A method for preparing a polyarylether medical material with a hydrogel coating

Abstract

The application provides a preparation method of a polyarylether medical material with a hydrogel coating on the surface, which comprises the following steps: firstly, treating a polyarylether sheet by plasma to endow the sheet with reactive functional groups; and then, spin-coating a hydrogel precursor solution onto the surface of the polyarylether sheet treated by plasma, and curing the sheet in an ultraviolet curing box to obtain a polyarylether medical material with a hydrogel coating on the surface; the hydrogel precursor solution comprises the following components in percentage by mass: acrylic acid-N-succinimidyl ester (AAc-N-NHS) 1-5%; methacrylic anhydride modified chitosan (CSMA) 1-3%; methacrylic anhydride modified gelatin (GelMA) 4-8%; alpha-ketoglutaric acid 0.2%; and water in the rest. The hydrogel coating and the polyarylether substrate are combined by chemical bonds, the bonding force between the hydrogel coating and the substrate is enhanced, the biocompatibility of the polyarylether material is improved, the polyarylether material is endowed with antibacterial and adhesive properties, and the polyarylether material has a wide application prospect in bone implant materials.

Description

TECHNICAL FIELD

[0001] The present application belongs to the field of biomedical materials, and relates to a preparation method of a polyarylether medical material with a hydrogel coating. BACKGROUND

[0002] Bone implant material refers to a kind of biomaterial that can be used to treat human bone diseases, replace damaged or necrotic bone tissue, and restore normal physiological function of bone. It mainly includes joint replacement, bone plate and dental implant materials. The ideal bone implant material needs to meet the following points: (1) good biocompatibility, no toxic and side effects to human tissues and cells; (2) good mechanical properties, including matching mechanical properties with natural bone and good biomechanical adaptability; (3) excellent corrosion resistance and wear resistance; (4) good biological bonding, which can be tightly combined with bone tissue and fixed well; (5) good bone conduction and bone induction to guide the growth of new bone tissue along the material surface and induce osteogenic differentiation and mineralization. In addition, bone replacement materials should also have the characteristics of easy processing, high plasticity, low cost, and convenient medical examination.

[0003] The main materials currently used for bone implant include metal materials (such as titanium, magnesium and its alloys, stainless steel, cobalt-chromium alloy, etc.), inorganic non-metallic materials (hydroxyapatite, bioceramics, etc.), organic polymer materials (polyarylether, polylactic acid, etc.). Among them, polyarylether is a kind of high-performance thermoplastic resin with good processing and molding properties, and has good biocompatibility, close to the elastic model of bone and X-ray transparency, which has been widely used in orthopedic surgery, orthopedics and dentistry, and has great application potential in the field of medical device raw materials. However, due to the smooth and dense surface morphology and significant hydrophobicity, polyarylether (including polyether ether ketone PEEK, heteronaphthalene polyarylether such as PPEK, etc.) cannot be fused with the surrounding head and facial flaps after implantation, which in turn causes the risk of skin abrasion and wound ulceration under repeated friction, seriously affecting its safety in use. In order to improve the fusion of polyarylether with soft tissue, some scholars have carried out a series of researches on its surface structure and chemical modification. The hydrogel coating with good compatibility with soft tissue has high water retention and biocompatibility, and has been successfully applied to the surface modification of medical guide wires and other devices, but its antibacterial property, adhesion with soft tissue and bonding force with implant need to be improved. SUMMARY

[0004] The present application intends to adopt degradable hydrogel coating to modify the surface of polyarylether (including PEEK and heteronaphthalene polyphenyl ether), to enhance the binding force between the coating and the substrate, to endow the polyarylether surface coating with adhesion and antibacterial properties and other multifunctional properties, and to realize the fusion of bone implant and soft tissue. The present application aims to provide a preparation method of polyarylether medical material with hydrogel coating, which adopts degradable hydrogel coating to modify the surface of medical polyarylether implant: first, the polyarylether is treated by plasma to endow it with reactive functional groups, so that the hydrogel coating is combined with the polyarylether substrate through chemical bonds; the coating includes degradable gelatin, antibacterial components and adhesive components, to endow the implant with antibacterial properties and soft tissue adhesion.

