WO2016023403A1 - 一种低模量医用植入多孔支架结构 - Google Patents

一种低模量医用植入多孔支架结构 Download PDF

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WO2016023403A1
WO2016023403A1 PCT/CN2015/082066 CN2015082066W WO2016023403A1 WO 2016023403 A1 WO2016023403 A1 WO 2016023403A1 CN 2015082066 W CN2015082066 W CN 2015082066W WO 2016023403 A1 WO2016023403 A1 WO 2016023403A1
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modulus
bone
implant
central communication
quadrangular prism
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PCT/CN2015/082066
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English (en)
French (fr)
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林锦新
吴松全
林俊杰
卢衍锦
甘艺良
赵超前
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中国科学院福建物质结构研究所
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Priority to US15/502,540 priority Critical patent/US20170224491A1/en
Priority to EP15832600.9A priority patent/EP3181097B1/en
Publication of WO2016023403A1 publication Critical patent/WO2016023403A1/zh

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Definitions

  • the invention relates to a porous stent structure, in particular to a low modulus medical implanted porous stent structure, belonging to the field of medical implant materials.
  • implant replacement of diseased bone surgery is a common prevention of further deterioration of bone diseases, avoiding later fractures and even disability.
  • common implants mainly include autologous bone, allogeneic bone, bioceramics, organic high molecular polymers, degradable materials and metal materials. Due to the shortcomings of donor bone pain and limited source in autologous bone transplantation, allogeneic bone transplantation may have immune reaction and virus infection. Bioceramics have intrinsic brittleness, organic polymer has too low strength, and degradable materials are still in laboratory research.
  • Metal materials such as stainless steel, Co-Cr-based alloys, titanium-based alloys, etc., have been widely used in clinical practice because they provide good mechanical properties and have both corrosion resistance and biocompatibility.
  • the modulus of the metal material (stainless steel: about 200 GPa, Co-Cr-based alloy: about 230 GPa, titanium-based alloy: 50-110 GPa) is significantly higher than the bone tissue modulus (the modulus of the cortical bone is about 2 - 25GPa)
  • the modulus of the cortical bone is about 2 - 25GPa
  • the stress occlusion effect ie the stress is mainly transmitted through the metal implant.
  • the bone tissue around the metal implant will withstand a low load for a long time, which will lead to bone absorption and osteoporosis.
  • the implant is extremely loose and the bone tissue is prone to fracture when stressed.
  • the "stress occlusion effect” is an important reason for shortening the service time of metal implants, which invisibly increases the number of replacements of patient implants, and increases the pain and treatment time for patients.
  • the first problem is to solve the modulus problem of the implant itself, that is, the modulus of the implant is reduced to match the modulus of bone tissue.
  • the prior art is to prepare the material into a porous shape to reduce the apparent modulus of the material as a whole, but at the same time, the strength and plasticity of the material also decrease greatly with the increase of the porosity, so according to the existing
  • the porous materials prepared by the technology are difficult to achieve the ideal match of low modulus and high strength.
  • the porous structure has high permeability, and as an implant, it will be beneficial for bone cell adhesion, nutrient transfer and promotion of new bone tissue growth.
  • the pore size and distribution of these porous metal materials are in a random state, which is different from the bone tissue morphology in which the human body is oriented.
  • the randomly distributed isotropic pores not only do not support the growth of bone cells and bone tissues, but also In the stress distribution, the stress is large There is no distinction between the direction and the direction of the stress; in addition, these porous metal materials have complicated processing processes, often have internal defects, and may be doped with substances that are unfavorable to human health.
  • the present invention proposes a low modulus medical implanted porous stent structure which not only reduces the implant modulus, but also allows the implant to be implanted.
  • the modulus and strength are ideally matched, the configuration of the traditional metal implant is improved, the mechanical distribution is optimized, and the stress shielding effect is weakened.
  • the structure has a regular through-hole structure, which is beneficial to the growth of bone tissue and can increase bone. The interlocking of the tissue and the implant shortens the recovery time of the patient.
  • a low modulus medical implanted porous scaffold structure which is formed by sequentially stacking a plurality of basic units in a three-dimensional direction in a three-dimensional direction, each basic unit being formed by four or six side walls and having a central communication hole It is composed of a quadrangular prism or a hexagonal cylinder, and each side wall is composed of an "X-shaped" frame structure formed by the intersection of two ribs, and the center of the basic unit adjacently arranged along the axis of the quadrangular prism or the hexagonal cylinder
  • the communication holes are connected to each other.
  • the implant with the stent structure has a modulus matching with the bone tissue, which can reduce or avoid the "stress shielding effect" which is easy to occur during the treatment, and the strength of the material is sufficient to provide mechanics.
  • the scaffold structure has high porosity and high permeability, and the application on the implant will facilitate bone cell adhesion, nutrient transfer and promote the growth of new bone tissue;
  • the quadrangular prism or the hexagonal cylinder with the central communication hole is stacked in the vertical direction, and the central communication hole forms an oriented upper and lower hollow conduit, which is beneficial to osteoblasts, chondrocytes, fibroblasts and Capillaries proliferate in the direction of the duct to differentiate into bone, which is beneficial to bone healing.
  • the cross section of the rib of the prism may be a solid circle, a solid ellipse or a solid polygon to meet different requirements for the implant in different situations; or the cross section of the rib may also adopt a hollow circle Rings, hollow elliptical rings or hollow polygonal rings, when the boundary conditions are the same as the load and the required strength is the same, the hollow prisms are less material than the solid prisms, saving material while still saving Reduce the weight and further reduce the modulus.
