Zhang et al 2024c - Revision history

Zxzhe13: WERQERQWERQWER

2024-11-13T15:18:56Z

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Zxzhe13: 21122112

2024-11-13T15:12:58Z

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Zxzhe13: correct the paragraph before Figure 6

2024-06-14T02:56:24Z

correct the paragraph before Figure 6

Rimni at 13:57, 11 June 2024

2024-06-11T13:57:16Z

Rimni: /* Acknowledgments */

2024-06-11T11:53:23Z

‎Acknowledgments

Rimni at 11:15, 11 June 2024

2024-06-11T11:15:09Z

Rimni at 11:14, 11 June 2024

2024-06-11T11:14:21Z

Rimni at 11:12, 11 June 2024

2024-06-11T11:12:39Z

Rimni: /* 3.2 Construction and finite element results of tibial segmental bone defect scaffold */

2024-06-11T11:10:52Z

‎3.2 Construction and finite element results of tibial segmental bone defect scaffold

Rimni at 11:10, 11 June 2024

2024-06-11T11:10:28Z

@@ Line 209: / Line 209: @@
 {| style="text-align: center; margin:auto;width: 100%;"
 |-
-| style="text-align: center;" | x → tran[[1]], y → tran[[2]], z → tran[[3]]
+| style="text-align: center;" | <math> {\displaystyle {\begin{aligned}x\to &{\rm {tran}}[[1]],\,\,y\to {\rm {tran}}[[2]],
 |}
 |}

@@ Line 152: / Line 152: @@
 {| class="wikitable" style="margin: 0em auto 0.1em auto;border-collapse: collapse;width:auto;"
 |-style="background:white;"
-|style="text-align: center;padding:10px;"| [[Image:Draft_Zhang_149466663-picture- 2.svg|center|600px]]
+|style="text-align: center;padding:10px;"|[[File:4 upscayl 4x realesrgan-x4plus.png|centre|600x600px]]
 |-
 | style="background:#efefef;text-align:left;padding:10px;font-size: 85%;"| '''Figure 4'''. CFD Velocity results with different cell structures
@@ Line 163: / Line 163: @@
 {| class="wikitable" style="margin: 0em auto 0.1em auto;border-collapse: collapse;width:auto;"
 |-style="background:white;"
-|style="text-align: center;padding:10px;"| [[Image:Draft_Zhang_149466663-picture- 3.svg|center|600px]]
+|style="text-align: center;padding:10px;"|[[File:5 upscayl 4x realesrgan-x4plus.png|centre|600x600px]]
 |-
 | style="background:#efefef;text-align:left;padding:10px;font-size: 85%;"| '''Figure 5'''. Results of CFD flow pressure with different cell structures

@@ Line 229: / Line 229: @@
 |}
-where <math display="inline"> A </math> and <math display="inline"> B </math> are constants and <math display="inline">A^2 +B^2=1</math>. As shown in [[#img-6|Figure 6]], are the orthographic, upper and lower diagrams of the constructed function, respectively, in which the upper surface is similar to the G structure, the upper surface is similar to the D structure, and the lower surface is similar to the P structure, so the model of this mixed microstructure is defined as GDP scaffold.
+where <math display="inline"> A </math> and <math display="inline"> B </math> are constants and <math display="inline">A^2 +B^2=1</math>. As shown in [[#img-6|Figure 6]], the orthographic, upper, and lower diagrams of the constructed function are presented, respectively. The upper surface is similar to the G structure, the middle surface is similar to the D structure, and the lower surface is similar to the P structure. Therefore, the model of this mixed microstructure is defined as the GDP scaffold.
 <div id='img-6'></div>

