Artificial total temporomandibular joint prosthesis with bionic elastic modulus local functionalization and preparation method of artificial total temporomandibular joint prosthesis

Abstract

The invention discloses an artificial total temporomandibular joint prosthesis with bionic elastic modulus local functionalization and a preparation method of the artificial total temporomandibular joint prosthesis, and relates to the technical field of artificial total temporomandibular joint prostheses. The method comprises the following steps: mixing nano graphene and polyether-ether-ketone to respectively prepare mixed powder A and mixed powder B; and designing a digital model of the total temporomandibular joint prosthesis, then carrying out material concentration linear function modeling, setting a printing path, selecting 90-degree printing deflection of each layer, and carrying out 3D printing to obtain the total temporomandibular joint prosthesis. The artificial total temporomandibular joint prosthesis with gradient elastic modulus and regional functionalization characteristics can be prepared, the preparation process is simple, personalized prostheses can be customized for patients, and the artificial total temporomandibular joint prosthesis is more in line with individual anatomical physiological structures. The problems that in the prior art, the elastic modulus of an artificial total temporomandibular joint prosthesis is not matched with that of a natural bone, and the prosthesis is prone to loosening are effectively solved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of total artificial temporomandibular joint prosthesis, and particularly relates to a total artificial temporomandibular joint prosthesis with local functionalization of bionic elastic modulus and a preparation method thereof. BACKGROUND

[0002] Artificial temporomandibular joint replacement is the final treatment for severe temporomandibular joint ankylosis, trauma, tumor or joint absorption, which can replace the morphology and function of the original joint by a total artificial joint prosthesis. Since the material of the total artificial temporomandibular joint prosthesis currently used in clinical is mainly titanium and its alloy, the great difference in mechanical strength between the joint prosthesis and the bone can cause uneven distribution of stress, excessive load on the bone around the joint prosthesis, and further lead to bone resorption, osteoporosis and even implant failure. Therefore, it is of great significance in clinical practice to prepare an artificial prosthesis with an elastic modulus matching the natural bone and capable of providing maximum continuous stress protection to the surrounding bone.

[0003] The artificial total temporomandibular joint is structurally composed of two parts, a mandibular condyle prosthesis and a joint socket prosthesis. The mandibular prosthesis is divided into a joint handle end in contact with the bone for fixation, a joint handle for transmitting masticatory stress and restoring mandibular height, and a condyle end for joint function movement. The artificial total temporomandibular joint prosthesis needs to use a material with strong bioactivity at the joint handle end of the mandibular prosthesis to form a stable bone bond between the surrounding bones and increase the stability of the prosthesis. The condyle part of the mandibular prosthesis and the joint socket prosthesis part need a material with high bio-inertness to avoid bone ankylosis between the joint activity and the joint socket, which can cause joint ankylosis, and the area requires high mechanical properties of the prosthesis. Therefore, from the perspective of functional anatomy, the functions required by the artificial total temporomandibular joint at different positions are different, and different materials can be used to make functional gradient materials to meet the functional requirements of different parts of the prosthesis. In addition, the design and material properties of the joint prosthesis have a great influence on the stability and long-term performance of the total temporomandibular joint. For example, if the joint handle structure or material design causes high stress in the prosthesis fixation area, local bone fracture or prosthesis fatigue failure at the prosthesis-bone interface is likely to occur. Therefore, special attention should be paid to the structural component design of the material when different materials are used to prepare the prosthesis to avoid stress concentration areas.

[0004] A non-homogeneous composite material with continuous or discontinuous changes in composition structure and performance in a certain direction of the material, i.e. a functional gradient material, can be prepared by 3D printing. The gradient material with gradual change in chemical composition can effectively alleviate the local stress enhancement caused by the sudden change in interfacial elastic modulus, optimize the stress distribution in the material, and avoid material structural defects caused by stress concentration. The use of gradient design can make the material obtain anisotropic performance enhancement to meet the different performance requirements of different parts of the material.

[0005] The artificial total temporomandibular joint prosthesis commonly used in the clinic at present is mostly of uniform modulus, and no artificial total temporomandibular joint prosthesis prepared from a functional gradient material has been reported. SUMMARY

[0006] In order to solve the above technical problems, the purpose of the present application is to provide an artificial total temporomandibular joint prosthesis with local functionalization of bionic elastic modulus and a preparation method thereof, so as to solve the problems of mismatch between the artificial total temporomandibular joint prosthesis and the elastic modulus of natural bone and easy loosening of the prosthesis in the prior art.

