A new personalized prosthesis design method, device, medium, and product

Abstract

The application discloses a novel personalized prosthesis design method, device, medium and product, relates to the technical field of computer-aided design and medical device prosthesis implant structure design, and the method comprises the following steps: determining target prosthesis rigidity and matrix material rigidity to be designed according to an actual repair site, combining a geometric parameter and rigidity relationship model to determine geometric parameters of a unit cell, and generating a target prosthesis model according to the geometric parameters; wherein, the diamond unit cell structure is used for designing the porous prosthesis, a mathematical model for representing the relationship between the geometric parameters of the unit cell and the overall rigidity of the porous prosthesis is derived based on the Euler-Bernoulli beam theory, and the geometric parameters of the unit cell are determined by using the mathematical model. Apparently, the application can directly and accurately design the structure of the porous prosthesis according to the rigidity requirement of the actual repair site, and effectively improves the design efficiency of the porous prosthesis.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of computer-aided design and medical device prosthesis implant structure design, in particular to a novel personalized prosthesis design method, device, medium and product. BACKGROUND

[0002] Due to trauma, tumors, deformities, degeneration and population aging, more and more patients need to use bone prosthesis for repair treatment. Titanium and its alloys are ideal bone prosthesis materials, but considering that the implantation of solid titanium alloy prosthesis will bear most of the load, which will significantly reduce the stress level of the bone tissue near the titanium alloy prosthesis, resulting in stress shielding effect, thereby inducing bone resorption, titanium alloy prosthesis loosening, failure and other problems. Therefore, people have begun to study various porous structure titanium alloy prostheses. Due to the loose and porous characteristics of the porous structure titanium alloy prosthesis, the stiffness of the titanium alloy prosthesis can be effectively reduced, and the elastic modulus is more close to human bone.

[0003] At present, in the design of porous prosthesis (implant), there are generally two ways, one is to obtain the required porous prosthesis by changing the parameter value and performing multiple experiments, but this way is low in efficiency and cannot directly design the structure of the porous prosthesis according to the stiffness requirement. The other is to use the relationship between the porosity of the porous prosthesis and the stiffness of the porous prosthesis to regulate the stiffness of the porous prosthesis, but the relationship between the two is rough, so this way also cannot directly design the structure of the porous prosthesis according to the stiffness requirement. SUMMARY

[0004] The purpose of the present application is to provide a novel personalized prosthesis design method, device, medium and product, which can directly design the structure of the porous prosthesis according to the required stiffness requirement of the actual repair site, and effectively improve the design efficiency of the porous prosthesis.

[0005] To achieve the above purpose, the present application provides the following scheme:

[0006] In a first aspect, the present application provides a novel personalized prosthesis design method, comprising:

[0007] According to the bone information adjacent to the first bone, the stiffness of the target prosthesis to be designed is determined; the first bone is the bone to be replaced.

[0008] The stiffness of the matrix material is determined.

[0009] According to the rigidity of the target prosthesis to be designed, the rigidity of the matrix material, and a geometric parameter and rigidity relationship model, geometric parameters of the unit cell are determined; the geometric parameter and rigidity relationship model is determined according to a diamond unit cell structure and Euler-Bernoulli beam theory; the structure of the unit cell is a diamond unit cell structure; and the geometric parameters include strut length and strut diameter in the unit cell structure.

[0010] According to the geometric parameters of the unit cell, a target prosthesis model is generated; and the target prosthesis model includes a plurality of unit cells.

[0011] In a second aspect, the present application provides a computer device, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor executes the computer program to implement the novel personalized prosthesis design method in the above.

[0012] In a third aspect, the present application provides a computer readable storage medium having a computer program stored thereon, and the computer program is executed by a processor to implement the novel personalized prosthesis design method in the above.

[0013] In a fourth aspect, the present application provides a computer program product comprising a computer program, and the computer program is executed by a processor to implement the novel personalized prosthesis design method in the above.

