Self-lubricating hydrogel titanium alloy bionic joint bearing interface and preparation method thereof

Abstract

This invention discloses a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface and its preparation method. The self-lubricating hydrogel titanium alloy biomimetic joint bearing interface is composed of a porous titanium alloy substrate, a functionalized interface layer, a negatively charged hydrogel layer, and a self-lubricating adsorption layer. A laser drilling method is used to create a porous structure on the surface of a Ti6Al4V substrate. A hydrogel precursor solution is coated onto the surface of the Ti6Al4V sample and cured by ultraviolet irradiation to obtain a negatively charged hydrogel titanium alloy composite sample. The negatively charged hydrogel titanium alloy composite sample is subjected to freeze-thaw cycles and then immersed in zwitterionic or cationic solutions for adsorption, resulting in a hydrogel titanium alloy biomimetic joint bearing interface with self-lubricating properties. The hydrogel titanium alloy biomimetic joint bearing interface of this invention significantly improves the lubrication performance of titanium alloy materials used in artificial joints, achieving biomimetic design of natural joints in terms of tissue structure and lubrication function, and is suitable for the repair and replacement of damaged articular cartilage.

Description

Technical Field

[0001] This invention belongs to the field of biomimetic joint material structure and preparation technology, and particularly relates to a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface and its preparation method. Background Technology

[0002] Titanium alloys possess high specific strength, hardness and elasticity similar to human bone, excellent corrosion resistance, and outstanding biocompatibility, making them the most widely used material for artificial joints. Typically, the acetabular cup and gluteal stem of artificial hip joints, as well as the tibial plateau in artificial knee joints, are made of titanium alloys. Clinical trials have also demonstrated that pure titanium can be used in areas with low stress, while Ti6Al4V alloys can be used in areas with high stress. However, the high coefficient of friction and poor wear resistance of titanium alloy surfaces limit their application in the load-bearing interfaces of artificial joints.

[0003] Patents CN117379593A and CN11950679A only achieve biomimicry of the hydrogel / titanium alloy composite structure, focusing on improving the bonding strength between the hydrogel layer and the substrate, while neglecting the crucial lubrication properties of artificial joints. Furthermore, the use of magnetron sputtering to deposit tantalum suffers from cumbersome processes and high costs. Patent CN109137036A discloses a composite coating of a ceramic layer grafted with hydrogel on a titanium alloy surface and its preparation method, achieving biomimicry of the hydrogel / titanium alloy composite structure of natural joints. However, the micro-arc oxidation technology used has drawbacks such as complex processes and high energy consumption, and the coefficient of friction of the hydrogel / titanium alloy composite sample is around 0.3, which is far from the excellent lubrication properties of natural joints (0.0005-0.04). Therefore, to meet practical applications, further optimization and improvement of the lubrication performance of the load-bearing interface of the hydrogel / titanium alloy biomimetic joint are needed.

[0004] The excellent load-bearing, shear-resistant, and lubricating capabilities of natural joints are closely related to the articular cartilage covering their surface. Proteoglycans (rich in carboxylic and sulfonic acid groups) interspersed in the superficial layer of cartilage make the cartilage surface hydrophilic and negatively charged. Aggregated proteoglycans form large aggregates with hyaluronic acid, trapped within the collagen network, generating osmotic pressure that resists compressive loads. This property plays a positive role in the highly efficient lubrication of natural joints. On the other hand, biomolecules in the articular cartilage or synovial fluid can tightly absorb water molecules to form a robust hydrated lubricating layer, jointly maintaining long-lasting superlubricating properties. Summary of the Invention

[0005] Purpose of the invention: In order to overcome the shortcomings of the existing technology, the present invention provides a self-lubricating hydrogel titanium alloy bionic joint bearing interface and its preparation method. The self-lubricating hydrogel titanium alloy joint bearing interface is constructed through bionic design, and the friction coefficient is reduced to a level close to that of a natural joint by using a dynamic hydration lubricating film. Combined with the interface strengthening process, the wear resistance is improved and the life of the artificial joint is extended.

