CN109992820B - Mechanical property evaluation method of porous bone implant based on dodecahedron rod structure - Google Patents
Mechanical property evaluation method of porous bone implant based on dodecahedron rod structure Download PDFInfo
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Abstract
The invention discloses a mechanical property evaluation method of a porous bone implant based on a dodecahedron rod structure, wherein the porous bone implant is formed by splicing at least one dodecahedron rod structure basic unit by using a modeling method; the dodecahedron rod structure basic unit comprises a rhombic dodecahedron formed by twenty-four trabeculae and trabeculae which extend outwards from two opposite vertexes of twelve faces of the rhombic dodecahedron respectively, pores are formed between adjacent trabeculae, and a plurality of pores which are distributed in a three-dimensional space are formed in the dodecahedron rod structure basic unit; establishing a first quantitative analysis relation between the equivalent modulus difference value of the porous bone implant and the trabecular size, and predicting the mechanical property of the porous bone implant according to the first quantitative analysis relation; the equivalent modulus difference is the difference between the equivalent elastic modulus of the porous bone implant obtained by using the simulation analysis method and the equivalent elastic modulus of the porous bone implant obtained by using the sample piece test.
Description
Technical Field
The invention relates to the technical field of biomedical prostheses, in particular to a mechanical property evaluation method of a porous bone implant based on a dodecahedron rod structure.
Background
With the deep of the aging society and the occurrence of traffic accidents and natural disasters, the demands for bone repair and bone replacement are increasing, and how to provide a bone implant (bone implant comprises a bone bracket, a bone prosthesis and the like, and the bone prosthesis comprises a bone plate, a bone nail and the like) with good mechanical properties and tissue regeneration performance is one of the clinical problems to be solved urgently. The existing metal solid bone implant is generally made of 316 stainless steel, cobalt-based alloy, titanium alloy and other metal materials, the rigidity of the metal bone implant is far greater than that of human bones (compact bone 3-30 GPa; cancellous bone 0.02-2 GPa), the problems of mismatching of mechanical properties of bone plates and original bones, stress shielding and the like are easily caused, the problems of adjacent bone osteoporosis, prosthesis loosening and the like are caused, and the porous bionic bone implant has the characteristics of low rigidity, small stress shielding, easiness in cell adhesion growth and tissue regeneration, personalized customization and the like, and has huge clinical requirements and wide application prospects.
Research shows that the form and shape parameters of the porous structure of the porous bionic bone implant are important factors affecting mechanical properties. At present, most of the porous structures of the bionic bone implants are designed along a single direction, the structure is single, and the performance difference is not great; meanwhile, the personalized design of the porous bionic bone implant depends on experience, a controllable and quantitative scientific design method is not yet available, and the problems of mismatching of mechanical properties, high potential risk, poor tissue regeneration performance and the like exist, so that the clinical application and popularization of the porous bionic bone implant are greatly limited; moreover, at present, the porous bionic bone implant is generally prepared by using a 3D printing technology, and is limited by the 3D printing technology, the process characteristics accumulated layer by layer and the size of the metal powder particle size have larger influence on the mechanical properties and tissue regeneration properties of different porous structures, so that the designed porous bionic bone implant has larger mechanical property difference from the bone implant prepared by 3D printing, and the long-term effective service is extremely unfavorable for the mechanical property adaptation of the bone implant and host bone.
Disclosure of Invention
In view of the above, the present invention aims to provide a method for evaluating mechanical properties of a porous bone implant based on a dodecahedron rod structure, wherein the porous bone implant is formed by splicing at least one dodecahedron rod structure basic unit by using a modeling method, and the porous bone implant has a plurality of pores distributed in three-dimensional space, so that the mechanical properties of the porous bone implant can be quantitatively analyzed and predicted.