  • the radius of the inscribed circle of the cross section of the central communicating hole is 150 ⁇ m-750 ⁇ m, which is favorable for the growth of osteoblasts, chondrocytes and bone tissue, and increases the mutual locking of the bone tissue and the scaffold material; the radius of the inscribed circle is too small For example, when it is less than 150 ⁇ m, osteoblasts, chondroblasts, and bone tissues are not easily grown, and the radius of the inscribed circle is too large. For example, when the diameter is larger than 750 ⁇ m, osteoblasts, chondrocytes, and bone tissues are not easily mounted.
  • the inner wall of the hollow duct formed by connecting the upper and lower communicating holes of the center is easy to fall off.
  • the change of the inscribed circle radius of the cross section of the central communication hole of the bracket structure is not isolated and is determined by the internal parameters of the structure, and the relationship is as follows:
  • r is the radius of the inscribed circle of the cross section of the central communicating hole
  • t is the thickness of the rib or the equivalent circular diameter of the cross section of the rib
  • a is the length of the bottom side of the quadrangular prism or the hexagonal cylinder.
  • the ratio of the length of the bottom edge of the side wall of the quadrangular prism or the hexagonal cylinder, the overall modulus of the stent increases as it increases.
  • the ratio of the equivalent circular diameter of the cross section of the rib to the length of the rib is 0.1-0.5; the quadrangular prism or the hexagonal prism
  • the ratio of the height of the body to the length of the bottom edge of the side wall of the quadrangular prism or the hexagonal cylinder is 1.0-2.5.
  • the cross-sectional area of the central communicating hole is preferably larger than that of the The cross-sectional area of the aperture of the "X-shaped" frame structure on the side wall.
  • the invention principle of a low modulus medical implanted porous stent structure is as follows:
  • the modulus is generally a structurally insensitive property, which is difficult to change greatly through the adjustment of composition, process or organization.
  • the overall apparent modulus can be further adjusted by the change of porosity.
  • such adjustments often result in a significant sacrifice in material strength, which would result in high porosity materials often failing to meet high strength requirements.
  • 3D printing technology the pore structure and size of the material can be precisely controlled. Compared with traditional methods, 3D printing technology actually increases the control factor for porous material design, which means that the modulus and strength of the material can pass the pore parameters. The design is controlled to achieve an ideal match between material modulus and strength.
  • the implant For the treatment of bearing bone defects, it is not only required that the implant has a modulus that can match the bone tissue to reduce or avoid the "stress shielding effect" which is easy to occur during the treatment, and the material is required to have sufficient strength to provide mechanical support. Therefore, porous implants generally have to meet the dual design requirements of low modulus and high strength.
  • This patent selects the "X-type" structure as the basic frame stacking three-dimensional porous support, and achieves sufficient mechanical support by the control of the support parameters to accurately control the modulus of the support.
  • bone tissue is a porous material with obvious orientation, wherein the porous skeleton plays a mechanical support role, and the oriented pores facilitate the transfer of nutrients and promote the metabolism of bone tissue.
  • the present invention performs a through-hole structure design on the implant stent, and the specific scheme is: using a "X-shaped" frame to form a hexagonal prism or a quadrangular prism through-hole unit, and then these units are in space.
  • a porous scaffold having regularly arranged hexagonal or quadrilateral through holes is obtained after periodic stacking to facilitate biological functions such as substance transport, bone tissue guidance or induction and vascularization after implant implantation.
  • the scaffold structure is mainly divided into a tensile-dominant structure (the ribs are mainly pulled and deformed under external load to resist external load and overall deformation) and the curved dominant structure ( The ribs are mainly in a bending deformation mode under external load to resist external load and overall deformation).
  • the different force modes of the inner ribs of the two types of structures cause great differences in specific stiffness and specific strength between the two types of structural materials.
  • the tensile dominant structure is strong and brittle, and the curved dominant structure is soft and tough. According to the performance requirements of bone implant materials, the above two types of structures can not fully meet the requirements.
  • the present invention chooses to utilize an "X-shaped" frame structure that can increase the deformability of the scaffold material as much as possible while not reducing the strength of the scaffold structural material.
  • a cylindrical rigid rod with the same relative density (43.4%) is selected as the tensile dominant structure model, diamond shape.
  • the dodecahedron is the main guide structure model of bending.
  • the modulus and strength of the "X-shaped" frame structure are between the tensile-oriented structure and the curved-oriented structure.
  • Inclusion material (Ta: 183GPa, Zr: 99GPa, medical 316 stainless steel: 193GPa, hydroxyapatite: 165GPa, Co-Cr-Mo: 248GPa, Co-Cr-W: 232GPa, Co-based: 194GPa, Mg: 44GPa)
  • the "X-shaped" frame structure can increase the deformation ability of the stent material as much as possible while not reducing the strength of the stent structural material.
  • the final porous support structure is selected by the "X-shaped" frame as a side wall to form a hexagonal prism or a quadrangular prism structural unit, and then the structural unit is in space. Make a periodic translation.
  • the material having the structure has high porosity, large specific surface area, excellent impact energy absorption characteristics, and sufficient strength to provide mechanical support in the case of high strength requirements.
  • Oriented pores are beneficial to the transfer of nutrients and promote the metabolism of bone tissue, and are beneficial to biological functions such as substance transport, bone tissue guidance or induction and vascularization after implant implantation.
