Preparation of bimetallic ion hydrogel coating on surface of polyether-ether-ketone bone implant
By constructing a hydrogel coating with synergistic effects of Mg2+ and Ag+ on the surface of PEEK bone implants, the shortcomings of PEEK bone implants in osteointegration and antibacterial properties were solved, and efficient and safe modification effects were achieved, promoting osteoblast proliferation and inhibiting bacterial growth.
Patent Information
- Application Number
- CN202510191772.6
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2025-02-21
- Publication Date
- 2025-07-04
AI Technical Summary
Existing PEEK bone implants have shortcomings in osteointegration and antibacteriality, and traditional modification methods are complex and may affect biosafety.
The polyether ether ketone substrate was pretreated by acid-base, and a photocuring method was combined with the photocuring method to construct a bimetallic ion hydrogel coating. The coating contained Mg2+ and Ag+, which was used to improve osseous integration and antibacterial properties.
Significantly promote osteoblast proliferation, improve bone mineralization and deposition, inhibit bacterial growth, simplify process flow, reduce production costs, and improve biosafety.
Smart Images
Figure CN120242157A_ABST
Abstract
Description
Technical Field
[0001] The present invention relates to the technical field of surface modification of biomedical materials, and particularly to the preparation of a bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant. Background Art
[0002] As a high-performance orthopedic implant biomedical material, polyetheretherketone (PEEK) has attracted much attention in the fields of orthopedics and dental restoration due to its excellent biocompatibility, mechanical strength, and chemical stability. Its density and elastic modulus are close to those of human cortical bone, which can effectively reduce the stress shielding effect during long-term implantation, thereby maintaining the physiological load of bone tissue. In addition, PEEK has excellent X-ray transparency and magnetic resonance imaging (MRI) compatibility, which helps clinicians monitor the healing of bone tissue around the implant after surgery. However, despite its many advantages, the inherent biological inertness of PEEK makes it difficult to induce osteoblast adhesion and proliferation after implantation, affects the bone tissue integration ability, and increases the risk of implant failure.
[0003] Osseointegration is an important prerequisite for the long-term stability of bone implants, which includes the attachment, proliferation, and differentiation of osteoblasts, as well as the deposition and maturation of new bone. Existing PEEK modification strategies mainly focus on improving osteogenic activity, such as surface treatment (sulfonation, plasma spraying, magnetron sputtering, etc.) or coating modification (hydroxyapatite, bone collagen, etc.). Although these methods have enhanced the bone integration ability of PEEK to a certain extent, they still fail to meet the clinical requirements of high-performance orthopedic implants. In addition, implant-related infections are also challenges that need to be addressed urgently in clinical applications, which may lead to secondary surgery or even implant removal in severe cases. Therefore, how to endow PEEK with antibacterial properties while improving its bone integration performance is a research hotspot in the field of biomedical materials.
[0004] Among many bioactive metal ions, magnesium ion (Mg 2+ ) has attracted extensive attention due to its unique biological functions. Mg 2+ is not only the fourth most abundant metal ion in the human body but also has been proven to effectively promote bone mineralization, induce osteoblast proliferation and differentiation, and play an important role in the bone repair process. At the same time, Mg 2+ can also stimulate angiogenesis and accelerate the bone regeneration process. And silver ion (Ag + ) can effectively inhibit the growth of Gram-positive and Gram-negative bacteria due to its broad-spectrum antibacterial properties, shows good biocompatibility at low concentrations, and only exhibits certain toxicity to mammalian cells at high concentrations. Therefore, the synergistic effect of Mg 2+ and Ag + is expected to provide dual functions of enhanced bone integration and antibacterial properties on the surface of PEEK.
