A method for predicting the elastic modulus of bone defect repair scaffolds based on finite element analysis

Abstract

The present invention relates to a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, and a three-dimensional model of a bone defect repair scaffold for simulating the bone defect filling area is established, and is divided into a plurality of scaffold sub-models pi. After simulating the strain load applied by the patient's physiological weight, the strain value ε(i) borne by p(i) under the corresponding finite element simulated physiological load is calculated; it is judged whether the strain value ε(i) of each scaffold sub-model p(i) meets the normal strain range value, and the finite element simulation is performed on the unsatisfied scaffold sub-model p(i) until the normal strain is met. In this way, the ε(i) and elastic modulus E(i) of each scaffold sub-model p(i) are obtained and output for the subsequent preparation of a bone defect repair scaffold. This scheme takes into account the influence of the scaffold elastic modulus and the strain generated when the scaffold is subjected to physiological loads, so as to avoid the problem that the bone is damaged and unfavorable for osteogenesis due to insufficient elastic modulus.

Description

Technical Field

[0001] The present invention relates to the technical field of medical orthopedic prostheses, and in particular to a method and device for predicting the elastic modulus of a bone defect repairing bracket based on finite element analysis, and a prediction device. Background Art

[0002] Repairing large bone defects is a difficult problem in orthopedics. The current clinical method for defect repair is to implant a prosthesis using a fixed steel plate + scaffold material, which is also an important method for treating bone defects.

[0003] There are many types of scaffold materials and designs, all of which are designed to make bones heal faster and better.

[0004] Because bone is a mechanically regulated tissue organ, bone growth in the scaffold is closely related to mechanical factors. Studies have shown that the strain value borne by the callus determines the differentiation trend of the callus and whether it is conducive to osteogenesis.

[0005] The design of bone defect scaffolds is a complex process involving multiple steps such as medical image reconstruction, defect tissue generation, bone scaffold manufacturing and cell culture. The following are the conventional design steps of existing bone defect scaffolds:

[0006] 1. Medical image reconstruction: First, detailed images of the defective bone are acquired through medical imaging techniques (such as CT or MRI). Then, these images are reconstructed using image processing techniques to obtain a three-dimensional model of the defective part.

[0007] 2. Defect tissue contour reconstruction algorithm: Based on the 3D model reconstructed from medical images, a specific algorithm is used to reconstruct the contour of the defect tissue. This step is very critical because it determines the degree of match between the final stent and the defect site.

[0008] 3. Bone scaffold manufacturing: According to the designed scaffold model, appropriate manufacturing technology (such as 3D printing, biomaterial molding, etc.) is used to manufacture the bone defect scaffold. During the manufacturing process, key parameters such as the biocompatibility, mechanical properties and pore structure of the material need to be strictly controlled.

[0009] When designing the structure of the stent material, there are also the following technical defects:

[0010] The design of existing bone defect scaffolds does not take into account the influence of the scaffold elastic modulus and the strain of the scaffold when it is subjected to physiological loads. When the strain of the scaffold when subjected to physiological loads is lower than the normal strain range of the bone, the bone will be damaged and it is not conducive to osteogenesis. If it is higher than the lower limit of this area, it is not conducive to osteogenesis differentiation and affects bone healing.

[0011] Therefore, it is impossible to ensure that the strain is within a range that promotes bone healing and growth, and there is a lack of design considerations for the elastic modulus of the scaffold. Summary of the invention

[0012] In order to solve the technical problems existing in the prior art, the embodiment of the present invention provides a method and device for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis. The technical solution is as follows:

[0013] On the one hand, a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis is provided, the method being implemented by a prediction device, and the method comprising:

[0014] S1. constructing a three-dimensional finite element analysis model of tibial fracture internal fixation, and establishing a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model to simulate filling the bone defect area;

[0015] S2. According to the linear trend of the bone defect area, the three-dimensional model of the bone defect repair scaffold is divided into a number of scaffold sub-models pi (i=1, 2, 3.....1000), and a corresponding finite element model analysis parameter S is configured for each of the scaffold sub-models p(i):

[0016] make:

[0017] Si=(E0,σ(i),G F (i)),

[0018] in:

[0019] σ(i)=G F (i) / A(i),

[0020] E0 is the initial elastic model value set for each of the bracket sub-models p(i);

[0021] σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0022] G F (i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i);

[0023] A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i);

[0024] S3, performing finite element simulation analysis to calculate the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0025] S4, judging whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation:

[0026] ε(i)∈{εmin(i0), εmax(i0)},

[0027] If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the condition is bound;

[0028] If not, calculate the strain value ε(i) that satisfies the condition, including:

[0029] When ε(i)>εmax(i0):

[0030] make:

[0031] εt(i)=(1-k)εt(i-1),

[0032] When ε(i)≤εmin(i0):

[0033] make:

[0034] εt(i)=(1+k)εt(i-1),

[0035] in,

[0036] i is the number of times the strain value of the stent sub-model p(i) is calculated,

[0037] The value of k is 2.5~15%,

[0038] εt(i-1) is the strain value of the previous bracket sub-model p(i),

[0039] εt(i) is the strain value of the bracket sub-model p(i) at this time;

[0040] After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound;

[0041] S5. Traverse σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i):

[0042] E(i) = σ(i) / ε(i).

[0043] Furthermore, the method further comprises the following steps:

[0044] Mark each of the support sub-models p(i) with a model id;

[0045] When the strain value ε(i) and the corresponding elastic modulus E(i) of each of the bracket sub-models p(i) are obtained:

[0046] Bind the strain value ε(i) and the corresponding elastic modulus E(i) of the stent sub-model p(i) to the model id of the corresponding stent sub-model p(i), and generate finite element model simulation parameters of each stent sub-model p(i);

[0047] The finite element model simulation parameters of the bracket sub-model p(i) are saved in the MySQL database.