[0014] According to the specific embodiments provided by the present application, the following technical effects are disclosed:

[0015] The present application provides a novel personalized prosthesis design method, device, medium and product. Firstly, the rigidity of the target prosthesis to be designed and the rigidity of the matrix material are determined, and then the geometric parameter and rigidity relationship model based on the diamond unit cell structure and Euler-Bernoulli beam theory is used to determine the geometric parameters of the unit cell, and finally the target prosthesis model is generated according to the geometric parameters of the unit cell. The present application designs the porous prosthesis by adopting the diamond unit cell structure, and deduces the mathematical model of the relationship between the geometric parameters of the unit cell and the overall rigidity of the porous prosthesis based on the Euler-Bernoulli beam theory, so that the structure of the porous prosthesis can be accurately designed directly according to the rigidity requirement of the actual repair site, and the design efficiency of the porous prosthesis is effectively improved. BRIEF DESCRIPTION OF DRAWINGS

[0016] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the accompanying drawings needed in the embodiments will be briefly introduced. Obviously, the accompanying drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained based on these drawings without creative labor.

[0017] Figure 1 A flowchart of a new personalized prosthesis design method in an embodiment of the present application;

[0018] Figure 2 A schematic diagram of a diamond cubic cell structure provided in an embodiment of the present application;

[0019] Figure 3 A schematic diagram of a porous prosthesis model generation flow provided in an embodiment of the present application;

[0020] Figure 4 A flowchart of a new personalized prosthesis design method provided in another embodiment of the present application;

[0021] Figure 5 A schematic diagram of a cylindrical porous prosthesis provided in an embodiment of the present application;

[0022] Figure 6 A schematic diagram of a right zygomatic maxillary bone osteotomy area of a beagle dog provided in an embodiment of the present application;

[0023] Figure 7 A schematic diagram of a personalized jaw bone repair porous prosthesis provided in an embodiment of the present application;

[0024] Figure 8 A schematic diagram of another personalized jaw bone repair porous prosthesis provided in an embodiment of the present application;

[0025] Figure 9 A structural schematic diagram of a computer device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0026] The technical solutions in the embodiments of the present application will be described clearly and completely in combination with the accompanying drawings in the embodiments of the present application. Obviously, the described embodiments are only some embodiments of the present application, not all embodiments. Based on the embodiments in the present application, all other embodiments obtained by those skilled in the art without creative labor are within the protection scope of the present application.

[0027] Due to trauma, tumor, deformity, degeneration and population aging, more and more patients need to be repaired and treated by personalized prosthesis. Cells are not easy to adhere and grow on traditional prosthesis, which leads to poor combination of prosthesis and host tissue. The ideal prosthesis should simulate the natural extracellular matrix as much as possible to support cell attachment, proliferation and differentiation. In addition, the prosthesis should also have similar macrostructure to the natural bone. This feature can provide space for the growth of cells and new tissues, as well as serve as a carrier for growth factors. Another important issue is the mechanical properties of the prosthesis. Studies have shown that the mechanical properties of the bone have a significant impact on bone integration. Because the natural bone has super-elastic biomechanical properties, its Young's modulus is in the range of 1-27 GPa, which is the strength, stiffness and mechanical properties that the ideal prosthesis material should have, which can avoid bone resorption and subsequent implant failure due to stress shielding effect. It is very important to study the ideal prosthesis material and preparation method for designing the prosthesis with similar structure and function to the natural bone. Titanium and its alloys are ideal bone prosthesis materials, but there are also some problems. Studies have shown that low elastic modulus titanium alloy has better load transfer characteristics than high elastic modulus titanium alloy. At the same time, considering the implantation of solid titanium alloy prosthesis, the dense titanium alloy prosthesis will bear most of the load, and the stress level of the bone tissue near the prosthesis will be significantly reduced, resulting in stress shielding effect, which induces bone resorption, prosthesis loosening, failure and other problems. Therefore, people have begun to study various porous titanium alloy prostheses. Due to the loose and porous characteristics of the porous titanium alloy prosthesis, the stiffness of the titanium alloy prosthesis can be effectively reduced, and its elastic modulus is more close to human bone. The porous titanium alloy prosthesis has advantages, but it is difficult to manufacture the porous titanium alloy prosthesis by traditional machining manufacturing technology, which requires 3D printing technology.