[0005] Currently, the surface modification methods of bioactive metal ions include plasma spraying, micro-arc oxidation, electro-deposition, magnetron sputtering, and electrophoretic deposition, etc. However, these methods have complex processes, expensive equipment, and some methods require the use of toxic chemical reagents, which may affect biological safety. Therefore, developing a simple, environmentally friendly, and efficient PEEK surface modification method to simultaneously improve its bone integration and antibacterial and anti-inflammatory properties has important clinical value and application prospects. Summary of the Invention
[0006] Aiming at the deficiencies existing in the prior art, the purpose of the present invention is to provide the preparation of a double-metal ion hydrogel coating on the surface of a polyetheretherketone bone implant. Through acid-base pretreatment, photo-curing hydrogel construction, and double-metal ion loading, a bioactive coating with excellent bone integration ability and antibacterial performance is formed on the surface of PEEK. This method has a simple process, strong controllability, is suitable for large-scale production, and at the same time avoids the use of toxic reagents in traditional modification methods, improving biological safety. To achieve the above object and other advantages according to the present invention, the preparation of a double-metal ion hydrogel coating on the surface of a polyetheretherketone bone implant is provided, including the following steps:
[0007] S1. Select a polyetheretherketone substrate;
[0008] S2. Perform surface acid treatment on the polyetheretherketone substrate to obtain a modified polyetheretherketone material;
[0009] S3. Perform alkaline treatment on the modified polyetheretherketone material to obtain a pretreated polyetheretherketone material;
[0010] S4. Synthesize chitosan grafted with methacrylic acid by amidation reaction of CS and MA;
[0011] S5. Perform esterification chemical reaction on citric acid and chitosan grafted with methacrylic acid, and add magnesium ions to obtain a hydrogel solution containing Mg 2+ ;
[0012] S6. Cure the hydrogel solution containing Mg 2+ on the surface of the pretreated polyetheretherketone material by photo-curing to form a Mg 2+ -hydrogel coating;
[0013] S7. Make Ag + combine with the Mg 2+ -hydrogel coating on the polyetheretherketone material in step S6 by impregnation method to obtain a bioactive hydrogel coating with double-metal ions.
[0014] Preferably, the polyetheretherketone material is treated with acid and alkali to form micro-nano pores on the PEEK surface, improving the surface roughness. On the one hand, it increases the physical adhesion between cells and the surface coating; on the other hand, it introduces active groups such as -OH to establish bonding with the coating components, increasing the coating adhesion and stability.
[0015] Preferably, Mg is formed on the pretreated polyetheretherketone material 2+ -hydrogel coating. Through blue light-initiated polymerization, CSMA and CA form a stable hydrogel network, improving the bioactivity and mechanical stability.
[0016] Preferably, through the synergistic effect of Mg 2+ and Ag + endows the polyetheretherketone with good osteogenic induction and antibacterial and anti-inflammatory properties.
[0017] Compared with the prior art, the beneficial effects of the present invention are: the biocompatibility, antibacterial activity and bone integration performance of the modified PEEK material are verified through in vitro cell experiments and animal models. The results show that compared with unmodified PEEK, the hydrogel coating containing bimetallic ions can significantly promote the proliferation of osteoblasts, accelerate bone mineralization deposition, and effectively inhibit bacterial adhesion and growth. This application provides an efficient, controllable and environmentally friendly PEEK modification strategy, laying a foundation for the further optimization and clinical application of orthopedic implants.
[0018] The use of a bioactive hydrogel coating containing active bimetallic ions improves the bone integration and antibacterial and anti-inflammatory properties of the polyetheretherketone material, which is beneficial to bone repair. At the same time, it simplifies the process flow, reduces the production cost, and is conducive to large-scale popularization and application. Brief Description of the Drawings
[0019] Figure 1 It is a flow chart for the preparation of a bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention.
[0020] Figure 2 It is a surface topography diagram of pure PEEK (a) and sulfonated SPEEK (b) for the preparation of a bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention.
[0021] Figure 3 It is for the preparation of a bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention. (a) is the nuclear magnetic resonance spectrum of CS and CSMA; (b) is the FTIR spectrum of the hydrogel.
[0022] Figure 4Element content distribution diagrams of (a) CSMA-CA, (b) CSMA-CA-Mg, and (c) CSMA-CA-Mg@Ag hydrogels for the preparation of the bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention.
[0023] Figure 5 For the preparation of the bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention, (a) is a comparative immunofluorescence staining image of a hydrogel-coated modified PEEK sample against human bone marrow stromal cells (hBMSCs) and the corresponding; (b) is a quantitative immunofluorescence analysis graph.