[0048] Furthermore, the method further comprises the following steps:

[0049] When designing a bone defect scaffold, it is necessary to refer to the finite element model simulation parameters of the corresponding scaffold sub-model p(i):

[0050] According to the model id marked on the corresponding scaffold sub-model p(i), the finite element model simulation parameters bound to the model id are retrieved from the MySQL database, and the finite element model simulation parameters are returned to the front end for constructing a bone defect repair scaffold.

[0051] Further, in step S3, the strain value ε(i) is:

[0052]

[0053] in,

[0054] and are the displacement components of the support sub-model p(i) in the u and v coordinate axis directions,

[0055] and The strain components of the support sub-model p(i) in the x and y coordinate directions, u, v coordinates, and the conversion functions between x, y coordinates are as follows:

[0056] x=f(u,v),

[0057] y=g(u,v).

[0058] Furthermore, the value of k is 10%.

[0059] Further, S1, constructing a three-dimensional finite element analysis model of tibial fracture internal fixation, and establishing a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model, simulating filling the bone defect area, including:

[0060] Scan and obtain three-dimensional clinical medical scanning data of tibial fracture internal fixation;

[0061] Reconstructing a three-dimensional finite element analysis model of the tibial fracture internal fixation according to the three-dimensional clinical medical scanning data;

[0062] According to the point cloud scanning density of the internally fixed bone defect repair bracket in the three-dimensional clinical medical scanning data, the bone defect area is identified on the three-dimensional finite element analysis model, and the regional contour of the bone defect area is marked;

[0063] The marked area outline is copied and removed, and the space surrounded by the area outline is simulated and filled to simulate and generate a three-dimensional model of the bone defect repair scaffold.

[0064] On the other hand, a device for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis is provided, the device is used to implement the method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, and the device comprises:

[0065] A three-dimensional finite element simulation unit is used to construct a three-dimensional finite element analysis model of tibial fracture internal fixation, and to establish a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model to simulate filling the bone defect area;

[0066] The network division unit is used to divide the three-dimensional model of the bone defect repair scaffold into a plurality of scaffold sub-models pi (i=1, 2, 3.....1000) according to the linear trend of the bone defect area, and configure the corresponding finite element model analysis parameter S for each scaffold sub-model p(i):

[0067] make:

[0068] Si=(E0,σ(i),G F (i)),

[0069] in:

[0070] σ(i)=G F (i) / A(i),

[0071] E0 is the initial elastic model value set for each of the bracket sub-models p(i);

[0072] σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0073] G F(i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i);

[0074] A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i);

[0075] A strain calculation unit, used for performing finite element simulation analysis, and calculating the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0076] The judging unit is used to judge whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation:

[0077] ε(i)∈{εmin(i0), εmax(i0)},

[0078] If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the condition is bound;

[0079] If not, calculate the strain value ε(i) that satisfies the condition, including:

[0080] When ε(i)>εmax(i0):

[0081] make:

[0082] εt(i)=(1-k)εt(i-1),

[0083] When ε(i)≤εmin(i0):

[0084] make:

[0085] εt(i)=(1+k)εt(i-1),

[0086] in,

[0087] i is the number of times the strain value of the stent sub-model p(i) is calculated,

[0088] The value of k is 2.5~15%,

[0089] εt(i-1) is the strain value of the previous bracket sub-model p(i),

[0090] εt(i) is the strain value of the bracket sub-model p(i) at this time;

[0091] After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound;

[0092] The elastic modulus calculation unit is used to traverse the σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i):

[0093] E(i) = σ(i) / ε(i).

[0094] On the other hand, a prediction device is provided, comprising: a processor; a memory, wherein the memory stores computer-readable instructions, and when the computer-readable instructions are executed by the processor, any one of the above-mentioned methods for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis is implemented.

[0095] On the other hand, a computer-readable storage medium is provided, wherein at least one instruction is stored in the storage medium, and the at least one instruction is loaded and executed by a processor to implement any one of the above-mentioned methods for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis.

[0096] The beneficial effects brought about by the technical solution provided by the embodiment of the present invention include at least:

[0097] The present invention establishes a three-dimensional model of a bone defect repair scaffold that simulates the bone defect area, and divides it into a number of scaffold sub-models pi. After simulating the strain load applied by the patient's physiological weight, calculate the strain value ε(i) that p(i) bears under the corresponding finite element simulated physiological load; judge whether the strain value ε(i) of each scaffold sub-model p(i) meets the normal strain range value, and perform finite element simulation on the unsatisfied scaffold sub-model p(i) until the normal strain is met. In this way, ε(i) and elastic modulus E(i) of each scaffold sub-model p(i) are obtained and output for the subsequent preparation of bone defect repair scaffolds. This scheme takes into account the influence of the scaffold elastic modulus and the strain that occurs when the scaffold is subjected to physiological loads, so as to avoid the problem that the bone is damaged due to insufficient elastic modulus and is not conducive to osteogenesis. BRIEF DESCRIPTION OF THE DRAWINGS

[0098] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following briefly introduces the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0099] Figure 1 It is a flow chart of a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis provided by an embodiment of the present invention;

[0100] Figure 2is a schematic diagram of contour marking of an internal fixation bone defect model provided by an embodiment of the present invention;

[0101] Figure 3 It is a block diagram of a device for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis provided by an embodiment of the present invention;

[0102] Figure 4 It is a structural schematic diagram of a prediction device provided by an embodiment of the present invention. DETAILED DESCRIPTION

[0103] The technical solution of the present invention is described below in conjunction with the accompanying drawings.