[0005] The technical scheme of the present application is as follows:

[0006] A preparation method of polyarylether medical material with hydrogel coating on the surface, comprising the following steps:

[0007] S1: treating the polyarylether sheet by plasma: the plasma treatment conditions are to generate nitrogen plasma in a quartz reaction kettle, the treatment power is 120-160 w, and the treatment time is 180-300 s;

[0008] S2: spin coating the hydrogel precursor solution onto the surface of the polyarylether sheet treated by plasma, and placing it in a ultraviolet curing box to be cured for 5-10 minutes to obtain the polyarylether medical material with hydrogel coating on the surface;

[0009] The hydrogel precursor solution includes but is not limited to the following components in mass percentage: AAc-N-NHS (acrylic acid-N-succinimidyl ester) 1-5%; methyl methacrylate modified chitosan 1-3%; methyl methacrylate modified gelatin 4-8%; alpha-ketoglutaric acid 0.2%; and water in balance.

[0010] The hydrogel coating has degradability, antibacterial property and soft tissue adhesion, and is chemically connected with the polyarylether with amino groups introduced after plasma treatment, thereby enhancing the binding force between the hydrogel coating and the substrate.

[0011] The preparation method of the hydrogel precursor solution comprises the following steps: placing AAc-N-NHS, methyl methacrylate modified chitosan, alpha-ketoglutaric acid and methyl methacrylate modified gelatin in deionized water and stirring to dissolve them thoroughly to obtain the hydrogel precursor solution.

[0012] The polyarylether includes polyether ether ketone PEEK and heteronaphthalene polyphenyl ether; the molecular chain of the heteronaphthalene polyphenyl ether contains a naphthalene ketone biphenyl structure, the structural expression of PEEK is formula (I), and the structural expression of the molecular chain containing a naphthalene ketone biphenyl structure is formula (II):

[0013] (I)

[0014] (II)

[0015] wherein Ar1 is the main structure of the dihalogen monomer, and is one or more of the following structures:

[0016] ;

[0017] Ar2 is the main structure of the bisphenol monomer, and is one or more of the following structures:

[0018] ;

[0019] wherein R1, R2, R3, R4 are hydrogen, halogen substituent, phenyl, phenoxy, straight-chain alkyl containing at least 1 carbon atom, branched alkyl containing at least 1 carbon atom, or branched alkoxy containing at least 1 carbon atom, and R1, R2, R3 and R4 are the same or different in structure.

[0020] m is a positive integer;

[0021] n is 0 or a positive integer.

[0022] The specific process of plasma treatment of the polyarylether sheet in S1 is as follows: the polyarylether sheet is immersed in acetone for ultrasonic cleaning for 10-20 min, immersed in ethanol for ultrasonic cleaning for 10-20 min, immersed in ultrapure water for ultrasonic cleaning for 10-20 min, and then placed in a plasma reaction kettle after drying; high-purity N2 (99.999 %) is introduced into the system at a flow rate of 300 ml / min for 5-15 min to remove air in the system; then, the flow meter is adjusted to keep the flow rate constant at 20-40 ml / min, the radio frequency power supply of the plasma device is turned on, the voltage and current are adjusted, nitrogen plasma is excited in the quartz reaction kettle, and the plasma treatment is performed at a power in the range of 120-160 w for 180-300 s to obtain a plasma-treated polyarylether sheet.

