changing its structure and morphology, such as its molecular weight and cross-linking. 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its application in bone repair, it can promote new bone formation when combined with other biomaterials. For instance, a silk fibroin/chitosan/HAP composite combined with autologous concentrated growth factors significantly promoted the adhesion, proliferation, and osteogenic differentiation of bone marrow MSCs and efficiently repaired bone defects in a rabbit radius-critical bone defect model. $ ^{[80]} $ The 3D-printed mesoporous BG/silk fibroin composite scaffold showed good biocompatibility, superior compressive strength, and stimulated bone regeneration compared with mesoporous BG/PCL composite scaffolds. $ ^{[81]} $ In recent years, researchers have improved silk fibroin's mechanical properties and bioactivity by modifying and compounding it, thereby expanding its application in bone tissue engineering. For instance, researchers can compound silk fibroin with other materials such as hydroxyapatite and nanocarbon fibers to prepare composite materials with excellent mechanical properties and bioactivity for bone regeneration and repair. Additionally, researchers can regulate silk fibroin's mechanical properties and bioactivity by changing its structure and morphology, such as its molecular weight and cross-linking. Overall, silk fibroin has potential application value in bone regeneration and repair, but further research and improvement are needed to meet the mechanical demands and bioactivity of bone tissue.", "bbox": [90, 149, 582, 678], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "osteogenesis of silk fibroin limits its application in bone repair, it can promote new bone formation when combined with other biomaterials. For instance, a silk fibroin/chitosan/HAP composite combined with autologous concentrated growth factors significantly promoted the adhesion, proliferation, and osteogenic differentiation of bone marrow MSCs and efficiently repaired bone defects in a rabbit radius-critical bone defect model. $ ^{[80]} $ The 3D-printed mesoporous BG/silk fibroin composite scaffold showed good biocompatibility, superior compressive strength, and stimulated bone regeneration compared with mesoporous BG/PCL composite scaffolds. $ ^{[81]} $ In recent years, researchers have improved silk fibroin's mechanical properties and bioactivity by modifying and compounding it, thereby expanding its application in bone tissue engineering. For instance, researchers can compound silk fibroin with other materials such as hydroxyapatite and nanocarbon fibers to prepare composite materials with excellent mechanical properties and bioactivity for bone regeneration and repair. Additionally, researchers can regulate silk fibroin's mechanical properties and bioactivity by changing its structure and morphology, such as its molecular weight and cross-linking. Overall, silk fibroin has potential application value in bone regeneration and repair, but further research and improvement are needed to meet the mechanical demands and bioactivity of bone tissue."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 529, "left": 90, "top": 149, "right": 582, "bottom": 678, "x_center": 336.0, "x_center_bucket": 325, "y_center": 413.5, "x_ratio": 0.2821, "y_ratio": 0.2642, "width_ratio": 0.4131, "height_ratio": 0.338, "line_count": 1}, "span_signature": {"font_size": 8.9, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 270}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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Lactic acid and glycolic acid are degradation products of these synthetic polymers in the human body and are therefore excreted by natural metabolism."}, "layout_signature": {"width": 491, "width_bucket": 500, "height": 132, "left": 90, "top": 763, "right": 581, "bottom": 895, "x_center": 335.5, "x_center_bucket": 325, "y_center": 829.0, "x_ratio": 0.2817, "y_ratio": 0.5297, "width_ratio": 0.4123, "height_ratio": 0.0843, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 36}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 8, "block_id": 6, "raw_label": "text", "raw_order": 4, "bbox": [89, 895, 582, 1446], "text": "PLA is characterized by cytocompatibility, non-toxic degradation products, and thermal stability. $ ^{[82,83]} $ Grémare et al. reported that the cell viability and metabolic activity of human bone marrow stromal cells cultured on 3D-printed PLA scaffolds with different pore sizes, biodegradability, and sufficient mechanical integrity were not affected. $ ^{[84]} $ The composites of PLA and other polymers or ceramics exhibit both osteoconductivity and osteoinductivity. A 3D-printed PLA/HAP scaffold with microvascular mimicking channels and bone-formation-supporting structures showed enhanced cell proliferation, adhesion, osteogenesis, and vascular cell growth. $ ^{[85]} $ Electrospun nanofibrous meshes comprising PLA and gelatin enhanced the osteogenic differentiation of MSCs sheets and increased new calcified bone formation within rat cranial defects. $ ^{[86]} $ Meng et al. synthesized a biomimetic reinforced composite scaffold combining the poly L-lactic acid (PLLA) lattice with gelatin/genipin/bioglass hydrogel, the composite scaffold shows excellent interconnectivity, high storage modulus and improved storage modulus (Figure 3A–C). $ ^{[87]} $ However, the slow biodegradation rate of PLA may lead to chronic inflammation and tissue necrosis. To overcome these issues, researchers have begun exploring PLA modification and compounding. For example, researchers have successfully compounded PLA with other materials such as hydroxyapatite and nanocarbon fibers to improve its bioactivity and mechanical properties. 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metabolic activity of human bone marrow stromal cells cultured on 3D-printed PLA scaffolds with different pore sizes, biodegradability, and sufficient mechanical integrity were not affected. $ ^{[84]} $ The composites of PLA and other polymers or ceramics exhibit both osteoconductivity and osteoinductivity. A 3D-printed PLA/HAP scaffold with microvascular mimicking channels and bone-formation-supporting structures showed enhanced cell proliferation, adhesion, osteogenesis, and vascular cell growth. $ ^{[85]} $ Electrospun nanofibrous meshes comprising PLA and gelatin enhanced the osteogenic differentiation of MSCs sheets and increased new calcified bone formation within rat cranial defects. $ ^{[86]} $ Meng et al. synthesized a biomimetic reinforced composite scaffold combining the poly L-lactic acid (PLLA) lattice with gelatin/genipin/bioglass hydrogel, the composite scaffold shows excellent interconnectivity, high storage modulus and improved storage modulus (Figure 3A–C). $ ^{[87]} $ However, the slow biodegradation rate of PLA may lead to chronic inflammation and tissue necrosis. To overcome these issues, researchers have begun exploring PLA modification and compounding. For example, researchers have successfully compounded PLA with other materials such as hydroxyapatite and nanocarbon fibers to improve its bioactivity and mechanical properties. Additionally, researchers can regulate PLA's biodegradation rate and mechanical properties by changing its structure and morphology, such as its molecular weight and cross-linking.", "bbox": [89, 895, 582, 1446], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "PLA is characterized by cytocompatibility, non-toxic degradation products, and thermal stability. $ ^{[82,83]} $ Grémare et al. reported that the cell viability and metabolic activity of human bone marrow stromal cells cultured on 3D-printed PLA scaffolds with different pore sizes, biodegradability, and sufficient mechanical integrity were not affected. $ ^{[84]} $ The composites of PLA and other polymers or ceramics exhibit both osteoconductivity and osteoinductivity. A 3D-printed PLA/HAP scaffold with microvascular mimicking channels and bone-formation-supporting structures showed enhanced cell proliferation, adhesion, osteogenesis, and vascular cell growth. $ ^{[85]} $ Electrospun nanofibrous meshes comprising PLA and gelatin enhanced the osteogenic differentiation of MSCs sheets and increased new calcified bone formation within rat cranial defects. $ ^{[86]} $ Meng et al. synthesized a biomimetic reinforced composite scaffold combining the poly L-lactic acid (PLLA) lattice with gelatin/genipin/bioglass hydrogel, the composite scaffold shows excellent interconnectivity, high storage modulus and improved storage modulus (Figure 3A–C). $ ^{[87]} $ However, the slow biodegradation rate of PLA may lead to chronic inflammation and tissue necrosis. To overcome these issues, researchers have begun exploring PLA modification and compounding. For example, researchers have successfully compounded PLA with other materials such as hydroxyapatite and nanocarbon fibers to improve its bioactivity and mechanical properties. Additionally, researchers can regulate PLA's biodegradation rate and mechanical properties by changing its structure and morphology, such as its molecular weight and cross-linking."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 551, "left": 89, "top": 895, "right": 582, "bottom": 1446, "x_center": 335.5, "x_center_bucket": 325, "y_center": 1170.5, "x_ratio": 0.2817, "y_ratio": 0.7479, "width_ratio": 0.4139, "height_ratio": 0.3521, "line_count": 1}, "span_signature": {"font_size": 8.78, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 242}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 8, "block_id": 8, "raw_label": "text", "raw_order": 6, "bbox": [598, 213, 1093, 1049], "text": "PGA has a high tensile modulus and porosity and can be easily manipulated and manufactured into various shapes. $ ^{[88]} $ However, its rapid degradation rate, low mechanical strength, and acidic degradation products, which lead to a severe inflammatory response, restrict its bone regenerative applications. $ ^{[89]} $ PGA is often used in combination with PLGA for bone repair. PLGA is the most widespread synthetic polymer biomaterial and has good biocompatibility and degradation rate tunability by varying the proportion of copolymers. The in situ tissue engineering scaffold (iTE-scaffold) effectively promoted the angiogenesis of periodontal ligament stem cells (PDLSCs) and induced macrophage polarization into pro-healing M2 phenotype to modulate inflammation (Figure 3D,E). $ ^{[90]} $ PLGA/HAP composite fibrous scaffolds exhibit enhanced hydrophilicity via polydopamine modification, and the polydopamine coating effectively immobilized BMP-2 on the composites. PLGA/HAP composite fibrous scaffolds promoted cell proliferation and attachment and increased ALP activity and calcium deposition. $ ^{[91]} $ PLGA-HAP porous scaffolds printed in a reproductive manner are biocompatible, have high cell viability, and promote osteogenic differentiation in vitro. Moreover, there was limited inflammation after implantation of 3D-printed PLGA-HAP porous scaffolds in vivo. $ ^{[92]} $ PLGA/chitosan microspheres possessed stronger compressive strength, more sustained drug release, and increased cell proliferation and mineralization than PLGA alone. $ ^{[93]} $ However, its suboptimal mechanical properties, poor cell adhesion, and osteoinductivity limit its application in bone tissue engineering. Furthermore, PLGA's degradation products are acidic, which may cause acidification of surrounding tissues and affect bone repair and regeneration. The degradation rate of PLGA is affected by various factors, such as molecular weight, copolymer ratio, crystallinity, etc., which may lead to its unstable degradation rate. The preparation methods of PLGA are subject to certain limitations, such as the solvent evaporation method only being applicable to prepare films, while the melt extrusion method is applicable to prepare 3D scaffolds. 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PLGA is the most widespread synthetic polymer biomaterial and has good biocompatibility and degradation rate tunability by varying the proportion of copolymers. The in situ tissue engineering scaffold (iTE-scaffold) effectively promoted the angiogenesis of periodontal ligament stem cells (PDLSCs) and induced macrophage polarization into pro-healing M2 phenotype to modulate inflammation (Figure 3D,E). $ ^{[90]} $ PLGA/HAP composite fibrous scaffolds exhibit enhanced hydrophilicity via polydopamine modification, and the polydopamine coating effectively immobilized BMP-2 on the composites. PLGA/HAP composite fibrous scaffolds promoted cell proliferation and attachment and increased ALP activity and calcium deposition. $ ^{[91]} $ PLGA-HAP porous scaffolds printed in a reproductive manner are biocompatible, have high cell viability, and promote osteogenic differentiation in vitro. Moreover, there was limited inflammation after implantation of 3D-printed PLGA-HAP porous scaffolds in vivo. $ ^{[92]} $ PLGA/chitosan microspheres possessed stronger compressive strength, more sustained drug release, and increased cell proliferation and mineralization than PLGA alone. $ ^{[93]} $ However, its suboptimal mechanical properties, poor cell adhesion, and osteoinductivity limit its application in bone tissue engineering. Furthermore, PLGA's degradation products are acidic, which may cause acidification of surrounding tissues and affect bone repair and regeneration. The degradation rate of PLGA is affected by various factors, such as molecular weight, copolymer ratio, crystallinity, etc., which may lead to its unstable degradation rate. The preparation methods of PLGA are subject to certain limitations, such as the solvent evaporation method only being applicable to prepare films, while the melt extrusion method is applicable to prepare 3D scaffolds. Future research should focus on addressing these shortcomings to further improve the application of PLGA in bone tissue engineering.", "bbox": [598, 213, 1093, 1049], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "PGA has a high tensile modulus and porosity and can be easily manipulated and manufactured into various shapes. $ ^{[88]} $ However, its rapid degradation rate, low mechanical strength, and acidic degradation products, which lead to a severe inflammatory response, restrict its bone regenerative applications. $ ^{[89]} $ PGA is often used in combination with PLGA for bone repair. PLGA is the most widespread synthetic polymer biomaterial and has good biocompatibility and degradation rate tunability by varying the proportion of copolymers. The in situ tissue engineering scaffold (iTE-scaffold) effectively promoted the angiogenesis of periodontal ligament stem cells (PDLSCs) and induced macrophage polarization into pro-healing M2 phenotype to modulate inflammation (Figure 3D,E). $ ^{[90]} $ PLGA/HAP composite fibrous scaffolds exhibit enhanced hydrophilicity via polydopamine modification, and the polydopamine coating effectively immobilized BMP-2 on the composites. PLGA/HAP composite fibrous scaffolds promoted cell proliferation and attachment and increased ALP activity and calcium deposition. $ ^{[91]} $ PLGA-HAP porous scaffolds printed in a reproductive manner are biocompatible, have high cell viability, and promote osteogenic differentiation in vitro. Moreover, there was limited inflammation after implantation of 3D-printed PLGA-HAP porous scaffolds in vivo. $ ^{[92]} $ PLGA/chitosan microspheres possessed stronger compressive strength, more sustained drug release, and increased cell proliferation and mineralization than PLGA alone. $ ^{[93]} $ However, its suboptimal mechanical properties, poor cell adhesion, and osteoinductivity limit its application in bone tissue engineering. Furthermore, PLGA's degradation products are acidic, which may cause acidification of surrounding tissues and affect bone repair and regeneration. The degradation rate of PLGA is affected by various factors, such as molecular weight, copolymer ratio, crystallinity, etc., which may lead to its unstable degradation rate. The preparation methods of PLGA are subject to certain limitations, such as the solvent evaporation method only being applicable to prepare films, while the melt extrusion method is applicable to prepare 3D scaffolds. Future research should focus on addressing these shortcomings to further improve the application of PLGA in bone tissue engineering."}, "layout_signature": {"width": 495, "width_bucket": 500, "height": 836, "left": 598, "top": 213, "right": 1093, "bottom": 1049, "x_center": 845.5, "x_center_bucket": 850, "y_center": 631.0, "x_ratio": 0.7099, "y_ratio": 0.4032, "width_ratio": 0.4156, "height_ratio": 0.5342, "line_count": 1}, "span_signature": {"font_size": 8.78, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 282}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 8, "block_id": 9, "raw_label": "text", "raw_order": 7, "bbox": [598, 1049, 1093, 1446], "text": "PCL is an aliphatic polymer, consisting of hexanoate units, and has high crystallinity, easily manipulable mechanical characteristics, and good biocompatibility. Lin et al. reported that the PCL/cobalt-substituted HAP composite decreased the crystallinity of the PCL membrane, which led to greater degradation, promoted cell proliferation of osteoblasts, and increased calcium deposition compared to pure PCL membranes. $ ^{[94]} $ Torres et al. found that PCL scaffolds with an average roughness of 0.93 $ \\mu $m promoted the expression of the osteogenic markers and mineralization in the absence of dexamethasone. $ ^{[95]} $ Jang et al. entrapped HA in PCL/HA hybrid microspheres, and the data revealed that PCL/HA hybrid microspheres promoted the proliferation and osteogenic differentiation of human periosteum-derived cells and accelerated bone regeneration in vivo. $ ^{[96]} $ The fabricated bioactive calcium silicate nanowires reinforced poly (e-caprolactone) (CS-PCL) composite electrospun fibrous membranes (EFMs) could promote bone regeneration both in vitro and in vivo (Figure 3F–K). $ ^{[97]} $ However, its relatively slow", "page_width": 1191, 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Lin et al. reported that the PCL/cobalt-substituted HAP composite decreased the crystallinity of the PCL membrane, which led to greater degradation, promoted cell proliferation of osteoblasts, and increased calcium deposition compared to pure PCL membranes. $ ^{[94]} $ Torres et al. found that PCL scaffolds with an average roughness of 0.93 $ \\mu $m promoted the expression of the osteogenic markers and mineralization in the absence of dexamethasone. $ ^{[95]} $ Jang et al. entrapped HA in PCL/HA hybrid microspheres, and the data revealed that PCL/HA hybrid microspheres promoted the proliferation and osteogenic differentiation of human periosteum-derived cells and accelerated bone regeneration in vivo. $ ^{[96]} $ The fabricated bioactive calcium silicate nanowires reinforced poly (e-caprolactone) (CS-PCL) composite electrospun fibrous membranes (EFMs) could promote bone regeneration both in vitro and in vivo (Figure 3F–K). $ ^{[97]} $ However, its relatively slow", "bbox": [598, 1049, 1093, 1446], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "PCL is an aliphatic polymer, consisting of hexanoate units, and has high crystallinity, easily manipulable mechanical characteristics, and good biocompatibility. Lin et al. reported that the PCL/cobalt-substituted HAP composite decreased the crystallinity of the PCL membrane, which led to greater degradation, promoted cell proliferation of osteoblasts, and increased calcium deposition compared to pure PCL membranes. $ ^{[94]} $ Torres et al. found that PCL scaffolds with an average roughness of 0.93 $ \\mu $m promoted the expression of the osteogenic markers and mineralization in the absence of dexamethasone. $ ^{[95]} $ Jang et al. entrapped HA in PCL/HA hybrid microspheres, and the data revealed that PCL/HA hybrid microspheres promoted the proliferation and osteogenic differentiation of human periosteum-derived cells and accelerated bone regeneration in vivo. $ ^{[96]} $ The fabricated bioactive calcium silicate nanowires reinforced poly (e-caprolactone) (CS-PCL) composite electrospun fibrous membranes (EFMs) could promote bone regeneration both in vitro and in vivo (Figure 3F–K). $ ^{[97]} $ However, its relatively slow"}, "layout_signature": {"width": 495, "width_bucket": 500, "height": 397, "left": 598, "top": 1049, "right": 1093, "bottom": 1446, "x_center": 845.5, "x_center_bucket": 850, "y_center": 1247.5, "x_ratio": 0.7099, "y_ratio": 0.7971, "width_ratio": 0.4156, "height_ratio": 0.2537, "line_count": 1}, "span_signature": {"font_size": 8.83, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 263}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_138", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 9, "block_id": 27, "raw_label": "text", "raw_order": 1, "bbox": [95, 1200, 588, 1443], "text": "degradation rate and poor hydrophilicity restrict its application in bone tissue engineering. To overcome these shortcomings, PCL can be compounded with other materials, doped and modified. Among them, compounding PCL with inorganic materials such as hydroxyapatite (HAP) can improve the mechanical properties and bioactivity of PCL. In addition, compounding PCL with biodegradable polymers such as polylactic acid (PLA) can improve the degradation rate and bioactivity of PCL. In summary, PCL has broad potential applications in bone repair and regeneration, but further research and improvement are needed.