[0104] In the embodiments of the present invention, words such as "exemplarily" and "for example" are used to indicate examples, illustrations or explanations. Any embodiment or design described as "example" in the present invention should not be interpreted as being more preferred or more advantageous than other embodiments or designs. Specifically, the use of the word "example" is intended to present the concept in a specific way. In addition, in the embodiments of the present invention, the meaning expressed by "and / or" can be both, or it can be either of the two.

[0105] In the embodiments of the present invention, "image" and "picture" can sometimes be used interchangeably. It should be noted that when the difference between them is not emphasized, the meanings they intend to express are the same. "of", "corresponding, relevant" and "corresponding" can sometimes be used interchangeably. It should be noted that when the difference between them is not emphasized, the meanings they intend to express are the same.

[0106] In the embodiments of the present invention, sometimes a subscript such as W1 may be mistakenly written as a non-subscript such as W1. When the difference is not emphasized, the meanings to be expressed are consistent.

[0107] In order to make the technical problems, technical solutions and advantages to be solved by the present invention more clear, a detailed description will be given below with reference to the accompanying drawings and specific embodiments.

[0108] The embodiment of the present invention provides a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis. The method can be implemented by a prediction device, which can be a terminal or a server. Figure 1 The flowchart of the method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis is shown. The processing flow of the method may include the following steps:

[0109] S1. Constructing a three-dimensional finite element analysis model of tibial fracture internal fixation, and establishing a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model, simulating filling the bone defect area, including:

[0110] Scan and obtain three-dimensional clinical medical scanning data of tibial fracture internal fixation;

[0111] Reconstructing a three-dimensional finite element analysis model of the tibial fracture internal fixation according to the three-dimensional clinical medical scanning data;

[0112] According to the point cloud scanning density of the internally fixed bone defect repair bracket in the three-dimensional clinical medical scanning data, the bone defect area is identified on the three-dimensional finite element analysis model, and the regional contour of the bone defect area is marked;

[0113] The marked area outline is copied and removed, and the space surrounded by the area outline is simulated and filled to simulate and generate a three-dimensional model of the bone defect repair scaffold.

[0114] The present invention utilizes finite element simulation software to perform simulation construction and analysis of three-dimensional models, and selects finite element software suitable for biomedical engineering analysis, such as ANSYS, ABAQUS, COMSOL, etc., which is not limited in this embodiment.

[0115] According to the three-dimensional clinical medical scanning data, the detailed steps of reconstructing the three-dimensional finite element analysis model of tibial fracture internal fixation are as follows:

[0116] Data acquisition:

[0117] The three-dimensional data of the tibial fracture site were obtained by CT scanning.

[0118] 3D Reconstruction:

[0119] Import the CT data into professional software (such as Mimics) and perform threshold segmentation, region growing and other processing to generate a three-dimensional model of the tibia and surrounding tissues.

[0120] The tibia model was exported and further processed in software such as Geomagic to generate a geometric model.

[0121] Constructing the internal fixation device:

[0122] Construct a 3D model of the internal fixation device (such as a screw) in software such as Solidwork.

[0123] Finite element analysis pre-processing:

[0124] The models of the tibia and internal fixation device were imported into software such as Hypermesh for meshing.

[0125] Assign material properties, construct ligaments, and set loads and interactions in software such as Abaqus.

[0126] Combination Figure 2As shown, because the internal fixation bracket is different from the bone in the three-dimensional scanning image of the bone, it will be differentially developed, and the corresponding scanning image density displayed in different scanning sequences is also different. Therefore, the contour of the bone defect area can be marked according to the difference in scanning data.

[0127] To identify the bone defect area on the 3D finite element analysis model and mark the contour of the area based on the point cloud scan density of the internal fixation bone defect repair bracket in the 3D clinical medical scan data, the following steps can be followed:

[0128] 1. Data preparation:

[0129] Import 3D clinical medical scan data, which typically includes DICOM files generated by CT or MRI scans.

[0130] Import the CAD model of the internal fixation bone defect repair scaffold and ensure that it is aligned with the scan data in the coordinate system.

[0131] 2. Point cloud processing:

[0132] Point cloud data were extracted from the scan data, with a particular focus on the area associated with the bone defect repair scaffold.

[0133] The point cloud scan density is analyzed to identify areas of abnormal or missing density that may correspond to bone defects.

[0134] 3. Update of 3D finite element model:

[0135] The identified bone defect area information is mapped onto the three-dimensional finite element analysis model.

[0136] In the finite element model, the contour of the bone defect area was marked based on the analysis results of the point cloud scan density.

[0137] 4. Contour marking:

[0138] Use appropriate graphical tools or software functions to clearly mark the outline of the bone defect area on the 3D finite element model. Figure 2 Outline of the area marked as shown.

[0139] This can be achieved by creating boundary conditions, surface markers, or specific geometry so that it can be easily identified in subsequent analysis.

[0140] 5. Subsequent analysis:

[0141] Further finite element analysis, such as stress distribution and displacement, is performed using the marked bone defect area information.

[0142] Based on the analysis results, the effect of the internal fixation bone defect repair scaffold was evaluated and guidance was provided for subsequent clinical treatment.

[0143] Through the above steps, the bone defect area can be accurately identified and marked on the three-dimensional finite element analysis model, providing strong support for subsequent analysis and treatment.

[0144] For the marked area contour, the model body of the three-dimensional area contour area can be copied and moved out in the finite element three-dimensional application software, and the space surrounded by the area contour can be simulated and filled to simulate and generate the three-dimensional model of the bone defect repair scaffold.