Based on the above object, the present invention provides a method for evaluating mechanical properties of a porous bone implant based on a dodecahedron rod structure, comprising:
the porous bone implant is formed by splicing at least one dodecahedron rod structure basic unit by using a modeling method;
the dodecahedron rod structural basic unit comprises: the rhombic dodecahedron consists of twenty-four trabeculae and trabeculae which extend outwards from two opposite vertexes of twelve faces of the rhombic dodecahedron respectively, pores are formed between adjacent trabeculae, and a plurality of pores which are distributed in three-dimensional space are formed in the basic unit of the dodecahedron rod structure;
establishing a first quantitative analysis relation between an equivalent modulus difference value and a trabecular size of the porous bone implant, and predicting the mechanical property of the porous bone implant according to the first quantitative analysis relation;
the equivalent modulus difference is the difference between the equivalent elastic modulus of the porous bone implant obtained by using a simulation analysis method and the equivalent elastic modulus of the porous bone implant obtained by using a sample piece test.
Optionally, the constitutive relationship between the equivalent modulus difference of the porous bone implant and the trabecular size is y= 25.091x 3.1856 Wherein x is the trabecular size and y is the equivalent modulus difference.
Optionally, establishing a second quantitative analysis relation between the shape parameter of the porous bone implant and the equivalent elastic modulus of the porous bone implant, and determining the equivalent elastic modulus of the porous bone implant according to the second quantitative analysis relation according to the preset shape parameter; wherein the shape parameters include: the porous bone implant has a volume, a porosity, a surface area, a specific surface area, and a pore size of a largest pore.
Optionally, the method is based on a simulation analysis method: the trabecular size is equal to the porous bone implantConstitutive relation between effective elastic moduli is y= 30.321x 2.589 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relationship between the trabecular size and the equivalent elastic modulus of the porous bone implant is y=6.11 x-07263, where y is the equivalent elastic modulus of the porous bone implant sample and x is the trabecular size.
Optionally, the method is based on a simulation analysis method: the constitutive relationship between the porosity of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=7e+12x -6.15 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relation between the porosity of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= -0.0989x+9.5125, where y is the equivalent elastic modulus of the porous bone implant and x is the porosity of the porous bone implant.
Optionally, the method is based on a simulation analysis method: the constitutive relationship between the pore size of the largest pore of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= 39.772x -4.005 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relation between the pore diameter of the largest pore of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= -3.9826x+6.8216, wherein y is the equivalent elastic modulus of the porous bone implant and x is the pore diameter of the largest pore of the porous bone implant.
Optionally, the method is based on a simulation analysis method: the constitutive relationship between the volume of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.0024 x 1.4493 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relation between the volume of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.0042 x-0.3371, where y is the equivalent elastic modulus of the porous bone implant and x is the volume of the porous bone implant.
Optionally, the method is based on a simulation analysis method: the constitutive relationship between the surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=5e-11 x 3.444 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the surface area of the porous bone implant and the porous bone implantThe constitutive relationship between the equivalent elastic moduli of the body is y=0.002 x-2.8805, where y is the equivalent elastic modulus of the porous bone implant and x is the surface area of the porous bone implant.
Optionally, the method is based on a simulation analysis method: the constitutive relation between the specific surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.0096 x 2.4973 Wherein y is the equivalent elastic modulus of the porous bone implant; based on the sample test, the following steps are obtained: the constitutive relation between the specific surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= 0.1626x-1.5883, wherein y is the equivalent elastic modulus of the porous bone implant and x is the specific surface area of the porous bone implant.
Optionally, the cross section of the trabecula is round, and the trabecula is made of titanium alloy.
The invention has the advantages that:
1. according to the method for evaluating the mechanical properties of the porous bone implant based on the dodecahedron rod structure, provided by the invention, a quantitative analysis relation between the trabecular size and the equivalent modulus difference is established, the mechanical properties of the manufactured porous bone implant sample can be predicted according to the quantitative analysis relation, and the degree of mechanical property matching between the manufactured porous bone implant and host bone is estimated in advance, so that the clinical adaptation and popularization and application of the personalized porous bone implant prepared by 3D printing are facilitated;
2. the mechanical property evaluation method of the porous bone implant based on the dodecahedron rod structure also establishes quantitative analysis relation between the shape parameters of the porous bone implant model and the equivalent elastic modulus of the porous bone implant under two measurement methods, can provide data basis for controllable, quantitative and scientific design of the porous bone implant, and is beneficial to clinical application and popularization of the personalized bionic bone implant;
3. the dodecahedron rod structure basic unit provided by the invention has a plurality of pores which are distributed in a three-dimensional space, has isotropic mechanical properties, is beneficial to promoting the transportation and the removal of nutrient substances and metabolites, and promotes the adhesion, differentiation and propagation of cells and the regeneration of tissues;
4. the dodecahedron rod structure basic unit provided by the invention is in an axisymmetric structure, six splicing surfaces are arranged, and a plurality of dodecahedron rod structure basic units are arranged and spliced to form the porous bone implant, so that the diversified individualized porous bone implant can be conveniently designed according to actual requirements.