\nDifferent kinds of polymeric scaffolds have increasingly been employed in bone repair and regeneration for the past few years. Polymeric scaffolds combined with growth factors and stem cells can modulate the physicochemical properties of biological tissue. 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To overcome these shortcomings, PCL can be compounded with other materials, doped and modified. Among them, compounding PCL with inorganic materials such as hydroxyapatite (HAP) can improve the mechanical properties and bioactivity of PCL. In addition, compounding PCL with biodegradable polymers such as polylactic acid (PLA) can improve the degradation rate and bioactivity of PCL. In summary, PCL has broad potential applications in bone repair and regeneration, but further research and improvement are needed.\nDifferent kinds of polymeric scaffolds have increasingly been employed in bone repair and regeneration for the past few years. Polymeric scaffolds combined with growth factors and stem cells can modulate the physicochemical properties of biological tissue. The advantages and disadvantages of natural polymers and synthetic polymers were listed as follows (Table 2). Polymeric scaffolds combined with some materials that possess appropriate properties, such as mechanical, biocompatible, and biodegradable properties, as well as structural similarity to the ECM of natural bone may offer a suitable environment for cell proliferation, adhesion, differentiation, and new bone formation. The", "bbox": [95, 1200, 588, 1443], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "degradation rate and poor hydrophilicity restrict its application in bone tissue engineering. To overcome these shortcomings, PCL can be compounded with other materials, doped and modified. Among them, compounding PCL with inorganic materials such as hydroxyapatite (HAP) can improve the mechanical properties and bioactivity of PCL. In addition, compounding PCL with biodegradable polymers such as polylactic acid (PLA) can improve the degradation rate and bioactivity of PCL. 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| Natural polymers | Chitosan | Resistance to bacteria Easy properties tunability Cell-binding, differentiation and migration properties Controlled biodegradability | Poor mechanical strength Low solubility | [54,55] |
| Alginate | Easy gelling Tunable properties High abundance resources | Low cell adhesion Difficult to sterilize | [60,61] |
| Hyaluronic acid | Biodegradability Easy manipulation Water solubility Osteoinduction | Poor mechanical properties Rapid degradation | [65,66] |
| Collagen | Similar to ECM Possible injectability Cell-binding properties Versatility in being processed in different physical forms High porosity Facility for combining with other polymers | Difficult disinfection Difficult handling Low mechanical strength | [70,71] |
| Gelatin | Porosity tunability Biodegradability Osteoconductivity | Poor mechanical properties Low stability in physiological conditions | [73,74] |
| Silk fibroin | Immunogenicity Controlled biodegradability High mechanical strength Easy chemical modification | Low osteogenic capacity | [79,80] |
| Synthetic polymers | PLA | Tunable properties Thermal stability Sufficient mechanical properties | Poor osteoinduction Poor cell adhesion | [82,83] |
| PGA | Cytocompatibility Composited with other biomaterials | Poor mechanical strength Low cell adhesion Rapid biodegradability Poor osteoinduction | [88,89] |
| PLGA | Tunable degradation rate Biocompatibility Biodegradability Controllable mechanical properties | Poor osteoconductivity Poor cell adhesion Suboptimal mechanical properties | [91,92] |
| PCL | Biodegradability Slow degradation rate Excellent mechanical properties | Low biodegradability Poor hydrophilicity Low bioactivity | [94,95] |
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| Natural polymers | Chitosan | Resistance to bacteria Easy properties tunability Cell-binding, differentiation and migration properties Controlled biodegradability | Poor mechanical strength Low solubility | [54,55] |
| Alginate | Easy gelling Tunable properties High abundance resources | Low cell adhesion Difficult to sterilize | [60,61] |
| Hyaluronic acid | Biodegradability Easy manipulation Water solubility Osteoinduction | Poor mechanical properties Rapid degradation | [65,66] |
| Collagen | Similar to ECM Possible injectability Cell-binding properties Versatility in being processed in different physical forms High porosity Facility for combining with other polymers | Difficult disinfection Difficult handling Low mechanical strength | [70,71] |
| Gelatin | Porosity tunability Biodegradability Osteoconductivity | Poor mechanical properties Low stability in physiological conditions | [73,74] |
| Silk fibroin | Immunogenicity Controlled biodegradability High mechanical strength Easy chemical modification | Low osteogenic capacity | [79,80] |
| Synthetic polymers | PLA | Tunable properties Thermal stability Sufficient mechanical properties | Poor osteoinduction Poor cell adhesion | [82,83] |
| PGA | Cytocompatibility Composited with other biomaterials | Poor mechanical strength Low cell adhesion Rapid biodegradability Poor osteoinduction | [88,89] |
| PLGA | Tunable degradation rate Biocompatibility Biodegradability Controllable mechanical properties | Poor osteoconductivity Poor cell adhesion Suboptimal mechanical properties | [91,92] |
| PCL | Biodegradability Slow degradation rate Excellent mechanical properties | Low biodegradability Poor hydrophilicity Low bioactivity | [94,95] |
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| Natural polymers | Chitosan | Resistance to bacteria Easy properties tunability Cell-binding, differentiation and migration properties Controlled biodegradability | Poor mechanical strength Low solubility | [54,55] |
| Alginate | Easy gelling Tunable properties High abundance resources | Low cell adhesion Difficult to sterilize | [60,61] |
| Hyaluronic acid | Biodegradability Easy manipulation Water solubility Osteoinduction | Poor mechanical properties Rapid degradation | [65,66] |
| Collagen | Similar to ECM Possible injectability Cell-binding properties Versatility in being processed in different physical forms High porosity Facility for combining with other polymers | Difficult disinfection Difficult handling Low mechanical strength | [70,71] |
| Gelatin | Porosity tunability Biodegradability Osteoconductivity | Poor mechanical properties Low stability in physiological conditions | [73,74] |
| Silk fibroin | Immunogenicity Controlled biodegradability High mechanical strength Easy chemical modification | Low osteogenic capacity | [79,80] |
| Synthetic polymers | PLA | Tunable properties Thermal stability Sufficient mechanical properties | Poor osteoinduction Poor cell adhesion | [82,83] |
| PGA | Cytocompatibility Composited with other biomaterials | Poor mechanical strength Low cell adhesion Rapid biodegradability Poor osteoinduction | [88,89] |
| PLGA | Tunable degradation rate Biocompatibility Biodegradability Controllable mechanical properties | Poor osteoconductivity Poor cell adhesion Suboptimal mechanical properties | [91,92] |
| PCL | Biodegradability Slow degradation rate Excellent mechanical properties | Low biodegradability Poor hydrophilicity Low bioactivity | [94,95] |
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+{"paper_id": "2HEUD5P9", "page": 11, "block_id": 3, "raw_label": "text", "raw_order": 1, "bbox": [95, 149, 588, 610], "text": "ions released by metal degradation, such as magnesium, iron, zinc, and strontium, have important effects on bone healing by affecting the balance between bone cells and are regarded as biological factors in bone formation. $ ^{[103-105]} $ For example, magnesium ions can stimulate osteoblast activity, proliferation, and new bone formation and are excreted in urine, avoiding the toxicity caused by concentrated ions. $ ^{[106]} $ Various metal nanomaterials that are easily synthesized and modified have been reported to facilitate osteogenic differentiation. Gold nanoparticles (AuNPs) with different physicochemical characteristics can promote the osteogenic differentiation of MSCs through their interaction with cell membranes or cytoplasmic proteins. $ ^{[107,108]} $ Silver nanoparticles with antimicrobial and antiviral properties enhanced cell proliferation, cytoskeletal tension, and osteogenic differentiation in vitro, and promoted the formation of new bone in vivo. $ ^{[109]} $ However, most metallic materials lack biodegradability and require additional surgery to remove the implants after bone healing. Moreover, stress-shielding effects, and metal wear debris can lead to the production of toxic substances and a decline in bone density. It is difficult to introduce other osteoinductive biomaterials onto the surface of metal scaffolds.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", 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"dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 3, "page": 11, "raw_label": "text", "text": "ions released by metal degradation, such as magnesium, iron, zinc, and strontium, have important effects on bone healing by affecting the balance between bone cells and are regarded as biological factors in bone formation. $ ^{[103-105]} $ For example, magnesium ions can stimulate osteoblast activity, proliferation, and new bone formation and are excreted in urine, avoiding the toxicity caused by concentrated ions. $ ^{[106]} $ Various metal nanomaterials that are easily synthesized and modified have been reported to facilitate osteogenic differentiation. Gold nanoparticles (AuNPs) with different physicochemical characteristics can promote the osteogenic differentiation of MSCs through their interaction with cell membranes or cytoplasmic proteins. $ ^{[107,108]} $ Silver nanoparticles with antimicrobial and antiviral properties enhanced cell proliferation, cytoskeletal tension, and osteogenic differentiation in vitro, and promoted the formation of new bone in vivo. $ ^{[109]} $ However, most metallic materials lack biodegradability and require additional surgery to remove the implants after bone healing. Moreover, stress-shielding effects, and metal wear debris can lead to the production of toxic substances and a decline in bone density. It is difficult to introduce other osteoinductive biomaterials onto the surface of metal scaffolds.", "bbox": [95, 149, 588, 610], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "ions released by metal degradation, such as magnesium, iron, zinc, and strontium, have important effects on bone healing by affecting the balance between bone cells and are regarded as biological factors in bone formation. $ ^{[103-105]} $ For example, magnesium ions can stimulate osteoblast activity, proliferation, and new bone formation and are excreted in urine, avoiding the toxicity caused by concentrated ions. $ ^{[106]} $ Various metal nanomaterials that are easily synthesized and modified have been reported to facilitate osteogenic differentiation. Gold nanoparticles (AuNPs) with different physicochemical characteristics can promote the osteogenic differentiation of MSCs through their interaction with cell membranes or cytoplasmic proteins. $ ^{[107,108]} $ Silver nanoparticles with antimicrobial and antiviral properties enhanced cell proliferation, cytoskeletal tension, and osteogenic differentiation in vitro, and promoted the formation of new bone in vivo. $ ^{[109]} $ However, most metallic materials lack biodegradability and require additional surgery to remove the implants after bone healing. Moreover, stress-shielding effects, and metal wear debris can lead to the production of toxic substances and a decline in bone density. It is difficult to introduce other osteoinductive biomaterials onto the surface of metal scaffolds."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 461, "left": 95, "top": 149, "right": 588, "bottom": 610, "x_center": 341.5, "x_center_bucket": 350, "y_center": 379.5, "x_ratio": 0.2867, "y_ratio": 0.2425, "width_ratio": 0.4139, "height_ratio": 0.2946, "line_count": 1}, "span_signature": {"font_size": 8.79, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 201}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 11, "block_id": 4, "raw_label": "text", "raw_order": 2, "bbox": [95, 610, 588, 1226], "text": "Metal-organic frameworks (MOFs) with intramolecular pores and intrinsic bioactivity comprise metal ions and organic ligands. The large specific surface area of MOFs is conducive to cell adhesion and proliferation, and their diverse pore structures and porosities are suitable for loading and releasing biomolecules and antimicrobials. A MOF-coated magnesium alloy exhibited excellent bioactivity conducive to bone remodeling, and the MOF coating improved the hydrophilicity and corrosion resistance of the magnesium alloy. Furthermore, in vitro cytocompatibility results indicated that the MOF coating exhibited good biocompatibility. Previous studies have shown that MOFs could promote osteogenic differentiation in vitro. Zn-based MOF films prepared on porous titanium surfaces increased ALP activity, ECM mineralization, and expression of osteogenic markers in MG63 cells and inhibited the proliferation of Streptococcus mutans. $ ^{[110]} $ Magnesium-MOF74 exhibited good biocompatibility, anti-inflammatory, and antibacterial properties and promoted early osteogenesis and angiogenesis in vivo. $ ^{[111]} $ PLGA/Exo-Mg-GA MOF composite scaffolds steadily released exosomes and magnesium ions, promoted cell adhesion and proliferation, enhanced anti-inflammatory and angiogenic effects, and accelerated new bone formation (Figure 4A–C). $ ^{[112]} $ Asymmetric double-layer polycaprolactone/collagen (PCL/Col) membrane could be modified by MOF crystals, the MOF crystals can provide a pH-responsive release of $ Zn^{2+} $ ions, which facilitated the barrier layer functions to prevent the infiltration of fibrous connective tissue and enhance osteogenesis and angiogenesis in vitro (Figure 4D–F). $ ^{[113]} $", 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"wmode": 0}, {"size": 5.97760009765625, "font": "ScalaPro-Regular", "flags": 4, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}, {"size": 5.97760009765625, "font": "ScalaPro-Regular", "flags": 5, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}, {"size": 5.97760009765625, "font": "ScalaPro-Regular", "flags": 5, "color": 255, "dir": [1.0, 0.0], "wmode": 0}, {"size": 5.97760009765625, "font": "ScalaPro-Regular", "flags": 5, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 4, "page": 11, "raw_label": "text", "text": "Metal-organic frameworks (MOFs) with intramolecular pores and intrinsic bioactivity comprise metal ions and organic ligands. The large specific surface area of MOFs is conducive to cell adhesion and proliferation, and their diverse pore structures and porosities are suitable for loading and releasing biomolecules and antimicrobials. A MOF-coated magnesium alloy exhibited excellent bioactivity conducive to bone remodeling, and the MOF coating improved the hydrophilicity and corrosion resistance of the magnesium alloy. Furthermore, in vitro cytocompatibility results indicated that the MOF coating exhibited good biocompatibility. Previous studies have shown that MOFs could promote osteogenic differentiation in vitro. Zn-based MOF films prepared on porous titanium surfaces increased ALP activity, ECM mineralization, and expression of osteogenic markers in MG63 cells and inhibited the proliferation of Streptococcus mutans. $ ^{[110]} $ Magnesium-MOF74 exhibited good biocompatibility, anti-inflammatory, and antibacterial properties and promoted early osteogenesis and angiogenesis in vivo. $ ^{[111]} $ PLGA/Exo-Mg-GA MOF composite scaffolds steadily released exosomes and magnesium ions, promoted cell adhesion and proliferation, enhanced anti-inflammatory and angiogenic effects, and accelerated new bone formation (Figure 4A–C). $ ^{[112]} $ Asymmetric double-layer polycaprolactone/collagen (PCL/Col) membrane could be modified by MOF crystals, the MOF crystals can provide a pH-responsive release of $ Zn^{2+} $ ions, which facilitated the barrier layer functions to prevent the infiltration of fibrous connective tissue and enhance osteogenesis and angiogenesis in vitro (Figure 4D–F). $ ^{[113]} $", "bbox": [95, 610, 588, 1226], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Metal-organic frameworks (MOFs) with intramolecular pores and intrinsic bioactivity comprise metal ions and organic ligands. The large specific surface area of MOFs is conducive to cell adhesion and proliferation, and