[0145] S2. According to the linear trend of the bone defect area, the three-dimensional model of the bone defect repair scaffold is divided into a number of scaffold sub-models pi (i=1, 2, 3.....1000), and a corresponding finite element model analysis parameter S is configured for each of the scaffold sub-models p(i):

[0146] make:

[0147] Si=(E0,σ(i),G F (i)),

[0148] in:

[0149] σ(i)=G F (i) / A(i),

[0150] E0 is the initial elastic model value set for each of the bracket sub-models p(i);

[0151] σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0152] G F (i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i);

[0153] A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i);

[0154] In order to improve the efficiency of the analysis, this department divides the model into several sub-models along the direction of the bone defect, and performs finite element simulation analysis on each sub-model to complete the analysis of the entire bone defect repair scaffold. Through unit division and analysis, the bone defect area can be analyzed in detail, and the practicality of the bone defect repair scaffold can be further accurately analyzed and tested.

[0155] When dividing the sub-models, in order to divide the three-dimensional model of the bone defect repair scaffold into several scaffold sub-models according to the linear trend of the bone defect area, the following steps can be followed:

[0156] 1. Analyze the bone defect area:

[0157] Carefully study the three-dimensional clinical medical scanning data, especially the linear direction and morphology of the bone defect area.

[0158] Determine the main axes or characteristic lines of the bone defect area, which will serve as the basis for dividing the scaffold sub-model.

[0159] 2. Determine the partitioning strategy:

[0160] According to the linear orientation of the bone defect area, decide how to divide the scaffold sub-model.

[0161] It is possible to consider dividing the bracket into multiple parts along the main axis, with each part corresponding to a sub-model.

[0162] Make sure that the divided sub-models can completely cover the bone defect area and that there is a certain overlap or connection area between the sub-models to ensure the integrity and stability after repair.

[0163] 3. Create the bracket sub-model:

[0164] Use three-dimensional modeling software (such as CAD software) to open the three-dimensional model of the bone defect repair scaffold.

[0165] According to the determined division strategy, the stent model is divided into several stent sub-models using the cutting tool or Boolean operation function of the software.

[0166] Name and number each sub-model to facilitate subsequent management and assembly.

[0167] 4. Optimize sub-model design:

[0168] Check the shape and size of each scaffold sub-model to ensure that it meets the repair requirements of the bone defect area.

[0169] Make necessary adjustments and optimizations to the sub-model, such as modifying the shape, adjusting the size, adding connection structures, etc., to improve the repair effect and stability.

[0170] The divided scaffold sub-model was compared with the original bone defect repair scaffold model to ensure the accuracy and completeness of the division.

[0171] Carry out necessary simulation tests or experimental verification to evaluate the performance and effect of the divided bracket sub-model in practical applications.

[0172] 5. Assembly and fixing:

[0173] In practical applications, the divided bracket sub-models are assembled and fixed as needed.

[0174] Use appropriate connectors or fixtures to ensure that the sub-models are tightly connected to form a stable overall structure.

[0175] Through the above steps, the three-dimensional model of the bone defect repair scaffold can be divided into several scaffold sub-models according to the linear direction of the bone defect area, so as to provide convenience and support for subsequent repair surgery or treatment.

[0176] After the division, the finite element parameters are configured, mainly configuring the corresponding finite element model analysis parameters S for each of the bracket sub-models p(i):

[0177] E0 is the initial elastic model value set for each of the bracket sub-models p(i);

[0178] σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0179] G F (i) is the finite element simulated physiological load configured for the stent sub-model p(i), and the finite element simulated physiological load is generated through finite element simulation according to the physiological weight of the patient at the corresponding part of the stent sub-model p(i).

[0180] Finite element simulation of physiological loads, which are added by the user.

[0181] S3, performing finite element simulation analysis to calculate the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0182] In order to perform finite element simulation analysis and calculate the strain value ε(i) of each stent sub-model (p(i)) under the corresponding finite element simulated physiological load, the following steps can be taken:

[0183] 1. Preparatory stage

[0184] 2. Pre-treatment

[0185] a. Constructing finite element model

[0186] Import the geometric data of the bracket sub-model into the finite element software.

[0187] The model is simplified as necessary to reduce the amount of computation while retaining key features.

[0188] b. Grid division

[0189] Mesh the bracket submodel and select an appropriate mesh type and size.

[0190] Ensure the quality of the mesh and avoid deformed meshes that affect calculation accuracy.

[0191] c. Define material properties

[0192] Set the mechanical properties parameters of the material in the finite element software.

[0193] If material properties vary with conditions such as temperature and humidity, the effects of these factors need to be considered.

[0194] d. Apply boundary conditions and loads

[0195] According to the actual situation, appropriate boundary conditions are applied to the bracket sub-model.

[0196] Simulate physiological loads such as pressure, tension, torque, etc. and apply them to the model.

[0197] 3. Solution

[0198] a. Select solver

[0199] Select the appropriate solver based on the analysis type (static, dynamic, nonlinear, etc.).

[0200] b. Run the simulation

[0201] Start the solver and perform finite element simulation analysis.

[0202] Monitor the solution process to ensure that the analysis converges.

[0203] 4. Post-processing

[0204] a. Extraction results

[0205] Extract analysis results from the solver including displacements, stresses, strains, and more.

[0206] Special attention is paid to the strain value ε(i) of the scaffold sub-model under physiological load.