@@ Line 61: / Line 61: @@
 where, <math display="inline">\rho</math> is the fluid density;  <math display="inline">u</math> the fluid velocity; <math display="inline">t</math> the time; <math display="inline">\mu</math> the dynamic viscosity of fluid; <math display="inline">\nabla</math> the del operator; <math display="inline">P</math> the pressure; and <math display="inline">F</math> the gravity or centrifugal force.
-The boundary conditions applied for CFD analysis are shown in [[#img-1|Figure 1]](d), and the region with <math display="inline">F \ge  C</math> is considered as the fluid model. The inflow surface (Inlet), outflow surface (Outlet), solid wall 1 (Wall1), and solid wall 2 (Wall2) are shown in the figure. The liquid flowing through the pore area of the scaffold is assumed to be capillary blood, with an inlet flow rate of 0.0005m/s applied on the inlet surface and 0 outlet pressure applied on the outlet surface. Wall1 and Wall2 are defined as non sliding wall surfaces, with a fluid viscosity of 4.2mPa•s. The relevant settings are summarized in [[#tab-1|Table 1]].
+The boundary conditions applied for CFD analysis are shown in [[#img-1|Figure 1]](d), and the region with <math display="inline">F \ge  C</math> is considered as the fluid model. The inflow surface (Inlet), outflow surface (Outlet), solid wall 1 (Wall1), and solid wall 2 (Wall2) are shown in the figure. The liquid flowing through the pore area of the scaffold is assumed to be capillary blood, with an inlet flow rate of 0.0005m/s applied on the inlet surface and 0 outlet pressure applied on the outlet surface. Wall1 and Wall2 are defined as non sliding wall surfaces, with a fluid viscosity of 4.2mPa·s. The relevant settings are summarized in [[#tab-1|Table 1]].
 <div class="center" style="font-size: 85%;">'''Table 1'''.  Related settings in permeability calculation</div>