Drawings
In order to more clearly illustrate the embodiments of the invention or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described, it being obvious that the drawings in the following description are only some embodiments of the invention, and that other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic view of a dodecahedron pole construction base unit according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of the mechanical conduction of the structure shown in FIG. 1;
FIG. 3 is a top view of the structure shown in FIG. 1;
FIGS. 4A and 4B are schematic views of two porous bone implants with different porosities formed by arranging and splicing the structures shown in FIG. 1;
FIG. 5A is a schematic representation of the constitutive relationship of trabecular size to porosity in accordance with an embodiment of the present invention;
FIG. 5B is a schematic representation of the constitutive relationship of trabecular size to pore size of the largest pores in accordance with embodiments of the present invention;
FIG. 5C is a schematic diagram of the constitutive relationship of trabecular size to volume according to an embodiment of the present invention;
FIG. 5D is a schematic representation of the constitutive relationship of trabecular size to surface area in accordance with an embodiment of the present invention;
FIG. 5E is a schematic diagram of the constitutive relationship of trabecular size to specific surface area according to an embodiment of the present invention;
FIG. 6A is a schematic diagram of the constitutive relationship of trabecular size and equivalent elastic modulus according to an embodiment of the present invention;
FIG. 6B is a schematic diagram of the constitutive relation of porosity to equivalent elastic modulus according to an embodiment of the invention;
FIG. 6C is a schematic diagram of the constitutive relation of pore size and equivalent elastic modulus according to an embodiment of the invention;
FIG. 6D is a schematic diagram of the constitutive relationship of volume and equivalent elastic modulus according to an embodiment of the invention;
FIG. 6E is a schematic representation of the constitutive relationship of surface area to equivalent elastic modulus for an embodiment of the invention;
FIG. 6F is a schematic diagram showing constitutive relation between specific surface area and equivalent elastic modulus according to an embodiment of the present invention;
FIG. 7 is a schematic diagram showing the correspondence between the trabecular dimensions and the equivalent elastic moduli obtained by finite element analysis and mechanical testing, respectively, according to an embodiment of the present invention;
fig. 8 is a schematic diagram of the constitutive relation of the trabecular size and the equivalent modulus difference in an embodiment of the present invention.
Detailed Description
The present invention will be further described in detail below with reference to specific embodiments and with reference to the accompanying drawings, in order to make the objects, technical solutions and advantages of the present invention more apparent.
It should be noted that, in the embodiments of the present invention, all the expressions "first" and "second" are used to distinguish two entities with the same name but different entities or different parameters, and it is noted that the "first" and "second" are only used for convenience of expression, and should not be construed as limiting the embodiments of the present invention, and the following embodiments are not described one by one.
Fig. 1 is a schematic structural view of a dodecahedron rod structural basic unit according to an embodiment of the present invention, fig. 2 is a schematic mechanical conduction diagram of the structure shown in fig. 1, and fig. 3 is a plan view of the structure shown in fig. 1. As shown in the drawing, the dodecahedron rod structural basic unit 1 provided by the embodiment of the present invention includes a rhombic dodecahedron (a black line portion in the middle of the structure shown in fig. 1) formed by twenty-four trabeculae 10, and trabeculae 10 respectively extending outwards from opposite two vertexes of twelve faces of the rhombic dodecahedron, and voids 12 are formed between adjacent trabeculae 10, so that the entire dodecahedron rod structural unit 1 is formed with a plurality of voids 12 distributed in three-dimensional space.