[0028] In addition, the diamond structure has excellent mechanical properties such as ultra-light weight, high specific strength, high specific stiffness, etc. In terms of function, it also has the characteristics of energy absorption and shock absorption, sound absorption and heat dissipation, electromagnetic shielding, water and air permeability, etc. Therefore, the application proposes a new type of personalized prosthesis design method, equipment, medium and product using diamond structure. The designed personalized prosthesis uses diamond unit cell structure inside and the geometry contour consistent with the replaced bone part outside.

[0029] In order to make the above-mentioned purposes, features and advantages of the application more obvious and easy to understand, the application will be further described in detail below in combination with the drawings and specific embodiments.

[0030] In an exemplary embodiment, as shown in Figure 1 A new type of personalized prosthesis design method is provided, comprising:

[0031] S01: determining the stiffness of the target prosthesis to be designed according to the bone information adjacent to the first bone; the first bone is the bone to be replaced.

[0032] S02: determining the rigidity of the matrix material.

[0033] S03: determining the geometric parameters of the unit cell according to the rigidity of the target prosthesis to be designed, the rigidity of the matrix material, and a geometric parameter-rigidity relationship model; the geometric parameter-rigidity relationship model is determined according to a diamond unit cell structure and Euler-Bernoulli beam theory; the structure of the unit cell is a diamond unit cell structure; the geometric parameters include the length and diameter of the strut in the unit cell structure.

[0034] S04: generating a target prosthesis model according to the geometric parameters of the unit cell; the target prosthesis model includes a plurality of unit cells.

[0035] The unit cell structure includes a plurality of marker points and struts for connecting adjacent marker points; the marker points correspond to carbon atoms in the diamond unit cell structure, and the struts correspond to covalent bonds between carbon atoms in the diamond unit cell structure.

[0036] As an optional implementation, the geometric parameter-rigidity relationship model is:

[0037]

[0038] E UC is the elastic modulus of the target prosthesis to be designed; E S is the elastic modulus of the matrix material; is the apparent density of the unit cell, d is the diameter of the strut in the unit cell structure, and L is the length of the strut in the unit cell structure.

[0039] In this embodiment, the rigidity is characterized by the elastic modulus.

[0040] The following is the design principle of the personalized prosthesis based on the diamond structure of the present application:

[0041] The mechanical properties of the prosthesis are an important indicator for measuring whether the prosthesis can meet the bearing requirements, and the porous prosthesis provides sufficient bearing for the bone defect site and meets certain strength and rigidity. Since the mechanical properties of the porous structure are mainly affected by the geometric parameters of the structure, in order to select appropriate porous structure parameters according to the mechanical requirements in the design stage, it is necessary to quantitatively analyze the relationship between the geometric parameters of the structure and the mechanical properties of the porous structure. The diamond cubic unit cell is an isotropic geometric body with fourteen vertices and sixteen equal edges (i.e. struts), as shown in Figure 2The nodes are connected to other four nodes, and the angle between each strut is 109.5°. Each node or vertex corresponds to a carbon atom. The length of each strut L, the length of the geometry a and the angle θ between the strut and the horizontal plane are related to each other by the following relations:

[0042]

[0043] The apparent density is defined as the ratio of the total volume of the cell to the volume occupied by the corresponding solid material (i.e. the struts). Since each diamond unit cell is connected to other unit cells through the boundary nodes and there is no shared strut between the unit cells, the apparent density calculated based on one cell also represents the apparent density of the whole porous structure.

[0044] Therefore, the total volume V of the cubic cell is:

[0045]

[0046] The volume occupied by all the struts of the cell V st is:

[0047] V st = 4πd 2 ; (4)

[0048] Therefore, the apparent density formula of a single cell is:

[0049]

[0050] where d is the diameter of the strut of the cell.