[0023] The preparation method of the methacrylic anhydride modified gelatin comprises the following steps: Type A gelatin (300 g bloom) is put into a round-bottom flask containing a PBS buffer solution, the round-bottom flask is placed in a water bath kettle for magnetic stirring and water bath heating at 55-65 ℃ until the gelatin is completely dissolved to obtain a light yellow transparent solution, and the mass percentage of the gelatin is 8-12%. Methacrylic anhydride is added dropwise, and after reaction at 55-65 ℃ for 1-1.5 h, the solution is absorbed into a dialysis bag with a molecular weight cut-off of 14,000, and dialysis is performed in a deionized water bath at 40 ℃ for 7 days. A white precipitate is separated out, the upper clear solution is absorbed, and the solution is freeze-dried in a freeze dryer and stored at -20 ℃ for standby use.

[0024] The preparation method of the methyl acrylate modified chitosan comprises the following steps: pouring chitosan (CS) powder into 0.1 mol / L acetic acid solution, stirring and dissolving for 10-12 hours to completely dissolve the chitosan, and the mass volume percentage of the chitosan is 1-1.5%. After the CS solution is completely dissolved, the solution is placed in a 35-45 ℃ oil bath, then 55-65 ml of methyl acrylate is added dropwise into the CS solution, and the solution is reacted at 40 ℃ for 12 hours in the dark, then the solution is absorbed into a dialysis bag with a molecular weight cut-off of 14,000, and dialysis is carried out in a 40 ℃ water bath for 3 days, white precipitate is separated out, the upper clear liquid is absorbed, and the liquid is freeze-dried in a freeze dryer, and then stored at -20 ℃.

[0025] 1. The polyarylene ether with a hydrogel coating layer is prepared by a simple method, large equipment is not needed, and the surface modification can be performed on parts with complex shapes.

[0026] 2. The hydrogel prepared in the application has good biocompatibility and multifunctionality. In the case of not affecting the mechanical properties of the polyarylene ether, the bonding force between the hydrogel coating layer and the substrate is enhanced, the biocompatibility of the polyarylene ether material is improved, the polyarylene ether material is endowed with antibacterial and adhesive properties, and has a broad application prospect in bone implant materials. BRIEF DESCRIPTION OF DRAWINGS

[0027] Figure 1 FIG. 1 is an X-ray photoelectron spectroscopy (XPS) spectrum of PPEK before and after plasma treatment in Example 1.

[0028] Figure 2 (a) is the surface water contact angle of PPEK in Example 1, and (b) is the surface water contact angle of PPEK after plasma treatment in Example 1.

[0029] Figure 3 FIG. 6 is a 90° peeling test of the hydrogel coating layer in Example 1.

[0030] Figure 4 (a) is the displacement-adhesion strength curve of the hydrogel coating layer and pig skin lap joint in Example 1, and (b) is the adhesion strength quantitative analysis in Example 1.

[0031] Figure 5 FIG. 9 is an antibacterial experiment comparison of PPEK, PPEK-P-Coating (G4C0N3) and PPEK-P-Coating (G4C3N3) in Example 1.

[0032] Figure 6 FIG. 13 is an X-ray photoelectron spectroscopy (XPS) spectrum of PEEK before and after plasma treatment in Example 2.

[0033] Figure 7(a) is the surface water contact angle of PEEK in Example 2, (b) is the surface water contact angle of PEEK after plasma treatment in Example 2.

[0034] Figure 8 The results of the mechanical stability test of the hydrogel coating in Example 2.

[0035] Figure 9 The MTT toxicity test of PPEK, PEEK, PPEK-P-Coating (G4C3N3), PEEK-P-Coating (G4C3N3) samples in Example 2.

[0036] Figure 10 The antibacterial experiment comparison of PEEK, PEEK-P-Coating (G4C0N3) and PEEK-P-Coating (G4C3N3) in Example 2. DETAILED DESCRIPTION

[0037] The substantial features and significant progress of the present application are further illustrated below through specific examples, but the content of the present application is not limited only to the following examples, and can be adjusted according to actual conditions.