[0207] The calculation formula of the strain value ε(i) is as follows:

[0208]

[0209] in,

[0210] and are the displacement components of the support sub-model p(i) in the u and v coordinate axis directions,

[0211] and The strain components of the support sub-model p(i) in the x and y coordinate directions, u, v coordinates, and the conversion functions between x, y coordinates are as follows:

[0212] x=f(u,v),

[0213] y=g(u,v).

[0214] The specific parameters can be calculated according to the user's input.

[0215] b. Data processing

[0216] The extracted strain values ​​are collated and analyzed.

[0217] Calculate statistics such as average strain, maximum strain, and minimum strain.

[0218] c. Result visualization

[0219] Use the visualization tool of the finite element software to display the strain distribution of the bracket sub-model.

[0220] The size and distribution of strain values ​​are intuitively represented by means of colors, contour lines, etc.

[0221] Through the above steps, you can complete the finite element simulation analysis and calculate the strain values ​​of each stent sub-model (p(i)) under the corresponding finite element simulated physiological load. These strain values ​​are of great significance for evaluating the performance, stability and safety of the stent.

[0222] S4, judging whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation:

[0223] ε(i)∈{εmin(i0), εmax(i0)},

[0224] εmin(i0) is the minimum strain threshold set for each sub-model, and εmax(i0) is the maximum strain threshold set for each sub-model, which can be set according to the location of the bone defect area where each sub-model is located;

[0225] If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound; the strain value ε(i) corresponding to the qualified bracket sub-model p(i) is calculated here, and the binding facilitates the subsequent reading of qualified simulation analysis parameters;

[0226] If not, calculate the strain value ε(i) that satisfies the condition, including:

[0227] When ε(i)>εmax(i0):

[0228] make:

[0229] εt(i)=(1-k)εt(i-1),

[0230] When ε(i)≤εmin(i0):

[0231] make:

[0232] εt(i)=(1+k)εt(i-1),

[0233] in,

[0234] i is the number of times the strain value of the stent sub-model p(i) is calculated,

[0235] The value of k is 2.5~15%,

[0236] εt(i-1) is the strain value of the previous bracket sub-model p(i),

[0237] εt(i) is the strain value of the bracket sub-model p(i) at this time;

[0238] After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound;

[0239] Here the strain values ​​are corrected:

[0240] When the strain value of the sub-model exceeds the maximum strain threshold of this time, it is necessary to perform a reduction correction. The strain value of the current sub-model p(i) is recalculated based on the strain value of the stent sub-model p(i) calculated last time. For example, if the value of k is 10%, the strain value of the stent sub-model p(i) recalculated this time is 90% of the last calculated result, thereby reducing its strain result and performing a correction of the qualified range.

[0241] If it is greater, it will be enlarged in the same way.

[0242] Through the above correction, the strain values ​​of all sub-models are in a qualified state and can be used for subsequent calculations and simulation analysis after correction.

[0243] S5. Traverse σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i):

[0244] E(i) = σ(i) / ε(i).

[0245] After the strain and elastic modulus simulation calculations of each sub-model,

[0246] Furthermore, the method further comprises the following steps:

[0247] Mark each of the support sub-models p(i) with a model id;

[0248] When the strain value ε(i) and the corresponding elastic modulus E(i) of each of the bracket sub-models p(i) are obtained:

[0249] Bind the strain value ε(i) and the corresponding elastic modulus E(i) of the stent sub-model p(i) to the model id of the corresponding stent sub-model p(i), and generate finite element model simulation parameters of each stent sub-model p(i);

[0250] The finite element model simulation parameters of the bracket sub-model p(i) are saved in the MySQL database.

[0251] Furthermore, the method further comprises the following steps:

[0252] When designing a bone defect scaffold, it is necessary to refer to the finite element model simulation parameters of the corresponding scaffold sub-model p(i):

[0253] According to the model id marked on the corresponding scaffold sub-model p(i), the finite element model simulation parameters bound to the model id are retrieved from the MySQL database, and the finite element model simulation parameters are returned to the front end for constructing a bone defect repair scaffold.

[0254] The present invention can extract the strain value and elastic modulus value of each scaffold sub-model by traversing, and obtain the strain value and elastic modulus value of the entire model by summing up each scaffold sub-model. When summing, weights can be assigned to each scaffold sub-model according to the linear trend of the bone defect area, and the model strain and elastic modulus parameters of the entire bone defect repair scaffold are obtained by summing the weights and the product of the strain value or elastic modulus value of each sub-model.

[0255] After the above sub-model division, the model can be marked with the model ID number to facilitate the construction of the corresponding sub-model simulation analysis directory, which is convenient for users to search by ID according to the number. After traversing and obtaining the corresponding parameters of the corresponding sub-model, it can be bound to the ID of the model, which is convenient for the administrator to query the corresponding data of each sub-model according to the ID.

[0256] By binding the ID, the access parameters of each sub-model can be generated and saved in the MYSQL database. If the user wants to query the sub-model of a certain bone defect area in the future, he can perform navigation query through the ID.

[0257] You can also configure the ID attributes of the sub-models. For example, the feature description of the defect area of ​​each model, the CT image of the feature defect area, etc. can all be bound to the ID and configured with corresponding attributes.

[0258] When constructing a bone defect repair scaffold, the repair parameters of a certain defect area can be designed based on the binding parameters of the sub-model of the area. For example, for a certain bone defect area, the ID of the corresponding sub-model can be retrieved in the MYSQL database based on its attributes, and the strain or elastic modulus parameters of the sub-model can be retrieved, so that users can design the bone defect repair scaffold of the corresponding area for reference.