@@ Line 287: / Line 287: @@
 In this study, the microstructure design of tibial segmental implant scaffolds was the focus of research. Finite element analysis was initially conducted on three scaffold structures. The results showed that the structural performance of the G-type scaffold was more stable, with a uniform distribution of Mises stress. Within the microscale curvature range of 0-1, the Mises stress decreased as the curvature increased. When the curvature was 1, the local Mises stress value was <math display="inline">0.07\times 10^8</math> N/m<math display="inline">^2</math>. The G-type scaffold had the lowest flow velocity compared to the P and D-type scaffolds, but it exhibited better fluidity, making it suitable for inward bone tissue ingrowth. Based on these findings and considering the mechanical and biological requirements of tibial implant scaffolds, a composite scaffold structure, termed GDP, was constructed. Through finite element analysis and discussion, it was concluded that the GDP scaffold meets the design requirements of the tibial diaphysis.
-=Acknowledgments=
+==Acknowledgments==
 The author(s) disclosed receipt of the following ﬁnancial support for the research, authorship, and/or publication of this article: National Natural Science Foundation of China（No.52165026）,Open Subjects of State Key Laboratory of Mechanical Manufacturing Systems Engineering, Xi'an Jiaotong University (No.sklms2021011) for their support to this research.
-=='''References'''==
+==References==
-[1] Li L.,Wang P.,Liang H.X.,Jin J.,Zhang Y.B.,Shi J.P.,Zhang Y.,He S.Y.,Mao H.L.,Xue B.,Lai J.C.,Zhu L.,Jiang Q. Design of a Haversian system-like gradient porous scaffold based on triply periodic minimal surfaces for promoting bone regeneration. Journal of advanced research, 54:89-104, 2023.
+[1] Li L., Wang P., Liang H.X., Jin J., Zhang Y.B., Shi J.P., Zhang Y., He S.Y., Mao H.L., Xue B., Lai J.C., Zhu L., Jiang Q. Design of a Haversian system-like gradient porous scaffold based on triply periodic minimal surfaces for promoting bone regeneration. Journal of Advanced Research, 54:89-104, 2023.
-[2] Jin H., Zhuo Y., Sun Y., Fu H., Han Z. Microstructure design and degradation performance in vitro of three-dimensional printed bioscaffold for bone tissue engineering. Advances in Mechanical Engineering, 11(10): 1687814019883784, 2019.
+[2] Jin H., Zhuo Y., Sun Y., Fu H., Han Z. Microstructure design and degradation performance in vitro of three-dimensional printed bioscaffold for bone tissue engineering. Advances in Mechanical Engineering, 11(10), 2019.
-[3] Pei H.L.,Fan Q.W.,Ma D., Yang Y. F. Design and Geometric Characterization of Three-Dimensional Gradient Heterogeneous Bone Tissue Structures Based on Voronoi. Science of Advanced Materials, 15(4): 561-570, 2023.
+[3] Pei H.L., Fan Q.W., Ma D., Yang Y.F. Design and geometric characterization of three-dimensional gradient heterogeneous bone tissue structures based on Voronoi. Science of Advanced Materials, 15(4):561-570, 2023.
-[4] Gryko A.,Prochor P.,Sajewicz E. Finite element analysis of the influence of porosity and pore geometry on mechanical properties of orthopaedic scaffolds. Journal of the Mechanical Behavior of Biomedical Materials, 132, 105275, 2022.
+[4] Gryko A., Prochor P., Sajewicz E. Finite element analysis of the influence of porosity and pore geometry on mechanical properties of orthopaedic scaffolds. Journal of the Mechanical Behavior of Biomedical Materials, 132, 105275, 2022.
-[5] Peng W.,Liu Y.,Wang C. Definition, measurement, and function of pore structure dimensions of bioengineered porous bone tissue materials based on additive manufacturing: A review. Frontiers in Bioengineering and Biotechnology, 10, 1081548, 2023.
+[5] Peng W., Liu Y., Wang C. Definition, measurement, and function of pore structure dimensions of bioengineered porous bone tissue materials based on additive manufacturing: A review. Frontiers in Bioengineering and Biotechnology, 10, 1081548, 2023.
-[6] Lv Y.,Liu G.,Wang B., Tang Y.,Lin Z.,Liu J.,Wang L. Pore strategy design of a novel NiTi-Nb biomedical porous scaffold based on a triply periodic minimal surface. Frontiers in Bioengineering and Biotechnology, 10, 910475, 2022.
+[6] Lv Y., Liu G., Wang B., Tang Y., Lin Z., Liu J., Wang L. Pore strategy design of a novel NiTi-Nb biomedical porous scaffold based on a triply periodic minimal surface. Frontiers in Bioengineering and Biotechnology, 10, 910475, 2022.
-[7] Alkentar R.,Kladovasilakis N.,Tzetzis D.,Mankovits T. Effects of Pore Size Parameters of Titanium Additively Manufactured Lattice Structures on the Osseointegration Process in Orthopedic Applications: A Comprehensive Review. Crystals, 13(1), 113, 2023.
+[7] Alkentar R., Kladovasilakis N., Tzetzis D., Mankovits T. Effects of pore size parameters of titanium additively manufactured lattice structures on the osseointegration process in orthopedic applications: A comprehensive review. Crystals, 13(1), 113, 2023.
-[8] Yao Y.T.,Yang Y.,Ye Q.,Cao S.S.,Zhang X.P., Zhao,K.,Jian Y. Effects of pore size and porosity on cytocompatibility and osteogenic differentiation of porous titanium. Journal of Materials Science: Materials in Medicine, 32(6), 72, 2021.
+[8] Yao Y.T., Yang Y., Ye Q., Cao S.S., Zhang X.P., Zhao, K., Jian Y. Effects of pore size and porosity on cytocompatibility and osteogenic differentiation of porous titanium. Journal of Materials Science: Materials in Medicine, 32(6), 72, 2021.
-[9] Bisht B.,Hope A.,Mukherjee A.,Paul M.K. Advances in the fabrication of scaffold and 3D printing of biomimetic bone graft. Annals of biomedical engineering, 49(4), 1128-1150, 2021.
+[9] Bisht B., Hope A., Mukherjee A., Paul M.K. Advances in the fabrication of scaffold and 3D printing of biomimetic bone graft. Annals of Biomedical Engineering, 49(4):1128-1150, 2021.
-[10] Al-Barqawi M.O.,Church B.,Thevamaran M.,Thoma D.J.,Rahman A. Design and Validation of Additively Manufactured Metallic Cellular Scaffold Structures for Bone Tissue Engineering. Materials, 15(9), 3310, 2022.
+[10] Al-Barqawi M.O., Church B., Thevamaran M., Thoma D.J., Rahman A. Design and validation of additively manufactured metallic cellular scaffold structures for bone tissue engineering. Materials, 15(9), 3310, 2022.
-[11] Li L.,Li J.,Zou Q.,Zuo Y.,Lin L.,Cai B.,Li Y. Lotus root and osteons‐inspired channel structural scaffold mediate cell biomineralization and vascularized bone tissue regeneration. Journal of Biomedical Materials Research Part B: Applied Biomaterials, 110(5), 1178-1191, 2022.
+[11] Li L., Li J., Zou Q., Zuo Y., Lin L., Cai B., Li Y. Lotus root and osteons‐inspired channel structural scaffold mediate cell biomineralization and vascularized bone tissue regeneration. Journal of Biomedical Materials Research Part B: Applied Biomaterials, 110(5):1178-1191, 2022.
-[12] Zhang J.,Chen X.,Sun Y.,Yang J.,Chen R., Xong Y.,Bai L. Design of a biomimetic graded TPMS scaffold with quantitatively adjustable pore size. Materials & Design, 218, 110665, 2022.
+[12] Zhang J., Chen X., Sun Y., Yang J., Chen R., Xong Y., Bai L. Design of a biomimetic graded TPMS scaffold with quantitatively adjustable pore size. Materials & Design, 218, 110665, 2022.
-[13] Chen X.,Gao C.Y.,Chu X.Y.,Zheng C.Y.,Luan Y.Y.,He X.,Zhang D.L. VEGF-loaded heparinised gelatine-hydroxyapatite-tricalcium phosphate scaffold accelerates bone regeneration via enhancing osteogenesis-angiogenesis coupling. Frontiers in Bioengineering and Biotechnology, 10, 915181, 2022.
+[13] Chen X., Gao C.Y., Chu X.Y., Zheng C.Y., Luan Y.Y., He X., Zhang D.L. VEGF-loaded heparinised gelatine-hydroxyapatite-tricalcium phosphate scaffold accelerates bone regeneration via enhancing osteogenesis-angiogenesis coupling. Frontiers in Bioengineering and Biotechnology, 10, 915181, 2022.
-[14] Zhang Y.,Wang P., JIN J.Y., Li L., He S.Y.,Zhou P.,Wen C. In silico and in vivo studies of the effect of surface curvature on the osteoconduction of porous scaffolds. Biotechnology and Bioengineering, 119(2), 591-604, 2022.
+[14] Zhang Y., Wang P., Jin J.Y., Li L., He S.Y., Zhou P., Wen C. In silico and in vivo studies of the effect of surface curvature on the osteoconduction of porous scaffolds. Biotechnology and Bioengineering, 119(2):591-604, 2022.
-[15] Nauman E.A.,Fong K.E.,Keaveny T.M. Dependence of intertrabecular permeability on flow direction and anatomic site. Annals of biomedical engineering, 27, 517-524, 1999.
+[15] Nauman E.A., Fong K.E., Keaveny T.M. Dependence of intertrabecular permeability on flow direction and anatomic site. Annals of Biomedical Engineering, 27:517-524, 1999.
-[16] Ali D.,Sen S. Finite element analysis of mechanical behavior, permeability and fluid induced wall shear stress of high porosity scaffolds with gyroid and lattice-based architectures. Journal of the mechanical behavior of biomedical materials, 75, 262-270, 2017.
+[16] Ali D., Sen S. Finite element analysis of mechanical behavior, permeability and fluid induced wall shear stress of high porosity scaffolds with gyroid and lattice-based architectures. Journal of the Mechanical Behavior of Biomedical Materials, 75:262-270, 2017.
-[17] Ma S.,Tang Q., Han X., Feng Q., Song J., Setchi R., Liu Y., Liu Y., Goulas A., Engstrom D.S., Tse Y.Y., Zhen N. Manufacturability, mechanical properties, mass-transport properties and biocompatibility of TPMS scaffolds fabricated by selective laser melting. Materials & Design, 195, 2020, 109034.
+[17] Ma S., Tang Q., Han X., Feng Q., Song J., Setchi R., Liu Y., Liu Y., Goulas A., Engstrom D.S., Tse Y.Y., Zhen N. Manufacturability, mechanical properties, mass-transport properties and biocompatibility of TPMS scaffolds fabricated by selective laser melting. Materials & Design, 195, 2020, 109034.
-[18] Pires T.,Santos J.,Ruben R.B.,Gouveia B.P.,Castro A.P.,Fernandes P. R. Numerical-experimental analysis of the permeability-porosity relationship in triply periodic minimal surfaces scaffolds. Journal of Biomechanics, 117, 110263, 2021.
+[18] Pires T., Santos J., Ruben R.B., Gouveia B.P., Castro A.P., Fernandes P.R. Numerical-experimental analysis of the permeability-porosity relationship in triply periodic minimal surfaces scaffolds. Journal of Biomechanics, 117, 110263, 2021.
-[19] Zhang Z.,Zhang H.,Li Y.,Duan M.,Qin S. A Modeling method of graded porous scaffold based on triply periodic minimal surfaces. Mathematical Problems in Engineering, 2022, 2022, 7129482.
+[19] Zhang Z., Zhang H., Li Y., Duan M., Qin S. A modeling method of graded porous scaffold based on triply periodic minimal surfaces. Mathematical Problems in Engineering, 2022:1-18, 7129482, 2022.
-[20] Günther F.,Pilz S.,Hirsch F.,Wagner M.,Kästner M.,Gebert A.,Zimmermann M. Shape optimization of additively manufactured lattices based on triply periodic minimal surfaces. Additive Manufacturing, 73, 103659, 2023.
+[20] Günther F., Pilz S., Hirsch F., Wagner M., Kästner M., Gebert A., Zimmermann M. Shape optimization of additively manufactured lattices based on triply periodic minimal surfaces. Additive Manufacturing, 73, 103659, 2023.
-[21] Li Y.,Guo S. Triply periodic minimal surface using a modified Allen–Cahn equation. Applied Mathematics and Computation, 295, 84-94, 2017.
+[21] Li Y.,Guo S. Triply periodic minimal surface using a modified Allen–Cahn equation. Applied Mathematics and Computation, 295:84-94, 2017.