The vertex of any one of the rhombic dodecahedron is taken as a center point 13, the vertex of the extending trabecula is not arranged, the straight line of one pair of two opposite extending trabecula 101, 103 is taken as an S axis, the straight line of the other pair of two opposite extending trabecula 102, 104 is taken as a Z axis, the straight line of the perpendicular line of the endpoint connecting line of the two adjacent extending trabecula 101, 104 is taken as a Y axis, the straight line of the perpendicular line of the endpoint connecting line of the two adjacent extending trabecula 104, 103 is taken as an X axis, the X, Y, Z, S axis is intersected at the center point 13, and the included angle between the two adjacent axes is 45 degrees. The dodecahedron rod structural units 1 are in axisymmetric structures by taking X, Y, Z, S axes as symmetry axes respectively, so that the dodecahedron rod structural units 1 have isotropic mechanical properties.
For the trabecula that extends, cut out level three tangent planes 11 with its tip for the external profile of whole dodecahedron pole structural unit 1 is the square shape, and dodecahedron pole structural unit 1 of square shape has six concatenation faces, and the concatenation face of each dodecahedron pole structural unit 1 forms diversified individualized porous bone implant through concatenation, arrangement form.
Fig. 4A and 4B are schematic views of two porous bone implants having different porosities, which are arranged and spliced from the structure shown in fig. 1. As shown in the figure, when a specific porous bone implant is designed, the dodecahedron rod structure basic unit 1 can be used as a basic unit, and the solid bone implant is designed into a bone implant with different shape parameters through modeling methods such as linear array, mirror image, boolean operation and the like.
In the embodiment of the present invention, the trabeculae 10 constituting the dodecahedron rod structural basic unit 1 may be designed in size and cross-sectional shape according to performance requirements. For example, the cross-section of the trabeculae may be square, circular, regular triangular, oval, etc. For a trabecula with a square cross section, the trabecula size is the side length of the square, the trabecula with a regular triangle cross section, the trabecula size is the side length of the regular triangle, the trabecula with a circular cross section, the trabecula size is the diameter of the circle, the trabecula with an elliptical cross section, and the trabecula size is the major axis and the minor axis of the ellipse.
In the embodiment of the invention, the porous bone implant is formed by splicing at least one dodecahedron rod structure basic unit 1 through a modeling method, and one dodecahedron rod structure basic unit can be regarded as a small bone implant. Wherein the shape parameters of the porous bone implant based on the dodecahedron rod structural basic unit 1 include: the volume of the porous bone implant, the pore size of the largest pore of the porous bone implant, the porosity of the porous bone implant, the surface area of the porous bone implant, the specific surface area of the porous bone implant, etc. By adjusting the trabecular size of the dodecahedron rod structural basic unit 1, the various form parameters of the dodecahedron rod structural basic unit 1 can be adjusted according to the corresponding quantitative analysis relationship, thereby adjusting the form parameters of the porous bone implant designed by the dodecahedron rod structural basic unit 1. The specific method is as follows:
in one embodiment, the dodecahedron pole construction base unit 1 is sized: the length, width and height of the trabecula are equal to 5, 5 and 5mm, the trabecula is made of titanium alloy, the cross section of the trabecula is circular, and the dimension (i.e. the diameter of the circular shape) of the trabecula is respectively phi 0.5mm, phi 0.7mm, phi 0.9mm and phi 1.1mm. The modeling operations such as mirroring, array, boolean operation and the like are carried out on the dodecahedron rod structure basic unit 1, so that the porous bone scaffold or prosthesis with any shape and different shape parameters can be designed. In one embodiment, a first porous bone scaffolding model with a square outer contour and a length x width x height equal to 10 x 20mm is designed for experimentally deriving the relationship between trabecular size and shape parameters. In Solidworks or Rhinoceros or other design software, the volume, surface area, specific surface area, porosity, pore diameter of maximum pore and other shape parameters of the first porous bone scaffold model are measured and calculated, statistical software (such as SPSS software) is utilized to perform data analysis, and according to the data processing result,the trabecular size has obvious mathematical constitutive relation with the shape parameter of the porous bone scaffold, and the fitting degree value R 2 Are all close to 1.