  • the porous size or structure and the treatment of the stent surface can be adjusted according to different human bones and biological environment.
  • Figure 1 is a plan view of a basic unit of a hexagonal prism of the present invention
  • Figure 2 is a side elevational view of the basic unit of the hexagonal prism of the present invention.
  • Figure 3 is a plan view of the basic unit of the quadrangular prism of the present invention.
  • Figure 4 is a side elevational view of the basic unit of the quadrangular prism of the present invention.
  • Figure 5 is a flow chart of the finite element analysis of the present invention.
  • Figure 6 is a bar graph of the relative modulus and yield strength of the cylindrical vertical rod structure, "X-shaped" hexagonal prism, rhombohedral dodecahedron structure of the present invention.
  • Figure 7 is a finite element meshing of the basic unit of the hexagonal cylinder of the present invention.
  • Figure 8 is a finite element meshing of the basic unit of a quadrangular prism of the present invention.
  • Figure 9 is a finite element simulation analysis process diagram of the basic unit of the hexagonal prism of the present invention.
  • Figure 10 is a finite element simulation analysis process diagram of the basic unit of the quadrangular prism of the present invention.
  • Figure 11 is a view showing the state of the basic unit modulus of the hexagonal prism of the present invention as a function of structural parameters
  • Figure 12 is a view showing the state of the basic unit modulus of the quadrangular prism of the present invention as a function of structural parameters
  • r is the inscribed circle radius of the cross section of the central communication hole
  • t is the thickness of the ribs constituting the "X-shaped" frame or its cross-sectional equivalent circular diameter
  • l is the length of the ribs that make up the "X-shaped" frame
  • c is the height of a quadrangular prism or a hexagonal cylinder
  • a is the base side length of a quadrangular prism or a hexagonal cylinder
  • ⁇ 1 is the ratio of the height c of the quadrangular prism or the hexagonal cylinder to the length a of the base side.
  • a low modulus medical implanted porous scaffold structure which is formed by sequentially stacking a plurality of basic units in a three-dimensional direction in a three-dimensional direction, each basic unit being formed by four or six side walls and having a central communication hole It is composed of a quadrangular prism or a hexagonal cylinder, and each side wall is composed of an "X-shaped" frame structure formed by the intersection of two ribs, and the center of the basic unit adjacently arranged along the axis of the quadrangular prism or the hexagonal cylinder
  • the communication holes are connected to each other.
  • the cross section of the rib is a solid circle, a solid ellipse, a solid polygon, a hollow ring, a hollow elliptical ring or a hollow polygonal ring.
  • the inscribed circle radius r of the cross section of the central communication hole is 150 ⁇ m to 750 ⁇ m.
  • the ratio of the length of the bottom edge is 1.0-2.5.
  • the cross-sectional area of the central communication aperture is greater than the cross-sectional area of the aperture of the "X-shaped" frame structure on the sidewall.
  • the overall modulus of the stent structure is calculated using the finite element method.
  • the mapping software uses the mapping software to establish the bracket geometry model (such as "X-type” quadrangular prism or "X-type” hexagonal prism, etc.), and set the support structure parameters (r, ⁇ 1 and ⁇ 2 ); then import the finite element analysis software (such as Ansys, Comsol or Abaqus, etc., define material parameters (E and ⁇ , etc.), set boundary conditions, loading conditions and mesh; perform finite element calculation and analysis; according to the modulus below 30GPa, if If the overall modulus of the selected bracket structure meets the requirements, then the selected bracket structure scheme will be established. Otherwise, the structural parameters of the bracket (r, ⁇ 1 and ⁇ 2 ) will be reset and calculated and judged according to the above steps, and finally the low modulus is satisfied.
  • Conditional bracket structure material and parameter range such as "X-type” quadrangular prism or "X-type” hexagonal prism, etc.
  • the relative modulus of the scaffold material and the relative density of the stent can be calculated by the finite element method. Relationship. The results show that the range of ⁇ 1 is chosen to be 1.0-2.5, the range of ⁇ 2 is chosen to be 0.10-0.50, and the radius of the inscribed circle of the through hole is selected in the range of 150 ⁇ m-750 ⁇ m. The relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.
  • the relative modulus of the scaffold material and the relative density of the stent are calculated by the finite element method. Relationship. The results show that the range of ⁇ 1 is chosen to be 1.0-2.5, the range of ⁇ 2 is chosen to be 0.1-0.35, and the radius of the inscribed circle of the via is selected in the range of 150 ⁇ m-750 ⁇ m. The relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.
  • the results show that the range of ⁇ 1 is chosen to be 1-2.5, the range of ⁇ 2 is chosen to be 0.1-0.5, and the radius of the inscribed circle of the through hole is selected in the range of 150 ⁇ m-750 ⁇ m.
  • the relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.
  • the results show that the range of ⁇ 1 is chosen to be 1.2-2.5, the range of ⁇ 2 is chosen to be 0.15-0.50, and the radius of the inscribed circle of the through hole is selected in the range of 150 ⁇ m-750 ⁇ m.
  • the relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.
  • the finite element method is used to calculate the relative modulus and support of the stent material.
  • the relationship between relative density show that the range of ⁇ 1 is chosen to be 1.0-1.5, the range of ⁇ 2 is chosen to be 0.10-0.25, and the radius of the inscribed circle of the through hole is selected in the range of 150 ⁇ m-750 ⁇ m.
  • the relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.
  • the finite element method is used to calculate the relative modulus and support of the stent material.
  • the relationship between relative density show that the range of ⁇ 1 is chosen to be 1.0-2.3, the range of ⁇ 2 is chosen to be 0.10-0.45, and the radius of the inscribed circle of the through hole is selected in the range of 150 ⁇ m-750 ⁇ m.
  • the relative modulus of the scaffold material will be lower than that. 30GPa, which meets the range of human cortical bone modulus.