[0006] Technical solution: To achieve the above objectives, the present invention provides a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface, comprising:

[0007] Porous titanium alloy substrate: made of Ti6Al4V alloy, with a regularly distributed pit structure on the surface, the pit diameter is 100-300μm and the pit spacing is 50-200μm, and an oxide layer is formed by thermal oxidation treatment;

[0008] Functionalized interface layer: The surface of the porous titanium alloy substrate is treated with hydroxylation and modified with a silane coupling agent, wherein the silane coupling agent is γ-propyltrimethoxysilane with carbon-carbon double bonds.

[0009] Negatively charged hydrogel layer: covering the functionalized interface layer, composed of acrylamide, 2-acryloylamino-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol;

[0010] The mass ratio of acrylamide, 2-acrylamide-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol is 1.0-2.0:0.3-1.0:0.005-0.02:0.005-0.02:0.1-1.0;

[0011] Self-lubricating adsorption layer: It is attached to the surface of the negatively charged hydrogel layer by electrostatic adsorption and is composed of zwitterionic or cationic monomers with an adsorption concentration of 5-25 mg / ml.

[0012] The friction coefficient of the self-lubricating hydrogel titanium alloy bionic joint bearing interface is 0.02-0.08 under a load of 2-3N.

[0013] Furthermore, the diameter of the pit is 200 μm, and the spacing between the pits is 100 μm.

[0014] Furthermore, the crosslinking agent is N,N'-methylenebisacrylamide, and the photoinitiator is α-ketoglutaric acid.

[0015] Furthermore, the zwitterionic monomer is a betaine-based N,N-dimethylammonium propanesulfonic acid inner salt.

[0016] Furthermore, the thickness of the negatively charged hydrogel layer is 50-200 μm.

[0017] A method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface includes the following steps:

[0018] Step 1: Pre-treat the Ti6Al4V substrate surface, including sanding, mechanical polishing, ultrasonic cleaning and nitrogen drying. Then, use laser drilling to drill holes in the Ti6Al4V substrate surface to form a porous structure with pit diameter of 100-300μm and spacing of 50-200μm. Then, perform secondary grinding and polishing on the edges of the micropores to eliminate the heat-affected zone at the edges of the micropores.

[0019] Step 2: The porous Ti6Al4V sample prepared in Step 1 is subjected to thermal oxidation treatment at 700-800℃ for 5-30 hours, and then cooled in the furnace;

[0020] Step 3: Perform surface hydroxylation treatment and silane coupling agent modification on the sample after thermal oxidation in Step 2;

[0021] Step 4: Construct a soft hydrogel layer on the sample from Step 3 by mixing and dissolving acrylamide, 2-acrylamido-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol in deionized water to obtain a hydrogel precursor solution.

[0022] Step 5: Coat the surface of the Ti6Al4V sample obtained in Step 3 with the hydrogel precursor solution and cure it by ultraviolet irradiation to obtain a negatively charged hydrogel titanium alloy composite sample.

[0023] Step 6: The negatively charged hydrogel titanium alloy composite sample obtained in Step 5 is subjected to freeze-thaw cycle treatment and then immersed in zwitterionic or cationic solutions for adsorption to obtain a hydrogel titanium alloy biomimetic joint bearing interface with self-lubricating properties.

[0024] Furthermore, in step 2, the temperature is increased to 700°C at a heating rate of 10°C / min, maintained at the thermal oxidation temperature of 700°C for 10 hours, and then cooled to room temperature.

[0025] Further, in step 4, the hydrogel precursor solution comprises: 1.6324 g of acrylamide, 0.5 g of 2-acrylamido-2-methyl-1-propanesulfonic acid, 0.01 g of N,N'-methylenebisacrylamide, 0.01 g of α-ketoglutaric acid, and 0.4 g of polyvinyl alcohol.

[0026] Furthermore, in step 5, the ultraviolet irradiation is performed under an ultraviolet lamp for 30 minutes.

[0027] Furthermore, in step 6, the number of freeze-thaw cycles is 3-5, the concentration of the adsorption solution is 5-25 mg / ml, and the adsorption time is 12-48 hours.