their diverse pore structures and porosities are suitable for loading and releasing biomolecules and antimicrobials. A MOF-coated magnesium alloy exhibited excellent bioactivity conducive to bone remodeling, and the MOF coating improved the hydrophilicity and corrosion resistance of the magnesium alloy. Furthermore, in vitro cytocompatibility results indicated that the MOF coating exhibited good biocompatibility. Previous studies have shown that MOFs could promote osteogenic differentiation in vitro. Zn-based MOF films prepared on porous titanium surfaces increased ALP activity, ECM mineralization, and expression of osteogenic markers in MG63 cells and inhibited the proliferation of Streptococcus mutans. $ ^{[110]} $ Magnesium-MOF74 exhibited good biocompatibility, anti-inflammatory, and antibacterial properties and promoted early osteogenesis and angiogenesis in vivo. $ ^{[111]} $ PLGA/Exo-Mg-GA MOF composite scaffolds steadily released exosomes and magnesium ions, promoted cell adhesion and proliferation, enhanced anti-inflammatory and angiogenic effects, and accelerated new bone formation (Figure 4A–C). $ ^{[112]} $ Asymmetric double-layer polycaprolactone/collagen (PCL/Col) membrane could be modified by MOF crystals, the MOF crystals can provide a pH-responsive release of $ Zn^{2+} $ ions, which facilitated the barrier layer functions to prevent the infiltration of fibrous connective tissue and enhance osteogenesis and angiogenesis in vitro (Figure 4D–F). $ ^{[113]} $"}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 616, "left": 95, "top": 610, "right": 588, "bottom": 1226, "x_center": 341.5, "x_center_bucket": 350, "y_center": 918.0, "x_ratio": 0.2867, "y_ratio": 0.5866, "width_ratio": 0.4139, "height_ratio": 0.3936, "line_count": 1}, "span_signature": {"font_size": 8.83, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 330}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 11, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [95, 1223, 588, 1445], "text": "There are several methods for preparing MOFs, including solvothermal synthesis (mixing metal ions and organic ligands in an organic solvent, heating to a certain temperature, and forming crystals), hydrothermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), vapor diffusion synthesis (mixing metal ions and organic ligands in the gas phase, and forming crystals through diffusion reaction), water-thermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), and water-thermal-solvent synthesis (mixing metal ions and organic ligands in water and organic solvents, heating to a certain temperature, and forming crystals). Each of these methods has its own advantages and disadvantages, and the specific method chosen depends on the properties and application scenarios of the desired MOFs. The preparation method of MOFs has a significant impact on their properties, such as crystal structure, pore size, porosity, surface area, stability, and biocompatibility. For example, MOFs prepared by solvothermal synthesis have the characteristics of complete crystal structure, adjustable pore size, large porosity, and large surface area, but require the use of organic solvents, which cause some environmental pollution. MOFs prepared by hydrothermal synthesis have the advantages of simple preparation and no need for organic solvents, but the pore size and porosity are difficult to control. Therefore, choosing the appropriate preparation method is very important for preparing MOFs with specific properties.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 5, "page": 11, "raw_label": "text", "text": "There are several methods for preparing MOFs, including solvothermal synthesis (mixing metal ions and organic ligands in an organic solvent, heating to a certain temperature, and forming crystals), hydrothermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), vapor diffusion synthesis (mixing metal ions and organic ligands in the gas phase, and forming crystals through diffusion reaction), water-thermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), and water-thermal-solvent synthesis (mixing metal ions and organic ligands in water and organic solvents, heating to a certain temperature, and forming crystals). Each of these methods has its own advantages and disadvantages, and the specific method chosen depends on the properties and application scenarios of the desired MOFs. The preparation method of MOFs has a significant impact on their properties, such as crystal structure, pore size, porosity, surface area, stability, and biocompatibility. For example, MOFs prepared by solvothermal synthesis have the characteristics of complete crystal structure, adjustable pore size, large porosity, and large surface area, but require the use of organic solvents, which cause some environmental pollution. MOFs prepared by hydrothermal synthesis have the advantages of simple preparation and no need for organic solvents, but the pore size and porosity are difficult to control. Therefore, choosing the appropriate preparation method is very important for preparing MOFs with specific properties.", "bbox": [95, 1223, 588, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "There are several methods for preparing MOFs, including solvothermal synthesis (mixing metal ions and organic ligands in an organic solvent, heating to a certain temperature, and forming crystals), hydrothermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), vapor diffusion synthesis (mixing metal ions and organic ligands in the gas phase, and forming crystals through diffusion reaction), water-thermal synthesis (mixing metal ions and organic ligands in water, heating to a certain temperature, and forming crystals), and water-thermal-solvent synthesis (mixing metal ions and organic ligands in water and organic solvents, heating to a certain temperature, and forming crystals). Each of these methods has its own advantages and disadvantages, and the specific method chosen depends on the properties and application scenarios of the desired MOFs. The preparation method of MOFs has a significant impact on their properties, such as crystal structure, pore size, porosity, surface area, stability, and biocompatibility. For example, MOFs prepared by solvothermal synthesis have the characteristics of complete crystal structure, adjustable pore size, large porosity, and large surface area, but require the use of organic solvents, which cause some environmental pollution. MOFs prepared by hydrothermal synthesis have the advantages of simple preparation and no need for organic solvents, but the pore size and porosity are difficult to control. 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In addition, LDH exhibits anti-inflammatory and immunoregulatory properties in the tissue microenvironment. $ ^{[114]} $ As the transport vehicle of the osteoinductive miRNA let-7d, LDH synergistically regulate BMSCs toward the osteoblastic lineage, The LDH/let-7d complex resulted in a better induction of osteogenesis than LDH alone (Figure 5A,B). $ ^{[115]} $ The corrosion resistance and biocompatibility of magnesium alloys are enhanced by the addition of MgAl-LDH, and this composite exhibits superior osteogenic differentiation, angiogenic capacity, and anti-inflammatory effects (Figure 5C–E). $ ^{[116]} $ The presence of LDH nanoparticles in $ \\beta $-TCP nanocomposite granules increased the compressive modulus. $ ^{[117]} $ LDH-chitosan porous scaffolds loaded with PFT $ \\alpha $ significantly promoted the osteogenic differentiation in vitro, and accelerated bone tissue repair in cranial defect model rats. $ ^{[118]} $ Gallium-strontium LDH films on titanium substrates have strong 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In addition, LDH exhibits anti-inflammatory and immunoregulatory properties in the tissue microenvironment. $ ^{[114]} $ As the transport vehicle of the osteoinductive miRNA let-7d, LDH synergistically regulate BMSCs toward the osteoblastic lineage, The LDH/let-7d complex resulted in a better induction of osteogenesis than LDH alone (Figure 5A,B). $ ^{[115]} $ The corrosion resistance and biocompatibility of magnesium alloys are enhanced by the addition of MgAl-LDH, and this composite exhibits superior osteogenic differentiation, angiogenic capacity, and anti-inflammatory effects (Figure 5C–E). $ ^{[116]} $ The presence of LDH nanoparticles in $ \\beta $-TCP nanocomposite granules increased the compressive modulus. $ ^{[117]} $ LDH-chitosan porous scaffolds loaded with PFT $ \\alpha $ significantly promoted the osteogenic differentiation in vitro, and accelerated bone tissue repair in cranial defect model rats. $ ^{[118]} $ Gallium-strontium LDH films on titanium substrates have strong antibacterial capabilities, promote the differentiation of osteogenic cells, stimulate ALP activity and collagen secretion, and enhance osseointegration capacity. $ ^{[119]} $", "bbox": [604, 609, 1098, 1094], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Several studies have focused on the application of layered double hydroxide (LDH) in the biomedical field, such as drug/gene delivery, bone repair and regeneration, and biological functional surface modification, owing to its excellent biocompatibility. In addition, LDH exhibits anti-inflammatory and immunoregulatory properties in the tissue microenvironment. $ ^{[114]} $ As the transport vehicle of the osteoinductive miRNA let-7d, LDH synergistically regulate BMSCs toward the osteoblastic lineage, The LDH/let-7d complex resulted in a better induction of osteogenesis than LDH alone (Figure 5A,B). $ ^{[115]} $ The corrosion resistance and biocompatibility of magnesium alloys are enhanced by the addition of MgAl-LDH, and this composite exhibits superior osteogenic differentiation, angiogenic capacity, and anti-inflammatory effects (Figure 5C–E). $ ^{[116]} $ The presence of LDH nanoparticles in $ \\beta $-TCP nanocomposite granules increased the compressive modulus. $ ^{[117]} $ LDH-chitosan porous scaffolds loaded with PFT $ \\alpha $ significantly promoted the osteogenic differentiation in vitro, and accelerated bone tissue repair in cranial defect model rats. $ ^{[118]} $ Gallium-strontium LDH films on titanium substrates have strong antibacterial capabilities, promote the differentiation of osteogenic cells, stimulate ALP activity and collagen secretion, and enhance osseointegration capacity. $ ^{[119]} $"}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 485, "left": 604, "top": 609, "right": 1098, "bottom": 1094, "x_center": 851.0, "x_center_bucket": 850, "y_center": 851.5, "x_ratio": 0.7145, "y_ratio": 0.5441, "width_ratio": 0.4148, "height_ratio": 0.3099, "line_count": 1}, "span_signature": {"font_size": 8.74, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 237}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 11, "block_id": 9, "raw_label": "text", "raw_order": 7, "bbox": [605, 1091, 1098, 1446], "text": "Multifunctional layered SrFe₁₂O₁₉-LDH/chitosan scaffolds composed of SrFe₁₂O₁₉ nanoparticles, LDH nanoparticles, and bioactive chitosan can inhibit bone resorption in osteoclasts and the release of proinflammatory factors by magnesium ions from LDH nanoparticles. Strontium ions released from this scaffold promoted osteoblast proliferation and bone mineralization (Figure 5F–H).[120] The surface functionalization of MgAlEu-LDH nanosheets on a porous HAP scaffold effectively promoted cell adhesion, osteogenic differentiation, and vascular regeneration in vitro and accelerated new bone formation in vivo.[121] The inclusion of LDH in the PCL scaffold enhanced the mechanical strength and compressive modulus and improved cell viability, proliferation, and adhesion. In addition, LDH increased the expression of osteogenic markers and mineral deposition.[122] Black Mn-containing LDH nanosheet-modified Mg-based implants was developed for integration of biodegradation.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, 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Strontium ions released from this scaffold promoted osteoblast proliferation and bone mineralization (Figure 5F–H).[120] The surface functionalization of MgAlEu-LDH nanosheets on a porous HAP scaffold effectively promoted cell adhesion, osteogenic differentiation, and vascular regeneration in vitro and accelerated new bone formation in vivo.[121] The inclusion of LDH in the PCL scaffold enhanced the mechanical strength and compressive modulus and improved cell viability, proliferation, and adhesion. In addition, LDH increased the expression of osteogenic markers and mineral deposition.[122] Black Mn-containing LDH nanosheet-modified Mg-based implants was developed for integration of biodegradation.", "bbox": [605, 1091, 1098, 1446], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Multifunctional layered SrFe₁₂O₁₉-LDH/chitosan scaffolds composed of SrFe₁₂O₁₉ nanoparticles, LDH nanoparticles, and bioactive chitosan can inhibit bone resorption in osteoclasts and the release of proinflammatory factors by magnesium ions from LDH nanoparticles. Strontium ions released from this scaffold promoted osteoblast proliferation and bone mineralization (Figure 5F–H).[120] The surface functionalization of MgAlEu-LDH nanosheets on a porous HAP scaffold effectively promoted cell adhesion, osteogenic differentiation, and vascular regeneration in vitro and accelerated new bone formation in vivo.[121] The inclusion of LDH in the PCL scaffold enhanced the mechanical strength and compressive modulus and improved cell viability, proliferation, and adhesion. 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F–H) Micro-CT(F), BMD (G) and BV/TV rate (H) of control, LDH/CS and SrFe $ _{12} $O $ _{19} $-LDH/CS. $ ^{[120]} $ Copyright 2022, Elsevier. I–L) Three-dimensional reconstruction images of Micro-CT results of the various samples after implantation in femur of SD rat for 8 and 12 weeks (I), yellow section indicate new bone. Calculated bone volume/tissue volume (BV/TV) (J) and trabecular thickness (Tb.Th) of the various samples after implantation for 8 and 12 weeks (K). VG staining of the various samples after femur implantation for 8 and 12 weeks (L). $ ^{[123]} $ Copyright 2022, Elsevier.", "page_width": 1191, "page_height": 1565, "role": "figure_caption", "role_confidence": 0.92, "evidence": ["figure_title label: Figure 5. A) ALP staining and ARS staining of Control, Let-7"], "seed_role": "figure_caption", "seed_confidence": 0.92, "seed_evidence": ["figure_title label: Figure 5. 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A) ALP staining and ARS staining of Control, Let-7d, LDH and LDH/let-7d groups on day 7 and day 14, respectively. Scale bars: 500 $ \\mu $m. B) LDH/let-7d-incorporated fibrin scaffolds promoted the subcutaneous ectopic osteogenesis of BMSCs in nude mice. Representative reconstructed micro-CT images. Scale bars: 100 $ \\mu $m. $ ^{[115]} $ Copyright 2021, American Chemical Society. C,D) Optical photograph of subcutaneous capsules (C) and SEM views (D) of Mg, Mg-Mg(OH) $ _{2} $, Mg-LDH after implantation for 4 weeks. E) Photomicrographs of histological section of Mg, Mg-Mg(OH) $ _{2} $, Mg-LDH after implantation for 4 and 8 weeks. The red asterisk represented the sample and blue arrow indicated neutrophils. $ ^{[116]} $ Copyright 2020, Elsevier. F–H) Micro-CT(F), BMD (G) and BV/TV rate (H) of control, LDH/CS and SrFe $ _{12} $O $ _{19} $-LDH/CS. $ ^{[120]} $ Copyright 2022, Elsevier. I–L) Three-dimensional reconstruction images of Micro-CT results of the various samples after implantation in femur of SD rat for 8 and 12 weeks (I), yellow section indicate new bone. Calculated bone volume/tissue volume (BV/TV) (J) and trabecular thickness (Tb.Th) of the various samples after implantation for 8 and 12 weeks (K). VG staining of the various samples after femur implantation for 8 and 12 weeks (L). $ ^{[123]} $ Copyright 2022, Elsevier.", "bbox": [95, 1254, 1100, 1428], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "figure_number", "raw_marker": "Figure 5", "number": 5, "kind": "figure", "normalized_text": "Figure 5. A) ALP staining and ARS staining of Control, Let-7d, LDH and LDH/let-7d groups on day 7 and day 14, respectively. Scale bars: 500 $ \\mu $m. B) LDH/let-7d-incorporated fibrin scaffolds promoted the subcutaneous ectopic osteogenesis of BMSCs in nude mice. Representative reconstructed micro-CT images. Scale bars: 100 $ \\mu $m. $ ^{[115]} $ Copyright 2021, American Chemical Society. C,D) Optical photograph of subcutaneous capsules (C) and SEM views (D) of Mg, Mg-Mg(OH) $ _{2} $, Mg-LDH after implantation for 4 weeks. E) Photomicrographs of histological section of Mg, Mg-Mg(OH) $ _{2} $, Mg-LDH after implantation for 4 and 8 weeks. The red asterisk represented the sample and blue arrow indicated neutrophils. $ ^{[116]} $ Copyright 2020, Elsevier. F–H) Micro-CT(F), BMD (G) and BV/TV rate (H) of control, LDH/CS and SrFe $ _{12} $O $ _{19} $-LDH/CS. $ ^{[120]} $ Copyright 2022, Elsevier. I–L) Three-dimensional reconstruction images of Micro-CT results of the various samples after implantation in femur of SD rat for 8 and 12 weeks (I), yellow section indicate new bone. Calculated bone volume/tissue volume (BV/TV) (J) and trabecular thickness (Tb.Th) of the various samples after implantation for 8 and 12 weeks (K). 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The main limitations of individual materials are the brittleness and low degradability of ceramics, weak mechanical strength and toxicity of the degradation products of polymers, and stress shielding effects and nonbiodegradability of metals, which can be resolved by combining several materials. Specifically, composites have been developed to mimic the structure, mechanical properties, biological activity, and osteoconductivity of real bone tissue.", "bbox": [89, 192, 581, 391], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "As mentioned above, each material has merits and shortcomings in bone tissue engineering. The main limitations of individual materials are the brittleness and low degradability of ceramics, weak mechanical strength and toxicity of the degradation products of polymers, and stress shielding effects and nonbiodegradability of metals, which can be resolved by combining several materials. Specifically, composites have been developed to mimic the structure, mechanical properties, biological activity, and osteoconductivity of real bone tissue."