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Abstract

一种用于植入骨组织的低模量医用植入多孔支架结构，由多个基本单元在三维空间沿三维方向依次叠加而成，每个基本单元是由四个或六个侧壁所包围形成的具有中心连通孔的四棱柱体或六棱柱体构成，每个侧壁均是由两根棱条交叉形成的"X型"框架结构构成，沿四棱柱体或六棱柱体轴线方向相邻排列的基本单元的中心连通孔相互连通。该结构不仅降低了植入体模量，使植入体模量与强度实现理想匹配，改进了传统金属植入体的构型，使其力学分布优化，应力遮挡效应减弱。而且该结构具有规则通孔结构，有利于骨组织长入，并能增加骨组织与植入体的相互锁固，缩短患者的康复时间。

Description

一种低模量医用植入多孔支架结构 技术领域
本发明涉及一种多孔支架结构，特别涉及一种低模量医用植入多孔支架结构，属于医用植入材料领域。
背景技术
在骨折或骨坏死等骨质疾病治疗和修复领域，尤其在对承力骨的治疗和修复方面，植入物替换病死骨手术是常见的预防骨质疾病进一步恶化、避免后期骨折甚至致残的有效方法。目前，常见的植入物主要包括自体骨、异体骨、生物陶瓷、有机高分子聚合物、可降解材料和金属材料等。由于自体骨移植存在供区疼痛、来源有限的缺点，异体骨移植存在免疫反应和病毒传染的可能，生物陶瓷存在本征脆性，有机高分子聚合物强度过低，可降解材料尚处于实验室研究阶段等问题，这些材料在承力骨的治疗和修复方面均未能得到广泛应用。而金属材料，如不锈钢、Co-Cr基合金、钛基合金等，由于可以提供良好的力学性能，并且兼具耐蚀性和生物相容性等，因此在临床一直被广泛应用。
但是，由于金属材料的模量(不锈钢：约200GPa，Co-Cr基合金：约230GPa，钛基合金：50-110GPa)明显要高于骨组织模量(皮质骨的模量范围约为2-25GPa)，这将引起所谓“应力遮挡效应”，即应力主要通过金属植入体传递。此时，金属植入体周围骨组织长期将承受低负荷状态，这将导致骨质吸收而造成骨质疏松，这种情况下植入体极易松动，骨组织受力时也容易发生骨折。目前，“应力遮挡效应”是缩短金属植入体服役时间的重要原因，无形地增加了患者植入体的置换次数，同时给患者增加了病痛和治疗时间。
针对植入体在治疗骨质疾病过程中出现的“应力遮挡”问题，首先要解决植入体本身的模量问题，即要求植入体模量降低至能与骨组织模量相匹配的程度。现有技术是将材料制备成多孔状来降低材料整体的表观模量，但这么做的同时，材料的强度、塑性等也会随着孔隙率的增加而发生大幅度下降，因此按照现有技术所制备的多孔材料很难达到低模量与高强度的理想匹配。另外，经研究发现，多孔结构具有高渗透性，作为植入物将有利于骨细胞黏附，营养物质传递和促进新生骨组织长入等。但是，现有技术中这些金属多孔材料孔径尺寸及分布呈随机状态，区别于人体取向生长的骨组织形态；同时，随机分布的各向同性的孔不仅不支持骨细胞、骨组织长入，而且在应力分布上，应力大的 方向和应力小的方向没有区分；另外，这些多孔金属材料加工工艺复杂，常存在内部缺陷，并且可能掺杂对人体健康不利的物质等。
发明内容
为了克服上述现有技术中的结构在骨缺损或坏死治疗中存在的问题，本发明提出一种低模量医用植入多孔支架结构，该结构不仅降低了植入体模量，使植入体模量与强度实现理想匹配，改进了传统金属植入体的构型，使其力学分布优化，应力遮挡效应减弱；而且该结构具有规则通孔结构，有利于骨组织长入，并能增加骨组织与植入体的相互锁固，缩短患者的康复时间。
本发明的技术方案如下：
一种低模量医用植入多孔支架结构，它由多个基本单元在三维空间沿三维方向依次叠加而成，每个基本单元是由四个或六个侧壁所包围形成的具有中心连通孔的四棱柱体或六棱柱体构成，每个侧壁均是由两根棱条交叉形成的“X型”框架结构构成，沿四棱柱体或六棱柱体轴线方向相邻排列的基本单元的中心连通孔相互连通。
首先，对于承力骨缺损治疗，采用该支架结构的植入体具有与骨组织匹配的模量，能降低或避免发生治疗过程中易出现的“应力遮挡效应”，同时材料的强度足够提供力学支承；
其次，该支架结构的孔隙率高，具有高渗透性，应用在植入物上将有利于骨细胞黏附，营养物质传递和促进新生骨组织长入；
第三，具有中心连通孔的四棱柱体或六棱柱体在垂直方向上堆积，中心连通孔形成了具有取向性的上下连通的中空导管，有利于成骨细胞、成软骨细胞、成纤维细胞及毛细血管沿导管方向增殖向分化成骨方向发展，对骨愈合有利。
所述棱柱所述棱条的横截面可以采用实心圆形、实心椭圆形或者实心多边形，以满足不同情况下对于植入物的不同需求；或者，所述棱条的横截面也可以采用中空圆环、中空椭圆环或者中空多边形环，在边界条件和受载一样的情况下且所需的强度一样大时，空心棱柱与实心棱柱相比较，空心棱柱所用材料较少，节省材料的同时还能减轻自重，并进一步降低模量。
所述中心连通孔的横截面的内接圆半径为150μm-750μm，有利于成骨细胞、成软骨细胞及骨组织长入，增加骨组织与支架材料的相互锁固；内接圆半径过小，例如小于150μm时，成骨细胞、成软骨细胞及骨组织不容易长入，内接圆半径过大，例如大于750μm时，成骨细胞、成软骨细胞及骨组织不易挂载 在中心连通孔上下连通形成的中空导管内壁上，容易脱落。另外，支架结构中心连通孔的横截面的内接圆半径的变化不是孤立的，是由结构内部参数决定的，其关系如下：
对于六棱柱体有：
r＝0.866a-t
对于四棱柱有：
r＝0.5a-t
其中r为中心连通孔的横截面的内接圆半径，t为棱条厚度或棱条横截面的等效圆直径，a为四棱柱体或六棱柱体的底边边长。