[0038] The X-ray photoelectron spectrometer (XPS) was used to analyze the changes in the content of the main elements on the surface of PPEK / PEEK before and after plasma treatment. The water contact angle measuring instrument was used to characterize the hydrophilic and hydrophobic properties of the sample surface, the flat plate bacterial colony counting method was used to evaluate the antibacterial activity of the material, and the universal mechanical testing machine was used to test the lap shear adhesion strength of the hydrogel.

[0039] The adhesion test process is as follows: fresh pigskin is cut into 30×10×3 mm 3 , and in order to keep the pigskin moist, the cut pigskin is soaked in a beaker containing PBS (pH=7.4) and stored in a 4 ℃ refrigerator, and the surface excess water is absorbed with filter paper before the experiment. The hydrogel is bonded with the pigskin tissue surface and then ultraviolet cured, with an area of about 10×10 mm 2 . The lap shear adhesion strength of the composite hydrogel is tested by the universal mechanical testing machine Instron Model 5567, with a tensile speed of 5 mm / min, a 100N sensor, and a room temperature.

[0040] The antibacterial test process is as follows: 1 mL of 10 8 CFU / mL bacterial solution is centrifuged for 5 min, the supernatant is discarded, 1 mL of PBS solution is added and the bacteria are blown apart, centrifuged again, washed three times to completely remove the culture medium, and finally dispersed into 1 mL of PBS solution, then the bacterial solution is diluted to 10 6CFU / mL. The hydrogel coating-modified PPEK material was placed in a 24-well plate, 1 mL (10 6 CFU / mL) bacterial solution was added, after 3 h of shaking, the sample was taken out, the remaining liquid was serially diluted and plated on agar plates, which were incubated at 37 °C for 24 h, and the number of colonies was counted.

[0041] Cytotoxicity test was as follows: first, prepare 5 mg / mL MTT solution, store at 4 °C in the dark. PPEK, PPEK-P-Coating (G4C3N3), PEEK, PEEK-P-Coating (G4C3N3) were respectively immersed in 3 mL a-MEM medium, 37 °C for 24 h, to obtain the extract of the material. Using the double dilution method, the extract was diluted. MC3T3-E1 cells were seeded in a 96-well plate at a density of 5x10 3 per well, 100 μl per well, and three replicates were set. After the cells adhered, the medium was aspirated, 100 μl of gradient concentration of extract was added to each well, and after 1 day and 3 days of culture at 37 °C, 10 μl of MTT solution was added to each well, and after 4 h of incubation at 37 °C, the extract was aspirated, 100 μl of DMSO solution was added to each well, mixed, and the OD value of each well was measured on a microplate reader at 490 nm wavelength and the relative proliferation rate of each well of cells was calculated.

[0042] Example 1

[0043] First, active functional groups were introduced on the surface of PPEK by plasma treatment, and the structure of PPEK is formula (III). The PPEK sheet was immersed in acetone and ultrasonically cleaned for 15 minutes, immersed in ethanol and ultrasonically cleaned for 15 minutes, and immersed in ultrapure water and ultrasonically cleaned for 15 minutes. A 1 cm 2 square PPEK sheet was placed in a plasma reactor, and before the experiment, 5 min of high-purity N2 (99.999 %) was introduced into the system at a flow rate of 300 ml / min to remove air in the system. Then, adjust the flow meter to a constant flow rate of 30 ml / min, turn on the radio frequency power of the plasma device, adjust the voltage and current, and generate a nitrogen plasma in the quartz reactor, treat it at a power of 160 w for 300 s, and obtain a plasma-treated polyarylether sheet. The PPEK obtained has active functional groups on the surface.