[0028] Beneficial effects: 1) By combining laser drilling and thermal oxidation in a two-phase treatment method, a porous titanium alloy substrate with high wear resistance can be constructed. This method has the advantages of simpler preparation process, better repeatability, faster speed and environmental friendliness.

[0029] 2) By introducing a silane coupling agent containing carbon-carbon double bonds, it can covalently crosslink with the carbon-carbon double bond monomers in the hydrogel precursor solution under ultraviolet light irradiation, thereby further improving the bonding performance between the hydrogel layer and the substrate.

[0030] 3) By using electrostatic adsorption technology, zwitterionic ions of SBMA are dynamically adsorbed onto the surface of the negatively charged hydrogel layer, which simulates the adsorption of biomacromolecules in synovial fluid by natural cartilage during movement, and further improves the hydration boundary lubrication capability of the composite bearing interface. Attached Figure Description

[0031] Figure 1 A schematic diagram illustrating the construction mechanism of the load-bearing interface of a self-lubricating hydrogel titanium alloy bionic joint;

[0032] Figure 2 A schematic diagram of the SEM morphology of the self-lubricating hydrogel titanium alloy bionic joint bearing interface.

[0033] Figure 3 This is a schematic diagram showing the average friction coefficient of the self-lubricating hydrogel titanium alloy biomimetic joint bearing interface measured under 2N and 3N loads. Detailed Implementation

[0034] The invention will now be further described with reference to the accompanying drawings.

[0035] like Figure 1 , Figure 2 as well as Figure 3 As shown, a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface is characterized by comprising:

[0036] Porous titanium alloy substrate: made of Ti6Al4V alloy, with a regularly distributed pit structure on the surface, the pit diameter is 100-300μm and the pit spacing is 50-200μm, and an oxide layer is formed by thermal oxidation treatment;

[0037] Functionalized interface layer: The surface of the porous titanium alloy substrate is hydroxylated and modified with a silane coupling agent, wherein the silane coupling agent is γ-(methacryloyloxy)propyltrimethoxysilane (KH570) with carbon-carbon double bonds.

[0038] Negatively charged hydrogel layer: covering the functionalized interface layer, composed of acrylamide (AM), 2-acrylamide-2-methyl-1-propanesulfonic acid (AMPS), crosslinking agent, photoinitiator, and polyvinyl alcohol (PVA); wherein the mass ratio of acrylamide (AM), 2-acrylamide-2-methyl-1-propanesulfonic acid (AMPS), crosslinking agent, photoinitiator, and polyvinyl alcohol (PVA) is 1.0-2.0:0.3-1.0:0.005-0.02:0.005-0.02:0.1-1.0;

[0039] Self-lubricating adsorption layer: It is attached to the surface of the negatively charged hydrogel layer by electrostatic adsorption and is composed of zwitterionic or cationic monomers with an adsorption concentration of 5-25 mg / ml; wherein, the friction coefficient of the self-lubricating hydrogel titanium alloy bionic joint bearing interface under a load of 2-3 N is 0.02-0.08.

[0040] The diameter of the pit is 200 μm and the spacing between the pits is 100 μm.

[0041] The crosslinking agent is N,N'-methylenebisacrylamide (MBAA), and the photoinitiator is α-ketoglutaric acid (KA).

[0042] The zwitterionic monomer is betaine-based N,N-dimethyl(methacryloyloxyethyl)ammonium propanesulfonic acid inner salt (SBMA).

[0043] The thickness of the negatively charged hydrogel layer is 50-200 μm.

[0044] A method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface includes the following steps:

[0045] Step 1: Pre-treat the Ti6Al4V substrate surface, including sanding, mechanical polishing, ultrasonic cleaning and nitrogen drying. Then, use laser drilling to drill holes in the Ti6Al4V substrate surface to form a porous structure with pit diameter of 100-300μm and spacing of 50-200μm. Then, perform secondary grinding and polishing on the edges of the micropores to eliminate the heat-affected zone at the edges of the micropores.