@@ Line 285: / Line 285: @@
 ==4. Conclusion==
-In this study, the microstructure design of tibial segmental implant scaffolds was the focus of research. Finite element analysis was initially conducted on three scaffold structures. The results showed that the structural performance of the G-type scaffold was more stable, with a uniform distribution of Mises stress. Within the microscale curvature range of 0-1, the Mises stress decreased as the curvature increased. When the curvature was 1, the local Mises stress value was <math display="inline">0.07\times 10^8</math> N/m<sup>2</sup>. The G-type scaffold had the lowest flow velocity compared to the P and D-type scaffolds, but it exhibited better fluidity, making it suitable for inward bone tissue ingrowth. Based on these findings and considering the mechanical and biological requirements of tibial implant scaffolds, a composite scaffold structure, termed GDP, was constructed. Through finite element analysis and discussion, it was concluded that the GDP scaffold meets the design requirements of the tibial diaphysis.
+In this study, the microstructure design of tibial segmental implant scaffolds was the focus of research. Finite element analysis was initially conducted on three scaffold structures. The results showed that the structural performance of the G-type scaffold was more stable, with a uniform distribution of Mises stress. Within the microscale curvature range of 0-1, the Mises stress decreased as the curvature increased. When the curvature was 1, the local Mises stress value was <math display="inline">0.07\times 10^8</math> N/m<math display="inline">^2</math>. The G-type scaffold had the lowest flow velocity compared to the P and D-type scaffolds, but it exhibited better fluidity, making it suitable for inward bone tissue ingrowth. Based on these findings and considering the mechanical and biological requirements of tibial implant scaffolds, a composite scaffold structure, termed GDP, was constructed. Through finite element analysis and discussion, it was concluded that the GDP scaffold meets the design requirements of the tibial diaphysis.
 =Acknowledgments=