[0007] The technical solution of the present application for solving the above technical problems is as follows: a preparation method of an artificial total temporomandibular joint prosthesis with local functionalization of bionic elastic modulus is provided, comprising the following steps: (1) mixing nanographene and polyether ether ketone to obtain a mixture, adding ethanol, stirring, filtering and drying to prepare a mixed powder A; wherein the amount of nanographene in the mixture is 1wt%; (2) using the same method as step (1), a mixed powder B is prepared; wherein the amount of nanographene in the mixture is 5wt%; (3) designing a digital model of the total temporomandibular joint prosthesis, then performing material concentration linear function modeling, and setting the printing path to select each layer printing deflection 90°, and performing 3D printing; wherein the joint fossa prosthesis of the artificial total temporomandibular joint prosthesis is printed by using the mixed powder A prepared in step (1), and the mandibular condylar process prosthesis of the artificial total temporomandibular joint prosthesis is uniformly printed by using the mixed powder A prepared in step (1) and the mixed powder B of step (2) from the condylar process part to the joint handle part in turn; after printing, cooling to room temperature, peeling off, to obtain an artificial total temporomandibular joint prosthesis with local functionalization of bionic elastic modulus.

[0008] On the basis of the above technical solution, the present application can also be improved as follows: Further, in step (1), the mass-volume ratio of the mixture and ethanol is 1g:5-10mL.

[0009] Further, in step (1), the mass-volume ratio of the mixture and ethanol is 1g:8mL.

[0010] Further, in step (1), magnetic stirring is performed at room temperature for 20-30min.

[0011] Further, in step (1), magnetic stirring is performed at room temperature for 25min.

[0012] Further, in step (1), vacuum filtration is used.

[0013] Further, in step (1), drying is performed at 50-60℃.

[0014] Further, in step (1), drying is carried out at 55 DEG C.

[0015] Further, in step (3), using the CT data of the patient's maxillofacial region, the three-dimensional facial appearance of the patient and the patient's dental model data, referring to the healthy side joint morphology and the aesthetic requirements of the maxillofacial region, the whole temporomandibular joint prosthesis digital model is calculated.

[0016] The application also provides the artificial whole temporomandibular joint prosthesis with local functionalization of bionic elastic modulus prepared by the above method.

[0017] The application has the following beneficial effects: 1. The application can prepare an artificial whole temporomandibular joint prosthesis with gradient elastic modulus and regional functionalization characteristics, which has low raw material cost, good processing performance, can avoid bone loss at the edge of the prosthesis, has good stability, simple and easy-to-operate preparation process, can quickly prepare an artificial whole temporomandibular joint prosthesis, effectively solves the problems of mismatch between the artificial whole temporomandibular joint prosthesis and the natural bone elastic modulus and easy loosening of the prosthesis in the prior art, and is convenient for popularization and use.

[0018] 2. For the mismatch problem of pure titanium prosthesis and natural bone elastic modulus, a high molecular material polyether ether ketone (PEEK) matching the natural bone elastic modulus is used as a base material, high-concentration nano-graphene is used to prepare a PEEK composite at the end of the mandibular prosthesis joint handle to improve the osteogenic potential of PEEK, and low-concentration nano-graphene is used to prepare a PEEK composite at the end of the mandibular prosthesis condyle and the joint socket prosthesis to enhance the mechanical properties of the material. The functional gradient design composite artificial whole temporomandibular joint prosthesis with linearly increasing nano-graphene content from top to bottom is prepared by the method of gradient modeling and anisotropic material printing of different component nano-graphene / polyether ether ketone composites using a two-component 3D printer.

[0019] 3. The gradient artificial whole temporomandibular joint prosthesis with gradually changing chemical composition can effectively relieve the local stress enhancement caused by the sudden change of interface elastic modulus, optimize the stress distribution in the material, and avoid the material structure defects caused by stress concentration. The use of gradient design can make the artificial whole temporomandibular joint prosthesis obtain anisotropic performance enhancement, and meet the different performance requirements of different parts of the artificial whole temporomandibular joint prosthesis.