[0046] Step 2: The porous Ti6Al4V sample prepared in Step 1 is subjected to thermal oxidation treatment at 700-800℃ for 5-30 hours, and then cooled in the furnace;

[0047] In step 2, the temperature is increased to 700°C at a heating rate of 10°C / min, and the thermal oxidation temperature of 700°C is maintained for 10 hours, followed by cooling to room temperature.

[0048] Step 3: Perform surface hydroxylation treatment and silane coupling agent modification on the sample after thermal oxidation in Step 2.

[0049] Step 4: Construct a soft hydrogel layer on the sample from Step 3 by mixing and dissolving acrylamide, 2-acrylamido-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol in deionized water to obtain a hydrogel precursor solution.

[0050] In step 4, the hydrogel precursor solution is composed of: 1.6324 g of acrylamide (AM), 0.5 g of 2-acrylamido-2-methyl-1-propanesulfonic acid (AMPS), 0.01 g of N,N'-methylenebisacrylamide (MBAA), 0.01 g of α-ketoglutaric acid (KA), and 0.4 g of polyvinyl alcohol (PVA).

[0051] Step 5: Coat the surface of the Ti6Al4V sample obtained in Step 3 with the hydrogel precursor solution and cure it by ultraviolet irradiation to obtain a negatively charged hydrogel titanium alloy composite sample.

[0052] In step 5, the ultraviolet irradiation is performed under an ultraviolet lamp for 30 minutes.

[0053] Step 6: The negatively charged hydrogel titanium alloy composite sample obtained in Step 5 is subjected to freeze-thaw cycle treatment and then immersed in zwitterionic or cationic solutions for adsorption to obtain a hydrogel titanium alloy biomimetic joint bearing interface with self-lubricating properties.

[0054] In step 6, the number of freeze-thaw cycles is 3-5, the concentration of the adsorption solution is 5-25 mg / ml, and the adsorption time is 12-48 hours.

[0055] To better understand the lubrication advantages of the self-lubricating hydrogel titanium alloy biomimetic joint bearing interface of this invention, combined with Figure 2 and Figure 3 The analysis is as follows from both microscopic physical and chemical biological perspectives:

[0056] 1. Structure and function of porous titanium alloy matrix

[0057] 1.1) Microscopic morphology design: The regular pit structure (diameter 100-300μm, spacing 50-200μm) formed by laser drilling enhances lubrication in the following ways:

[0058] Liquid storage effect: The pits act as "micro-liquid reservoirs" that can adsorb and slowly release lubricants (such as zwitterionic solutions, calf serum, and phosphate buffer solutions) to continuously replenish the lubrication interface.

[0059] Stress dispersion: The porous structure disperses contact stress, reduces local pressure, and prevents the lubricating film from rupturing.

[0060] 1.2) Thermal oxide layer reinforcement:

[0061] The oxide layer (such as TiO2) generated by thermal oxidation treatment at 700-800℃ significantly improves the hardness and wear resistance of the substrate and reduces the generation of microcracks and abrasive particles during the friction process.

[0062] 2. Covalent bonding in the functional interface layer

[0063] Hydroxylation and silane coupling agent modification:

[0064] 2.1) Hydroxylation treatment enriches the surface of titanium alloy with hydroxyl groups (-OH), which hydrolyze with the methoxy group (-OCH3) of silane coupling agent (KH570) to form Si-O-Ti covalent bonds;

[0065] 2.2) The terminal carbon-carbon double bond (C=C) of KH570 undergoes free radical copolymerization with acrylamide monomers in the hydrogel precursor to form strong interfacial covalent bonds, preventing the hydrogel layer from peeling off during friction.

[0066] 3. Biomimetic lubrication mechanism of negatively charged hydrogel layers

[0067] 3.1) Chemical composition:

[0068] The hydrogel is composed of acrylamide (AM), 2-acrylamido-2-methyl-1-propanesulfonic acid (AMPS), etc., in which the sulfonic acid group (-SO3H) of AMPS endows the hydrogel with negative charge.

[0069] 3.2) Electrostatic adsorption and lubrication layer formation:

[0070] Negatively charged hydrogels adsorb cations or zwitterions (such as SBMA) through electrostatic interactions, forming a dynamic hydrated lubricating layer.