[0024] Figure 6 Comparative photos of the antibacterial effects of the hydrogel-coated modified PEEK samples prepared for the preparation of the bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention against E. coli and S. aureus.
[0025] Figure 7 For the preparation of the bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant according to the present invention, (a) is a top view and cross-sectional view of the three-dimensional reconstruction image of the skull 84 days after transplantation; (b) are the quantitative values of BV / TV, BMD, Tb.Th, and Tb.N (n = 4 - 6). Detailed implementation manners
[0026] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts shall fall within the protection scope of the present invention.
[0027] Refer to Figure 1 , the preparation of the bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant includes the following steps:
[0028] 1: PEEK surface pretreatment
[0029] Preparation and cleaning of the PEEK substrate
[0030] Provide a medical-grade PEEK standard part, and polish it successively with 2500# and 5000# sandpapers to improve the surface smoothness and cleanliness. Put the samples into acetone, ethanol, and deionized water in turn, and ultrasonically clean each step for 8 minutes to remove surface impurities, and then air dry naturally.
[0031] 1.2 Surface activation of the PEEK substrate
[0032] (1) Sulfonation treatment
[0033] The cleaned and dried PEEK samples were completely immersed in concentrated sulfuric acid with a concentration greater than 98% for 5 minutes to introduce sulfonic acid groups (-SO3H) on the material surface and increase surface hydrophilicity. The treated samples were successively ultrasonically cleaned in acetone, absolute ethanol, and deionized water to remove the residual acidic solution, and then dried at room temperature to obtain sulfonated PEEK (SPEEK).
[0034] (2) Alkali treatment
[0035] The sulfonated SPEEK samples were immersed in 10M NaOH solution at a temperature of 60 °C for 48 hours to remove the excessive sulfonic acid groups on the surface, optimize the distribution of surface active functional groups, and improve the biocompatibility of the material. The treated samples were ultrasonically cleaned again successively with acetone, absolute ethanol, and deionized water, and then dried at room temperature to obtain the final pretreated SPEEK material.
[0036] As Figure 2 shown, compared with pure PEEK( Figure 2 a), the surface is smooth, while after the sulfonation treatment in steps S2 and S3, a uniform three-dimensional microporous structure is formed on the PEEK surface( Figure 2 b). The increased specific surface area of the micropores is beneficial to cell attachment, growth, and nutrient exchange, which is crucial for orthopedic implants because it can enhance the adhesion between the implant and the surrounding bone tissue, promote healing and osseointegration, thereby improving the long-term stability and clinical effect of the implant.
[0037] 2: Preparation of bioactive hydrogel coating
[0038] 2.1 Preparation of chitosan grafted with methacrylic acid (CSMA)
[0039] 6 g of chitosan (CS) was dissolved in 100 mL of 4% (v / v) glacial acetic acid solution and stirred until completely dissolved.
[0040] Under light-shielded conditions, 6 mL of methacrylic acid (MA) was added dropwise and stirred at 40 °C for 12 hours to promote the grafting reaction.
[0041] After the reaction, the resulting solution was dialyzed in a dialysis bag (12 - 14 kDa) in 5 L of deionized water for 4 days, and the deionized water was changed twice a day to remove the unreacted substances and small molecule impurities.
[0042] The dialyzed product was freeze-dried and stored at room temperature to obtain CSMA powder.
[0043] 2.2 Mg 2+ Hydrogel solution preparation
[0044] Dissolve 0.3 g of CSMA in 10 mL of 1.5% (v / v) glacial acetic acid solution and stir at 60 °C until completely dissolved.
[0045] Add 0.1 g of citric acid (CA), and then dropwise add 1.25 mL of EDC / NHS MES solution (where 0.4 mmol of EDC and 0.2 mmol of NHS are dissolved in 5 mL of 0.01 M MES buffer solution, pH = 6).
[0046] Finally, add 0.15 g of magnesium nitrate (Mg(NO3)2) and continue to stir evenly to form a hydrogel pre-solution containing Mg 2+ of the hydrogel.