[0259] Figure 3 The present invention is a block diagram of a device for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to an exemplary embodiment. The device is used in a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis. Figure 3 The device includes a three-dimensional finite element simulation unit 310, a network division unit 320, a strain calculation unit 330, a judgment unit 340 and an elastic modulus calculation unit 350. Among them:

[0260] A three-dimensional finite element simulation unit is used to construct a three-dimensional finite element analysis model of tibial fracture internal fixation, and to establish a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model to simulate filling the bone defect area;

[0261] The network division unit is used to divide the three-dimensional model of the bone defect repair scaffold into a plurality of scaffold sub-models pi (i=1, 2, 3.....1000) according to the linear trend of the bone defect area, and configure the corresponding finite element model analysis parameter S for each scaffold sub-model p(i):

[0262] make:

[0263] Si=(E0,σ(i),G F (i)),

[0264] in:

[0265] σ(i)=G F (i) / A(i),

[0266] E0 is the initial elastic model value set for each of the bracket sub-models p(i);

[0267] σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0268] G F (i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i);

[0269] A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i);

[0270] A strain calculation unit, used for performing finite element simulation analysis, and calculating the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load;

[0271] The judging unit is used to judge whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation:

[0272] ε(i)∈{εmin(i0), εmax(i0)},

[0273] If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the condition is bound;

[0274] If not, calculate the strain value ε(i) that satisfies the condition, including:

[0275] When ε(i)>εmax(i0):

[0276] make:

[0277] εt(i)=(1-k)εt(i-1),

[0278] When ε(i)≤εmin(i0):

[0279] make:

[0280] εt(i)=(1+k)εt(i-1),

[0281] in,

[0282] i is the number of times the strain value of the stent sub-model p(i) is calculated,

[0283] The value of k is 2.5~15%,

[0284] εt(i-1) is the strain value of the previous bracket sub-model p(i),

[0285] εt(i) is the strain value of the bracket sub-model p(i) at this time;

[0286] After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound;

[0287] The elastic modulus calculation unit is used to traverse the σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i):

[0288] E(i) = σ(i) / ε(i).

[0289] The functions and interactive relationships of the various modules of the above-mentioned device should be understood in conjunction with the above-mentioned method, and will not be elaborated in this embodiment.

[0290] Figure 4 is a schematic diagram of a structure of a prediction device provided by an embodiment of the present invention, such as Figure 4 As shown, the prediction device may include the above Figure 3 The elastic modulus prediction device for bone defect repair scaffold based on finite element analysis is shown. Optionally, the prediction device 410 may include a first processor 2001 .

[0291] Optionally, the prediction device 410 may further include a memory 2002 and a transceiver 2003 .

[0292] The first processor 2001, the memory 2002 and the transceiver 2003 may be connected via a communication bus.

[0293] Combine the following Figure 4 The components of the prediction device 410 are described in detail:

[0294] The first processor 2001 is the control center of the prediction device 410, and may be a processor or a general term for multiple processing elements. For example, the first processor 2001 is one or more central processing units (CPUs), or an application specific integrated circuit (ASIC), or one or more integrated circuits configured to implement the embodiments of the present invention, such as one or more microprocessors (digital signal processors, DSPs), or one or more field programmable gate arrays (FPGAs).

[0295] Optionally, the first processor 2001 may perform various functions of the prediction device 410 by running or executing a software program stored in the memory 2002 and calling data stored in the memory 2002 .

[0296] In a specific implementation, as an embodiment of a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, the first processor 2001 may include one or more CPUs, for example Figure 4 CPU0 and CPU1 are shown in FIG.

[0297] In a specific implementation, as an embodiment of a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, the prediction device 410 may also include multiple processors, such as Figure 4 The first processor 2001 and the second processor 2004 are shown in FIG. Each of these processors can be a single-core processor (single-CPU) or a multi-core processor (multi-CPU). The processor here can refer to one or more devices, circuits, and / or processing cores for processing data (e.g., computer program instructions).

[0298] The memory 2002 is used to store the software program for executing the solution of the present invention, and is controlled to be executed by the first processor 2001. The specific implementation method can refer to the above method embodiment, which will not be repeated here.

[0299] Optionally, the memory 2002 may be a read-only memory (ROM) or other types of static storage devices that can store static information and instructions, a random access memory (RAM) or other types of dynamic storage devices that can store information and instructions, or an electrically erasable programmable read-only memory (EEPROM), a compact disc read-only memory (CD-ROM) or other optical disc storage, optical disc storage (including compressed optical disc, laser disc, optical disc, digital versatile disc, Blu-ray disc, etc.), a magnetic disk storage medium or other magnetic storage device, or any other medium that can be used to carry or store the desired program code in the form of instructions or data structures and can be accessed by a computer, but is not limited thereto. The memory 2002 may be integrated with the first processor 2001, or may exist independently, and may be accessed through the interface circuit ( Figure 4 (not shown) is coupled to the first processor 2001, which is not specifically limited in this embodiment of the present invention.

[0300] The transceiver 2003 is used to communicate with a network device or a terminal device.

[0301] Optionally, the transceiver 2003 may include a receiver and a transmitter ( Figure 4 The receiver is used to implement a receiving function, and the transmitter is used to implement a sending function.

[0302] Optionally, the transceiver 2003 may be integrated with the first processor 2001, or may exist independently, and may be connected to the first processor 2001 through the interface circuit ( Figure 4 (not shown) is coupled to the first processor 2001, which is not specifically limited in this embodiment of the present invention.

[0303] It should be noted that Figure 4 The structure of the prediction device 410 shown in the figure does not constitute a limitation on the router, and the actual knowledge structure recognition device may include more or fewer components than shown in the figure, or combine certain components, or arrange the components differently.

[0304] In addition, the technical effects of the prediction device 410 can refer to the technical effects of the bone defect repair scaffold elastic modulus prediction method based on finite element analysis described in the above method embodiment, which will not be repeated here.