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 199, "left": 89, "top": 192, "right": 581, "bottom": 391, "x_center": 335.0, "x_center_bucket": 325, "y_center": 291.5, "x_ratio": 0.2813, "y_ratio": 0.1863, "width_ratio": 0.4131, "height_ratio": 0.1272, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 85}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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Titanium-reinforced CaP implants promote in situ cranial defect repair and osseointegration. $ ^{[128]} $ Nano-HAP reinforces the bioactivity of porous magnesium alloy foam, which is an excellent scaffold for bone regeneration. $ ^{[129]} $ Metal–polymer composites for use in bone repair have also been investigated. Chitosan- $ TiO_{2} $ nanotube scaffolds exhibited an improved compressive modulus and a lower degradation rate, and the functionalization of composites with $ Ca^{2+} $ ions promoted cell adhesion, proliferation, and early osteogenic differentiation. $ ^{[130]} $ A PCL-BG coating improved the bioactivity, mechanical integrity, degradation resistance, and apatite layer formation of a magnesium scaffold. $ ^{[131]} $ In addition, some composites can be used for osteochondral repair. Three-layer chitosan/silk fibroin/HAP scaffolds synthesized by electrospinning could mimic the subchondral bone, calcified, and chondral layers to facilitate osteochondral repair. $ ^{[132]} $ Bilayered chitosan/chitosan- $ \\beta $-TCP composite scaffolds manufactured by lyophilization could maintain the viability and proliferation of cells seeded into both layers, which differentiated into chondrogenic and osteogenic lineages. $ ^{[133]} $ A bilayer hydrogel scaffold with a PGA/chitosan/cellulose hydrogel cartilage layer and a porous nano-HA-containing PGA/chitosan/cellulose hydrogel osteogenic layer was successfully prepared based on the bionic principle, the addition of $ Mg^{2+} $ and $ Cu^{2+} $ ions modulated the mechanical and biological properties of the composite to be similar to those of natural cartilage. Bioactive ions also endow scaffolds with excellent antibacterial, osteogenic, and chondrogenic properties. $ ^{[134]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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Numerous studies have applied ceramic and polymer composites in bone tissue engineering. For example, a chitosan/HAP/ $ \\beta $-TCP/ composite is cytocompatible and promoted cell proliferation, which is required for efficient new bone formation. $ ^{[124]} $ The porous collagen-carboxymethyl cellulose/HAP composite exhibited increased compressive strength and cell proliferation. $ ^{[125]} $ The addition of HAP improved the mechanical properties of the PLA scaffold, as well as the cell proliferation and osteogenic ability. $ ^{[126,127]} $ Composites of ceramics and metals have been proposed to counteract the corrosion of metals, and their superior mechanical properties are retained. Titanium-reinforced CaP implants promote in situ cranial defect repair and osseointegration. $ ^{[128]} $ Nano-HAP reinforces the bioactivity of porous magnesium alloy foam, which is an excellent scaffold for bone regeneration. $ ^{[129]} $ Metal–polymer composites for use in bone repair have also been investigated. Chitosan- $ TiO_{2} $ nanotube scaffolds exhibited an improved compressive modulus and a lower degradation rate, and the functionalization of composites with $ Ca^{2+} $ ions promoted cell adhesion, proliferation, and early osteogenic differentiation. $ ^{[130]} $ A PCL-BG coating improved the bioactivity, mechanical integrity, degradation resistance, and apatite layer formation of a magnesium scaffold. $ ^{[131]} $ In addition, some composites can be used for osteochondral repair. Three-layer chitosan/silk fibroin/HAP scaffolds synthesized by electrospinning could mimic the subchondral bone, calcified, and chondral layers to facilitate osteochondral repair. $ ^{[132]} $ Bilayered chitosan/chitosan- $ \\beta $-TCP composite scaffolds manufactured by lyophilization could maintain the viability and proliferation of cells seeded into both layers, which differentiated into chondrogenic and osteogenic lineages. $ ^{[133]} $ A bilayer hydrogel scaffold with a PGA/chitosan/cellulose hydrogel cartilage layer and a porous nano-HA-containing PGA/chitosan/cellulose hydrogel osteogenic layer was successfully prepared based on the bionic principle, the addition of $ Mg^{2+} $ and $ Cu^{2+} $ ions modulated the mechanical and biological properties of the composite to be similar to those of natural cartilage. Bioactive ions also endow scaffolds with excellent antibacterial, osteogenic, and chondrogenic properties. $ ^{[134]} $", "bbox": [89, 392, 583, 1245], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Composite scaffolds have been used to regulate scaffold properties and repair bone defects. Numerous studies have applied ceramic and polymer composites in bone tissue engineering. For example, a chitosan/HAP/ $ \\beta $-TCP/ composite is cytocompatible and promoted cell proliferation, which is required for efficient new bone formation. $ ^{[124]} $ The porous collagen-carboxymethyl cellulose/HAP composite exhibited increased compressive strength and cell proliferation. $ ^{[125]} $ The addition of HAP improved the mechanical properties of the PLA scaffold, as well as the cell proliferation and osteogenic ability. $ ^{[126,127]} $ Composites of ceramics and metals have been proposed to counteract the corrosion of metals, and their superior mechanical properties are retained. Titanium-reinforced CaP implants promote in situ cranial defect repair and osseointegration. $ ^{[128]} $ Nano-HAP reinforces the bioactivity of porous magnesium alloy foam, which is an excellent scaffold for bone regeneration. $ ^{[129]} $ Metal–polymer composites for use in bone repair have also been investigated. Chitosan- $ TiO_{2} $ nanotube scaffolds exhibited an improved compressive modulus and a lower degradation rate, and the functionalization of composites with $ Ca^{2+} $ ions promoted cell adhesion, proliferation, and early osteogenic differentiation. $ ^{[130]} $ A PCL-BG coating improved the bioactivity, mechanical integrity, degradation resistance, and apatite layer formation of a magnesium scaffold. $ ^{[131]} $ In addition, some composites can be used for osteochondral repair. Three-layer chitosan/silk fibroin/HAP scaffolds synthesized by electrospinning could mimic the subchondral bone, calcified, and chondral layers to facilitate osteochondral repair. $ ^{[132]} $ Bilayered chitosan/chitosan- $ \\beta $-TCP composite scaffolds manufactured by lyophilization could maintain the viability and proliferation of cells seeded into both layers, which differentiated into chondrogenic and osteogenic lineages. $ ^{[133]} $ A bilayer hydrogel scaffold with a PGA/chitosan/cellulose hydrogel cartilage layer and a porous nano-HA-containing PGA/chitosan/cellulose hydrogel osteogenic layer was successfully prepared based on the bionic principle, the addition of $ Mg^{2+} $ and $ Cu^{2+} $ ions modulated the mechanical and biological properties of the composite to be similar to those of natural cartilage. Bioactive ions also endow scaffolds with excellent antibacterial, osteogenic, and chondrogenic properties. $ ^{[134]} $"}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 853, "left": 89, "top": 392, "right": 583, "bottom": 1245, "x_center": 336.0, "x_center_bucket": 325, "y_center": 818.5, "x_ratio": 0.2821, "y_ratio": 0.523, "width_ratio": 0.4148, "height_ratio": 0.545, "line_count": 1}, "span_signature": {"font_size": 8.71, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 432}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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"color": 2301728, "dir": [1.0, 0.0], "wmode": 0}, {"size": 7.970099925994873, "font": "ScalaSansPro-Regular", "flags": 4, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}, {"size": 7.970099925994873, "font": "ScalaSansPro-Regular", "flags": 4, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 25, "page": 15, "raw_label": "figure_title", "text": "Figure 6. A,B) SEM image of scaffolds after soaking in SBF for 5 days (A1, A2: MBG/SF scaffold; B1, B2: MBG/PCL scaffold) and EDS spectra (A3: MBG/SF scaffold; B3:MBG/PCL scaffold). C) The relative expression of BMP-2, BSP, COL-1 and OCN of hBMSCs cultured on MBG/SF and MBG/PCL scaffolds for 7 and 14 days.[81] Copyright 2019, Elsevier. D) Schematic of fabrication of two-level macro and micro porous hierarchical CaP scaffolds a); The ceramic mandible and square shape specimens fabricated by 3D printing method. b–d). [32] Copyright 2018, Elsevier. E) The gross images of CLH (on the left, dyed with methyl orange), OLH (on the right) (a) and the bilayered hydrogels (b). F) 3D printability of the pregelation solution of the hydrogels. The designed patterns (a) and the 3D printed patterns by CLH pregel solution (b). G) Micro-CT analysis images, histological images of H&E, Masson, ARS and immunohistochemical staining for OCN after in vivo subcutaneous implantation for 28 days. Scale bar = 50 μm.[144] Copyright 2023, Wiley-VCH.", "bbox": [95, 1098, 1100, 1252], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "figure_number", "raw_marker": "Figure 6", "number": 6, "kind": "figure", "normalized_text": "Figure 6. A,B) SEM image of scaffolds after soaking in SBF for 5 days (A1, A2: MBG/SF scaffold; B1, B2: MBG/PCL scaffold) and EDS spectra (A3: MBG/SF scaffold; B3:MBG/PCL scaffold). C) The relative expression of BMP-2, BSP, COL-1 and OCN of hBMSCs cultured on MBG/SF and MBG/PCL scaffolds for 7 and 14 days.[81] Copyright 2019, Elsevier. D) Schematic of fabrication of two-level macro and micro porous hierarchical CaP scaffolds a); The ceramic mandible and square shape specimens fabricated by 3D printing method. b–d). [32] Copyright 2018, Elsevier. E) The gross images of CLH (on the left, dyed with methyl orange), OLH (on the right) (a) and the bilayered hydrogels (b). F) 3D printability of the pregelation solution of the hydrogels. The designed patterns (a) and the 3D printed patterns by CLH pregel solution (b). G) Micro-CT analysis images, histological images of H&E, Masson, ARS and immunohistochemical staining for OCN after in vivo subcutaneous implantation for 28 days. 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{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 3, "page": 16, "raw_label": "text", "text": "architecture of native bone. $ ^{[136]} $ In addition, several 3D bioprinting techniques, such as inkjet, extrusion, and laser-assisted bioprinting, have been developed in regenerative medicine, which can deposit living cells, ECM, and other materials in user-defined patterns to build implants or complex tissues for bone-defect repair in orthopedics. 3D bioprinting can be used to manufacture artificial tissue scaffolds with controllable cell distributions. Cell spheroids exhibit improved ECM development and intercellular communication than cells cultured in a monolayer, potentially facilitating the growth of bioprinted structures towards specific tissues. The development of bioprinting protocols and compatible ink materials for bone tissue engineering has facilitated the manufacturing of superior tissue scaffolds for bone repair.", "bbox": [90, 149, 582, 436], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "architecture of native bone. $ ^{[136]} $ In addition, several 3D bioprinting techniques, such as inkjet, extrusion, and laser-assisted bioprinting, have been developed in regenerative medicine, which can deposit living cells, ECM, and other materials in user-defined patterns to build implants or complex tissues for bone-defect repair in orthopedics. 3D bioprinting can be used to manufacture artificial tissue scaffolds with controllable cell distributions. Cell spheroids exhibit improved ECM development and intercellular communication than cells cultured in a monolayer, potentially facilitating the growth of bioprinted structures towards specific tissues. The development of bioprinting protocols and compatible ink materials for bone tissue engineering has facilitated the manufacturing of superior tissue scaffolds for bone repair."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 287, "left": 90, "top": 149, "right": 582, "bottom": 436, "x_center": 336.0, "x_center_bucket": 325, "y_center": 292.5, "x_ratio": 0.2821, "y_ratio": 0.1869, "width_ratio": 0.4131, "height_ratio": 0.1834, "line_count": 1}, "span_signature": {"font_size": 8.82, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 60}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 16, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [90, 521, 582, 1115], "text": "The mechanical integrity, microstructure, biocompatibility, biodegradability, and osteoconductivity are crucial properties of scaffolds for bone repair and regeneration, and it is essential to achieve an equilibrium of cell viability, cell function, and mechanical properties under weight-bearing conditions. Bone scaffolds must exhibit superior mechanical strength and promote bone cell adhesion, migration, proliferation, and osteogenic differentiation, without triggering immune or inflammatory responses. Strict control over the mechanical properties, topography, and porosity of scaffolds is essential for bone repair and regeneration. The mechanical properties of scaffolds, determined by the material properties and pore structures, should provide sufficient mechanical strength for structures in load-bearing bones until new bone formation. Porous structures are conducive to the diffusion of metabolic wastes and nutrients and enhance the metabolism of osteoblasts. $ ^{[137]} $ An interconnected porous structure with a porosity of more than 90% and pore size between 300 and 500 $ \\mu $m facilitates nutrient delivery, cell penetration, and vascularization. $ ^{[137]} $ Bioprinted scaffolds should gradually degrade with cell growth, and the degradation rate of the scaffolds should match the rate of new bone formation. Meanwhile, the degradation products should have no toxic effects and should be excreted from the human body through metabolism. The osteoconductivity of scaffolds is conducive to ECM formation on their surface and pores and can suppress the generation of fibrous tissue encapsulation, forming a connection between the bone and scaffold.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", 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mechanical properties under weight-bearing conditions. Bone scaffolds must exhibit superior mechanical strength and promote bone cell adhesion, migration, proliferation, and osteogenic differentiation, without triggering immune or inflammatory responses. Strict control over the mechanical properties, topography, and porosity of scaffolds is essential for bone repair and regeneration. The mechanical properties of scaffolds, determined by the material properties and pore structures, should provide sufficient mechanical strength for structures in load-bearing bones until new bone formation. Porous structures are conducive to the diffusion of metabolic wastes and nutrients and enhance the metabolism of osteoblasts. $ ^{[137]} $ An interconnected porous structure with a porosity of more than 90% and pore size between 300 and 500 $ \\mu $m facilitates nutrient delivery, cell penetration, and vascularization. $ ^{[137]} $ Bioprinted scaffolds should gradually degrade with cell growth, and the degradation rate of the scaffolds should match the rate of new bone formation. Meanwhile, the degradation products should have no toxic effects and should be excreted from the human body through metabolism. The osteoconductivity of scaffolds is conducive to ECM formation on their surface and pores and can suppress the generation of fibrous tissue encapsulation, forming a connection between the bone and scaffold.", "bbox": [90, 521, 582, 1115], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "The mechanical integrity, microstructure, biocompatibility, biodegradability, and osteoconductivity are crucial properties of scaffolds for bone repair and regeneration, and it is essential to achieve an equilibrium of cell viability, cell function, and mechanical properties under weight-bearing conditions. Bone scaffolds must exhibit superior mechanical strength and promote bone cell adhesion, migration, proliferation, and osteogenic differentiation, without triggering immune or inflammatory responses. Strict control over the mechanical properties, topography, and porosity of scaffolds is essential for bone repair and regeneration. The mechanical properties of scaffolds, determined by the material properties and pore structures, should provide sufficient mechanical strength for structures in load-bearing bones until new bone formation. Porous structures are conducive to the diffusion of metabolic wastes and nutrients and enhance the metabolism of osteoblasts. $ ^{[137]} $ An interconnected porous structure with a porosity of more than 90% and pore size between 300 and 500 $ \\mu $m facilitates nutrient delivery, cell penetration, and vascularization. $ ^{[137]} $ Bioprinted scaffolds should gradually degrade with cell growth, and the degradation rate of the scaffolds should match the rate of new bone formation. Meanwhile, the degradation products should have no toxic effects and should be excreted from the human body through metabolism. The osteoconductivity of scaffolds is conducive to ECM formation on their surface and pores and can suppress the generation of fibrous tissue encapsulation, forming a connection between the bone and scaffold."