[0044] (III)

[0045] Secondly, the hydrogel precursor solution was prepared. 3% methacrylic anhydride modified chitosan, 4% methacrylic anhydride modified gelatin, 0.2% alpha-ketoglutaric acid, and 0%, 1%, 2%, or 3% AAc-N-NHS were added to deionized water and fully stirred to dissolve, to obtain a hydrogel precursor solution, which was used as G4C3N0 solution, G4C3N1 solution, G4C3N2 solution, and G4C3N3 solution, wherein G represents methacrylic anhydride modified gelatin, C represents methacrylic anhydride modified chitosan, and N represents AAc-N-NHS; similarly, 3% methacrylic anhydride modified chitosan was replaced by 0%, and 3% AAc-N-NHS was added, to obtain G4C0N3 solution.

[0046] The preparation method of the methacrylic anhydride modified gelatin comprises: 10 g of Type A gelatin (300 g bloom) is poured into a round-bottom flask containing 100 ml of PBS buffer solution, the round-bottom flask is placed in a water bath heater and magnetically stirred at 60°C until the gelatin is completely dissolved, to obtain a 10% (w / v) light yellow transparent solution. Methacrylic anhydride is added dropwise, and after 1 h of reaction under 60°C water bath heating, the solution is absorbed into a dialysis bag with a molecular weight cut-off of 14,000, and dialyzed in a deionized water bath at 40°C for 7 days. Centrifugation is performed at 4000 rpm for 20 min, the white precipitate is separated, and the supernatant is collected to obtain the methacrylic anhydride modified gelatin, which is freeze-dried in a freeze dryer for 48 h and stored at -20°C.

[0047] The preparation method of the methacrylic anhydride modified chitosan comprises: 1.5 g of chitosan (CS) powder is poured into 100 mL of 0.1 mol / L acetic acid solution and stirred to dissolve for 12 h, so that the CS solution is completely dissolved. The CS solution is placed in a 40°C oil bath, and then 60 ml of methacrylic anhydride is added dropwise to the CS solution, which is reacted at 40°C in the dark for 12 h. The solution is absorbed into a dialysis bag with a molecular weight cut-off of 14,000, and dialyzed in a deionized water bath at 40°C for 3 days. Centrifugation is performed at 4000 rpm for 20 min, the white precipitate is separated, and the supernatant is collected to obtain the methacrylic anhydride modified chitosan, which is freeze-dried in a freeze dryer for 48 h and stored at -20°C.

[0048] Thirdly, polyarylether hydrogel coating was prepared. The hydrogel precursor solution prepared in the second step was spin-coated onto the surface of the plasma-treated PPEK, and was placed in a UV curing box for curing for 5-10 minutes to obtain PPEK-P-Coating (G4C3N0), PPEK-P-Coating (G4C3N1), PPEK-P-Coating (G4C3N2), PPEK-P-Coating (G4C3N3) and PPEK-P-Coating (G4C0N3) respectively. The G4C3N3 solution was spin-coated onto the surface of PPEK (without plasma treatment), and was placed in a UV curing box for curing for 5-10 minutes to obtain PPEK-Coating (G4C3N3).

[0049] The PPEK sheet with multifunctional hydrogel coating prepared by the above method has the following properties:

[0050] As shown in the XPS spectrum (as shown in Figure 1 , the sharp peak at 400.45 eV is the peak of N, and after plasma treatment, the content of N is increased from 6% to 12%, which proves that the active functional groups are successfully introduced on the surface of the PPEK sheet through plasma treatment.

[0051] The water contact angle of the surface of the plasma-treated PPEK sheet is smaller than that of the surface of the PPEK sheet without surface modification (as shown in Figure 2 , from 90° to 45°. It shows that the surface energy of the PPEK sheet has changed, and the active functional groups have improved the hydrophilicity of the surface of the PPEK sheet.

[0052] The adhesion of the hydrogel coating to the substrate was tested by 90° peeling method, as shown in Figure 3 . The results show that the adhesion of PPEK-P-Coating (G4C3N3) is 5 times that of PPEK-Coating (G4C3N3).