[0020] 4. By the method of 3D printing, the polyether ether ketone and polyether ether ketone / nano graphene are mixed layer by layer to print the two-component, and the integrated structure, modulus gradient, and local functional composite artificial total temporomandibular joint prosthesis can be prepared. The elastic modulus of the artificial total temporomandibular joint prosthesis is adapted to the elastic modulus of the natural bone, the material stress distribution is uniform, and there is no stress concentration area. The prosthesis has higher osteogenesis efficiency at the joint handle in contact with the bone, and the bone is firmly combined. The mandibular prosthesis condyle and the prosthesis have higher mechanical properties in the joint cavity, and can resist the stress of masticatory movement. The use of such prosthesis can greatly reduce the risk of prosthesis loosening and improve the success rate of joint replacement surgery. In addition, the PEEK artificial total temporomandibular joint prosthesis has radio-transparency, does not produce artifacts in imaging examination, is convenient for clinical imaging to track the observation of surgical efficacy, does not affect radiotherapy, and can be used for occlusal reconstruction after head and neck tumor radiotherapy.

[0021] 5. The present application firstly mixes nano graphene and polyether ether ketone, then adds anhydrous ethanol for magnetic stirring, so that the nano graphene is uniformly dispersed in the polyether ether ketone, which is convenient for subsequent printing, and the obtained artificial total temporomandibular joint prosthesis is uniform in composition; the digital model of the artificial total temporomandibular joint prosthesis is designed and functionally modeled, and each layer is printed with a deflection of 90° so that the materials are staggered and uniformly distributed; in the 3D printing process, the mixing device continuously works to realize dynamic mixing between different material components, the material printing process of fused deposition modeling is promoted, the material digital feeding is realized, and the continuous gradient distribution of the printing material components in the z-axis direction is realized. After printing, the test piece is peeled off after being cooled to room temperature, and the artificial total temporomandibular joint prosthesis with local functionalization of bionic elastic modulus is obtained. BRIEF DESCRIPTION OF DRAWINGS

[0022] Figure 1 It is a schematic diagram of in vivo and in vitro experimental test pieces; Figure 2 It is a tensile modulus statistical diagram; Figure 3 It is a compression modulus statistical diagram; Figure 4 It is a bending modulus statistical diagram; Figure 5 It is a scanning electron microscope observation schematic diagram of a tensile test piece fracture surface; Figure 6 It is a scanning electron microscope observation schematic diagram of BMSCs inoculated for 2h; Figure 7 It is a schematic diagram of the proportion of proliferative cells; Figure 8 It is a schematic diagram of the quantitative detection result of alkaline phosphatase (ALP); Figure 9 It is a schematic diagram of RT-PCR detection of bone formation related genes Figure 1 ; Figure 10Schematic diagram for RT-PCR detection of osteogenesis-related gene expression Figure 2 ; Figure 11 Schematic diagram for RT-PCR detection of osteogenesis-related gene expression Figure 3 ; Figure 12 Schematic diagram for WB detection of osteogenesis-related protein expression Figure 1 ; Figure 13 Schematic diagram for WB detection of osteogenesis-related protein expression Figure 2 ; Figure 14 Schematic diagram for WB detection of osteogenesis-related protein expression Figure 3 ; Figure 15 Schematic diagram for WB detection of osteogenesis-related protein expression Figure 4 ; Figure 16 Schematic diagram of the process of implanting materials into the mandible of rabbits in vivo Figure 17 Three-dimensional reconstruction images of 4-week and 12-week samples Figure 18 Micro CT data analysis 1 of 4-week samples Figure 19 Micro CT data analysis 2 of 4-week samples Figure 20 Micro CT data analysis 3 of 4-week samples Figure 21 Micro CT data analysis 4 of 4-week samples Figure 22 Micro CT data analysis 1 of 12-week samples Figure 23 Micro CT data analysis 2 of 12-week samples Figure 24 Micro CT data analysis 3 of 12-week samples Figure 25 Micro CT data analysis 4 of 12-week samples Figure 26 Methylene blue-acid fuchsin staining results Figure 27 Data analysis of 4-week bone contact ratio Figure 28 Data analysis of 12-week bone contact ratio DETAILED DESCRIPTION

[0023] The principles and features of the present application are described below in conjunction with the accompanying drawings, which are presented only for the purpose of illustrating the present application and are not intended to limit the scope of the present application. The specific conditions not specified in the examples are carried out under conventional conditions or manufacturer's recommended conditions. The reagents or instruments used are not specified by the manufacturer, but are conventional products that can be obtained by commercial purchase.