选择不同材料(Ta:183GPa、Zr:99GPa、α-Ti:110GPa、医用316不锈钢:193GPa、羟基磷灰石:165GPa、Co-Cr-Mo:248GPa、Co-Cr-W:232GPa、Co-基:194GPa、Mg:44GPa)，按上述方案模拟支架整体模量与支架材料本征模量及结构参数关系发现：结构一定，不同材料支架的整体模量与支架材料本征模量成正比；材料一定，改变结构内部棱条横截面的等效圆直径与所述棱条的长度的比值，支架的整体模量随其增加而增加；材料一定，改变四棱柱体或六棱柱体的高度与所述四棱柱体或六棱柱体的侧壁底边边长的比值，支架的整体模量随其增加而增加。为了使不同材料支架整体模量处于2-30GPa的范围要求，所述棱条的横截面的等效圆直径与所述棱条的长度的比值为0.1-0.5；所述四棱柱体或六棱柱体的高度与所述四棱柱体或六棱柱体的侧壁底边边长的比值为1.0-2.5。
由于植入体植入后在垂直方向上的骨组织引导或诱导、血管组织的生成以及营养物质输运将大于水平方向上的需要，因此，所述中心连通孔的横截面面积最好大于所述侧壁上的“X型”框架结构的孔隙的横截面面积。
本发明所提供的一种低模量医用植入多孔支架结构的发明原理如下：
(一)模量的控制：
对于实体材料，模量一般属于结构不敏感属性，很难再通过成分、工艺或组织的调整进行大幅度改变；而对于多孔材料，其整体的表观模量可以通过孔隙率的变化进一步调整，但这种调整常常会大幅度地牺牲材料强度，这将导致高孔隙率材料往往无法满足高强度要求的场合。伴随3D打印技术的出现，材料的孔隙结构及尺寸可以得到精确控制。相对于传统方法，3D打印技术实际为多孔材料设计增加了控制因素，这就意味着材料的模量与强度可以通过孔隙参数 的设计进行控制，实现材料模量与强度的理想匹配。
对于承力骨缺损治疗，不但要求植入体具有能与骨组织匹配的模量以降低或避免发生治疗过程中易出现的“应力遮挡效应”，而且要求材料具有足够的强度以提供力学支承，因此多孔植入体一般同时要满足低模量和高强度的双重设计要求。本专利选择“X型”结构作为基本框架堆垛三维多孔支架，通过支架参数的控制实现足够力学支承的同时对支架的模量进行精确控制。
(二)通孔的设计：
通过骨切片实验形态观察已经发现，骨组织就是取向性明显的多孔材料，其中多孔骨架起到力学支承作用，而取向性孔隙有利于营养物质的传递和促进骨组织的新陈代谢。模仿骨组织孔隙状态特征，本发明对植入体支架进行了通孔结构设计，具体方案为：利用“X型”框架围成六棱柱体或四棱柱体通孔单元，然后将这些单元在空间进行周期性堆垛后得到具有规则排列的六边形或四边形通孔的多孔支架，以利于植入体植入后物质输运、骨组织引导或诱导和血管化等生物功能作用。
(三)结构的选择：
根据多孔支架材料内部棱条受力特征的不同，支架结构主要分为拉伸主导型结构(棱条在外载下主要呈拉、压变形模式以抵抗外载和整体变形)和弯曲主导型结构(棱条在外载下主要呈弯曲变形模式以抵抗外载和整体变形)。两类结构内部棱条的受力模式不同造成两类结构材料在比刚度和比强度方面有着极大的差异，拉伸主导型结构强而脆，弯曲主导型结构柔而韧。根据骨植入材料的性能要求，以上两类结构实际都不能完全满足需求。介于两类结构的综合，本发明选择利用“X型”框架结构，该结构可以在不过分降低支架结构材料强度的同时尽可能地增加支架材料的变形能力。
当植入体的材料选取α-Ti(E＝110GPa，ν＝0.33)时，如图6所示：选择相对密度相同(43.4％)的圆柱形坚直杆作为拉伸主导型结构模型、菱形十二面体作为弯曲主要导型结构模型，与“X型”六棱柱比较可知“X型”框架结构的模量和强度均处于拉伸主导型结构和弯曲主导型结构之间，通过选择不同植入体的材料(Ta:183GPa、Zr:99GPa、医用316不锈钢:193GPa、羟基磷灰石:165GPa、Co-Cr-Mo:248GPa、Co-Cr-W:232GPa、Co-基:194GPa、Mg:44GPa)进行实验可得：“X型”框架结构可以在不过分降低支架结构材料强度的同时尽可能地增加支架材料的变形能力。
另外，鉴于“模量的控制”和“通孔的设计”要求，最终多孔支架结构选择由“X型”框架作为侧壁围成六棱柱体或四棱柱体结构单元，再由结构单元在空间作周期平移构成。
本发明所提供的一种低模量医用植入多孔支架结构有如下优点：
1)具有该结构的材料不仅孔隙率高，比表面积大，具有优异的冲击能量吸收特性，而且在具有较高强度要求的场合，具有足够的强度以提供力学支承。
2)具有取向性的孔隙，有利于营养物质的传递和促进骨组织新陈代谢的作用，有利于植入体植入后物质输运、骨组织引导或诱导和血管化等生物功能作用。
3)可以根据不同人体骨骼以及生物环境来调整多孔尺寸或结构以及支架表面的处理。
4)实现了植入体模量与强度的理想匹配以降低甚至消除由于实体金属与骨组织模量差别所带来的“应力遮挡效应”，增加植入体的服役寿命，减轻患者的痛苦。
5)规则通孔结构有利于骨组织长入，增加骨组织与支架材料的相互锁固，减少患者的康复时间。
附图说明
图1是本发明的六棱柱体基本单元的俯视图；
图2是本发明的六棱柱体基本单元的侧视图；
图3是本发明的四棱柱体基本单元的俯视图；
图4是本发明的四棱柱体基本单元的侧视图；
图5是本发明的有限元分析流程图；
图6是本发明的圆柱形竖直杆结构、“X型”六棱柱、菱形十二面体结构的相对模量和屈服强度的柱状图；
图7是本发明的六棱柱体基本单元的有限元网格划分；
图8是本发明的四棱柱体基本单元的有限元网格划分；
图9是本发明的六棱柱体基本单元的有限元模拟分析过程图；