[0047] As Figure 3 shown in a, the synthesis of CSMA was achieved through the amide reaction between chitosan (CS) and methacrylic anhydride (MA), and its structure was determined by nuclear magnetic resonance (NMR). The characteristic peaks of chitosan appeared in the region of 3.0 - 3.8 ppm, corresponding to the proton signals on the glucosamine ring. The characteristic peaks of MA were in the region of 5.6 - 6.0 ppm, and the appearance of its characteristic alkenyl double bond signal was clearly visible in the NMR spectrum of CSMA. The characteristic peaks of the amide structure of methacrylated chitosan were in the region of 1.0 - 1.5 ppm, confirming the successful grafting of CSMA. This indicates that the alkenyl functional group of MA was successfully introduced onto the main chain of CS, forming a stable amide bond.
[0048] To further explore the chemical structures of CS, CSMA, and CSMA-CA, Fourier transform infrared spectroscopy (FTIR) was used in this study to characterize them in detail. The FTIR spectra are as Figure 3 (b) shown. CS exhibited typical -OH functional group absorption peaks at 3423 cm -1 , medium-intensity absorption peaks at 2923 cm -1 and 2875 cm -1 could be attributed to the stretching vibration of the -CH functional group, and the -NH2 functional group absorption peak was at 884 cm -1 . In the spectra of CSMA and CSMA-CA, the characteristic absorption peak at 1638 cm -1 proved the formation of the amide bond. For CSMA, this was the result of the covalent reaction between the amino group of CS and the anhydride on MA. For CSMA-CA, this was the result of the covalent reaction between the incompletely grafted amino group on CSMA and the carboxyl group of CA. It is not difficult to see that the characteristic peaks of the amino group were gradually weakening, while the characteristic peaks of the amide structure were strengthening. The presence of these characteristic absorption peaks confirmed the successful preparation of the hydrogel network structure.
[0049] 3: Construction of the hydrogel coating
[0050] 3.1 Hydrogel curing
[0051] Take the SPEEK sample and completely immerse it in the hydrogel pre-solution containing Mg 2+ so that it is uniformly coated on the material surface.
[0052] Irradiate with blue light (405 nm) for 30 minutes to cure the hydrogel on the material surface and form a stable CSMA-CA-Mg coating.
[0053] Immerse the cured sample in deionized water to remove unreacted solutes and residual cross-linking agents.
[0054] 4: Ag + Loading
[0055] 4.1 Silver ion penetration
[0056] Prepare a 0.5 mol / L silver nitrate (AgNO3) solution to ensure that silver ions can uniformly penetrate into the hydrogel coating.
[0057] Completely immerse the CSMA-CA-Mg sample in the AgNO3 solution and react for 30 minutes to achieve the loading of Ag + .
[0058] After taking out the sample, thoroughly wash it with deionized water to remove the unbound Ag + on the surface, and obtain the CSMA-CA-Mg@Ag-coated modified PEEK material.
[0059] This application gives the different element contents in CSMA-CA, CSMA-CA-Mg, and CSMA-CA-Mg@Ag hydrogels as shown in the following table:
[0060] Table 1 Element content distribution in CSMA-CA hydrogel
[0061] Element Wt% At% CK 54.33 59.91 NK 19.34 18.29 OK 26.33 21.80 Matris Correction ZAF
[0062] Table 2 Element content distribution in CSMA-CA-Mg hydrogel
[0063] Element Wt% At% CK 47.27 54.76 NK 18.21 18.09 OK 09.53 05.42 Matris Correction ZAF
[0064] Table 3 Element content distribution in CSMA-CA-Mg hydrogel
[0065]
[0066]
[0067] As shown by Figure 4 and the above table, for the unmodified CSMA-CA hydrogel (Figure 4 a), whose elemental composition is mainly C, N, and O. In the CSMA-CA-Mg hydrogel ( Figure 4 b), due to the addition of Mg 2+ , the EDS analysis results show that in addition to C, N, and O, the Mg element is also detected, accounting for 9.53%, indicating that Mg 2+ has been successfully integrated into the network structure of the hydrogel. For the CSMA-CA-Mg@Ag hydrogel ( Figure 4 c), the contents of Mg and Ag elements other than C, N, and O are 7.24% and 7.01% respectively, showing that both metal elements have been successfully doped into the material.