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 594, "left": 90, "top": 521, "right": 582, "bottom": 1115, "x_center": 336.0, "x_center_bucket": 325, "y_center": 818.0, "x_ratio": 0.2821, "y_ratio": 0.5227, "width_ratio": 0.4131, "height_ratio": 0.3796, "line_count": 1}, "span_signature": {"font_size": 8.91, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 348}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 16, "block_id": 9, "raw_label": "text", "raw_order": 7, "bbox": [598, 281, 1093, 1158], "text": "Composites can combine the merits of two or more different types of materials and thus meet the performance requirements of bone scaffolds to a large extent, including mechanical and biological properties, ease of manufacturing, and controllable degradation. Therefore, 3D-printed biodegradable composites have been extensively developed for bone tissue engineering applications. A cell-laden $ \\alpha $-TCP/collagen scaffold fabricated using a two-step printing process showed improved metabolic activity and mineralization of preosteoblasts and had potential application in bone repair and regeneration. $ ^{[139]} $ Gelatin/ $ \\alpha $-TCP/silk-fibroin designed by a temperature-controlled 3D printing process could enhance mechanical strength and significantly promote cell proliferation and differentiation of MG63 cells compared to a gelatin or gelatin/ $ \\alpha $-TCP scaffold. $ ^{[140]} $ Cell-laden ECM-ornamented 3D-printed PCL/PLGA/TCP composite scaffold accelerated osteoblastic differentiation and calcium deposition in vitro, and induced new bone formation in vivo, allowing this composite to be used as an off-the-shelf bone graft scaffold. $ ^{[141]} $ Bionic porous 3D collagen/HAP scaffolds retain the natural properties of the material after printing and increased cell proliferation, penetration, and mineralization and accelerated new bone formation in a rabbit femoral condyle defect model. $ ^{[142]} $ The 3D-printed HAP/PCL scaffold exhibited good elasticity and toughness, supported cell proliferation and viability, and promoted osteogenic differentiation without osteoinducing factors. The porous scaffold could integrate with the surrounding bone tissues and facilitate bone-defect repair without eliciting an immune response. $ ^{[143]} $ However, 3D printing technology has several drawbacks. The bioink of 3D bioprinting mainly comprises living cells and bioactive polymers, whereas few cells are extracted from patients, and foreign cells may trigger an immune response and pathogen infection. The polymers used in bioinks are limited owing to strict requirements for cytocompatibility and biodegradation. In addition, 3D bioprinting technology only builds tissues with a single function, whereas tissues with complex structures and physiological functions are difficult to print. The biomimetic construct of kartogenin (KGN) in the two well-integrated zones of chondral layer hydrogel (CLH) and osseous layer hydrogel (OLH) is developed, which can facilitate cartilage and subchondral bone restoration in the in vivo osteochondral defect (Figure 6E–G). $ ^{[144]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 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extent, including mechanical and biological properties, ease of manufacturing, and controllable degradation. Therefore, 3D-printed biodegradable composites have been extensively developed for bone tissue engineering applications. A cell-laden $ \\alpha $-TCP/collagen scaffold fabricated using a two-step printing process showed improved metabolic activity and mineralization of preosteoblasts and had potential application in bone repair and regeneration. $ ^{[139]} $ Gelatin/ $ \\alpha $-TCP/silk-fibroin designed by a temperature-controlled 3D printing process could enhance mechanical strength and significantly promote cell proliferation and differentiation of MG63 cells compared to a gelatin or gelatin/ $ \\alpha $-TCP scaffold. $ ^{[140]} $ Cell-laden ECM-ornamented 3D-printed PCL/PLGA/TCP composite scaffold accelerated osteoblastic differentiation and calcium deposition in vitro, and induced new bone formation in vivo, allowing this composite to be used as an off-the-shelf bone graft scaffold. $ ^{[141]} $ Bionic porous 3D collagen/HAP scaffolds retain the natural properties of the material after printing and increased cell proliferation, penetration, and mineralization and accelerated new bone formation in a rabbit femoral condyle defect model. $ ^{[142]} $ The 3D-printed HAP/PCL scaffold exhibited good elasticity and toughness, supported cell proliferation and viability, and promoted osteogenic differentiation without osteoinducing factors. The porous scaffold could integrate with the surrounding bone tissues and facilitate bone-defect repair without eliciting an immune response. $ ^{[143]} $ However, 3D printing technology has several drawbacks. The bioink of 3D bioprinting mainly comprises living cells and bioactive polymers, whereas few cells are extracted from patients, and foreign cells may trigger an immune response and pathogen infection. The polymers used in bioinks are limited owing to strict requirements for cytocompatibility and biodegradation. In addition, 3D bioprinting technology only builds tissues with a single function, whereas tissues with complex structures and physiological functions are difficult to print. The biomimetic construct of kartogenin (KGN) in the two well-integrated zones of chondral layer hydrogel (CLH) and osseous layer hydrogel (OLH) is developed, which can facilitate cartilage and subchondral bone restoration in the in vivo osteochondral defect (Figure 6E–G). $ ^{[144]} $", "bbox": [598, 281, 1093, 1158], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Composites can combine the merits of two or more different types of materials and thus meet the performance requirements of bone scaffolds to a large extent, including mechanical and biological properties, ease of manufacturing, and controllable degradation. Therefore, 3D-printed biodegradable composites have been extensively developed for bone tissue engineering applications. A cell-laden $ \\alpha $-TCP/collagen scaffold fabricated using a two-step printing process showed improved metabolic activity and mineralization of preosteoblasts and had potential application in bone repair and regeneration. $ ^{[139]} $ Gelatin/ $ \\alpha $-TCP/silk-fibroin designed by a temperature-controlled 3D printing process could enhance mechanical strength and significantly promote cell proliferation and differentiation of MG63 cells compared to a gelatin or gelatin/ $ \\alpha $-TCP scaffold. $ ^{[140]} $ Cell-laden ECM-ornamented 3D-printed PCL/PLGA/TCP composite scaffold accelerated osteoblastic differentiation and calcium deposition in vitro, and induced new bone formation in vivo, allowing this composite to be used as an off-the-shelf bone graft scaffold. $ ^{[141]} $ Bionic porous 3D collagen/HAP scaffolds retain the natural properties of the material after printing and increased cell proliferation, penetration, and mineralization and accelerated new bone formation in a rabbit femoral condyle defect model. $ ^{[142]} $ The 3D-printed HAP/PCL scaffold exhibited good elasticity and toughness, supported cell proliferation and viability, and promoted osteogenic differentiation without osteoinducing factors. The porous scaffold could integrate with the surrounding bone tissues and facilitate bone-defect repair without eliciting an immune response. $ ^{[143]} $ However, 3D printing technology has several drawbacks. The bioink of 3D bioprinting mainly comprises living cells and bioactive polymers, whereas few cells are extracted from patients, and foreign cells may trigger an immune response and pathogen infection. The polymers used in bioinks are limited owing to strict requirements for cytocompatibility and biodegradation. In addition, 3D bioprinting technology only builds tissues with a single function, whereas tissues with complex structures and physiological functions are difficult to print. The biomimetic construct of kartogenin (KGN) in the two well-integrated zones of chondral layer hydrogel (CLH) and osseous layer hydrogel (OLH) is developed, which can facilitate cartilage and subchondral bone restoration in the in vivo osteochondral defect (Figure 6E–G). $ ^{[144]} $"}, "layout_signature": {"width": 495, "width_bucket": 500, "height": 877, "left": 598, "top": 281, "right": 1093, "bottom": 1158, "x_center": 845.5, "x_center_bucket": 850, "y_center": 719.5, "x_ratio": 0.7099, "y_ratio": 0.4597, "width_ratio": 0.4156, "height_ratio": 0.5604, "line_count": 1}, "span_signature": {"font_size": 8.81, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 339}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_138", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 16, "block_id": 10, "raw_label": "text", "raw_order": 8, "bbox": [598, 1158, 1093, 1445], "text": "In recent years, increasing researchers have applied 3D printing technology to bone tissue regeneration. Polymer materials and hydrogel materials have their own advantages and disadvantages in bone repair applications. Single materials often cannot balance mechanical strength, printability, biocompatibility/bioactivity, and bone conduction. Through 3D printing technology, more precise bone tissue composite scaffolds can be manufactured. These scaffolds can better adapt to the shape of the patient's bone defect and allow new tissue infiltration, thereby showing better bone repair efficacy. In the future, 3D printing technology will continue to develop biomimetic ultrafine models, in-depth research on the microstructure characteristics of tantalum metal and its impact on biological function,", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 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| Photoresponsive strategy | Noninvasive with high controllability Precise multistaged light program Superior photothermal therapy effects | Low tissue penetration Phototoxicity | [146,147] |
| Electroresponsive strategy | Effective tissue regeneration Improved conductive properties Suitable mechanical properties | Low control precision Undesirable biocompatibility and biodegradability Restricted electrical stimulation | [150,151] |
| Magnetic-responsive strategy | High tissue-penetrating capabilities High control precision | Uncertain biocompatibility and Long-term safety | [154,155] |
| Ultrasound-responsive strategy | Superior tissue penetration depth No drug resistance Non-invasive Cytocompatible; Biocompatible | Low in vivo stability of sonosensitizer drugs Potential toxicity of sonosensitizers | [159,160] |
| Piezoelectricity-responsive strategy | Improved conductive characteristics Excellrnt regeneration effect Biocompatibility and non-toxicity | Unfavorable biodegradability Long-term biosafet | [161,162] |
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| Photoresponsive strategy | Noninvasive with high controllability Precise multistaged light program Superior photothermal therapy effects | Low tissue penetration Phototoxicity | [146,147] |
| Electroresponsive strategy | Effective tissue regeneration Improved conductive properties Suitable mechanical properties | Low control precision Undesirable biocompatibility and biodegradability Restricted electrical stimulation | [150,151] |
| Magnetic-responsive strategy | High tissue-penetrating capabilities High control precision | Uncertain biocompatibility and Long-term safety | [154,155] |
| Ultrasound-responsive strategy | Superior tissue penetration depth No drug resistance Non-invasive Cytocompatible; Biocompatible | Low in vivo stability of sonosensitizer drugs Potential toxicity of sonosensitizers | [159,160] |
| Piezoelectricity-responsive strategy | Improved conductive characteristics Excellrnt regeneration effect Biocompatibility and non-toxicity | Unfavorable biodegradability Long-term biosafet | [161,162] |
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| Electroresponsive strategy | Effective tissue regeneration Improved conductive properties Suitable mechanical properties | Low control precision Undesirable biocompatibility and biodegradability Restricted electrical stimulation | [150,151] |
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| Piezoelectricity-responsive strategy | Improved conductive characteristics Excellrnt regeneration effect Biocompatibility and non-toxicity | Unfavorable biodegradability Long-term biosafet | [161,162] |
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External physical stimuli, including light, magnetic and electric fields, ultrasound, or other proper mechanical stimuli, can affect the atomic arrangements inside materials, thus regulating cell fate and promoting bone-defect repair and regeneration. $ ^{[145]} $ This field has attracted much research attention, and various materials have been manufactured based on these strategies. The advantages and disadvantages of several physical stimuli-responsive strategies are summarized in Table 3.", "bbox": [95, 773, 588, 996], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Numerous strategies have been developed to manufacture physical stimuli-responsive materials for bone-tissue engineering. External physical stimuli, including light, magnetic and electric fields, ultrasound, or other proper mechanical stimuli, can affect the atomic arrangements inside materials, thus regulating cell fate and promoting bone-defect repair and regeneration. $ ^{[145]} $ This field has attracted much research attention, and various materials have been manufactured based on these strategies. The advantages and disadvantages of several physical stimuli-responsive strategies are summarized in Table 3."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 223, "left": 95, "top": 773, "right": 588, "bottom": 996, "x_center": 341.5, "x_center_bucket": 350, "y_center": 884.5, "x_ratio": 0.2867, "y_ratio": 0.5652, "width_ratio": 0.4139, "height_ratio": 0.1425, "line_count": 1}, "span_signature": {"font_size": 8.85, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": true, "italic": true, "span_count": 74}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "body_zone", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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Upon exposure to near-infrared irradiation, the composite increased the expression of heat shock proteins, ultimately promoting osteogenic differentiation in vitro and in vivo.[147] Similarly, black phosphorus nanosheets-SrCl₂/PLGA microspheres exhibit efficient near-infrared absorption and photothermal responses. Near-infrared light irradiation activates the release of Sr²⁺ by flawing the PLGA shells, ultimately promoting bone regeneration in rat femoral defect models.[148] Under 808-nm near-infrared light irradiation, HAP/graphene oxide/chitosan scaffolds with excellent photothermal conversion properties and osteogenic bioactivity could effectively kill human osteosarcoma cells at 48 °C and facilitate the osteogenic differentiation of MSCs at 42 °C by enhancing the BMP-2/Smad signaling pathway.[149] However, the severe attenuation of light by tissues limits the photothermal conversion performance, thus suppressing bone tissue regeneration. 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A completely biodegradable scaffold composed of black phosphorus nanosheets and PLGA showed an efficient near-infrared photothermal effect, even when covered by biological tissue. Upon exposure to near-infrared irradiation, the composite increased the expression of heat shock proteins, ultimately promoting osteogenic differentiation in vitro and in vivo.[147] Similarly, black phosphorus nanosheets-SrCl₂/PLGA microspheres exhibit efficient near-infrared absorption and photothermal responses. Near-infrared light irradiation activates the release of Sr²⁺ by flawing the PLGA shells, ultimately promoting bone regeneration in rat femoral defect models.[148] Under 808-nm near-infrared light irradiation, HAP/graphene oxide/chitosan scaffolds with excellent photothermal conversion properties and osteogenic bioactivity could effectively kill human osteosarcoma cells at 48 °C and facilitate the osteogenic differentiation of MSCs at 42 °C by enhancing the BMP-2/Smad signaling pathway.[149] However, the severe attenuation of light by tissues limits the photothermal conversion performance, thus suppressing bone tissue regeneration. 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Upon exposure to near-infrared irradiation, the composite increased the expression of heat shock proteins, ultimately promoting osteogenic differentiation in vitro and in vivo.[147] Similarly, black phosphorus nanosheets-SrCl₂/PLGA microspheres exhibit efficient near-infrared absorption and photothermal responses. Near-infrared light irradiation activates the release of Sr²⁺ by flawing the PLGA shells, ultimately promoting bone regeneration in rat femoral defect models.[148] Under 808-nm near-infrared light irradiation, HAP/graphene oxide/chitosan scaffolds with excellent photothermal conversion properties and osteogenic bioactivity could effectively kill human osteosarcoma cells at 48 °C and facilitate the osteogenic differentiation of MSCs at 42 °C by enhancing the BMP-2/Smad signaling pathway.[149] However, the severe attenuation of light by tissues limits the photothermal conversion performance, thus suppressing bone tissue regeneration. 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Among these electroactive biomaterials, conducting polymers such as polyaniline, polypyrrole, and poly(3,4-ethylenedioxythiophene) have attracted much attention in tissue engineering because of their high conductivities, which are comparable to those of inorganic semiconductor materials and metals, as well as their excellent biocompatibility and ease of manufacturing. $ ^{[151]} $ A cell-affinitive, electroactive, and osteoinductive porous titanium scaffold coated with a polypyrrole-polydopamine-HAP film promoted osteogenic cell differentiation under electrical stimulation. $ ^{[152]} $ When an electrical stimulus", "bbox": [605, 961, 1099, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Previous studies have shown that electrical stimuli can enhance bone regeneration and maintain the stemness of bone marrow MSCs. The mechanism of this effect is related to the stimulation of MSC proliferation and differentiation by electrical stimulation, which leads to an increased expression of bone morphogenetic proteins. These proteins activate the calcium-calmodulin pathway, TGF- $ \\beta $, and other cytokines, which are involved in bone formation and remodeling. $ ^{[150]} $ One strategy for delivering and responding to localized electrical stimuli is to incorporate electroactive materials, such as metals, carbon nanotubes, graphene, inorganic electroactive materials, and conductive polymers, into biomaterials. These materials modulate cellular activity and improve cell regeneration. 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+{"paper_id": "2HEUD5P9", "page": 18, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [89, 519, 583, 1315], "text": "Magnetic-responsive materials are composed of ferromagnetic or paramagnetic nanoparticles that can be manipulated by magnetic fields and act as therapeutic agents for magnetic hyperthermia. Magnetic nanoparticles, such as Fe₃O₄ nanoparticles, can produce heat under magnetic fields and enhance the osteogenic differentiation capability.[154] Therefore, this technology has significant potential for repairing bone defects. Magnetic Fe₃O₄ nanoparticles can generate heat under magnetic fields and raise the temperature to 42–45 °C, thus promoting apoptosis and death of cancer cells by causing hemorrhage or vascular occlusion without affecting nearby normal tissues. Moreover, although the underlying mechanisms are complex, magnetic hyperthermia may promote osteogenesis. Some studies have proposed that hyperthermia affects bone metabolism by increasing blood supply, while others have argued that hyperthermia enhances osteogenesis by boosting mitochondrial activity and the expression of osteogenic markers.[155] The specific mechanisms of osteogenic stimulation by magnetic hyperthermia require further clarification. Magnetothermal therapy under magnetic fields has the merit of high tissue penetration and is suitable for the treatment of lesions in deep tissues. Magnetic field-responsive strategies have been employed to develop versatile materials for bone repair and regeneration. The AKT-Fe₃O₄-CaO₂ composite scaffold triggered magnetic hyperthermia for rapid heating and the Fenton reaction in tumor oxidative therapy. The loaded CaO₂ nanoparticles generated H₂O₂, compensated for H₂O₂ consumption via the Fenton reaction, and sustainably released Ca²⁺ ions to promote osteogenesis.[156] α-TCP/calcium sulfate biphasic bone cement combined with Fe₃O₄/graphene oxide showed an outstanding magnetothermal effect, improved the effect of tumor treatment, and facilitated cell proliferation, adhesion, and osteogenic differentiation.[157] However, the field of bone therapy and regeneration induced by magnetic stimulation is still in its infancy. 