图10是本发明的四棱柱体基本单元的有限元模拟分析过程图；
图11是本发明的六棱柱体基本单元模量随结构参数变化的状态图；
图12是本发明的四棱柱体基本单元模量随结构参数变化的状态图；
图中附图标记表示为：
r是中心连通孔的横截面的内接圆半径；
t是组成“X型”框架的棱条的厚度或其横截面等效圆直径；
l是组成“X型”框架的棱条的长度；
c是四棱柱体或六棱柱体的高；
a是四棱柱体或六棱柱体的底边边长；
η1是四棱柱体或六棱柱体的高c与底边边长a的比值。
具体实施方式
下面结合具体实施方式和具体实施例来对本发明进行详细的说明。
具体实施方式如下：
一种低模量医用植入多孔支架结构，它由多个基本单元在三维空间沿三维方向依次叠加而成，每个基本单元是由四个或六个侧壁所包围形成的具有中心连通孔的四棱柱体或六棱柱体构成，每个侧壁均是由两根棱条交叉形成的“X型”框架结构构成，沿四棱柱体或六棱柱体轴线方向相邻排列的基本单元的中心连通孔相互连通。
所述棱条的横截面是实心圆形、实心椭圆形、实心多边形、中空圆环、中空椭圆环或者中空多边形环。
为了满足支架材料的生物功能性要求，所述中心连通孔的横截面的内接圆半径r为150μm-750μm。
所述棱条的横截面的等效圆直径与所述棱条的长度的比值为0.1-0.5；所述四棱柱体或六棱柱体的高度与所述四棱柱体或六棱柱体的侧壁底边边长的比值为1.0-2.5。
对于六棱柱体基本单元，其整体形状的结构特征可以由六棱柱体的高c与底边边长a的比值η1确定(η1＝c/a)；六棱柱体基本单元的相对密度可以由组成“X型”框架的棱条的厚度t(或其横截面等效圆直径)与长度l比值η2确定(η2＝t/l)。
对于四棱柱体基本单元，其整体形状的结构特征可以由四棱柱体的高c与底边边长a的比值η1确定(η1＝c/a)；四棱柱体基本单元的相对密度可以由组成“X型”框架的棱条的厚度t(或其横截面等效圆直径)与长度l比值η2确定(η2＝t/l)。
所述中心连通孔的横截面面积大于所述侧壁上的“X型”框架结构的孔隙的横截面面积。
支架结构整体模量利用有限元方法进行计算。首先利用作图软件建立支架几何模型(如“X型”四棱柱或“X型”六棱柱等)，同时设定支架结构参数(r，η1和η2)；然后导入有限元分析软件(如Ansys、Comsol或Abaqus等)，定义材料参数(E和ν等)，设定边界条件、加载条件和划分网格；再进行有限元计算、分析；按着模量低于30GPa的要求，如果所选支架结构整体模量满足要求，那么将确立所选支架结构方案，否则重新设定支架结构参数(r，η1和η2)按上述步骤再进行计算和判断，最终得到满足低模量条件的支架结构材料及参数范围。
α-Ti实施例组
实施例1
对于六棱柱体基本单元，当植入体的材料选取α-Ti(E＝110GPa，ν＝0.33)时，如图3所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1.0-2.5，η2取值范围选择在0.10-0.50，和通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
实施例2
对于四棱柱体基本单元，当植入体的材料选取α-Ti(E＝110GPa，ν＝0.33)时，如图4所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1.0-2.5，η2取值范围选择在0.1-0.35，和通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
Mg实施例组
实施例3
对于六棱柱体基本单元，当植入体的材料选取Mg(E＝44GPa，ν＝0.26)时，如图3所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1-2.5，η2取值范围选择在0.1-0.5，和 通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
实施例4
对于四棱柱体基本单元，当植入体的材料选取Mg(E＝44GPa，ν＝0.26)时，如图4所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1.2-2.5，η2取值范围选择在0.15-0.50，和通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
Co-Cr-Mo实施例组
实施例5
对于六棱柱体基本单元，当植入体的材料选取Co-Cr-Mo(E＝248GPa，ν＝0.30)时，如图3所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1.0-1.5，η2取值范围选择在0.10-0.25，和通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
实施例6
对于四棱柱体基本单元，当植入体的材料选取Co-Cr-Mo(E＝248GPa，ν＝0.30)时，如图4所示：利用有限元方法计算可得支架材料相对模量与支架相对密度的关系。结果表明，η1取值范围选择在1.0-2.3，η2取值范围选择在0.10-0.45，和通孔内接圆半径r选择在150μm-750μm范围时，支架材料的相对模量将低于30GPa，满足人体皮质骨模量范围。
上述具体实施方式只是对本发明的技术方案进行详细解释，本发明并不只仅仅局限于上述实施例，凡是依据本发明原理的任何改进或替换，均应在本发明的保护范围之内。