[0053] As shown in Figure 4 , by adjusting the content of AAc-N-NHS, the adhesion of the hydrogel coating to the soft tissue is obviously enhanced, and the adhesion strength reaches 142 MPa.

[0054] As shown in Figure 5 , compared with pure PPEK and PPEK-P-Coating (G4C0N3), the antibacterial property of the PPEK sheet modified by the hydrogel coating PPEK-P-Coating (G4C3N3) is obviously enhanced, and the inhibition zone diameter reaches 42 mm.

[0055] Example 2

[0056] The first step involves introducing active functional groups onto the PEEK surface through plasma treatment. The PEEK structure is shown in formula (Ⅰ). Active functional groups are then introduced onto the PEEK surface through plasma treatment. The PEEK sheet is immersed in acetone and ultrasonically cleaned for 15 minutes, then in ethanol and ultrasonically cleaned for 15 minutes, and finally immersed in ultrapure water and ultrasonically cleaned for 105 minutes. A 1 cm... 2 PEEK sheets were placed in a plasma reactor. Before the experiment, high-purity N2 (99.999%) was introduced into the system at a flow rate of 300 ml / min for 5 min to purge air from the system. Subsequently, the flow meter was adjusted to maintain a constant flow rate of 30 ml / min. The radio frequency power supply of the plasma device was turned on, and the voltage and current were adjusted to generate nitrogen plasma in the quartz reactor. The plasma was processed at 160 W for 300 s to obtain PEEK with active functional groups on its surface.

[0057] The second step is to prepare the hydrogel precursor solution.

[0058] 3% AAc-N-NHS, 0% or 3% methacrylic anhydride-modified chitosan, 0.2% α-ketoglutaric acid, and 4% methacrylic anhydride-modified gelatin were added to the mixture. The mixture was then thoroughly stirred and dissolved in deionized water to obtain the hydrogel precursor solution, denoted as G4C0N3 solution and G4C3N3 solution.

[0059] The preparation of methacrylic anhydride-modified chitosan and methacrylic anhydride-modified gelatin is as described in step 2 of Example 1.

[0060] The third step involves preparing the polyarylene ether hydrogel coating. The hydrogel precursor solution prepared in the previous step is spin-coated onto the plasma-treated PEEK surface and cured in a UV curing oven for 5-10 minutes to obtain PEEK-P-Coating (G4C3N3) and PEEK-P-Coating (G4C0N3). The G4C3N3 solution is then spin-coated onto the PPEK surface (not plasma-treated) and cured in a UV curing oven for 5-10 minutes to obtain PPEK-Coating (G4C3N3).

[0061] The PPEK sheets with a multifunctional hydrogel coating on their surface prepared by the above method have the following properties:

[0062] Through XPS spectra (e.g.) Figure 6 As shown in the figure, the peak at the electron binding energy of 400.45 eV is the peak of N. After plasma treatment, the N content increased from 0% to 9%, which proves that active functional groups were successfully introduced into the PPEK sheet surface through plasma treatment.

[0063] The surface water contact angle of surface-modified PEEK sheets is smaller than that of unmodified PEEK sheets (e.g.,Figure 7 As shown in the figure, the decrease from 88° to 55.5° indicates a change in the surface energy of the PEEK sheet, and the active functional groups improve the hydrophilicity of the PEEK sheet surface.

[0064] To further verify the mechanical stability of the hydrogel coating after plasma treatment, a grid experiment was conducted on the samples, such as... Figure 8 As shown. A grid-cutting apparatus (six cutting edges spaced 1 mm apart) was used to apply uniform pressure to both PEEK-Coating (G4C3N3) and PEEK-P-Coating (G4C3N3), followed by brushing with a soft brush back and forth 50 times. The results showed that the cut edges of PEEK-Coating (G4C3N3) were rough and exhibited coating peeling, while the cut edges of PEEK-P-Coating (G4C3N3) were completely smooth with no peeling at the grid edges, achieving ISO 0 grade. This indicates that after plasma treatment, the hydrogel coating adhered firmly to the PEEK surface, further demonstrating the high bonding strength between the hydrogel coating and the substrate.