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"text", "text": "Magnetic-responsive materials are composed of ferromagnetic or paramagnetic nanoparticles that can be manipulated by magnetic fields and act as therapeutic agents for magnetic hyperthermia. Magnetic nanoparticles, such as Fe₃O₄ nanoparticles, can produce heat under magnetic fields and enhance the osteogenic differentiation capability.[154] Therefore, this technology has significant potential for repairing bone defects. Magnetic Fe₃O₄ nanoparticles can generate heat under magnetic fields and raise the temperature to 42–45 °C, thus promoting apoptosis and death of cancer cells by causing hemorrhage or vascular occlusion without affecting nearby normal tissues. Moreover, although the underlying mechanisms are complex, magnetic hyperthermia may promote osteogenesis. Some studies have proposed that hyperthermia affects bone metabolism by increasing blood supply, while others have argued that hyperthermia enhances osteogenesis by boosting mitochondrial activity and the expression of osteogenic markers.[155] The specific mechanisms of osteogenic stimulation by magnetic hyperthermia require further clarification. Magnetothermal therapy under magnetic fields has the merit of high tissue penetration and is suitable for the treatment of lesions in deep tissues. Magnetic field-responsive strategies have been employed to develop versatile materials for bone repair and regeneration. The AKT-Fe₃O₄-CaO₂ composite scaffold triggered magnetic hyperthermia for rapid heating and the Fenton reaction in tumor oxidative therapy. The loaded CaO₂ nanoparticles generated H₂O₂, compensated for H₂O₂ consumption via the Fenton reaction, and sustainably released Ca²⁺ ions to promote osteogenesis.[156] α-TCP/calcium sulfate biphasic bone cement combined with Fe₃O₄/graphene oxide showed an outstanding magnetothermal effect, improved the effect of tumor treatment, and facilitated cell proliferation, adhesion, and osteogenic differentiation.[157] However, the field of bone therapy and regeneration induced by magnetic stimulation is still in its infancy. Future studies may focus on homogeneous temperature elevation by magnetic stimuli and develop strategies to minimize thermal injury to adjacent normal tissues.", "bbox": [89, 519, 583, 1315], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Magnetic-responsive materials are composed of ferromagnetic or paramagnetic nanoparticles that can be manipulated by magnetic fields and act as therapeutic agents for magnetic hyperthermia. Magnetic nanoparticles, such as Fe₃O₄ nanoparticles, can produce heat under magnetic fields and enhance the osteogenic differentiation capability.[154] Therefore, this technology has significant potential for repairing bone defects. Magnetic Fe₃O₄ nanoparticles can generate heat under magnetic fields and raise the temperature to 42–45 °C, thus promoting apoptosis and death of cancer cells by causing hemorrhage or vascular occlusion without affecting nearby normal tissues. Moreover, although the underlying mechanisms are complex, magnetic hyperthermia may promote osteogenesis. Some studies have proposed that hyperthermia affects bone metabolism by increasing blood supply, while others have argued that hyperthermia enhances osteogenesis by boosting mitochondrial activity and the expression of osteogenic markers.[155] The specific mechanisms of osteogenic stimulation by magnetic hyperthermia require further clarification. Magnetothermal therapy under magnetic fields has the merit of high tissue penetration and is suitable for the treatment of lesions in deep tissues. Magnetic field-responsive strategies have been employed to develop versatile materials for bone repair and regeneration. The AKT-Fe₃O₄-CaO₂ composite scaffold triggered magnetic hyperthermia for rapid heating and the Fenton reaction in tumor oxidative therapy. The loaded CaO₂ nanoparticles generated H₂O₂, compensated for H₂O₂ consumption via the Fenton reaction, and sustainably released Ca²⁺ ions to promote osteogenesis.[156] α-TCP/calcium sulfate biphasic bone cement combined with Fe₃O₄/graphene oxide showed an outstanding magnetothermal effect, improved the effect of tumor treatment, and facilitated cell proliferation, adhesion, and osteogenic differentiation.[157] However, the field of bone therapy and regeneration induced by magnetic stimulation is still in its infancy. Future studies may focus on homogeneous temperature elevation by magnetic stimuli and develop strategies to minimize thermal injury to adjacent normal tissues."}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 796, "left": 89, "top": 519, "right": 583, "bottom": 1315, "x_center": 336.0, "x_center_bucket": 325, "y_center": 917.0, "x_ratio": 0.2821, "y_ratio": 0.5859, "width_ratio": 0.4148, "height_ratio": 0.5086, "line_count": 1}, "span_signature": {"font_size": 8.74, "font_size_median": 8.97, "font_size_bucket": 8.5, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 377}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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The combined therapy effectively cured severe bone infections and enhanced osseointegration.[160] The ultrasound-responsive strategy, which is similar as the photoresponsive strategy, is noninvasive and highly controllable. 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HAP/barium titanate piezoelectric composites affected by cyclic loading promoted the proliferation of osteoblasts and their interaction with HA compared to pure HAP. $ ^{[162]} $ Polarized barium titanate/poly(vinylidene fluoride trifluoroethylene) nanocomposite membranes enhanced osteoinductivity and accelerated neovascularization. In addition, the composite combined with xenogeneic grafts of deproteinized bovine bone promoted mature bone structure formation within critically sized mandibular defects in rabbits. $ ^{[163]} $ A scaffold that mimics the structure and function of the periosteum by rationally combining poly(vinylidene fluoride-trifluoroethylene) (PVFT) and BGs significantly promoted cell proliferation, adhesion, and osteogenesis and facilitated periosteum-like tissue formation and critical-sized bone regeneration. Furthermore, the negative pole of PVFT attracts Ca $ ^{2+} $ from BGs, activating the calcium-sensing receptor of osteoblasts, thereby promoting osteogenesis. $ ^{[164]} $ 3D-printed acrylate epoxidized soybean oil (AESO) doped with Ag-TMSPM-pBT (ATP) piezoelectric scaffolds (AESO-ATP scaffolds) exhibited superior piezoelectric properties, close to the piezoelectric constants of bone tissue. Furthermore, this composite scaffolds facilitated osteogenic differentiation of BMSCs in vitro, and repaired bone defect in vivo. $ ^{[165]} $ However, piezoelectricity-responsive strategies have challenges such as the effects of densification, alkali evaporation, and high temperatures in the synthetic procedure, which remain to be solved. The underlying mechanisms and long-term biological safety of piezoelectricity-responsive materials should be investigated in future studies. 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In addition, the composite combined with xenogeneic grafts of deproteinized bovine bone promoted mature bone structure formation within critically sized mandibular defects in rabbits. $ ^{[163]} $ A scaffold that mimics the structure and function of the periosteum by rationally combining poly(vinylidene fluoride-trifluoroethylene) (PVFT) and BGs significantly promoted cell proliferation, adhesion, and osteogenesis and facilitated periosteum-like tissue formation and critical-sized bone regeneration. Furthermore, the negative pole of PVFT attracts Ca $ ^{2+} $ from BGs, activating the calcium-sensing receptor of osteoblasts, thereby promoting osteogenesis. $ ^{[164]} $ 3D-printed acrylate epoxidized soybean oil (AESO) doped with Ag-TMSPM-pBT (ATP) piezoelectric scaffolds (AESO-ATP scaffolds) exhibited superior piezoelectric properties, close to the piezoelectric constants of bone tissue. Furthermore, this composite scaffolds facilitated osteogenic differentiation of BMSCs in vitro, and repaired bone defect in vivo. $ ^{[165]} $ However, piezoelectricity-responsive strategies have challenges such as the effects of densification, alkali evaporation, and high temperatures in the synthetic procedure, which remain to be solved. The underlying mechanisms and long-term biological safety of piezoelectricity-responsive materials should be investigated in future studies. Triboelectric stimulation technology is used to achieve bone repair via mechanosensation of", "bbox": [598, 632, 1094, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Natural bone tissues exhibit bioelectrical properties that are essential for bone development. Piezoelectricity is the conversion of mechanical energy into electrical energy. Under physiological conditions, bones produce electrical signals when subjected to mechanical stimuli, ultimately stimulating bone regeneration. Piezoelectricity modulates cellular functions and enhances cell proliferation and osteogenesis. $ ^{[161]} $ Various piezoelectric biomaterials such as piezo-bioceramics and piezo-biopolymers have been extensively applied in bone tissue engineering. HAP/barium titanate piezoelectric composites affected by cyclic loading promoted the proliferation of osteoblasts and their interaction with HA compared to pure HAP. $ ^{[162]} $ Polarized barium titanate/poly(vinylidene fluoride trifluoroethylene) nanocomposite membranes enhanced osteoinductivity and accelerated neovascularization. In addition, the composite combined with xenogeneic grafts of deproteinized bovine bone promoted mature bone structure formation within critically sized mandibular defects in rabbits. $ ^{[163]} $ A scaffold that mimics the structure and function of the periosteum by rationally combining poly(vinylidene fluoride-trifluoroethylene) (PVFT) and BGs significantly promoted cell proliferation, adhesion, and osteogenesis and facilitated periosteum-like tissue formation and critical-sized bone regeneration. Furthermore, the negative pole of PVFT attracts Ca $ ^{2+} $ from BGs, activating the calcium-sensing receptor of osteoblasts, thereby promoting osteogenesis. $ ^{[164]} $ 3D-printed acrylate epoxidized soybean oil (AESO) doped with Ag-TMSPM-pBT (ATP) piezoelectric scaffolds (AESO-ATP scaffolds) exhibited superior piezoelectric properties, close to the piezoelectric constants of bone tissue. 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A,B) Water contact angle measurement for the Ti6Al4V substrate (A1) and Ti6Al4V substrate with BaTiO₃ coating (B1); Surface CLSM images of the Ti6Al4V substrate (A2) and Ti6Al4V substrate with BaTiO₃ coating (B2). C) Fluorescence staining of BMSCs (red, Rhodamine-phalloidin for F-actin; blue, DAPI for nucleus; green, fluorescein isothiocyanate for vinculin). Scale bar: 50 μm.[158] Copyright 2020 Elsevier. D) The osteogenic and proangiogenic functions of aged BMSCs, and activate mechanosensitive ion channel Piezo1 to promote Ca²⁺ influx.[16] Copyright 2020 Wiley-VCH. E) E-Au@H composite under NIR irradiation promoted the release of EGCG, which led to sterilization, promoted the formation of blood vessels, and accelerated the regeneration of periodontal bone tissue.[166] Copyright 2023 Elsevier.", "bbox": [95, 836, 1100, 954], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "figure_number", "raw_marker": "Figure 7", "number": 7, "kind": "figure", "normalized_text": "Figure 7. A,B) Water contact angle measurement for the Ti6Al4V substrate (A1) and Ti6Al4V substrate with BaTiO₃ coating (B1); Surface CLSM images of the Ti6Al4V substrate (A2) and Ti6Al4V substrate with BaTiO₃ coating (B2). C) Fluorescence staining of BMSCs (red, Rhodamine-phalloidin for F-actin; blue, DAPI for nucleus; green, fluorescein isothiocyanate for vinculin). Scale bar: 50 μm.[158] Copyright 2020 Elsevier. D) The osteogenic and proangiogenic functions of aged BMSCs, and activate mechanosensitive ion channel Piezo1 to promote Ca²⁺ influx.[16] Copyright 2020 Wiley-VCH. E) E-Au@H composite under NIR irradiation promoted the release of EGCG, which led to sterilization, promoted the formation of blood vessels, and accelerated the regeneration of periodontal bone tissue.[166] Copyright 2023 Elsevier."}, "layout_signature": {"width": 1005, "width_bucket": 1000, "height": 118, "left": 95, "top": 836, "right": 1100, "bottom": 954, "x_center": 597.5, "x_center_bucket": 600, "y_center": 895.0, "x_ratio": 0.5017, "y_ratio": 0.5719, "width_ratio": 0.8438, "height_ratio": 0.0754, "line_count": 1}, "span_signature": {"font_size": 7.78, "font_size_median": 7.97, "font_size_bucket": 8.0, "font_family_norm": "ScalaSansPro-Bold", "bold": true, "italic": true, "span_count": 150}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "display_zone", "style_family": "legend_like", "style_family_authority": "figure_marker", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.0, "decision": "body", "evidence": []}, "role_verification_status": "ACCEPT", "role_source": "accepted_figure_caption_artifact", "role_evidence": ["figure caption matched accepted figure artifact"]}
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+{"paper_id": "2HEUD5P9", "page": 19, "block_id": 5, "raw_label": "text", "raw_order": 2, "bbox": [95, 1113, 589, 1446], "text": "Physical stimuli-responsive strategies lack controllability, predictability, feasibility, and standardization in bone repair and regeneration applications according to existing research. These materials may cause damage to bone tissue, thereby affecting bone regeneration $ ^{1} $. However, physical stimuli-responsive strategies still have broad application prospects in bone repair and regeneration. For example, physical stimuli-responsive strategies can affect cell behavior by adjusting the physical properties of the extracellular matrix, thereby promoting bone repair and regeneration. In addition, physical stimuli-responsive strategies can be combined with other treatments such as drug therapy and gene therapy to improve treatment efficacy. With the development of technology, the development of physical stimuli-responsive materials will be a hot spot and new direction for the development of orthopedic biomaterials in the next decade. Multidisciplinary cross-fusion is also an inevitable trend in the clinical development of orthopedics. 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strategies lack controllability, predictability, feasibility, and standardization in bone repair and regeneration applications according to existing research. These materials may cause damage to bone tissue, thereby affecting bone regeneration $ ^{1} $. However, physical stimuli-responsive strategies still have broad application prospects in bone repair and regeneration. For example, physical stimuli-responsive strategies can affect cell behavior by adjusting the physical properties of the extracellular matrix, thereby promoting bone repair and regeneration. In addition, physical stimuli-responsive strategies can be combined with other treatments such as drug therapy and gene therapy to improve treatment efficacy. With the development of technology, the development of physical stimuli-responsive materials will be a hot spot and new direction for the development of orthopedic biomaterials in the next decade. Multidisciplinary cross-fusion is also an inevitable trend in the clinical development of orthopedics. Therefore, future research will focus on developing better materials to promote bone tissue regeneration and functional reconstruction.", "bbox": [95, 1113, 589, 1446], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Physical stimuli-responsive strategies lack controllability, predictability, feasibility, and standardization in bone repair and regeneration applications according to existing research. These materials may cause damage to bone tissue, thereby affecting bone regeneration $ ^{1} $. However, physical stimuli-responsive strategies still have broad application prospects in bone repair and regeneration. For example, physical stimuli-responsive strategies can affect cell behavior by adjusting the physical properties of the extracellular matrix, thereby promoting bone repair and regeneration. In addition, physical stimuli-responsive strategies can be combined with other treatments such as drug therapy and gene therapy to improve treatment efficacy. With the development of technology, the development of physical stimuli-responsive materials will be a hot spot and new direction for the development of orthopedic biomaterials in the next decade. Multidisciplinary cross-fusion is also an inevitable trend in the clinical development of orthopedics. Therefore, future research will focus on developing better materials to promote bone tissue regeneration and functional reconstruction."}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 333, "left": 95, "top": 1113, "right": 589, "bottom": 1446, "x_center": 342.0, "x_center_bucket": 350, "y_center": 1279.5, "x_ratio": 0.2872, "y_ratio": 0.8176, "width_ratio": 0.4148, "height_ratio": 0.2128, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 93}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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They have strong proliferative capacity and multi-lineage differentiation ability; therefore, they play an important role in tissue regeneration. Embryonic stem cells (ESCs) have self-renewal ability and pluripotency and can differentiate into various cell types, including the capacity to form osteogenic cells. $ ^{[167,168]} $ Induced pluripotent stem cells (iPSCs) possess limitless proliferation and pluripotent differentiation potential with no ethical issues and are thus regarded as a promising option for osteogenesis and bone repair. iPSCs are capable of differentiating into osteoblasts. $ ^{[169]} $ MSCs with outstanding proliferation and differentiation potential are multipotent stromal cells that can differentiate into several cell types, including osteoblasts, chondrocytes, adipocytes, myocytes, and endothelial cells. MSCs have immunomodulatory functions and retain the features of stem cells after multiple passages without immune rejection.", "bbox": [90, 192, 582, 565], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Stem cells are undifferentiated cells that self-renew and produce an abundance of undifferentiated offspring. They have strong proliferative capacity and multi-lineage differentiation ability; therefore, they play an important role in tissue regeneration. Embryonic stem cells (ESCs) have self-renewal ability and pluripotency and can differentiate into various cell types, including the capacity to form osteogenic cells. $ ^{[167,168]} $ Induced pluripotent stem cells (iPSCs) possess limitless proliferation and pluripotent differentiation potential with no ethical issues and are thus regarded as a promising option for osteogenesis and bone repair. iPSCs are capable of differentiating into osteoblasts. $ ^{[169]} $ MSCs with outstanding proliferation and differentiation potential are multipotent stromal cells that can differentiate into several cell types, including osteoblasts, chondrocytes, adipocytes, myocytes, and endothelial cells. MSCs have immunomodulatory functions and retain the features of stem cells after multiple passages without immune rejection."