[0305] It should be understood that the first processor 2001 in the embodiment of the present invention may be a central processing unit (CPU), and the processor may also be other general-purpose processors, digital signal processors (DSP), application specific integrated circuits (ASIC), field programmable gate arrays (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor may be a microprocessor or the processor may also be any conventional processor, etc.

[0306] It should also be understood that the memory in the embodiments of the present invention may be a volatile memory or a non-volatile memory, or may include both volatile and non-volatile memories. Among them, the non-volatile memory may be a read-only memory (ROM), a programmable read-only memory (PROM), an erasable programmable read-only memory (EPROM), an electrically erasable programmable read-only memory (EEPROM), or a flash memory. The volatile memory may be a random access memory (RAM), which is used as an external cache. By way of example and not limitation, many forms of random access memory (RAM) are available, such as static RAM (SRAM), dynamic random access memory (DRAM), synchronous DRAM (SDRAM), double data rate synchronous dynamic random access memory (DDR SDRAM), enhanced synchronous dynamic random access memory (ESDRAM), synchronous link DRAM (SLDRAM), and direct rambus RAM (DR RAM).

[0307] The above embodiments can be implemented in whole or in part by software, hardware (such as circuits), firmware or any other combination. When implemented by software, the above embodiments can be implemented in whole or in part in the form of a computer program product. The computer program product includes one or more computer instructions or computer programs. When the computer instructions or computer programs are loaded or executed on a computer, the process or function described in the embodiment of the present invention is generated in whole or in part. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device. The computer instructions can be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another computer-readable storage medium. For example, the computer instructions can be transmitted from one website, computer, server or data center to another website, computer, server or data center by wired (such as infrared, wireless, microwave, etc.). The computer-readable storage medium can be any available medium that can be accessed by a computer or a data storage device such as a server or data center that contains one or more available media sets. The available medium can be a magnetic medium (for example, a floppy disk, a hard disk, a tape), an optical medium (for example, a DVD), or a semiconductor medium. The semiconductor medium can be a solid-state hard disk.

[0308] It should be understood that the term "and / or" in this article is only a description of the association relationship of associated objects, indicating that there may be three relationships. For example, A and / or B can represent: the existence of A alone, the existence of A and B at the same time, and the existence of B alone, where A and B can be singular or plural. In addition, the character " / " in this article generally indicates that the previous and next associated objects are in an "or" relationship, but it may also indicate an "and / or" relationship, which can be understood by referring to the previous and next contexts.

[0309] In the present invention, "at least one" means one or more, and "more than one" means two or more. "At least one of the following" or similar expressions refers to any combination of these items, including any combination of single or plural items. For example, at least one of a, b, or c can be represented by: a, b, c, ab, ac, bc, or abc, where a, b, c can be single or multiple.

[0310] It should be understood that in various embodiments of the present invention, the size of the serial numbers of the above-mentioned processes does not mean the order of execution. The execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiments of the present invention.

[0311] Those of ordinary skill in the art will appreciate that the units and algorithm steps of each example described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of the present invention.

[0312] Those skilled in the art can clearly understand that, for the convenience and brevity of description, the specific working processes of the above-described equipment, devices and units can refer to the corresponding processes in the aforementioned method embodiments and will not be repeated here.

[0313] In the several embodiments provided by the present invention, it should be understood that the disclosed equipment, devices and methods can be implemented in other ways. For example, the device embodiments described above are only schematic. For example, the division of the units is only a logical function division of a method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis. There may be other division methods in actual implementation, such as multiple units or components can be combined or integrated into another device, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be an indirect coupling or communication connection through some interfaces, devices or units, which can be electrical, mechanical or other forms.

[0314] The units described as separate components may or may not be physically separated, and the components shown as units may or may not be physical units, that is, they may be located in one place or distributed on multiple network units. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of this embodiment.

[0315] In addition, each functional unit in each embodiment of the present invention may be integrated into one processing unit, or each unit may exist physically separately, or two or more units may be integrated into one unit.

[0316] If the functions are implemented in the form of software functional units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention can be essentially or partly embodied in the form of a software product that contributes to the prior art. The computer software product is stored in a storage medium and includes several instructions for enabling a computer device (which can be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the methods described in various embodiments of the present invention. The aforementioned storage medium includes: various media that can store program codes, such as a USB flash drive, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk or an optical disk.

[0317] The above is only a specific embodiment of the present invention, but the protection scope of the present invention is not limited thereto. Any person skilled in the art can easily think of changes or substitutions within the technical scope disclosed by the present invention, which should be included in the protection scope of the present invention. Therefore, the protection scope of the present invention should be based on the protection scope of the claims.

Claims

1. A method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, which is used to design the elastic modulus of a bone defect scaffold, characterized in that: The method comprises: S1. constructing a three-dimensional finite element analysis model of tibial fracture internal fixation, and establishing a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model to simulate filling the bone defect area; S2. According to the linear trend of the bone defect area, the three-dimensional model of the bone defect repair scaffold is divided into a number of scaffold sub-models pi (i=1, 2, 3.....1000), and a corresponding finite element model analysis parameter S is configured for each of the scaffold sub-models p(i): make: Si=(E0,σ(i),G F (and)), in: σ(i)=G F (i) / A(i), E0 is the initial elastic model value set for each of the bracket sub-models p(i); σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load; G F (i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i); A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i); S3, performing finite element simulation analysis to calculate the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load; S4, judging whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation: ε(i)∈{εmin(i0), εmax(i0)}, If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the condition is bound; If not, calculate the strain value ε(i) that satisfies the condition, including: When ε(i)>εmax(i0): make: εt(i)=(1-k)εt(i-1), When ε(i)≤εmin(i0): make: εt(i)=(1+k)εt(i-1), in, i is the number of times the strain value of the stent sub-model p(i) is calculated, The value of k is 2.5~15%, εt(i-1) is the strain value of the previous bracket sub-model p(i), εt(i) is the strain value of the bracket sub-model p(i) at this time; After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound; S5. Traverse σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i): E(i) = σ(i) / ε(i).