[0051] It is assumed that the porous structure is linear elastic and small deformation. Since the diamond cubic unit cell is an isotropic geometry, the mechanical properties are the same in different directions. For the study of porous structures, there are few mechanical analytical solutions for predicting the mechanical properties of cell structures. Often, a finite element model is established to obtain the structural modulus and other mechanical parameters of the porous structure. The structural modulus of the porous structure is closely related to the geometric parameters such as the apparent density. Therefore, the mechanical properties of the porous material are related to the apparent density:

[0052]

[0053]

[0054]

[0055] where σ y , σ max and E eff are the yield strength, ultimate strength and effective modulus of the porous structure. σy0 , σ max0 and E0are the yield strength, ultimate strength and elastic modulus of the bulk material (i.e. matrix material), p rel is the apparent density of the porous material.

[0056] However, the above formula is too rough to accurately calculate the mechanical properties of different cell structures. Since the diamond cubic cell is an isotropic geometric shape, the mechanical properties are the same in different directions, and the elastic modulus of the diamond-type cell structure is calculated using the Euler-Bernoulli beam theory. The equation relating the elastic modulus and Poisson's ratio of the diamond-type cell structure to the elastic modulus E s of the matrix material and the apparent density p of the porous structure is derived. Let P be the compression force transmitted to the y direction of any cell unit, due to symmetry, each strut bears force, and bending moment.

[0057] For each strut, there are two types of deformation, i.e. the deformation caused by the bending moment and the deformation caused by the axial force.

[0058] For the bending moment, the Euler-Bernoulli beam equation can be written as:

[0059]

[0060] where x is the coordinate of the strut in the X direction, and ω is the deflection, which can be expressed as:

[0061] ω = c0+ c1x + c2x 2 + c3x 3 ; (10)

[0062] c0-c3are constants, according to the Euler-Bernoulli beam theory, the deflection δ 22,b caused by the moment in the y direction is:

[0063]

[0064] where I is the second moment of inertia,

[0065] The deformation of the cell strut in the y direction caused by the axial force is δ 22,a :

[0066]

[0067] where A is the cross-sectional area of the strut.

[0068] Then the total deformation in the y direction is:

[0069]

[0070] Since there are four struts in the y direction for the unit cell, the total deformation of the cell (i.e. the unit cell) in the y direction is:

[0071]

[0072] Meanwhile, the stress-strain relationship of the unit cell structure can be written as:

[0073] σ UC = E UC ε 22,UC ; (15)

[0074] where E UC is the elastic modulus of the unit cell structure, which is equal to the elastic modulus of the porous prosthesis; σ UC is the cell stress; and ε 22,UC is the cell strain.

[0075] The cell stress is calculated by dividing the applied force P by the effective area A UC of the cell:

[0076]

[0077] The deformation of the cell in the y direction δ 22,UC is divided by the length a of the cell to obtain the cell strain:

[0078]

[0079] Further, the deformation of the cell is:

[0080]

[0081] Combining equation (14) and equation (18), the ratio of the elastic modulus of the unit cell structure to the elastic modulus of the matrix material, i.e. equation (1), can be derived, where

[0082]

[0083] As can be seen from equation (19), the desired prosthesis stiffness can be adjusted by controlling the strut length and strut diameter of the unit cell structure.

[0084] As an optional implementation, step S04 specifically comprises:

[0085] S04.1: creating a unit cell according to the geometric parameters of the unit cell;

[0086] S04.2: performing array operations on the created unit cell to obtain a porous structure model.

[0087] S04.3: performing a Boolean operation on the porous structure model and the contour model of the site where the first bone is located, to obtain the target prosthesis model.

[0088] As an optional implementation, before step S04, the new personalized prosthesis design method further comprises:

[0089] determining a contour model of the site where the first bone is located.