}, "layout_signature": {"width": 492, "width_bucket": 500, "height": 373, "left": 90, "top": 192, "right": 582, "bottom": 565, "x_center": 336.0, "x_center_bucket": 325, "y_center": 378.5, "x_ratio": 0.2821, "y_ratio": 0.2419, "width_ratio": 0.4131, "height_ratio": 0.2383, "line_count": 1}, "span_signature": {"font_size": 8.79, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 99}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_140", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 20, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [90, 566, 582, 1073], "text": "Bone biomaterials act as platforms to facilitate stem cell adhesion and growth during bone repair. The chemical components, surface characteristics, and topographic structure of bone biomaterials directly affect stem cell adhesion, proliferation, differentiation, and angiogenesis. Various attempts have been made to combine scaffolds and stem cells for bone regeneration. Human ESC-derived MSCs encapsulated in alginate microbeads in macroporous CaP cement exhibit good cytocompatibility, osteogenesis, and mineralization. $ ^{[170]} $ ECM-coated PLGA scaffolds enhanced the proliferation of ESCs, calcium deposition, and osteocalcin expression. $ ^{[171]} $ Poly(L-lactic acid) (PLLA) loaded with calcium-deficient nanohydroxyapatite (d-HAP) promotes the expression of osteogenic markers in iPSCs compared to pure PLLA. $ ^{[172]} $ Gingival MSC-laden alginate-based hydrogels with controllable mechanical properties exhibited good biocompatibility, biodegradability, and osteoconductivity after subcutaneous implantation in mice and facilitated craniofacial bone regeneration. $ ^{[173]} $ A composite of bone marrow-derived stromal cells and $ \\beta $-TCP transplanted into a monkey femoral defect exhibited enhanced bone regeneration compared to $ \\beta $-TCP alone. $ ^{[174]} $ A chitosan scaffold combined with osteogenically induced bone marrow MSCs promoted the formation of new bone and collagen in the pores of the scaffold and showed excellent biodegradability. $ ^{[175]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": 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This signaling is initiated by the binding of BMP to BMP receptors on the cell membrane, and the downstream Smad proteins are then phosphorylated by activated receptors. Smad complexes translocate into the nucleus, activating osteogenesis-related transcription factors and their corresponding downstream targets. BMPs regulate stem cell growth and differentiation and accelerate stem cell osteogenic differentiation. BMP-2, 4, 6, 7, and 9 effectively improve osteogenic differentiation in MSCs and induce new bone formation. Several biomaterials have been shown to activate the BMP signaling pathway. Nanofibrous HAP/chitosan nanocomposite scaffolds significantly promoted the proliferation and adhesion of MSCs, and the composite upregulated the expression of Smad1, BMP-2/4, Runx2, ALP, collagen I, integrin subunits, and myosins. 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Nanofibrous HAP/chitosan scaffolds combined with MSCs improved bone regeneration in cranial bone defects by initiating the integrin-BMP/Smad pathway. $ ^{[6]} $ Nanostructured titanium discs treated with $ H_{2}SO_{4}/H_{2}O_{2} $ promote osteoblast differentiation in osteoblastic cells by increasing the endogenous secretion of BMP-2 and regulating the BMP pathway. $ ^{[176]} $ BMP2-modified black phosphorus (BP@BMP2) nanosheets to PLLA electrospun fibrous scaffold, with a combination of recruiting osteoblast precursor cells and biomineralization properties for bone regeneration (Figure 8A,B). $ ^{[177]} $", "bbox": [90, 1376, 582, 1445], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "BMPs belong to the TGF- $ \\beta $ superfamily and are of great importance in bone formation and tissue homeostasis. This signaling is initiated by the binding of BMP to BMP receptors on the cell membrane, and the downstream Smad proteins are then phosphorylated by activated receptors. Smad complexes translocate into the nucleus, activating osteogenesis-related transcription factors and their corresponding downstream targets. BMPs regulate stem cell growth and differentiation and accelerate stem cell osteogenic differentiation. BMP-2, 4, 6, 7, and 9 effectively improve osteogenic differentiation in MSCs and induce new bone formation. Several biomaterials have been shown to activate the BMP signaling pathway. Nanofibrous HAP/chitosan nanocomposite scaffolds significantly promoted the proliferation and adhesion of MSCs, and the composite upregulated the expression of Smad1, BMP-2/4, Runx2, ALP, collagen I, integrin subunits, and myosins. Furthermore, the key proteins in the BMP signaling pathway, pSmad1/5/8, exhibited clear nuclear localization, and osteocalcin was significantly increased on the scaffold. 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+{"paper_id": "2HEUD5P9", "page": 20, "block_id": 12, "raw_label": "text", "raw_order": 10, "bbox": [600, 762, 1093, 1336], "text": "The Wnt/ $ \\beta $-catenin signaling pathway is recognized as a crucial signal for the regulation of stem cell osteogenic differentiation and is strongly associated with the formation and regeneration of bone. The binding of canonical Wnt proteins to the Frizzled/LRP receptor leads to the activation of $ \\beta $-catenin, ultimately regulating the expression of osteogenic transcription factors. The combination of non-canonical Wnt proteins with the Frizzled receptor activates heterotrimeric G protein and regulates intracellular Ca $ ^{2+} $ signaling through $ \\beta $-catenin independent pathways. The osteogenic functions of some materials are closely related to this signaling pathway. It has been shown that a PCL nanofiber scaffold promotes human MSCs adhesion and proliferation and significantly increases the osteogenic differentiation potency of MSCs by consistently activating the Wnt/ $ \\beta $-catenin and Smad3 pathways. $ ^{[178]} $ Silk braids with mechanical stiffness comparable to that of trabecular bone promoted human preosteoblast differentiation within their 3D microenvironment by the activation of Wnt/ $ \\beta $-catenin signaling. $ ^{[179]} $ The Wnt/ $ \\beta $-catenin pathway suppresses the adipogenic differentiation potential and alters the fate of cells from adipocytes to osteoblasts in adipose-derived MSCs. Chitosan-conjugated AuNPs increased the calcium deposit and the mRNA expression of osteogenic genes in human adipose-derived MSCs. Furthermore, immunofluorescence and Western blotting results indicate that the enhanced osteogenic effect is induced by the activation of the Wnt/ $ \\beta $-catenin signaling pathway. $ ^{[180]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "STIXMath-Italic", "flags": 6, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, 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The binding of canonical Wnt proteins to the Frizzled/LRP receptor leads to the activation of $ \\beta $-catenin, ultimately regulating the expression of osteogenic transcription factors. The combination of non-canonical Wnt proteins with the Frizzled receptor activates heterotrimeric G protein and regulates intracellular Ca $ ^{2+} $ signaling through $ \\beta $-catenin independent pathways. The osteogenic functions of some materials are closely related to this signaling pathway. 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E) The possible signaling pathways for the exosome-induced osteogenic differentiation of hMSCs by the PI3K/Akt and MAPK signaling pathways. $ ^{[101]} $ Copyright 2020 Wiley-VCH. F) Schematic model of matrix dynamics regulating BMSC differentiation by integrin $ \\beta $1-induced activation of YAP. $ ^{[188]} $ Copyright 2022 Elsevier.", "page_width": 1191, "page_height": 1565, "role": "figure_caption", "role_confidence": 0.92, "evidence": ["figure_title label: Figure 8. A) Schematic illustration of the procedure to fabr"], "seed_role": "figure_caption", "seed_confidence": 0.92, "seed_evidence": ["figure_title label: Figure 8. 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F) Schematic model of matrix dynamics regulating BMSC differentiation by integrin $ \\beta $1-induced activation of YAP. $ ^{[188]} $ Copyright 2022 Elsevier.", "bbox": [96, 1216, 1100, 1353], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "figure_number", "raw_marker": "Figure 8", "number": 8, "kind": "figure", "normalized_text": "Figure 8. A) Schematic illustration of the procedure to fabricate BP@BMP2 electrospun fibrous scaffolds and the effect of recruiting osteoblasts and releasing calcium-free phosphate therapy for promoting bone physiological regeneration in vivo. B) Radiological analysis in vivo. Representative microCT reconstruction images in coronal and sagittal view at 4 and 8 weeks in different groups. While the initial boundary of critical cranial defect was marked by the red dotted lines. $ ^{[177]} $ Copyright 2020 Wiley-VCH. C) Quantitative RT-qPCR result of in vivo BCP ceramic implantation. $ ^{[183]} $ Copyright 2020 Wiley-VCH. 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Overexpressed Notch intracellular domain inhibits BMP2-mediated Runx2 transcriptional activity and the Wnt-dependent osteogenesis pathway. $ ^{[181]} $ Silk fibroin, a core structural protein, can be used as an osteogenic biomaterial. Silk fibroin facilitates osteoblast differentiation into multipotent cells by suppressing the Notch pathway. $ ^{[182]} $ BCP ceramics increased ALP activity and the expression of osteogenesis (OPN/Col/Runx2) in bone marrow-derived stem cells compared with BCP ceramics with Notch signaling inhibitors and control groups (Figure 8C). Histological and histomorphometric analyses demonstrated that the Notch signaling inhibitor delayed bone formation. 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Upon cell-cell contact, Notch ligands (Jagged and Delta) interact with Notch receptors (Notch1–4), leading to the cleavage of the Notch intracellular domain. Subsequently, the Notch intracellular domain translocates to the nucleus, and the binding of the Notch intracellular domain to the DNA-binding protein CBF1, Suppressor of Hairless, Lag-1 (CSL) activates the transcription of Notch target genes. Activation of Notch signaling in human bone marrow MSCs stimulates early osteogenic differentiation while suppressing mature osteoblast formation by inhibiting Runx2 activity. Notch2 signaling modulates osteogenic differentiation initiated by BMP and Wnt signaling pathways. Overexpressed Notch intracellular domain inhibits BMP2-mediated Runx2 transcriptional activity and the Wnt-dependent osteogenesis pathway. $ ^{[181]} $ Silk fibroin, a core structural protein, can be used as an osteogenic biomaterial. Silk fibroin facilitates osteoblast differentiation into multipotent cells by suppressing the Notch pathway. $ ^{[182]} $ BCP ceramics increased ALP activity and the expression of osteogenesis (OPN/Col/Runx2) in bone marrow-derived stem cells compared with BCP ceramics with Notch signaling inhibitors and control groups (Figure 8C). Histological and histomorphometric analyses demonstrated that the Notch signaling inhibitor delayed bone formation. These findings indicated that the Notch pathway plays an important role in BCP-induced osteogenesis. $ ^{[183]} $", "bbox": [89, 148, 583, 701], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "and skeletal development. Upon cell-cell contact, Notch ligands (Jagged and Delta) interact with Notch receptors (Notch1–4), leading to the cleavage of the Notch intracellular domain. Subsequently, the Notch intracellular domain translocates to the nucleus, and the binding of the Notch intracellular domain to the DNA-binding protein CBF1, Suppressor of Hairless, Lag-1 (CSL) activates the transcription of Notch target genes. Activation of Notch signaling in human bone marrow MSCs stimulates early osteogenic differentiation while suppressing mature osteoblast formation by inhibiting Runx2 activity. Notch2 signaling modulates osteogenic differentiation initiated by BMP and Wnt signaling pathways. Overexpressed Notch intracellular domain inhibits BMP2-mediated Runx2 transcriptional activity and the Wnt-dependent osteogenesis pathway. $ ^{[181]} $ Silk fibroin, a core structural protein, can be used as an osteogenic biomaterial. Silk fibroin facilitates osteoblast differentiation into multipotent cells by suppressing the Notch pathway. $ ^{[182]} $ BCP ceramics increased ALP activity and the expression of osteogenesis (OPN/Col/Runx2) in bone marrow-derived stem cells compared with BCP ceramics with Notch signaling inhibitors and control groups (Figure 8C). Histological and histomorphometric analyses demonstrated that the Notch signaling inhibitor delayed bone formation. These findings indicated that the Notch pathway plays an important role in BCP-induced osteogenesis. $ ^{[183]} $"}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 553, "left": 89, "top": 148, "right": 583, "bottom": 701, "x_center": 336.0, "x_center_bucket": 325, "y_center": 424.5, "x_ratio": 0.2821, "y_ratio": 0.2712, "width_ratio": 0.4148, "height_ratio": 0.3534, "line_count": 1}, "span_signature": {"font_size": 8.88, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 319}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 22, "block_id": 5, "raw_label": "text", "raw_order": 3, "bbox": [89, 784, 582, 1446], "text": "The mitogen-activated protein kinase (MAPK) family comprises extracellular regulated kinase (ERK), p38, and c-Jun N-terminal kinase (JNK), which are associated with signal transduction in osteoblasts. The MAPK signaling pathway regulates cell proliferation, adhesion, migration, and differentiation in response to external stimuli. Several types of mechanical stimuli, such as compressive force, mechanical stretching, and fluid shear stress, have been reported to enhance osteogenesis through the p38/MAPK pathway. Studies have shown that the MAPK pathway is involved in biomaterial-induced osteogenesis. Akermanite bioceramics ( $ Ca_{2}MgSi_{2}O_{7} $) can promote cell growth, increase ALP activity, and the expression of osteogenic genes and angiogenic factors, while inhibiting the expression of osteoclastogenic factors by activating the ERK, P38, AKT, and STAT3 pathways. $ ^{[184]} $ BGs composed of calcium silicate facilitate osteoblast proliferation and differentiation by activating the MAPK pathway via the release of Si and Ca ions. $ ^{[185]} $ BMDMs cultured on Ti with low surface potential are more inclined polarize towards anti-inflammatory phenotype (M2) in vitro and in vivo. Whole gene expression analysis reveals that inhibition of the PI3K-Akt-mTOR signaling axis is responsible for the immune regulation ability of Ti with low surface potential (Figure 8D). $ ^{[186]} $ Bioactive ions from $ \\beta $-calcium silicate/poly(D, L-lactide-co-glycolide) composite scaffolds facilitate cell proliferation, ALP activity, calcium deposit, and stimulate osteogenic differentiation and angiogenesis through the activation of the MAPK and PI3K/AKT pathways. $ ^{[187]} $ RNA-sequencing suggests that the osteogenic exosomes induce the osteogenic differentiation by using their cargos to activate the PI3K/Akt and MAPK signaling pathways (Figure 8E). $ ^{[101]} $", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": 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The MAPK signaling pathway regulates cell proliferation, adhesion, migration, and differentiation in response to external stimuli. Several types of mechanical stimuli, such as compressive force, mechanical stretching, and fluid shear stress, have been reported to enhance osteogenesis through the p38/MAPK pathway. Studies have shown that the MAPK pathway is involved in biomaterial-induced osteogenesis. Akermanite bioceramics ( $ Ca_{2}MgSi_{2}O_{7} $) can promote cell growth, increase ALP activity, and the expression of osteogenic genes and angiogenic factors, while inhibiting the expression of osteoclastogenic factors by activating the ERK, P38, AKT, and STAT3 pathways. $ ^{[184]} $ BGs composed of calcium silicate facilitate osteoblast proliferation and differentiation by activating the MAPK pathway via the release of Si and Ca ions. $ ^{[185]} $ BMDMs cultured on Ti with low surface potential are more inclined polarize towards anti-inflammatory phenotype (M2) in vitro and in vivo. Whole gene expression analysis reveals that inhibition of the PI3K-Akt-mTOR signaling axis is responsible for the immune regulation ability of Ti with low surface potential (Figure 8D). $ ^{[186]} $ Bioactive ions from $ \\beta $-calcium silicate/poly(D, L-lactide-co-glycolide) composite scaffolds facilitate cell proliferation, ALP activity, calcium deposit, and stimulate osteogenic differentiation and angiogenesis through the activation of the MAPK and PI3K/AKT pathways. $ ^{[187]} $ RNA-sequencing suggests that the osteogenic exosomes induce the osteogenic differentiation by using their cargos to activate the PI3K/Akt and MAPK signaling pathways (Figure 8E). $ ^{[101]} $", "bbox": [89, 784, 582, 1446], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "The mitogen-activated protein kinase (MAPK) family comprises extracellular regulated kinase (ERK), p38, and c-Jun N-terminal kinase (JNK), which are associated with signal transduction in osteoblasts. The MAPK signaling pathway regulates cell proliferation, adhesion, migration, and differentiation in response to external stimuli. Several types of mechanical stimuli, such as compressive force, mechanical stretching, and fluid shear stress, have been reported to enhance osteogenesis through the p38/MAPK pathway. Studies have shown that the MAPK pathway is involved in biomaterial-induced osteogenesis. Akermanite bioceramics ( $ Ca_{2}MgSi_{2}O_{7} $) can promote cell growth, increase ALP activity, and the expression of osteogenic genes and angiogenic factors, while inhibiting the expression of osteoclastogenic factors by activating the ERK, P38, AKT, and STAT3 pathways. $ ^{[184]} $ BGs composed of calcium silicate facilitate osteoblast proliferation and differentiation by activating the MAPK pathway via the release of Si and Ca ions. $ ^{[185]} $ BMDMs cultured on Ti with low surface potential are more inclined polarize towards anti-inflammatory phenotype (M2) in vitro and in vivo. Whole gene expression analysis reveals that inhibition of the PI3K-Akt-mTOR signaling axis is responsible for the immune regulation ability of Ti with low surface potential (Figure 8D). $ ^{[186]} $ Bioactive ions from $ \\beta $-calcium silicate/poly(D, L-lactide-co-glycolide) composite scaffolds facilitate cell proliferation, ALP activity, calcium deposit, and stimulate osteogenic differentiation and angiogenesis through the activation of the MAPK and PI3K/AKT pathways. $ ^{[187]} $ RNA-sequencing suggests that the osteogenic exosomes induce the osteogenic differentiation by using their cargos to activate the PI3K/Akt and MAPK signaling pathways (Figure 8E). $ ^{[101]} $"}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 662, "left": 89, "top": 784, "right": 582, "bottom": 1446, "x_center": 335.5, "x_center_bucket": 325, "y_center": 1115.0, "x_ratio": 0.2817, "y_ratio": 0.7125, "width_ratio": 0.4139, "height_ratio": 0.423, "line_count": 1}, "span_signature": {"font_size": 8.8, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 331}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 22, "block_id": 7, "raw_label": "text", "raw_order": 5, "bbox": [599, 192, 1093, 524], "text": "In addition to the aforementioned pathways, bone development and homeostasis involve several other pathways that play an indispensable role in the osteogenic differentiation of undifferentiated and osteoprogenitor cells. For example, YAP/TAZ signaling, integrin signaling, calcium and phosphate signaling. Fast “dynamic bridges” to construct viscoelastic gelatin methacryloyl (GelMA)-based hydrogels, the viscous dissipation of hydrogels activated YAP by stabilizing integrin $ \\beta_1 $, and further promoted nuclear translocation of smad2/3 and $ \\beta $-catenin to enhance chondrogenesis and osteogenesis (Figure 8F). $ ^{[188]} $ NF- $ \\kappa $B signaling, and Hedgehog signaling have been proven to regulate osteogenic differentiation in stem cells. Therefore, elucidating the mechanisms through which biomaterial properties modulate cellular responses and molecular events during bone regeneration is critical for designing superior bone biomaterials.