As shown in fig. 5A, the trabecular size and the porosity of the porous bone scaffold have a linear decreasing relationship, and the constitutive relationship between the trabecular size and the porosity of the porous bone scaffold is y= -42.6x+113.36, where x is the trabecular size and y is the porosity of the porous bone scaffold. As shown in fig. 5B, the trabecular size and the pore diameter of the largest pore of the porous bone scaffold are in a linear decreasing relationship, and the constitutive relationship between the trabecular size and the pore diameter of the largest pore of the porous bone scaffold is y= -1.065x+2.1445, where x is the trabecular size and y is the pore diameter of the largest pore of the porous bone scaffold. As shown in fig. 5C, the trabecular size and the volume of the porous bone scaffold are in a linear increasing relationship, and the constitutive relationship between the two is y= 851.95x-267.19, where x is the trabecular size and y is the volume of the porous bone scaffold. As shown in fig. 5D, the trabecular size is in a linear increasing relationship with the surface area of the porous bone scaffold, where the constitutive relationship between the two is y=1467.8x+676.28, where x is the trabecular size and y is the surface area of the porous bone scaffold. As shown in fig. 5E, the trabecular size and the specific surface area of the porous bone scaffold are in a linear increasing relationship, and the constitutive relationship between the trabecular size and the specific surface area of the porous bone scaffold is y= 29.645x-2.4935, where x is the trabecular size and y is the specific surface area of the porous bone scaffold.
According to the constitutive relation between the obtained trabecular size and each body parameter (the porosity, the aperture of the maximum pore, the volume, the surface area and the specific surface area) of the porous bone scaffold, in the design process, any one body parameter of the porosity, the aperture of the maximum pore, the volume, the surface area and the specific surface area can be accurately designed, according to the determined specific body parameter, the trabecular size required to be designed is solved according to the constitutive relation between the trabecular size and the body parameter, and after the trabecular size is determined, other body parameters can be determined according to the constitutive relation between the trabecular size and the corresponding body parameter. It should be noted that, since the trabecular size and each of the shape parameters are linear at a time, and the shape parameters are mutually influenced, a specific shape parameter can be satisfied only by the preset trabecular size.
The embodiment of the invention provides a mechanical property evaluation method of a bone implant formed by the dodecahedron rod structure basic unit 1, which establishes a quantitative analysis relation between the trabecular size and the equivalent elastic modulus, and can adjust the mechanical property by adjusting the trabecular size of the dodecahedron rod structure basic unit 1, thereby adjusting the mechanical property of the bone implant designed by the dodecahedron rod structure basic unit 1.
In one embodiment, a second porous bone scaffold model with an outer contour of a cylinder and a diameter x height equal to phi 10 x 30mm is designed for mechanical property evaluation by experiment. And printing the second porous bone support model by using electron beam 3D printing equipment and titanium alloy (Ti 6Al 4V) metal powder under the condition of a layer thickness of 0.05mm to prepare a porous bone support sample made of titanium alloy, and performing mechanical property test (MPT, mechanics Performance Testing) on the porous bone support sample by using a mechanical testing machine to obtain the equivalent elastic modulus of the porous bone support. Meanwhile, virtual simulation analysis is performed on the basis of the second porous bone scaffold model by using finite element analysis software (FEA, finite Element Analysis) to obtain the equivalent elastic modulus of the porous bone scaffold. Further carrying out statistical processing on the data obtained by mechanical property test and finite element analysis by using SPSS statistical software to obtain the mathematical constitutive relation between the shape parameter of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold measured by two methods (finite element analysis and mechanical testing machine), and fitting the degree value R 2 Are all close to 1.
FIG. 6A is a schematic diagram showing the constitutive relation between the trabecular dimension and the equivalent elastic modulus according to the embodiment of the present invention, wherein the constitutive relation between the trabecular dimension and the equivalent elastic modulus of the porous bone scaffold is shown as an incremental power exponent according to the finite element simulation test analysis result (as FEA data in the figure), and the constitutive relation between the trabecular dimension and the equivalent elastic modulus is y= 30.321x 2.589 Wherein x is the trabecular size and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample (such as MPT data in the figure), the trabecular size and the equivalent elastic modulus of the porous bone scaffold are in a linear increasing relation, and the constitutive relation between the trabecular size and the equivalent elastic modulus is y=6.11 x-07263, which is thatWherein x is the trabecular size and y is the equivalent elastic modulus of the porous bone scaffold.