Claims (4)

  1. 一种低模量医用植入多孔支架结构，其特征在于：它由多个基本单元在三维空间沿三维方向依次叠加而成，每个基本单元是由四个或六个侧壁所包围形成的具有中心连通孔的四棱柱体或六棱柱体构成，每个侧壁均是由两根棱条交叉形成的“X型”框架结构构成，沿四棱柱体或六棱柱体轴线方向相邻排列的基本单元的中心连通孔相互连通。
  2. 根据权利要求1所述的低模量医用植入多孔支架结构，其特征在于：所述中心连通孔的横截面的内接圆半径为150μm-750μm。
  3. 根据权利要求2所述的低模量医用植入多孔支架结构，其特征在于：所述棱条的横截面的等效圆直径与所述棱条的长度的比值为0.1-0.5；所述四棱柱体或六棱柱体的高度与所述四棱柱体或六棱柱体的侧壁底边边长的比值为1.0-2.5。
  4. 根据权利要求3所述的低模量医用植入多孔支架结构，其特征在于：所述中心连通孔的横截面面积大于所述侧壁上的“X型”框架结构的孔隙的横截面面积。
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Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104207867B (zh) * 2014-08-13 2017-02-22 中国科学院福建物质结构研究所 一种低模量医用植入多孔支架结构
CN107898495B (zh) * 2017-07-24 2021-03-12 北京航空航天大学 具有拉胀结构的骨钉
CN110037832B (zh) * 2019-04-16 2021-06-01 华南协同创新研究院 一种骨修复用复合单元结构多孔支架及加工方法
CN109984871B (zh) * 2019-04-16 2021-06-01 华南协同创新研究院 一种骨损伤修复用的多孔植入体结构及加工方法
CN110737979B (zh) * 2019-10-12 2022-08-19 中国人民解放军国防科技大学 具有孔隙的仿生交错复合结构
CN111494060B (zh) * 2020-04-28 2022-10-04 河北科技大学 一种构建骨植入物的方法及骨植入物结构单元

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040010315A1 (en) * 2002-03-29 2004-01-15 Song John K. Self-expanding intervertebral device
US20110014081A1 (en) * 2004-12-30 2011-01-20 Howmedica Osteonics Corp. Laser-produced porous structure
CN102548509A (zh) * 2009-08-19 2012-07-04 史密夫和内修有限公司 多孔植入物结构
US20130123935A1 (en) * 2011-11-03 2013-05-16 Jessee Hunt Method of length preservation during bone repair
US20130178947A1 (en) * 2012-01-09 2013-07-11 Zimmer, Inc. Porous metal implants with bone cement
CN103445883A (zh) * 2012-06-04 2013-12-18 合硕生技股份有限公司 镂空网架医疗用植入物
CN104207867A (zh) * 2014-08-13 2014-12-17 中国科学院福建物质结构研究所 一种低模量医用植入多孔支架结构
CN204033546U (zh) * 2014-08-13 2014-12-24 中国科学院福建物质结构研究所 一种低模量医用植入多孔支架结构