[0090] Further, the determination of the contour model of the site where the first bone is located specifically comprises:

[0091] Step A: CT scanning the site where the first bone is located to obtain CT scanning data.

[0092] Step B: extracting the CT scanning data to obtain external contour data of the site where the first bone is located.

[0093] Step C: constructing a contour model of the site where the first bone is located according to the external contour data.

[0094] As an optional implementation, before step S04.2, the new personalized prosthesis design method further comprises:

[0095] determining the number of the array of unit cells.

[0096] Further, the determination of the number of the array of unit cells specifically comprises.

[0097] Step a: determining the center position of the contour model of the site where the first bone is located.

[0098] Step b: constructing a three-dimensional coordinate system with the center position as the origin.

[0099] Step c: determining the maximum size of the contour model in the X-axis, Y-axis and Z-axis directions according to the maximum and minimum values of the coordinates of the contour model in the X-axis, Y-axis and Z-axis.

[0100] Step d: determining the number of the array of unit cells according to the maximum size and the geometric parameters of the unit cells.

[0101] That is, the porous prosthesis model generation process includes: part import or creation, selection of unit cell type, then array formation of large-scale porous structure, and interactive operation to export the required porous structure model. Finally, the arranged porous structure model and the contour model of the site where the first bone is located are subjected to Boolean intersection operation to generate a porous prosthesis model (i.e. the target prosthesis model), see Figure 3For the determination of the array number, in the process of importing the model, first identify the center position of the contour model and the maximum and minimum positions of the X, Y and Z axes, and then obtain the size of the cell (i.e. the unit cell) according to the input cell geometry parameters. Divide the size of the contour model by the size of the cell to obtain the number of arrays in three directions. Then perform array and Boolean operations.

[0102] In another exemplary embodiment of the present application, after generating the target prosthesis model, further comprising:

[0103] sending the target prosthesis model to a 3D printer; the 3D printer is used to print a target prosthesis according to the target prosthesis model.

[0104] The present application also provides an application scenario for the new personalized prosthesis design method. Specifically, the new personalized prosthesis design method provided in this embodiment can be applied in a bone prosthesis implantation scenario. The bone prosthesis implantation scenario includes a defect site information acquisition link, a bone prosthesis design link and a bone prosthesis implantation link; the defect site information acquisition link acquires relevant information of the required replacement bone site and enters the bone prosthesis design link, generates a target prosthesis model according to the relevant information of the required replacement bone site, and then enters the downstream bone prosthesis implantation link for printing and implanting the bone prosthesis. The new personalized prosthesis design method provided in this embodiment belongs to the bone prosthesis design link. Specifically, the rigidity of the target prosthesis is determined according to the relevant information of the required replacement bone site, and then the geometric parameters of the unit cell are determined according to the geometric parameter and rigidity relationship model, and a target prosthesis model is generated to complete the prosthesis design.

[0105] In an exemplary embodiment, the new personalized prosthesis design method has a design step as shown in Figure 4 First, according to the CT data, the external contour of the part to be replaced is extracted, and a personalized prosthesis shape is constructed. Then, a porous structure design is introduced, and a diamond unit cell structure is used as the cell structure to control the overall rigidity of the prosthesis by controlling the strut length and strut diameter of the diamond unit cell structure. Finally, a personalized root-shaped implant structure with a porous structure and an overall structure rigidity similar to the replaced part of the bone is designed.

[0106] To make it easier to understand the new personalized prosthesis design method of the present application, the following cases are used for illustration:

[0107] 1. Design of cylindrical porous prosthesis:

[0108] The matrix material is titanium alloy, the elastic modulus is 100 Gpa, and the elastic modulus of the required porous prosthesis is 3.73 GPa. According to the formula (19) of the relationship between the geometric parameters and the equivalent elastic modulus derived from the Euler-Bernoulli beam theory, the geometric size of the cell structure is calculated: the strut diameter is 0.3 mm, and the strut length is 0.62 mm. The cell structure is arrayed and copied, and the Boolean operation is performed, and finally the cylindrical porous prosthesis model is obtained, as shown in Figure 5 The diameter of the cylindrical porous prosthesis is D = 10 mm, and the height L = 15 mm.