FIG. 6B is a schematic diagram showing the constitutive relation between the porosity and the equivalent elastic modulus of the porous bone scaffold according to the embodiment of the present invention, wherein the constitutive relation between the porosity of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is a power exponent decreasing relation, and the constitutive relation between the porosity of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is y=7E+12x, according to the result of finite element simulation test analysis -6.15 Wherein x is the porosity of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample, the porosity of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold are in a linear decreasing relation, and the constitutive relation between the porosity of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is y= -0.0989x+9.5125, wherein x is the porosity of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold.
FIG. 6C is a schematic diagram showing the constitutive relation between pore diameter and equivalent elastic modulus of the porous bone scaffold according to the present invention, wherein the constitutive relation between the pore diameter of the largest pore of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is a power exponent decreasing relation, and y= 39.772x -4.005 Wherein x is the pore diameter of the largest pore of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample, the pore diameter of the maximum pore of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold are in a linear decreasing relation, and the constitutive relation between the pore diameter of the maximum pore of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is y= -3.9826x+6.8216, wherein x is the pore diameter of the maximum pore of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold.
FIG. 6D is a schematic diagram showing the constitutive relation between the volume and the equivalent elastic modulus of the porous bone scaffold according to the embodiment of the present invention, wherein the constitutive relation between the volume of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is an exponential increasing relation, as shown in the figure, and the constitutive relation between the two is y=0.0024x 1.4493 Wherein x is the volume of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample piece, the volume of the porous bone scaffoldThe equivalent elastic modulus of the porous bone scaffold is in a linear increasing relation, and the constitutive relation between the porous bone scaffold and the porous bone scaffold is y=0.0042 x-0.3371, wherein x is the volume of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold.
FIG. 6E is a schematic diagram showing the constitutive relation between the surface area and the equivalent elastic modulus of the porous bone scaffold according to the embodiment of the present invention, wherein the constitutive relation between the surface area of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is an exponential increasing relation, and the constitutive relation between the two is y=5E-11 x, according to the result of finite element simulation test analysis 3.444 Wherein x is the surface area of the porous bone scaffold and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample, the surface area of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold are in a linear increasing relation, the constitutive relation between the surface area of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is y=0.002 x-2.8805, wherein x is the surface area of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold.
FIG. 6F is a schematic diagram showing the constitutive relation between the specific surface area and the equivalent elastic modulus of the porous bone scaffold according to the embodiment of the present invention, wherein the constitutive relation between the specific surface area and the equivalent elastic modulus of the porous bone scaffold is an exponential increasing relation, and y=0.0096 x according to the result of finite element simulation test analysis 2.4973 Wherein x is the specific surface area of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold. According to the test result of the mechanical testing machine of the porous bone scaffold sample, the specific surface area of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold are in a linear increasing relation, the constitutive relation between the specific surface area of the porous bone scaffold and the equivalent elastic modulus of the porous bone scaffold is y= 0.1626x-1.5883, wherein x is the specific surface area of the porous bone scaffold, and y is the equivalent elastic modulus of the porous bone scaffold.
According to fig. 6A to 6F, for the same second porous bone scaffold, the constitutive relation between the equivalent elastic modulus and the shape parameters obtained by finite element analysis is a power exponent relation; printing the second porous bone scaffold model into a porous bone scaffold sample, and testing the porous bone scaffold sample by using a mechanical testing machine to obtain the linear relationship between the equivalent elastic modulus and the shape parameters of the porous bone scaffold. Experiments prove that compared with a porous bone scaffold sample prepared by 3D printing, the designed second porous bone scaffold model has inconsistent mechanical properties, because the porous bone scaffold sample prepared by 3D printing has factors such as insufficient toughness, brittleness and the like which influence the mechanical properties of bone implantation.
Fig. 7 is a schematic diagram showing the correspondence between the trabecular dimensions and the equivalent elastic moduli obtained by the finite element analysis and the mechanical testing machine, respectively. As shown in the figure, under the condition that the trabecular size is the same, the equivalent elastic modulus of the porous bone scaffold obtained by utilizing finite element analysis is larger than that of a porous bone scaffold sample piece obtained by utilizing a mechanical testing machine, and the problems of powder residue, incomplete sintering, manufacturing defects and the like exist in the 3D printing process, so that the mechanical property of the prepared bone implant is reduced.