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, 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osteogenic differentiation of undifferentiated and osteoprogenitor cells. For example, YAP/TAZ signaling, integrin signaling, calcium and phosphate signaling. Fast “dynamic bridges” to construct viscoelastic gelatin methacryloyl (GelMA)-based hydrogels, the viscous dissipation of hydrogels activated YAP by stabilizing integrin $ \\beta_1 $, and further promoted nuclear translocation of smad2/3 and $ \\beta $-catenin to enhance chondrogenesis and osteogenesis (Figure 8F). $ ^{[188]} $ NF- $ \\kappa $B signaling, and Hedgehog signaling have been proven to regulate osteogenic differentiation in stem cells. Therefore, elucidating the mechanisms through which biomaterial properties modulate cellular responses and molecular events during bone regeneration is critical for designing superior bone biomaterials.", "bbox": [599, 192, 1093, 524], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "In addition to the aforementioned pathways, bone development and homeostasis involve several other pathways that play an indispensable role in the osteogenic differentiation of undifferentiated and osteoprogenitor cells. For example, YAP/TAZ signaling, integrin signaling, calcium and phosphate signaling. Fast “dynamic bridges” to construct viscoelastic gelatin methacryloyl (GelMA)-based hydrogels, the viscous dissipation of hydrogels activated YAP by stabilizing integrin $ \\beta_1 $, and further promoted nuclear translocation of smad2/3 and $ \\beta $-catenin to enhance chondrogenesis and osteogenesis (Figure 8F). $ ^{[188]} $ NF- $ \\kappa $B signaling, and Hedgehog signaling have been proven to regulate osteogenic differentiation in stem cells. Therefore, elucidating the mechanisms through which biomaterial properties modulate cellular responses and molecular events during bone regeneration is critical for designing superior bone biomaterials."}, "layout_signature": {"width": 494, "width_bucket": 500, "height": 332, "left": 599, "top": 192, "right": 1093, "bottom": 524, "x_center": 846.0, "x_center_bucket": 850, "y_center": 358.0, "x_ratio": 0.7103, "y_ratio": 0.2288, "width_ratio": 0.4148, "height_ratio": 0.2121, "line_count": 1}, "span_signature": {"font_size": 8.89, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 118}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_139", "display_cluster_candidate_id": "disp_27_0", "layout_region": "display_zone", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
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+{"paper_id": "2HEUD5P9", "page": 22, "block_id": 9, "raw_label": "text", "raw_order": 7, "bbox": [600, 588, 1093, 961], "text": "Herein, we summarized several biomaterials with unique biofunctions, bioactive compounds, 3D bioprinting techniques, and physical stimuli-responsive strategies for bone repair and regeneration. Among the materials, metals still need more research regarding their biocompatibility, biodegradability, and corrosion properties in vivo, as well as clinical evaluations, while ceramic biomaterials predominantly applied to fabricate bone scaffolds need to be combined with metals or polymers to obtain a suitable degradation rate and mechanical strength. Natural polymers have drawbacks such as low mechanical strength, high production cost, batch inconsistency, and immunogenicity, while synthetic polymers have limitations such as a lack of bioactivity, slow degradation, and harmful degradation products. These challenges have motivated biomaterial designers to develop new composites. Composites can enhance bioactivity and integrate the desirable properties of different materials to fully mimic the characteristics of natural bone.", "page_width": 1191, "page_height": 1565, "role": "body_paragraph", "role_confidence": 0.6, "evidence": ["default body_paragraph for text label"], "seed_role": "body_paragraph", "seed_confidence": 0.6, "seed_evidence": ["default body_paragraph for text label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 8.966400146484375, "font": "ScalaPro-Regular", "flags": 4, "color": 0, "dir": [1.0, 0.0], "wmode": 0}, {"size": 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"raw_label": "text", "text": "Herein, we summarized several biomaterials with unique biofunctions, bioactive compounds, 3D bioprinting techniques, and physical stimuli-responsive strategies for bone repair and regeneration. Among the materials, metals still need more research regarding their biocompatibility, biodegradability, and corrosion properties in vivo, as well as clinical evaluations, while ceramic biomaterials predominantly applied to fabricate bone scaffolds need to be combined with metals or polymers to obtain a suitable degradation rate and mechanical strength. Natural polymers have drawbacks such as low mechanical strength, high production cost, batch inconsistency, and immunogenicity, while synthetic polymers have limitations such as a lack of bioactivity, slow degradation, and harmful degradation products. These challenges have motivated biomaterial designers to develop new composites. Composites can enhance bioactivity and integrate the desirable properties of different materials to fully mimic the characteristics of natural bone.", "bbox": [600, 588, 1093, 961], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Herein, we summarized several biomaterials with unique biofunctions, bioactive compounds, 3D bioprinting techniques, and physical stimuli-responsive strategies for bone repair and regeneration. Among the materials, metals still need more research regarding their biocompatibility, biodegradability, and corrosion properties in vivo, as well as clinical evaluations, while ceramic biomaterials predominantly applied to fabricate bone scaffolds need to be combined with metals or polymers to obtain a suitable degradation rate and mechanical strength. Natural polymers have drawbacks such as low mechanical strength, high production cost, batch inconsistency, and immunogenicity, while synthetic polymers have limitations such as a lack of bioactivity, slow degradation, and harmful degradation products. These challenges have motivated biomaterial designers to develop new composites. Composites can enhance bioactivity and integrate the desirable properties of different materials to fully mimic the characteristics of natural bone."}, "layout_signature": {"width": 493, "width_bucket": 500, "height": 373, "left": 600, "top": 588, "right": 1093, "bottom": 961, "x_center": 846.5, "x_center_bucket": 850, "y_center": 774.5, "x_ratio": 0.7107, "y_ratio": 0.4949, "width_ratio": 0.4139, "height_ratio": 0.2383, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaPro-Regular", "bold": false, "italic": true, "span_count": 147}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "style_family": "unknown_like", "style_family_authority": "fallback", "reading_band_id": "band_138", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "zone": "body_zone", "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 22, "block_id": 10, "raw_label": "text", "raw_order": 8, "bbox": [598, 961, 1094, 1446], "text": "3D printing technology is a novel strategy in precision medicine that can produce bone implants using multiple materials based on digital models. With advances in 3D printing technology, novel composite materials with superior properties are rapidly emerging and being applied in clinical trials. 3D printing technology has great potential for personalized and accurate bone repair. Moreover, 3D bioprinting can precisely control the microstructure of the scaffolds. 3D printing can be used to customize scaffolds according to individual needs and to provide a suitable environment for cell adhesion and bone conduction. With the interdisciplinary development of 3D printing technology, 3D-printed bone scaffolds are expected to have excellent application prospects in bone repair and regeneration. In addition to 3D printing technology, physical stimuli-responsive strategies have received extensive attention. Physical stimuli-responsive biomaterials can use external triggers, such as light irradiation, electric and magnetic fields, ultrasound, or other mechanical stimuli, to achieve better therapeutic and regenerative outcomes. After eliminating severe infection, residual tumor tissue, or other bone diseases in a short and effective manner, a therapeutic biomaterial should promote cell attachment. 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Moreover, 3D bioprinting can precisely control the microstructure of the scaffolds. 3D printing can be used to customize scaffolds according to individual needs and to provide a suitable environment for cell adhesion and bone conduction. With the interdisciplinary development of 3D printing technology, 3D-printed bone scaffolds are expected to have excellent application prospects in bone repair and regeneration. In addition to 3D printing technology, physical stimuli-responsive strategies have received extensive attention. Physical stimuli-responsive biomaterials can use external triggers, such as light irradiation, electric and magnetic fields, ultrasound, or other mechanical stimuli, to achieve better therapeutic and regenerative outcomes. After eliminating severe infection, residual tumor tissue, or other bone diseases in a short and effective manner, a therapeutic biomaterial should promote cell attachment. 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Additionally, detailed protocols are required for the extraction, culturing, and seeding of stem cells on scaffolds to create tissues comparable to natural bone in terms of quality and stability. The application of biomaterials for bone regeneration still requires a thorough understanding of the complex molecular mechanisms involved in osteogenesis induction and faces several challenges that need to be addressed in future investigations.", "bbox": [96, 237, 587, 479], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "Despite the promising results presented herein, the literature primarily focuses on the development of scaffolds using advanced biomaterials, but lacks sufficient researches on the use of biomaterial-cell systems for bone repair and regeneration. Additionally, detailed protocols are required for the extraction, culturing, and seeding of stem cells on scaffolds to create tissues comparable to natural bone in terms of quality and stability. 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+{"paper_id": "2HEUD5P9", "page": 27, "block_id": 10, "raw_label": "number", "raw_order": null, "bbox": [527, 1484, 668, 1508], "text": "2301283 (27 of 27)", "page_width": 1191, "page_height": 1565, "role": "reference_item", "role_confidence": 0.9, "evidence": ["page number label"], "seed_role": "noise", "seed_confidence": 0.9, "seed_evidence": ["page number label"], "span_metadata": [{"size": 8.966400146484375, "font": "ScalaSansPro-Bold", "flags": 20, "color": 0, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 10, "page": 27, "raw_label": "number", "text": "2301283 (27 of 27)", "bbox": [527, 1484, 668, 1508], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "reference_numeric_dot", "raw_marker": "2301283", "number": 2301283, "kind": "reference", "normalized_text": "2301283 (27 of 27)"}, "layout_signature": {"width": 141, "width_bucket": 150, "height": 24, "left": 527, "top": 1484, "right": 668, "bottom": 1508, "x_center": 597.5, "x_center_bucket": 600, "y_center": 1496.0, "x_ratio": 0.5017, "y_ratio": 0.9559, "width_ratio": 0.1184, "height_ratio": 0.0153, "line_count": 1}, "span_signature": {"font_size": 8.97, "font_size_median": 8.97, "font_size_bucket": 9.0, "font_family_norm": "ScalaSansPro-Bold", "bold": true, "italic": true, "span_count": 1}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": true, "index_default": true, "zone": "reference_zone", "style_family": "reference_like", "style_family_authority": "reference_family_anchor", "reading_band_id": "band_141", "display_cluster_candidate_id": "", "layout_region": "reference_candidate", "boundary_before": "hard", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "reference_zone_fallback", "role_evidence": ["reference item accepted (pre-gate resolution, empty zone)"]}
+{"paper_id": "2HEUD5P9", "page": 27, "block_id": 11, "raw_label": "footer", "raw_order": null, "bbox": [938, 1487, 1095, 1506], "text": "© 2024 Wiley-VCH GmbH", "page_width": 1191, "page_height": 1565, "role": "noise", "role_confidence": 0.9, "evidence": ["footer label"], "seed_role": "noise", "seed_confidence": 0.9, "seed_evidence": ["footer label"], "span_metadata": [{"size": 6.973800182342529, "font": "ScalaSansPro-Regular", "flags": 4, "color": 2301728, "dir": [1.0, 0.0], "wmode": 0}], "raw_observation": {"block_id": 11, "page": 27, "raw_label": "footer", "text": "© 2024 Wiley-VCH GmbH", "bbox": [938, 1487, 1095, 1506], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "© 2024 Wiley-VCH GmbH"}, "layout_signature": {"width": 157, "width_bucket": 150, "height": 19, "left": 938, "top": 1487, "right": 1095, "bottom": 1506, "x_center": 1016.5, "x_center_bucket": 1025, "y_center": 1496.5, "x_ratio": 0.8535, "y_ratio": 0.9562, "width_ratio": 0.1318, "height_ratio": 0.0121, "line_count": 1}, "span_signature": {"font_size": 6.97, "font_size_median": 6.97, "font_size_bucket": 7.0, "font_family_norm": "ScalaSansPro-Regular", "bold": false, "italic": true, "span_count": 1}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": false, "index_default": false, "zone": "", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
+{"paper_id": "2HEUD5P9", "page": 27, "block_id": 12, "raw_label": "aside_text", "raw_order": null, "bbox": [1155, 31, 1171, 1536], "text": "2369606, 2024, 8, Downloaded from https://onlinelibrary.wiley.com/doi/10.1002/smld.202301283 by Shandong University Library, Wiley Online Library on [18/02/2026]. See the Terms and Conditions (https://onlinelibrary.wiley.com/terms-and-conditions) on Wiley Online Library for rules of use; OA articles are governed by the applicable Creative Commons License.", "page_width": 1191, "page_height": 1565, "role": "noise", "role_confidence": 0.95, "evidence": ["margin-band narrow/tall geometry; treated as noise"], "seed_role": "noise", "seed_confidence": 0.95, "seed_evidence": ["margin-band narrow/tall geometry; treated as noise"], "span_metadata": [{"size": 5.03000020980835, "font": "Times-Roman", "flags": 4, "color": 0, "dir": [0.0, 1.0], "wmode": 0}], "raw_observation": {"block_id": 12, "page": 27, "raw_label": "aside_text", "text": "2369606, 2024, 8, Downloaded from https://onlinelibrary.wiley.com/doi/10.1002/smld.202301283 by Shandong University Library, Wiley Online Library on [18/02/2026]. See the Terms and Conditions (https://onlinelibrary.wiley.com/terms-and-conditions) on Wiley Online Library for rules of use; OA articles are governed by the applicable Creative Commons License.", "bbox": [1155, 31, 1171, 1536], "page_width": 1191, "page_height": 1565}, "marker_signature": {"type": "none", "raw_marker": null, "number": null, "kind": "generic_text", "normalized_text": "2369606, 2024, 8, Downloaded from https://onlinelibrary.wiley.com/doi/10.1002/smld.202301283 by Shandong University Library, Wiley Online Library on [18/02/2026]. See the Terms and Conditions (https://onlinelibrary.wiley.com/terms-and-conditions) on Wiley Online Library for rules of use; OA articles are governed by the applicable Creative Commons License."}, "layout_signature": {"width": 16, "width_bucket": 25, "height": 1505, "left": 1155, "top": 31, "right": 1171, "bottom": 1536, "x_center": 1163.0, "x_center_bucket": 1175, "y_center": 783.5, "x_ratio": 0.9765, "y_ratio": 0.5006, "width_ratio": 0.0134, "height_ratio": 0.9617, "line_count": 1}, "span_signature": {"font_size": 5.03, "font_size_median": 5.03, "font_size_bucket": 5.0, "font_family_norm": "Times-Roman", "bold": false, "italic": true, "span_count": 1}, "_in_visual_container": null, "_container_bbox": null, "_container_text": null, "_text_source": null, "_ocr_raw_status": null, "_ocr_raw_error_type": null, "render_default": false, "index_default": false, "zone": "", "style_family": "body_like", "style_family_authority": "body_zone_with_anchor", "reading_band_id": "band_142", "display_cluster_candidate_id": "", "layout_region": "body_flow", "boundary_before": "none", "boundary_after": "none", "bridge_eligible": false, "insert_score": {"score": 0.15, "decision": "body", "evidence": ["narrow_width"]}, "role_verification_status": "ACCEPT", "role_source": "non_structural_normalized_role", "role_evidence": ["pre-gate normalized non-structural role preserved"]}
diff --git a/tests/test_ocr_figure_vnext_real_papers.py b/tests/test_ocr_figure_vnext_real_papers.py
new file mode 100644
index 00000000..c90af066
--- /dev/null
+++ b/tests/test_ocr_figure_vnext_real_papers.py
@@ -0,0 +1,14 @@
+from pathlib import Path
+
+from scripts.dev.compare_figure_inventory_legacy_vs_vnext import compare_blocks_file
+
+
+def test_real_paper_same_page_milestone_reports_diff_shape():
+ blocks_path = Path("tests/fixtures/ocr_vnext_real_papers/2HEUD5P9/blocks.structured.jsonl")
+ diff = compare_blocks_file(blocks_path)
+
+ assert diff["paper"] == "2HEUD5P9"
+ assert "legacy_matched_count" in diff
+ assert "vnext_matched_count" in diff
+ assert "legacy_consumed_block_ids" in diff
+ assert "vnext_consumed_block_ids" in diff