[0024] Example 1: A method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus local functionalization, comprising the following steps: (1) Mix 1wt% nanographene and polyether ether ketone to obtain a mixture, then add 8mL of anhydrous ethanol to each gram of the mixture, magnetically stir at room temperature for 20min, and then vacuum filter and dry at a temperature of 55°C to obtain 1wt% nanographene / polyether ether ketone mixed powder; (2) Obtain 5wt% nanographene / polyether ether ketone mixed powder by the same method; (3) Design a digital model of the artificial total temporomandibular joint prosthesis, then perform gradient material function modeling according to the scheme of gradually linearly transitioning from 5wt% nanographene / polyether ether ketone mixed powder to 1wt% nanographene / polyether ether ketone mixed powder from bottom to top in the artificial total temporomandibular joint prosthesis, and set the printing path to select a 90° deflection for each layer, then place the 1wt% nanographene / polyether ether ketone mixed powder and 5wt% nanographene / polyether ether ketone mixed powder obtained in step (1) in different barrels of a double-component 3D printer, and perform 3D printing, and after cooling to room temperature, peel off to obtain an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus local functionalization.

[0025] Experimental Example 1: Mechanical property experiment: at 367℃, different mass fractions (0.1%, 0.5%, 1%, 2%, 5%) of nanographene and polyether ether ketone were fully mixed by melt blending method, and the test pieces required for in vivo and in vitro experiments were prepared by hot pressing molding method (such as shown in Figure 1 The mechanical test pieces conforming to the ISQ international standard were prepared by injection molding method.

[0026] Five parallel samples were set in each group, and a universal mechanical testing machine was used to explore the bending, compression, and tensile modulus of the materials, and the fracture surfaces of the test pieces stretched to break were subjected to scanning electron microscopy, and the results are shown in Figures 2-5 .

[0027] As can be seen from Figures 2-5 , the addition of 0.1wt%, 0.5wt%, and 1wt% nanographene can simultaneously improve the mechanical properties of PEEK in the tensile and bending dimensions. However, the addition of 2wt% and 5wt% nanographene respectively leads to a partial decrease in the tensile and compression properties of the composite material.

[0028] Experimental Example 2: In vitro cell biology experiments: BMSCs derived from SD rats were isolated and cultured using the whole bone marrow adherent method. After seeding cells onto PEEK and G-PEEK materials (graphene nanoparticles / polyetheretherketone), the morphology of BMSCs and the effect of G-PEEK on cell adhesion were observed using scanning electron microscopy. Figure 6 The effect of G-PEEK on cell proliferation was investigated by flow cytometry, see [reference needed]. Figure 7 After osteogenic induction for 7 days, BMSCs implanted onto the surfaces of PEEK and G-PEEK were quantitatively detected by ALP. Figure 8 ), RT-PCR ( Figures 9-11 ) and Western Blot ( Figures 12-15 The effects of G-PEEK on osteogenic differentiation of rat BMSCs were studied using methods such as detection.

[0029] Depend on Figure 6 Under low magnification, the cells growing on the PEEK material surface in the control group showed initial adhesion, with irregular hemispherical shapes and incomplete extension. In the G-PEEK group, BMSCs showed good adhesion, with flattened cells adhering to the material surface, fully extended, and exhibiting typical polygonal shapes. The more the content of graphene nanoparticles increased, the more fully the cells extended. Under high magnification, the cells adhered poorly to the PEEK material surface in the control group, with significantly fewer and shorter filamentous pseudopodia compared to the G-PEEK group. In contrast, on the experimental G-PEEK material, cells were tightly connected to the material via filamentous pseudopodia, and the adhesion became more compact with increasing graphene nanoparticle content. Scanning electron microscopy results indicate that the addition of the desired concentration of graphene nanoparticles in this study promoted the adhesion of rat BMSCs to the PEEK material surface.

[0030] Depend on Figure 7 It was found that after culturing BMSCs on the material surface for 3 days, the proportion of cells in the proliferative phase on each group was relatively similar, around 20%, with no significant difference between groups. Flow cytometry results indicated that the addition of the concentration of nanographene in this study had no significant effect on the proliferation of rat BMSCs on polyetheretherketone (PEEK) material.