Fig. 8 is a schematic diagram showing constitutive relation between the trabecular size and the equivalent modulus difference (the difference in equivalent elastic modulus) in the embodiment of the present invention. As shown in the figure, the equivalent elastic modulus of the porous bone scaffold obtained by finite element analysis is subtracted by the equivalent elastic modulus of the porous bone scaffold obtained by mechanical test machine to obtain the difference value of the equivalent elastic modulus, SPSS statistical software is used for data statistical analysis to obtain the constitutive relation between the equivalent modulus difference value of the porous bone implant and the trabecular size as y= 25.091x 3.1856 Wherein x is the trabecular size and y is the equivalent modulus difference. On one hand, the mechanical properties of the printed porous bone implant sample are lower than those of the designed porous bone implant model under the influence of factors such as a manufacturing process, material characteristics and the like; on the other hand, the difference value obtained by subtracting the equivalent elastic modulus of the porous bone implant model obtained by finite element analysis from the equivalent elastic modulus of the porous bone implant sample obtained by mechanical test machine has an obvious constitutive relation with the trabecular size, and according to the quantitative analysis relation, the mechanical property of the manufactured porous bone implant sample can be rapidly and accurately predicted, and the adaptive porous bone implant model can be designed according to the preset mechanical property of the porous bone implant sample. Example(s)For example, knowing the trabecular size, the equivalent modulus of elasticity of a porous bone implant model can be obtained using finite element analysis, using the constitutive relationship y= 25.091x described above 3.1856 The method can rapidly and accurately predict the equivalent elastic modulus of the printed porous bone implant, and evaluate the mechanical property matching degree between the prepared porous bone implant and the host bone in advance, thereby being beneficial to the clinical adaptation, popularization and application of the personalized porous bone implant prepared by 3D printing; furthermore, to manufacture a porous bone implant sample meeting certain mechanical property conditions, based on the constitutive relation, the porous bone implant sample meeting the mechanical property conditions can be designed by adjusting the trabecular size and simultaneously utilizing finite element analysis to simulate the mechanical property of the porous bone implant model.
According to the mechanical property evaluation method of the porous bone implant based on the dodecahedron rod structure, provided by the embodiment of the invention, the dodecahedron rod structure basic unit is provided with a plurality of pores which are distributed in a three-dimensional space, so that the cell adhesion is promoted, and the tissue ingrowth and regeneration are promoted; the dodecahedron rod structure basic unit is in an axisymmetric structure and is provided with six splicing surfaces, and at least one dodecahedron rod structure unit is arranged and spliced to form a porous bone implant, so that a diversified individualized porous bone implant can be designed according to actual requirements; compared with the existing bone implant, the porous bone implant formed by arranging and splicing a plurality of dodecahedron rod structure basic units can reduce the rigidity of the bone implant, avoid the risk of stress shielding and have good mechanical properties; the mechanical property evaluation method of the porous bone implant establishes a quantitative analysis relation between the trabecular size and the equivalent modulus difference value, and can predict the mechanical property of the manufactured porous bone implant sample according to the quantitative analysis relation, and the mechanical property matching degree between the manufactured porous bone implant and the host bone is evaluated in advance, so that the clinical adaptation and popularization and application of the personalized porous bone implant prepared by 3D printing are facilitated; the quantitative analysis relation between the shape parameters of the porous bone implant model and the equivalent elastic modulus of the porous bone implant is also established, and the quantitative analysis relation can provide data basis for the controllable, quantitative and scientific design of the multi-bone implant, thereby being beneficial to the clinical application and popularization of the personalized bionic bone implant.
Those of ordinary skill in the art will appreciate that: the discussion of any of the embodiments above is merely exemplary and is not intended to suggest that the scope of the disclosure, including the claims, is limited to these examples; the technical features of the above embodiments or in the different embodiments may also be combined within the idea of the invention, the steps may be implemented in any order and there are many other variations of the different aspects of the invention as described above, which are not provided in detail for the sake of brevity.
The embodiments of the invention are intended to embrace all such alternatives, modifications and variances which fall within the broad scope of the appended claims. Therefore, any omission, modification, equivalent replacement, improvement, etc. of the present invention should be included in the scope of the present invention.