Family Cites Families (49)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2886855A (en) * 1954-08-30 1959-05-19 Petter Bruno Josef Buildings with multangular rooms, the ground plan of which is combined from hexagonal elements
US3152366A (en) * 1960-12-27 1964-10-13 Thomas L Mccrory Prefabricated building unit
US3974600A (en) * 1971-08-30 1976-08-17 Synestructics, Inc. Minimum inventory maximum diversity building system
US4059932A (en) * 1976-06-21 1977-11-29 Ronald Dale Resch Self-supporting structural unit having a three-dimensional surface
US4186533A (en) * 1977-05-16 1980-02-05 Jensen David C Modular building structure
US4095386A (en) * 1977-08-19 1978-06-20 Joseph Daniel Johnson Prismatic interlocking structural module
US4335558A (en) * 1980-08-22 1982-06-22 Domain Building Systems Corporation Prefabricated polygonal building
US4480414A (en) * 1982-09-24 1984-11-06 Tschudy Donald B Building construction
US4546583A (en) * 1983-12-05 1985-10-15 Gary Hussar Modular building construction system
US4872625A (en) * 1984-07-30 1989-10-10 Filley Charles C Universal module assembly for space structures
US5282561A (en) * 1987-07-13 1994-02-01 Herman Mihalich Portable beverage dispenser
US4903452A (en) * 1987-11-24 1990-02-27 Huang Yen T Modular space framed earthquake resistant structure
US5609635A (en) * 1988-06-28 1997-03-11 Michelson; Gary K. Lordotic interbody spinal fusion implants
US5147402A (en) * 1990-12-05 1992-09-15 Sulzer Brothers Limited Implant for ingrowth of osseous tissue
US5426900A (en) * 1992-03-11 1995-06-27 Springer; Robert H. Multi-purpose hexagonal building module
US5282861A (en) * 1992-03-11 1994-02-01 Ultramet Open cell tantalum structures for cancellous bone implants and cell and tissue receptors
DE4208247C1 (de) * 1992-03-14 1993-10-14 Eska Medical Gmbh & Co Implantat als Knochenersatz
US5560151A (en) * 1995-03-06 1996-10-01 Polyceramics, Inc. Building blocks forming hexagonal and pentagonal building units for modular structures
US5609367A (en) * 1995-12-01 1997-03-11 Alliedsignal Inc. Adjustable three-point restraint seat belt system for children and adults
US5897556A (en) * 1997-06-02 1999-04-27 Sdgi Holdings, Inc. Device for supporting weak bony structures
US6585770B1 (en) * 1997-06-02 2003-07-01 Sdgi Holdings, Inc. Devices for supporting bony structures
US6206924B1 (en) * 1999-10-20 2001-03-27 Interpore Cross Internat Three-dimensional geometric bio-compatible porous engineered structure for use as a bone mass replacement or fusion augmentation device
US6931812B1 (en) * 2000-12-22 2005-08-23 Stephen Leon Lipscomb Web structure and method for making the same
US20030220696A1 (en) * 2002-05-23 2003-11-27 Levine David Jerome Implantable porous metal
US6712852B1 (en) * 2002-09-30 2004-03-30 Depuy Spine, Inc. Laminoplasty cage
US7537664B2 (en) * 2002-11-08 2009-05-26 Howmedica Osteonics Corp. Laser-produced porous surface
CA2764495C (en) * 2003-06-25 2013-09-17 Ronald W. Lindsey Tissue integration design for seamless implant fixation
JP2006528515A (ja) * 2003-07-24 2006-12-21 テコメット・インコーポレーテッド 海綿状の構造体
US8062365B2 (en) * 2003-08-04 2011-11-22 Warsaw Orthopedic, Inc. Bone supporting devices with bio-absorbable end members
US20060085009A1 (en) * 2004-08-09 2006-04-20 Csaba Truckai Implants and methods for treating bone
US8728387B2 (en) * 2005-12-06 2014-05-20 Howmedica Osteonics Corp. Laser-produced porous surface
US8128626B2 (en) * 2007-04-24 2012-03-06 Flexfix, Llc System and method for delivery conformation and removal of intramedullary bone fixation devices
WO2009011029A1 (ja) * 2007-07-17 2009-01-22 Ichiro Takeshima 建築構造物
EP2214641A1 (en) * 2007-10-08 2010-08-11 Sureshan Sivanthan A scalable matrix for the in vivo cultivation of bone and cartilage
CN201200499Y (zh) * 2008-05-19 2009-03-04 曼德卡姆有限公司 网格状的金属骨科植入体
US8430930B2 (en) * 2008-12-18 2013-04-30 4-Web, Inc. Truss implant
CN102348641B (zh) * 2009-03-12 2014-03-19 三井化学株式会社 新型金属氧化物多孔质体、其制造方法及用途
DK2253291T3 (en) * 2009-05-19 2016-06-13 Nat Univ Ireland Galway The bone implants with a structure overfladeforankrende
US20100310623A1 (en) * 2009-06-05 2010-12-09 Laurencin Cato T Synergetic functionalized spiral-in-tubular bone scaffolds
US20110313532A1 (en) * 2010-06-18 2011-12-22 Jessee Hunt Bone implant interface system and method
US20130030529A1 (en) * 2011-07-29 2013-01-31 Jessee Hunt Implant interface system and method
CN103842562B (zh) * 2011-08-02 2017-05-24 意大利理工学院 八足形纳米晶体的有序超晶格结构、它们的制备方法及其应用
EP2811942B1 (en) * 2012-02-08 2018-11-07 4-web, Inc. Prosthetic implant for ball and socket joints
US9155819B2 (en) * 2012-02-09 2015-10-13 Mx Orthopedics, Corp. Dynamic porous coating for orthopedic implant
CN102764888B (zh) * 2012-06-07 2014-07-16 中国人民解放军第四军医大学 一种复合多孔β－TCP的钛合金人距骨支撑棒及其制备方法
WO2014052477A1 (en) * 2012-09-25 2014-04-03 4Web, Inc. Programmable implants and methods of using programmable implants to repair bone structures
US20140288650A1 (en) * 2013-03-15 2014-09-25 4Web, Inc. Motion preservation implant and methods
EP2967873A4 (en) * 2013-03-15 2017-03-01 4-web, Inc. Traumatic bone fracture repair systems and methods
CN103908357B (zh) * 2014-04-09 2017-01-11 飞而康快速制造科技有限责任公司 一种人造骨骼结构

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040010315A1 (en) * 2002-03-29 2004-01-15 Song John K. Self-expanding intervertebral device
US20110014081A1 (en) * 2004-12-30 2011-01-20 Howmedica Osteonics Corp. Laser-produced porous structure
CN102548509A (zh) * 2009-08-19 2012-07-04 史密夫和内修有限公司 多孔植入物结构
US20130123935A1 (en) * 2011-11-03 2013-05-16 Jessee Hunt Method of length preservation during bone repair
US20130178947A1 (en) * 2012-01-09 2013-07-11 Zimmer, Inc. Porous metal implants with bone cement
CN103445883A (zh) * 2012-06-04 2013-12-18 合硕生技股份有限公司 镂空网架医疗用植入物
CN104207867A (zh) * 2014-08-13 2014-12-17 中国科学院福建物质结构研究所 一种低模量医用植入多孔支架结构
CN204033546U (zh) * 2014-08-13 2014-12-24 中国科学院福建物质结构研究所 一种低模量医用植入多孔支架结构

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP3181097A4 *

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EP3181097B1 (en) 2019-08-07
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