[0071] SBMA's zwitterionic structure (containing quaternary ammonium cations and sulfonic acid anions) adsorbs a large number of water molecules through strong hydration, forming a hydrated film with a thickness of about 1-10 nm, achieving boundary lubrication and significantly reducing the coefficient of friction (down to 0.02).

[0072] 4. Dynamic response characteristics of the self-lubricating adsorption layer

[0073] 4.1) Lubrication enhancement mechanism of zwitterions:

[0074] SBMA molecules form an ordered hydrophilic layer on the surface of the hydrogel, and their hydration produces a "superlubricating effect" under frictional shear force.

[0075] Under load, the zwitterionic layer can dynamically adjust its orientation, reducing the direct contact area through the "molecular brush" effect, thereby further reducing frictional resistance.

[0076] 4.2) Micro-control of the freeze-thaw cycle:

[0077] Cyclic treatment induces the formation of a denser physical cross-linked network inside the hydrogel, improving its mechanical strength and lubricant retention capacity, and preventing the lubricant layer from extruding and failing under high pressure.

[0078] 5. Biomimetic synergistic effect of composite interfaces

[0079] 5.1) Biomimetic simulation of natural articular cartilage:

[0080] Soft / hard gradient structure: titanium alloy (hard) → hydrogel (soft) → zwitterionic lubricating layer (ultra-soft), simulating the layered mechanical properties of cartilage-subchondral bone to achieve gradient load transfer;

[0081] Biomimetic lubrication mechanism: The function of the proteoglycan-hyaluronic acid lubricating layer in natural joints is reproduced through negatively charged adsorption and hydration lubrication.

[0082] 5.2) Dynamic self-healing capability:

[0083] When local lubricant is lost during friction, the porous matrix can release the stored lubricant, and zwitterionic molecules diffuse to re-cover the surface, achieving dynamic repair of the lubricating layer.

[0084] In summary, the core logic for optimizing the lubrication performance of the self-lubricating hydrogel titanium alloy biomimetic joint bearing interface in this invention is as follows:

[0085] a. Structured liquid reservoir (porous matrix) → strong interfacial bonding (covalent bond) → molecular lubrication (zwitterionic hydration layer) → dynamic response (load adaptation and self-healing);

[0086] b. Through the synergistic effect of microstructure design and chemical composition, the coefficient of friction is reduced from 0.3-0.5 of titanium alloy to 0.02-0.08, which is close to the level of natural joints (0.0005-0.04), while also having high wear resistance and long-term stability.

[0087] It is important to note that, from Figure 3 As can be seen from the experimental bar chart, the friction coefficient of the zwitterionic adsorption solution is lowest at 10 mg / ml under 2N and 3N loads, while the friction coefficient of the zwitterionic adsorption solution at 15 mg / ml under 2N and 3N loads tends to be roughly balanced. Based on this, it is concluded that the preferred range of friction coefficient of the self-lubricating hydrogel titanium alloy bionic joint bearing interface of the present invention under 2-3N load is 0.02-0.08.

[0088] The advantages of this invention are as follows:

[0089] 1) A two-phase treatment method combining laser drilling and thermal oxidation is used to construct a porous titanium alloy substrate with high wear resistance. This method has advantages such as simpler preparation process, better repeatability, faster speed and environmental friendliness.

[0090] 2) By introducing a silane coupling agent containing carbon-carbon double bonds, it can covalently crosslink with the carbon-carbon double bond monomers in the hydrogel precursor solution under ultraviolet light irradiation, thereby further improving the bonding performance between the hydrogel layer and the substrate.

[0091] 3) By using electrostatic adsorption technology, zwitterionic ions of SBMA are dynamically adsorbed onto the surface of the negatively charged hydrogel layer, which simulates the adsorption of biomacromolecules in synovial fluid by natural cartilage during movement, and further improves the hydration boundary lubrication capability of the composite bearing interface.

[0092] The above description is only a preferred embodiment of the present invention. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of the present invention, and these improvements and modifications should also be considered within the scope of protection of the present invention.