Claims (9)
1. A method for evaluating mechanical properties of a porous bone implant based on a dodecahedron rod structure is characterized in that,
the porous bone implant is formed by splicing at least one dodecahedron rod structure basic unit by using a modeling method;
the dodecahedron rod structural basic unit comprises: the rhombic dodecahedron consists of twenty-four trabeculae and trabeculae which extend outwards from two opposite vertexes of twelve faces of the rhombic dodecahedron respectively, pores are formed between adjacent trabeculae, and a plurality of pores which are distributed in three-dimensional space are formed in the basic unit of the dodecahedron rod structure; the end part of the extended trabecula is provided with three tangent planes, so that the external contour of the dodecahedron rod structure basic unit is square, and the dodecahedron rod structure basic unit is provided with six splicing surfaces;
establishing a first quantitative analysis relation between the equivalent modulus difference value of the porous bone implant and the trabecular size, determining the equivalent elastic modulus of the porous bone implant obtained by the preset trabecular size by using a simulation analysis method, and according to the preset trabecular size and the equivalent elastic modulusPredicting the mechanical properties of the printed porous bone implant according to the quantitative and the first quantitative analysis relation; the constitutive relationship between the equivalent modulus difference of the porous bone implant and the trabecular size is y= 25.091x 3.1856 Wherein x is the trabecular size and y is the equivalent modulus difference;
the equivalent modulus difference is the difference between the equivalent elastic modulus of the porous bone implant obtained by using a simulation analysis method and the equivalent elastic modulus of the porous bone implant obtained by using a sample piece test.
2. The method according to claim 1, wherein a second quantitative analysis relationship between the shape parameter of the porous bone implant and the equivalent elastic modulus of the porous bone implant is established, and the equivalent elastic modulus of the porous bone implant is determined according to the second quantitative analysis relationship according to a preset shape parameter; wherein the shape parameters include: the porous bone implant has a volume, a porosity, a surface area, a specific surface area, and a pore size of a largest pore.
3. The method according to claim 1, wherein the simulation analysis method is used for obtaining: the constitutive relationship between the trabecular size and the equivalent elastic modulus of the porous bone implant is y= 30.321x 2.589 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relationship between the trabecular size and the equivalent elastic modulus of the porous bone implant is y=6.11 x-0.7263, where y is the equivalent elastic modulus of the porous bone implant sample and x is the trabecular size.
4. The method according to claim 2, wherein the simulation analysis method is used for obtaining: the constitutive relationship between the porosity of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=7e+12x -6.15 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relationship between the porosity of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= -0.0989x+9.5125, wherein y is the porous bone implantThe equivalent elastic modulus of the bone implant, x, is the porosity of the porous bone implant.
5. The method according to claim 2, wherein the simulation analysis method is used for obtaining: the constitutive relationship between the pore size of the largest pore of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= 39.772x -4.005 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relation between the pore diameter of the largest pore of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= -3.9826x+6.8216, wherein y is the equivalent elastic modulus of the porous bone implant and x is the pore diameter of the largest pore of the porous bone implant.
6. The method according to claim 2, wherein the simulation analysis method is used for obtaining: the constitutive relationship between the volume of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.0024 x 1.4493 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relation between the volume of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.0042 x-0.3371, where y is the equivalent elastic modulus of the porous bone implant and x is the volume of the porous bone implant.
7. The method according to claim 2, wherein the simulation analysis method is used for obtaining: the constitutive relationship between the surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=5e-11 x 3.444 The method comprises the steps of carrying out a first treatment on the surface of the Based on the sample test, the following steps are obtained: the constitutive relationship between the surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y=0.002 x-2.8805, where y is the equivalent elastic modulus of the porous bone implant and x is the surface area of the porous bone implant.
8. The method according to claim 2, wherein the simulation analysis method is used for obtaining: the specific surface area of the porous bone implant and the porous bone implantConstitutive relation between equivalent elastic moduli of the body is y=0.0096 x 2.4973 Wherein y is the equivalent elastic modulus of the porous bone implant; based on the sample test, the following steps are obtained: the constitutive relation between the specific surface area of the porous bone implant and the equivalent elastic modulus of the porous bone implant is y= 0.1626x-1.5883, wherein y is the equivalent elastic modulus of the porous bone implant and x is the specific surface area of the porous bone implant.
9. The method of claim 1, wherein the trabeculae are circular in cross-section and the trabeculae are of titanium alloy.
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