[0031] Depend on Figure 8It was found that after 7 days of osteogenic induction, the relative ALP activity of cells on the surface of the G-PEEK group was significantly higher than that of the PEEK control group. Furthermore, with the increase of the nanographene content, the relative ALP activity of cells adhering to the material in each G-PEEK group showed an increasing trend. Specifically, there was no significant difference between the 0.1% G-PEEK group and the control group, while the ALP expression level of the 0.5% G-PEEK group was significantly higher than that of the control group (p < 0.01). There was no significant difference in ALP expression levels among the 0.5%, 1%, and 2% G-PEEK groups. The ALP expression level of the 5% G-PEEK group was significantly higher than that of the other five groups (p < 0.001).

[0032] Depend on Figures 9-11 It was found that, except for the 0.1% G-PEEK group, the expression of G-PEEK-related genes in all experimental groups was upregulated compared to the control group, and the differences were statistically significant. With the increase of nanographene content, the expression of bone-related genes in each component generally showed a gradual upward trend. This indicates that 0.5%-5% G-PEEK significantly promoted the expression of osteogenic-related genes in BMSCs.

[0033] Depend on Figures 12-15 It was found that the expression levels of OPN, RUNX2, and ALP in the experimental group were significantly upregulated compared with those in the control group, and the differences between the groups were statistically significant (P < 0.05). Furthermore, this osteogenic effect showed a clear concentration-dependent effect; as the concentration of added graphene nanoparticles increased, the expression levels of osteogenic-related proteins were upregulated.

[0034] In vitro cell experiments showed that the addition of nano-graphene significantly promoted the adhesion and osteogenic differentiation of rat BMSCs on the surface of PEEK material, and this promoting effect was concentration-dependent; the higher the content of nano-graphene in the composite material, the stronger the promoting effect.

[0035] Experimental Example 3 In vitro animal experiments: G-PEEK and PEEK materials were implanted into the rabbit mandible (see...). Figure 16 The osteointegration effect of G-PEEK was evaluated based on the area of ​​newly formed bone and the bone contact rate around the material. Samples were harvested at 4 and 12 weeks after implantation, and the area of ​​newly formed bone and the bone contact rate around the material were evaluated using MicroCT scans and hard tissue staining. Since the results in Experiment 2 showed no significant difference among the 0.5%, 1%, and 2% groups in promoting osteogenic differentiation, this experiment retained the 1% G-PEEK experimental group and selected a pure PEEK control group, a 0.1% PEEK group, a 1% PEEK group, and a 5% PEEK group for the experiment.

[0036] At 4 and 12 weeks post-surgery, three rabbits were randomly sacrificed for micro-CT scans, and the Region of Interest (ROI) was analyzed using μCTEvaluation Program V6 (ROI defined as the area within 250 μm of the sample circumference). The 3D reconstructed images are shown below. Figure 17 As shown, the statistical analysis results of ROI for 4 weeks and 12 weeks are as follows: Figures 18-25 Following Micro-CT examination, the samples were embedded in hard tissue, sectioned, and stained with methylene blue and acid fuchsin. The osseointegration effect at the implant-bone interface after G-PEEK was observed under an optical microscope. The methylene blue and acid fuchsin staining results are as follows: Figure 26 As shown; to more intuitively evaluate the impact of G-PEEK composite implants on implant-bone interface osseointegration, ImageJ software was used to quantitatively analyze the implant-bone contact area / total area in methylene blue acid fuchsin stained images. The results are shown below. Figures 27-28 As shown.

[0037] Depend on Figure 17 It was observed that the PEEK material itself was not radiolucent; the white high-density areas represented newly formed bone tissue surrounding the material. Three-dimensional reconstruction showed that after 4 weeks, the G-PEEK group material surface had a certain degree of newly formed bone coverage, while the PEEK group material surface showed almost no obvious newly formed bone. Furthermore, the area of ​​newly formed bone coverage on the G-PEEK material surface increased with increasing graphene nanoparticle content. Three-dimensional reconstruction results after 12 weeks indicated that with prolonged implantation time, both G-PEEK and PEEK materials showed significant bone growth. The newly formed bone around the G-PEEK material was significantly thicker than at 4 weeks, with a significantly increased bone coverage area, while the PEEK control group material surface showed a thin layer of newly formed bone. The amount of newly formed bone in the G-PEEK group was greater than that in the PEEK group.