[0065] To demonstrate the cell compatibility of the material, an MTT toxicity test was conducted, and the test results are as follows: Figure 9 As shown, the cell viability of PEEK, PEEK-P-Coating (G4C3N3), PPEK, and PPEK-P-Coating (G4C3N3) were all above 80%, indicating that none of the four materials were cytotoxic.

[0066] Compared with pure PEEK and PEEK-P-Coating (G4C0N3), the hydrogel-coated modified PEEK sheet, PEEK-P-Coating (G4C3N3), exhibits significantly enhanced antibacterial properties, achieving an antibacterial rate of 90% (e.g., Figure 10 (As shown).

Claims

1. A method for preparing a polyarylene ether medical material with a hydrogel coating on its surface, characterized in that: Includes the following steps: S1 uses plasma to treat polyarylether sheets: the plasma treatment conditions are to generate nitrogen plasma in a quartz reactor, the treatment power is 120-160 W, and the treatment time is 180-300 s; S2 spin-coating the hydrogel precursor solution onto the surface of a plasma-treated polyarylene sheet, placing it in an ultraviolet curing oven, and curing for 5-10 minutes to obtain a polyarylene medical material with a hydrogel coating on the surface; The hydrogel precursor solution comprises the following components by mass percentage: AAc-N-NHS 1-5%; methacrylic anhydride-modified chitosan 1-3%; methacrylic anhydride-modified gelatin 4-8%; α-ketoglutaric acid 0.2-1%; water balance; The specific process of plasma treatment of polyarylene ether sheets in S1 is as follows: the polyarylene ether sheets are immersed in acetone for ultrasonic cleaning for 10-20 min, immersed in ethanol for ultrasonic cleaning for 10-20 min, immersed in ultrapure water for ultrasonic cleaning for 10-20 min, dried, and then placed in a plasma reactor; 99.999% high-purity N2 is introduced into the system at a flow rate of 300 ml / min for 5-15 min to remove air from the system; subsequently, the flow meter is adjusted to keep the flow rate constant at 20-40 ml / min, the radio frequency power supply of the plasma device is turned on, and the voltage and current are adjusted to generate nitrogen plasma in the quartz reactor. The process is carried out at a power range of 120-160 W for 180-300 s to obtain plasma-treated polyarylene ether sheets.

2. The method for preparing a polyarylene ether medical material with a hydrogel coating on its surface as described in claim 1, characterized in that: The preparation method of the hydrogel precursor solution includes the following steps: placing AAc-N-NHS, methacrylic anhydride-modified chitosan, α-ketoglutarate and methacrylic anhydride-modified gelatin in deionized water and stirring thoroughly to dissolve them, thereby obtaining the hydrogel precursor solution.

3. The method for preparing a polyarylene ether medical material with a hydrogel coating on its surface as described in claim 1, characterized in that: The polyaryl ethers include polyether ether ketone (PEEK) and heteronaphthyl biphenyl polyaryl ethers; the molecular chains of the heteronaphthyl biphenyl polyaryl ethers contain diazanaphthyl biphenyl structures, the structural expression of PEEK is formula (I), and the structural expression of the molecular chains containing diazanaphthyl biphenyl structures is formula (II). （I）； (II); Ar1 is the main structure of the dihalogenated monomer, which is one or more of the following structures: ； Ar2 is the main structure of the bisphenol monomer, and it is one or more of the following structures: ； Among them, R1, R2, R3, and R4 are hydrogen, halogen substituents, phenyl, phenoxy, straight-chain alkyl containing at least one carbon atom, branched alkyl containing at least one carbon atom, or branched alkoxy containing at least one carbon atom. The structures of R1, R2, R3, and R4 are the same or different. m is a positive integer; n is 0 or a positive integer.

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