@@ Line 283: / Line 283: @@
 |}
-=4.Conclusion=
+==4. Conclusion==
 In this study, the microstructure design of tibial segmental implant scaffolds was the focus of research. Finite element analysis was initially conducted on three scaffold structures. The results showed that the structural performance of the G-type scaffold was more stable, with a uniform distribution of Mises stress. Within the microscale curvature range of 0-1, the Mises stress decreased as the curvature increased. When the curvature was 1, the local Mises stress value was 0.07×10^8 N/m^2. The G-type scaffold had the lowest flow velocity compared to the P and D-type scaffolds, but it exhibited better fluidity, making it suitable for inward bone tissue ingrowth. Based on these findings and considering the mechanical and biological requirements of tibial implant scaffolds, a composite scaffold structure, termed GDP, was constructed. Through finite element analysis and discussion, it was concluded that the GDP scaffold meets the design requirements of the tibial diaphysis.

← Older revision		Revision as of 11:10, 11 June 2024
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	\| style="background:#efefef;text-align:left;padding:10px;font-size: 85%;"\| '''Figure 9'''. Stress conduction process of the GDP scaffold		\| style="background:#efefef;text-align:left;padding:10px;font-size: 85%;"\| '''Figure 9'''. Stress conduction process of the GDP scaffold
	\|}		\|}
−
−