[0109] 2. Personalized jaw bone repair porous prosthesis design

[0110] As shown in Figure 6 , one healthy adult male beagle dog was selected, and the bone defect position was designed at 0.5 cm behind the infraorbital foramen, 1 cm above the root tip, and behind the zygomatic frontal process. The CT data was scanned and imported into Mimics 17.0 for three-dimensional reconstruction. The contour of the three-dimensionally reconstructed bone defect site was imported into the porous prosthesis design software for porous prosthesis design, and a porous prosthesis model with a strut length of 0.52 mm and a strut diameter of 0.3 mm was obtained.

[0111] As shown in Figure 7 , the porous prosthesis perfectly fits the jaw bone defect position. According to the actual needs of the operation, an extension plate for fixation was designed, which was located at the front edge and the rear edge of the prosthesis, as shown in Figure 8 The final designed porous prosthesis model was saved as an STL file and imported into a selective laser melting printer Concept Laser M2 Cusing for printing, and then sandblasting, polishing, cleaning and disinfection were performed.

[0112] In an exemplary embodiment, a computer device, which can be a server or a terminal, is provided, and the internal structure diagram thereof can be as shown in Figure 9As shown in the figure. The computer device includes a processor, a memory, an input / output interface (I / O for short) and a communication interface. Among them, the processor, the memory and the input / output interface are connected through the system bus, and the communication interface is connected to the system bus through the input / output interface. Among them, the processor of the computer device is used to provide computing and control capability. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system, a computer program and a database. The internal memory provides an environment for the operation of the operating system and the computer program in the non-volatile storage medium. The database of the computer device is used to store the target prosthesis model. The input / output interface of the computer device is used to exchange information between the processor and external devices. The communication interface of the computer device is used to communicate with external terminals through network connection. The computer program is executed by the processor to realize a new type of personalized prosthesis design method.

[0113] Those skilled in the art can understand that, Figure 9 The structure shown in the figure is only a block diagram of part of the structure related to the scheme of the present application, and does not constitute a limitation on the computer device to which the scheme of the present application is applied. The specific computer device can include more or fewer components than those shown in the figure, or combine certain components, or have a different component arrangement.

[0114] In one exemplary embodiment, a computer device is also provided, including a memory and a processor, the memory storing a computer program, and the processor executing the computer program to realize each of the above method embodiments.

[0115] In one exemplary embodiment, a computer readable storage medium is provided, storing a computer program, which is executed by a processor to realize each of the above method embodiments.

[0116] In one exemplary embodiment, a computer program product is provided, including a computer program, which is executed by a processor to realize each of the above method embodiments.

[0117] It should be noted that the user information (including but not limited to user equipment information, user personal information, etc.) and data (including but not limited to data for analysis, stored data, displayed data, etc.) involved in the present application are all information and data authorized by the user or authorized by all parties, and the collection, use and processing of related data need to comply with relevant regulations.

[0118] Those skilled in the art can understand that all or part of the processes in the above-mentioned embodiment methods can be completed by instructing the relevant hardware through a computer program. The computer program can be stored in a non-volatile computer readable storage medium, and when the computer program is executed, the processes of the above-mentioned embodiments of the methods can be included. Any reference to memory, database or other medium used in the embodiments provided in the present application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical storage, high-density embedded non-volatile memory, resistive memory (ReRAM), magnetoresistive random access memory (MRAM), ferroelectric memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. As an illustration but not limitation, RAM can be in various forms, such as static random access memory (SRAM) or dynamic random access memory (DRAM), etc.

[0119] The database involved in the embodiments provided in the present application can include at least one of a relational database and a non-relational database. The non-relational database can include a distributed database based on a blockchain, etc., without being limited thereto. The processor involved in the embodiments provided in the present application can be a general-purpose processor, a central processing unit, a graphics processing unit, a digital signal processor, a programmable logic device, a data processing logic device based on quantum computing, etc., without being limited thereto.