[0068] Characterization and performance evaluation:
[0069] 5.1 Biocompatibility test - Cell proliferation assay (CCK-8)
[0070] Using human bone marrow mesenchymal stem cells (hBMSCs), the results show that on the surface of modified PEEK, the cell adhesion rate increases by 70% and the cell viability is enhanced. As Figure 5 shown, adult bone marrow stem cells (hBMSC) have become highly potential seed cells in bone tissue engineering due to their multi-directional differentiation potential. Under specific conditions, these cells can be directed to differentiate into osteoblasts, thus demonstrating their biological characteristics and application value in repairing bone defects.
[0071] In this study, the in vitro co-culture of hBMSC cells with different hydrogel-coated modified samples was observed to evaluate their biocompatibility. As Figure 5 (a) shows, hBMSC cells maintain normal growth when co-cultured with various modified samples, indicating that the samples have no cytotoxicity before and after modification. This finding shows that the modification of the three CSMA-CA, CSMA-CA-Mg, and CSMA-CA-Mg@Ag hydrogel coatings not only has no adverse effects, but also promotes the proliferation and growth of hBMSC cells. The CSMA-CA-Mg hydrogel coating shows excellent cell proliferation ability when co-cultured with hBMSC cells, indicating its good support for cell growth and stable biochemical indicators. Figure 5 (b) is the result of the quantitative statistics of the survival of hBMSC cells in Figure 5 (a). It can be found that although the effect of the CSMA-CA-Mg@Ag sample is slightly lower than that of CSMA-CA-Mg, it also shows a promoting effect on the growth of hBMSC cells.
[0072] 5.3 Bacterial inhibition rate test
[0073] The antibacterial properties were tested using Staphylococcus aureus (S. aureus) and Escherichia coli (E. coli). The results showed that bacterial infection is one of the most common complications after the use of implant materials. As Figure 6 shown, the comparative photographs of the antibacterial effects of the hydrogel-coated modified PEEK samples against E. coli and S. aureus. The results showed that the antibacterial effects of the CSMA-CA, CSMA-CA-Mg, and CSMA-CA-Mg@Ag hydrogel coatings were enhanced in sequence. Among them, the CSMA-CA-Mg@Ag coating containing bimetallic ions had the best antibacterial effect. The bacteriostatic rate of the CSMA-CA-Mg@Ag sample reached 100%, confirming the + potent antibacterial ability of Ag, which was significantly better than that of unmodified PEEK. Because Ag + can bind to sulfur proteins and phospholipids on the bacterial cell membrane, change the structure and permeability of the cell membrane, cause the leakage of cell contents, and ultimately lead to bacterial death.
[0074] 5.4 Animal experiment - Osteogenic activity test
[0075] In the rat skull model implantation experiment, Micro-CT scans at 4 weeks and 12 weeks after surgery showed that the new bone volume around the CSMA-CA-Mg@Ag sample increased by 3 times, and the trabecular bone structure was more complete. Histological sections (H&E staining) showed that the bone tissue was tightly bound to the coating surface and the inflammatory response was reduced.
[0076] As Figure 7 shown, Figure 7 (a) is the top view and cross-sectional view of the three-dimensional reconstruction image of the skull 84 days after transplantation; Figure 7 (b) are the quantitative values of BV / TV, BMD, Tb.Th, and Tb.N (n = 4 - 6). In this study, the bone integration ability of each sample was evaluated by implanting different PEEK hydrogel-coated modified samples in the SD rat animal model and using quantitative analysis of Micro-CT images. Figure 7 The Micro-CT image analysis of (a) was performed 84 days after implantation to measure the quality of newly regenerated bone Figure 7Four key parameters of (b): bone volume fraction (BV / TV), bone mineral density (BMD), trabecular bone thickness (Tb.Th), and trabecular bone number (Tb.N). Comparing PEEK loaded with three hydrogel coatings of CSMA-CA, CSMA-CA-Mg, and CSMA-CA-Mg@Ag with unmodified pure PEEK, the quantitative values of BV / TV, BMD, Tb.Th, and Tb.N increased successively. The bimetallic ion sample of CSMA-CA-Mg@Ag showed the highest bone volume fraction (BV / TV), with a specific value of 39.09%, and also showed the highest bone mineral density (BMD), trabecular bone thickness (Tb.Th), and trabecular bone number (Tb.N). The increase in these parameters is a key indicator of bone quality and strength, indicating not only more bone formation but also a relatively large amount of new bone formation in the bone defect area, thus confirming its excellent bone integration performance.