@@ Line 240: / Line 240: @@
-Figure 7 displays the finite element analysis results of the GDP scaffold. The GDP scaffold meets the preliminary design requirements for tibial scaffold. The proximal interface exhibits a tooth-like structure to provide initial mechanical bonding, while the distal interface offers a larger bone contact area, thus confirming the initial assumption.
+<div id='img-7'></div>
-[[Image:Draft_Zhang_149466663-picture- 5.svg|center|600px]]
+{| class="wikitable" style="margin: 0em auto 0.1em auto;border-collapse: collapse;width:auto;"
-</div>
+[[#img-8|Figure 8]] shows the fluid analysis results of the GDP pore scaffold. There is a greater difference in flow velocity between the center of the channels and the surrounding areas. In the <math display="inline"> Z </math>-direction, the fluid exhibits a "gourd" shape, and it is observed that the middle flow velocity of the GDP pore scaffold is faster. This is mainly because the design parameters of the GDP pore scaffold include the P structure, where the sides of the P structure are in a closed state, resulting in larger diameters of the central channels. Additionally, the curvature of the triply periodic minimal surface (TPMS) around the channels in the peripheral area of the flow is lower due to the presence of the P structure, and the connectivity of the P structure is not as strong as that of the G structure. Therefore, owing to the presence of the G structure elements, the scaffold exhibits higher flow velocity regardless of whether it is viewed from the <math display="inline"> Y </math>-axis or <math display="inline"> Z </math>-axis in the <math display="inline"> YZ </math> direction. Since the flow velocity on the outer side of the scaffold is lower, bone ingrowth is more likely to occur on the inner walls of the holes on the outer side. This further confirms that the GDP pore scaffold is more suitable for large segmental defects of the tibial diaphysis.
-Figure 8 shows the fluid analysis results of the GDP pore scaffold. There is a greater difference in flow velocity between the center of the channels and the surrounding areas. In the Z-direction, the fluid exhibits a "gourd" shape, and it is observed that the middle flow velocity of the GDP pore scaffold is faster. This is mainly because the design parameters of the GDP pore scaffold include the P structure, where the sides of the P structure are in a closed state, resulting in larger diameters of the central channels. Additionally, the curvature of the triply periodic minimal surface (TPMS) around the channels in the peripheral area of the flow is lower due to the presence of the P structure, and the connectivity of the P structure is not as strong as that of the G structure. Therefore, owing to the presence of the G structure elements, the scaffold exhibits higher flow velocity regardless of whether it is viewed from the Y-axis or Z-axis in the YZ direction. Since the flow velocity on the outer side of the scaffold is lower, bone ingrowth is more likely to occur on the inner walls of the holes on the outer side. This further confirms that the GDP pore scaffold is more suitable for large segmental defects of the tibial diaphysis.
+<div id='img-8'></div>
-[[Image:Draft_Zhang_149466663-picture- 6.svg|center|600px]]
+[[#img-9|Figure 9]] depicts the stress conduction process of the GDP scaffold. The stress variations of the bone and scaffold at the proximal end during the first, second, and third elastic stages are relatively close, indicating a good fit between the proximal interface bone and scaffold. After the third elastic deformation, the stress values within the bone decrease and gradually approach those of the distal scaffold. The Mises stress transfer process in the distal bone of the GDP scaffold exhibits a more stable range of variation. After the third elastic deformation, the Mises stress of the scaffold begins to stabilize, while the proximal bone continues to undergo 8 deformations after the third elastic deformation before reaching stability, due to its integration with the scaffold. Therefore, the stress conduction process of the GDP scaffold demonstrates optimal mechanical performance. The fitting mechanism at the proximal bone interface provides assurance for later mechanical stability, while the stable stress changes in the distal bone provide a platform for further bone ingrowth into the scaffold.
-Figure 8. CFD Finite Element Analysis Results of the GDP Scaffold
-</div>Figure 9 depicts the stress conduction process of the GDP scaffold. The stress variations of the bone and scaffold at the proximal end during the first, second, and third elastic stages are relatively close, indicating a good fit between the proximal interface bone and scaffold. After the third elastic deformation, the stress values within the bone decrease and gradually approach those of the distal scaffold. The Mises stress transfer process in the distal bone of the GDP scaffold exhibits a more stable range of variation. After the third elastic deformation, the Mises stress of the scaffold begins to stabilize, while the proximal bone continues to undergo 8 deformations after the third elastic deformation before reaching stability, due to its integration with the scaffold. Therefore, the stress conduction process of the GDP scaffold demonstrates optimal mechanical performance. The fitting mechanism at the proximal bone interface provides assurance for later mechanical stability, while the stable stress changes in the distal bone provide a platform for further bone ingrowth into the scaffold.[[Image:Draft_Zhang_149466663-picture- 7.svg|center|600px]]
+<div id='img-9'></div>
-As shown in Figure 10, the calculated elastic modulus and compressive strength of the support are 7.38Gpa and 326Mpa, and there is no excess deviation of the support during the compression process.[[Image:Draft_Zhang_149466663-picture- 8.svg|center|600px]]Figure 10. 3D printing of GDP bracket and its mechanical properties<span id="OLE_LINK2"></span>
 =4.Conclusion=