[0120] The technical features of the above embodiments can be combined arbitrarily. In order to make the description concise, all possible combinations of the technical features in the above embodiments are not described, however, as long as the combinations of the technical features do not exist contradictory, they should be considered as the scope of the present application.

[0121] The principles and implementation modes of the present application are described by applying specific examples in the present application. The above-mentioned embodiments are only used to help understand the method and its core idea of the present application; at the same time, for those skilled in the art, according to the idea of the present application, the specific implementation mode and application range will be changed. In conclusion, the content of the present application should not be understood as a limitation.

Claims

1. A novel personalized prosthesis design method, characterized by, The new personalized prosthesis design method comprises: determining the rigidity of the target prosthesis to be designed according to the bone information adjacent to the first bone; the first bone is the bone to be replaced; determining the rigidity of the matrix material; determining the geometric parameters of the unit cell according to the rigidity of the target prosthesis to be designed, the rigidity of the matrix material, and the geometric parameter and rigidity relationship model; the geometric parameter and rigidity relationship model is determined according to the diamond unit cell structure and the Euler-Bernoulli beam theory; the structure of the unit cell is a diamond unit cell structure; the geometric parameters include the strut length and strut diameter in the unit cell structure; generating a target prosthesis model according to the geometric parameters of the unit cell; the target prosthesis model comprises a plurality of unit cells; the geometric parameter and rigidity relationship model is: ； wherein, E UC is the elastic modulus of the target prosthesis to be designed; E S is the elastic modulus of the matrix material; is the apparent density of the unit cell, d is the strut diameter in the unit cell structure, L is the strut length in the unit cell structure.

2. The method of designing a new personalized prosthesis according to claim 1, characterized in that, generating a target prosthesis model according to the geometric parameters of the unit cell, specifically comprising: creating a unit cell according to the geometric parameters of the unit cell; performing array operation on the created unit cell to obtain a porous structure model; performing Boolean operation on the porous structure model and the contour model of the part where the first bone is located to obtain the target prosthesis model.

3. The method of designing a new personalized prosthesis according to claim 2, characterized in that, Further comprising: determining the contour model of the part where the first bone is located.

4. The method of designing a new personalized prosthesis according to claim 3, characterized in that, determining the contour model of the part where the first bone is located, specifically comprising: performing CT scanning on the part where the first bone is located to obtain CT scanning data; extracting the CT scanning data to obtain the external contour data of the part where the first bone is located; constructing the contour model of the part where the first bone is located according to the external contour data.

5. The method of designing a new personalized prosthesis according to claim 2, characterized in that, Before the step "performing array operation on the created unit cell to obtain a porous structure model", the new personalized prosthesis design method further comprises: determining the number of unit cell arrays, specifically comprising: determining the center position of the contour model of the part where the first bone is located; constructing a three-dimensional coordinate system with the center position as the origin; determining the maximum size of the contour model in the X-axis, Y-axis and Z-axis directions according to the maximum and minimum values of the coordinates of the contour model in the X-axis, Y-axis and Z-axis directions; determining the number of unit cell arrays according to the maximum size and the geometric parameters of the unit cell.

6. The method of designing a new and personalized prosthesis according to claim 1, characterized in that, After generating the target prosthesis model, further comprising: sending the target prosthesis model to a 3D printer; the 3D printer is used to print a target prosthesis according to the target prosthesis model.

7. A computer device comprising: A memory, a processor, and a computer program stored on the memory and executable on the processor, characterized in that the processor executes the computer program to implement the new personalized prosthesis design method of any one of claims 1-6.

8. A computer-readable storage medium having stored thereon a computer program, characterized in that, The computer program is executed by the processor to implement the new personalized prosthesis design method of any one of claims 1-6.

9. A computer program product comprising a computer program, characterized in that, The computer program is executed by the processor to implement the new personalized prosthesis design method of any one of claims 1-6.

Images