[0038] Depend on Figures 18-25 It was found that the bone volume / total volume (BV / TV) of the 1% and 5% G-PEEK groups at 4 weeks was significantly higher than that of the control group, and the difference between the groups was statistically significant (P < 0.01). Meanwhile, the number of trabecular bone (Tb.N) and the thickness of trabecular bone (Tb.Th) also showed an increasing trend with the increase of the nano-graphene content in the G-PEEK material. The intertrabecular spacing (Tb.Sp) showed a decreasing trend with the increase of the nano-graphene content.

[0039] Depend on Figure 26It was observed that 4 weeks post-implantation, the PEEK group showed almost no significant new bone formation. The G-PEEK groups exhibited significantly higher new bone area and trabecular bone thickness compared to the PEEK group, with the new bone volume gradually increasing with the increase in graphene content. At 12 weeks post-implantation, the new bone coverage area in each group was significantly increased compared to 4 weeks. A thin layer of new bone appeared on the surface of the PEEK group, while the G-PEEK group showed a significantly larger new bone area. Furthermore, the new bone area increased with the increase in graphene content, and the trabecular bone adhered tightly to the material surface.

[0040] Depend on Figures 27-28 It was observed that 4 weeks after implantation, the bone contact ratio increased with the addition of nano-graphene. There was no significant difference between the 0.1% G-PEEK group and the pure PEEK group, while the bone contact ratios of the 1% and 5% G-PEEK groups were significantly higher than those of the PEEK group, with statistically significant differences between groups (P < 0.01). 12 weeks after implantation, the bone contact ratios of all G-PEEK groups were still significantly higher than those of the PEEK group, with statistically significant differences (P < 0.05). The 0.1% G-PEEK, 1% G-PEEK, and 5% G-PEEK groups all achieved relatively complete bone contact, but there were no statistically significant differences between groups.

[0041] In vitro animal experiments showed that, compared with pure polyether ether ketone (PEEK group), the nano-graphene / polyether ether ketone composite implant (G-PEEK group) significantly promoted osseointegration at the interface after implantation into the rabbit mandible, and the osseointegration capacity increased with the increase of nano-graphene content in the composite material.

[0042] In summary, the mechanical properties of the graphene / polyetheretherketone (PEEK) material are improved when the mass concentration of graphene is low (0.1%-1%). At higher concentrations (2%-5%), the material exhibits superior osseointegration. Therefore, using 1wt%-5wt% graphene / PEEK composite materials to design functionally graded artificial temporomandibular joint prostheses yields the best results.

[0043] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization, characterized in that, Includes the following steps: (1) Nanographene and polyetheretherketone were mixed to obtain a mixture, ethanol was added, the mixture was stirred, filtered and dried to obtain mixed powder A; wherein the amount of nanographene in the mixture was 1 wt%; (2) Using the same method as in step (1), mixed powder B was prepared; wherein the amount of nano-graphene in the mixture was 5 wt%; (3) Design a digital model of the total temporomandibular joint prosthesis, then perform linear function modeling of material concentration, and set the printing path to select 90° deflection for each layer of printing, and perform 3D printing; wherein, the joint socket prosthesis of the artificial total temporomandibular joint prosthesis is printed with mixed powder A obtained in step (1), and the mandibular condyle prosthesis of the artificial total temporomandibular joint prosthesis is printed uniformly from the condyle to the joint stem by mixed powder A obtained in step (1) and mixed powder B obtained in step (2); after printing, cool to room temperature, peel off, and obtain an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized function.

2. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the mass-volume ratio of the mixture to ethanol is 1g:5-10mL.

3. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the mass-volume ratio of the mixture to ethanol is 1 g: 8 mL.

4. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the mixture is magnetically stirred for 20-30 minutes at room temperature.

5. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the mixture is magnetically stirred for 25 minutes at room temperature.

6. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), vacuum filtration is used.

7. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the product is dried at 50-60℃.

8. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (1), the product is dried at 55°C.

9. The method for preparing an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization according to claim 1, characterized in that, In step (3), the patient's maxillofacial CT data, the patient's three-dimensional facial features and the patient's dental model data are used to calculate the digital model of the temporomandibular joint prosthesis by referring to the joint morphology of the healthy side and the aesthetic requirements of the maxillofacial region.

10. The artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization, prepared by the method of any one of claims 1-9, is an artificial total temporomandibular joint prosthesis with biomimetic elastic modulus localized functionalization.

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