2. The method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to claim 1, characterized in that: The following steps are also included: Mark each of the support sub-models p(i) with a model id; When the strain value ε(i) and the corresponding elastic modulus E(i) of each of the bracket sub-models p(i) are obtained: Bind the strain value ε(i) and the corresponding elastic modulus E(i) of the stent sub-model p(i) to the model id of the corresponding stent sub-model p(i), and generate finite element model simulation parameters of each stent sub-model p(i); The finite element model simulation parameters of the bracket sub-model p(i) are saved in the MySQL database.

3. The method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to claim 1, characterized in that: The following steps are also included: When designing a bone defect scaffold, it is necessary to refer to the finite element model simulation parameters of the corresponding scaffold sub-model p(i): According to the model id marked on the corresponding scaffold sub-model p(i), the finite element model simulation parameters bound to the model id are retrieved from the MySQL database, and the finite element model simulation parameters are returned to the front end for constructing a bone defect repair scaffold.

4. The method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to claim 1, characterized in that: In step S3, the strain value ε(i) is: in, and are the displacement components of the support sub-model p(i) in the u and v coordinate axis directions, and are the strain components of the bracket sub-model p(i) in the x and y coordinate axis directions, The conversion function between u,v coordinates and x,y coordinates is as follows: x=f(u,v), y=g(u,v).

5. The method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to claim 1, characterized in that: The value of k is 10%.

6. The method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis according to claim 1, characterized in that: S1. Constructing a three-dimensional finite element analysis model of tibial fracture internal fixation, and establishing a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model, simulating filling the bone defect area, including: Scan and obtain three-dimensional clinical medical scanning data of tibial fracture internal fixation; Reconstructing a three-dimensional finite element analysis model of the tibial fracture internal fixation according to the three-dimensional clinical medical scanning data; According to the point cloud scanning density of the internally fixed bone defect repair bracket in the three-dimensional clinical medical scanning data, the bone defect area is identified on the three-dimensional finite element analysis model, and the regional contour of the bone defect area is marked; The marked area outline is copied and removed, and the space surrounded by the area outline is simulated and filled to simulate and generate a three-dimensional model of the bone defect repair scaffold.

7. A device for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis, the device being used to implement the method for predicting the elastic modulus of a bone defect repair scaffold based on finite element analysis as claimed in any one of claims 1 to 6, characterized in that: The device comprises: A three-dimensional finite element simulation unit is used to construct a three-dimensional finite element analysis model of tibial fracture internal fixation, and to establish a three-dimensional model of a bone defect repair scaffold matching the bone defect area in the three-dimensional finite element analysis model to simulate filling the bone defect area; The network division unit is used to divide the three-dimensional model of the bone defect repair scaffold into a plurality of scaffold sub-models pi (i=1, 2, 3.....1000) according to the linear trend of the bone defect area, and configure the corresponding finite element model analysis parameter S for each scaffold sub-model p(i): make: Si=(E0,σ(i),G F (and)), in: σ(i)=G F (i) / A(i), E0 is the initial elastic model value set for each of the bracket sub-models p(i); σ(i) is the stress value of each of the stent sub-models p(i) under the corresponding finite element simulated physiological load; G F (i) a finite element simulated physiological load configured for the stent sub-model p(i), the finite element simulated physiological load being generated by finite element simulation according to the physiological weight of the patient at the part corresponding to the stent sub-model p(i); A(i) is the stress cross-sectional area of ​​each of the bracket sub-models p(i); A strain calculation unit, used for performing finite element simulation analysis, and calculating the strain value ε(i) borne by each of the stent sub-models p(i) under the corresponding finite element simulated physiological load; The judging unit is used to judge whether the strain value ε(i) of each of the bracket sub-models p(i) satisfies the following strain range value of normal bone manifestation: ε(i)∈{εmin(i0), εmax(i0)}, If it is satisfied, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the condition is bound; If not, calculate the strain value ε(i) that satisfies the condition, including: When ε(i)>εmax(i0): make: e t (i)=(1-k)e t (i-1), When ε(i)≤εmin(i0): make: εt(i)=(1+k)εt(i-1), in, i is the number of times the strain value of the stent sub-model p(i) is calculated, The value of k is 2.5~15%, εt(i-1) is the strain value of the previous bracket sub-model p(i), εt(i) is the strain value of the bracket sub-model p(i) at this time; After the calculation is completed, the bracket sub-model p(i) corresponding to the strain value ε(i) of the bracket sub-model p(i) that meets the conditions is bound; The elastic modulus calculation unit is used to traverse the σ(i) and ε(i) of each of the bracket sub-models p(i) when the conditions are met, and calculate the elastic modulus E(i) corresponding to each of the bracket sub-models p(i): E(i) = σ(i) / ε(i).

8. A prediction device, characterized in that The prediction device comprises: processor; A memory having computer-readable instructions stored thereon, wherein when the computer-readable instructions are executed by the processor, the method according to any one of claims 1 to 6 is implemented.

9. A computer-readable storage medium, characterized in that: The computer-readable storage medium stores program codes, which can be called by a processor to execute the method according to any one of claims 1 to 6.

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