Claims

1. A self-lubricating hydrogel titanium alloy biomimetic joint bearing interface, characterized in that: include: Porous titanium alloy substrate: made of Ti6Al4V alloy, with a regularly distributed pit structure on the surface, the pit diameter is 100-300 μm and the pit spacing is 50-200 μm, and an oxide layer is formed by thermal oxidation treatment; Functionalized interface layer: The surface of the porous titanium alloy substrate is treated with hydroxylation and modified with a silane coupling agent, wherein the silane coupling agent is γ-(methacryloyloxy)propyltrimethoxysilane with carbon-carbon double bonds. Negatively charged hydrogel layer: covering the functionalized interface layer, composed of acrylamide, 2-acryloylamino-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol; The mass ratio of acrylamide, 2-acrylamide-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol is 1.0-2.0:0.3-1.0:0.005-0.02:0.005-0.02:0.1-1.0; Self-lubricating adsorption layer: It is attached to the surface of the negatively charged hydrogel layer by electrostatic adsorption and is composed of zwitterionic monomer SBMA with an adsorption concentration of 5-25 mg / mL. The friction coefficient of the self-lubricating hydrogel titanium alloy bionic joint bearing interface is 0.02-0.08 under a load of 2-3N.

2. The self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 1, characterized in that: The diameter of the pit is 200 μm and the spacing between the pits is 100 μm.

3. The self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 1, characterized in that: The crosslinking agent is N,N'-methylenebisacrylamide, and the photoinitiator is α-ketoglutaric acid.

4. The self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 1, characterized in that: The thickness of the negatively charged hydrogel layer is 50-200 μm.

5. The method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 1, characterized in that: Includes the following steps: Step 1: Pre-treat the Ti6Al4V substrate surface, including sanding, mechanical polishing, ultrasonic cleaning and nitrogen drying. Then, use laser drilling to drill holes in the Ti6Al4V substrate surface to form a porous structure with pit diameter of 100-300 μm and spacing of 50-200 μm. Then, perform secondary grinding and polishing on the edges of the micropores to eliminate the heat-affected zone at the edges of the micropores. Step 2: The porous Ti6Al4V sample prepared in Step 1 is subjected to thermal oxidation treatment at 700-800 ℃ for 5-30 hours, and then cooled in the furnace; Step 3: Perform surface hydroxylation treatment and silane coupling agent modification on the sample after thermal oxidation in Step 2; Step 4: Construct a negatively charged hydrogel layer surface for the sample from Step 3 by mixing and dissolving acrylamide, 2-acrylamido-2-methyl-1-propanesulfonic acid, crosslinking agent, photoinitiator and polyvinyl alcohol in deionized water to obtain a hydrogel precursor solution. Step 5: Coat the surface of the Ti6Al4V sample obtained in Step 3 with the hydrogel precursor solution and cure it by ultraviolet irradiation to obtain a negatively charged hydrogel titanium alloy composite sample. Step 6: The negatively charged hydrogel titanium alloy composite sample obtained in Step 5 is subjected to freeze-thaw cycle treatment and then immersed in zwitterionic SBMA solution for adsorption to obtain a hydrogel titanium alloy biomimetic joint bearing interface with self-lubricating properties.

6. The method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 5, characterized in that: In step 2, the temperature is increased to 700°C at a heating rate of 10°C / min, and the thermal oxidation temperature of 700°C is maintained for 10 hours, followed by cooling to room temperature.

7. The method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 5, characterized in that: In step 4, the hydrogel precursor solution is composed of: 1.6324 g of acrylamide, 0.5 g of 2-acrylamido-2-methyl-1-propanesulfonic acid, 0.01 g of N,N'-methylenebisacrylamide, 0.01 g of α-ketoglutaric acid, and 0.4 g of polyvinyl alcohol.

8. The method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 5, characterized in that: In step 5, the ultraviolet irradiation is performed under an ultraviolet lamp for 30 minutes.

9. The method for preparing a self-lubricating hydrogel titanium alloy biomimetic joint bearing interface according to claim 5, characterized in that: In step 6, the number of freeze-thaw cycles is 3-5, the concentration of the adsorption solution is 5-25 mg / mL, and the adsorption time is 12-48 hours.

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