[0077] The number of devices and the scale of processing described here are used to simplify the description of the present invention. Applications, modifications, and variations of the present invention will be apparent to those skilled in the art. Although the embodiments of the present invention have been disclosed above, it is not limited to the applications listed in the specification and the embodiments. It can be fully applied to various fields suitable for the present invention. For those familiar with the art, additional modifications can be easily achieved. Therefore, without departing from the general concept defined by the claims and the equivalent scope, the present invention is not limited to specific details and the examples shown and described here.
[0078] Table 1 Sample names and their composition descriptions
[0079]
Claims
1. Preparation of a bimetallic ion hydrogel coating on the surface of a polyetheretherketone bone implant, characterized in that, It includes the following steps: S1. Select a polyetheretherketone substrate; S2. Perform surface acid treatment on the polyetheretherketone substrate to obtain a modified polyetheretherketone material; S3. Perform alkaline treatment on the modified polyetheretherketone material to obtain a pretreated polyetheretherketone material; S4. Synthesize chitosan grafted with methacrylic acid by amidation reaction of CS and MA; S5. Perform esterification chemical reaction on citric acid and chitosan grafted with methacrylic acid, and add magnesium ions to obtain a hydrogel solution containing Mg2+; S6. Cure the hydrogel solution containing Mg2+ on the surface of the pretreated polyetheretherketone material by photocuring to form a Mg2+-hydrogel coating; S7. The polyetheretherketone material in step S6 is impregnated to combine Ag + with the Mg2+-hydrogel coating to obtain a bioactive hydrogel coating with bimetallic ions.
2. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the step S1, the polyetheretherketone substrate is a pure polyetheretherketone or a composite polyetheretherketone material.
3. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the step S2, the polyetheretherketone substrate is placed in an acidic solution of sulfuric acid or phosphoric acid with a concentration greater than 95% for surface treatment. The reaction time does not exceed 10 minutes, and the treatment temperature is controlled at 10-50°C. Then, multi-step cleaning is carried out to obtain a modified polyetheretherketone material.
4. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the step S3, the modified polyetheretherketone material is placed in an alkaline solution of sodium hydroxide with a concentration of 5-15M for reaction. The reaction temperature is 50-70°C, and the duration is 24-72 hours to remove surface acid groups. Then, cleaning is carried out to obtain a pretreated polyetheretherketone material.
5. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the step S4, the grafting reaction can be carried out by enzyme catalysis or chemical catalysis. The grafting reaction temperature is set at 30-50°C, and the reaction time is 8-24 hours. And the catalytic coupling agents used are 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide and N-hydroxysuccinimide.
6. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the process of synthesizing the hydrogel in the step S5, the reaction time of each component is set at 20-45 minutes, and the overall reaction temperature is 40-70°C.
7. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 6, characterized in that, The hydrogel solution containing Mg2+ contains a buffer, and the buffer is morpholineethanesulfonic acid or phosphate buffer solution.
8. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 1, characterized in that, In the step 7, the silver ion source includes soluble silver salt solutions of silver nitrate and silver acetate, with a concentration of 0.1-1.0mol / L, and the ion penetration reaction time is 20-45 minutes.
9. Preparation of the bimetallic ion hydrogel coating on the surface of the polyetheretherketone bone implant according to claim 3 or 4, characterized in that, All the cleaning is carried out by ultrasonic-assisted cleaning. The cleaning solvents are acetone, absolute ethanol and deionized water in sequence. Finally, the polyetheretherketone substrate is dried at room temperature.