Antibacterial titanium alloy coating with friction reduction and preparation method and application thereof

Abstract

This invention belongs to the field of friction-reducing and antibacterial coating technology, and discloses a friction-reducing and antibacterial titanium alloy coating, its preparation method, and its application. The method includes the following steps: preparing an interlaced elliptical microtexture on the surface of a titanium alloy; sequentially performing N-ion implantation and Cu-ion implantation; and then chemically plating copper onto the titanium alloy surface after ion implantation to obtain the friction-reducing and antibacterial titanium alloy coating. The textured surface prepared by this invention, combined with the metallic copper layer, results in better protein adhesion to the sample surface, significantly improved lubrication and antibacterial properties. The friction coefficient is 0.362-0.483 in the atmosphere, 0.222-0.326 in simulated body fluids, and 0.196-0.236 in serum, with an antibacterial rate of 98-100%. This invention features high preparation precision, regular shape, adjustable coating thickness, and a unique surface texture that can support at least one year of human activity, making it applicable to surgical implants such as artificial hip joints.

Description

Technical Field

[0001] This invention belongs to the field of friction-reducing and antibacterial coating technology, specifically relating to a friction-reducing and antibacterial titanium alloy coating, its preparation method, and its application. Background Technology

[0002] With the increasing aging population and improved quality of life in various countries, the demand for artificial joints is increasing year by year. Irregular work and rest schedules, lack of exercise, and abuse of hormone drugs can easily lead to femoral head necrosis. Therefore, the development of long-life hip joints is urgent. According to statistics, artificial joints begin to show "service failure" after about 10 years. This is due to the biomechanical mismatch or deterioration of friction properties between the implant and the body's bone, leading to loosening, displacement, or osteolysis or fracture of the prosthesis. Commonly used hip joint prosthesis materials include metal-polymer, ceramic-polymer, ceramic-metal, and metal-metal combinations. The polyethylene abrasion generated during the service of the clinically commonly used "ultra-high molecular weight polyethylene-metal prosthesis" can induce osteolysis, affecting the late-stage integrity rate and causing aseptic loosening. Metal prosthesis abrasion can lead to an increase in serum metal ion levels, increasing the risk of allergies and nephrotoxicity. Ceramic prostheses have high hardness, wear resistance, corrosion resistance, and the best bioinertness, but they are brittle, have low fracture strength and tensile strength, and are expensive. Bone joints play a role in bearing weight and coordinating movement. When artificial joints come into contact with the body, there is an active interface near the bone end and a friction interface near the ball end.

[0003] Titanium and titanium alloys possess advantages such as light weight, high specific strength, resistance to high and low temperatures, excellent corrosion resistance, and good biocompatibility, making them suitable for intramedullary nails, bone plates, dental implants, and various artificial joints. However, titanium and titanium alloys have poor wear resistance. Friction-generated wear debris affects the differentiation and maturation of osteoclasts and induces inflammatory responses in macrophages, leading to osteolysis and aseptic loosening. An ideal friction interface requires a low coefficient of friction, high wear resistance, and minimal wear debris. Therefore, the development of biomimetic interfaces to enhance friction reduction and wear resistance has emerged.

[0004] The hip joint, composed of the femoral head and acetabulum, is the largest ball-and-socket joint in the human body and also the joint that bears the most weight. Due to various reasons, its function fails, and total hip replacement surgery has been the most successful clinical treatment method for the past 50 years. However, various types of artificial hip joints still cannot achieve the good lubrication performance of natural joints, and most patients require secondary surgery due to osteolysis and subsequent prosthesis loosening. Therefore, studying the friction, wear, and lubrication mechanisms of artificial hip joints to reduce wear after implantation is crucial for their successful clinical use. Microtextures play a role in storing wear debris and reducing the contact area during friction. In the presence of a lubricating medium, they can also store synovial fluid and increase the thickness of the converging membrane between contact surfaces to provide additional load-bearing capacity. Meanwhile, bacterial infection after prosthesis implantation remains an unresolved clinical problem. Metal ions such as Ag, Cu, Zn, and Mn have bactericidal functions, attracting negatively charged cells, altering cell membrane permeability, or entering bacterial cells to disrupt enzyme activity, leading to bacterial death. Therefore, the strong bactericidal function of copper ions can be used to maintain the biocompatibility of the prosthesis. Summary of the Invention

[0005] Addressing the shortcomings of titanium and titanium alloys in terms of wear resistance and antibacterial properties, and their promising application prospects in artificial hip joints, the primary objective of this invention is to provide a method for preparing a friction-reducing and antibacterial titanium alloy coating. This method involves necessary surface modification to better suit its application in joint prostheses. This invention introduces microtextures into the titanium alloy surface for modification, thereby reducing the contact area at the friction interface, storing synovial fluid, and thus improving lubrication performance.

[0006] Another objective of this invention is to introduce a metallic Cu coating to enhance the antibacterial properties of titanium alloys and improve their biocompatibility.

[0007] Another object of the present invention is to provide a friction-reducing and antibacterial titanium alloy coating.

[0008] Another object of the present invention is to provide the application of the above-mentioned friction-reducing and antibacterial titanium alloy coating.

[0009] The objective of this invention is achieved through the following technical solution:

[0010] A method for preparing a friction-reducing and antibacterial titanium alloy coating includes the following steps:

[0011] An interlaced elliptical microtexture was prepared on the surface of a titanium alloy, followed by N-ion implantation and Cu-ion implantation. After ion implantation, the titanium alloy surface was electroless coated with copper to obtain a friction-reducing and antibacterial titanium alloy coating.

[0012] Preferably, the major axis of the ellipse is 100±5μm, the minor axis is 50±5μm, the depth is 150±20μm, the geometric center spacing of the elliptical microtexture is 99μm~280μm, and the density is 5%~40%.

[0013] Preferably, the crisscrossing elliptical microtexture is prepared using a picosecond ultraviolet laser with a power of 15W to 30W, a frequency of 500±200kHz, and a scanning speed of 1000±200mm / s.

[0014] Preferably, the vacuum degree during N ion implantation is 1×10⁻⁶. -3 ~6×10 -3 Pa, accelerating voltage 30–70 kV, injection dose 1 × 10 17 ~6×10 17 ions / cm 2 .

[0015] Preferably, the vacuum degree during Cu ion implantation is 1×10⁻⁶. -4 ~5×10 -4 Pa, accelerating voltage 30–60 kV, injection dose 1 × 10 17 ~8×10 17 ions / cm 2 conduct.

[0016] Preferably, the chemical copper plating conditions are as follows: the titanium alloy is suspended and immersed in a plating solution at 50-70°C for 5-15 minutes, the pH of the plating solution is 12.4±1, and the plating thickness is 2-3 μm;

[0017] The plating solution consists of: 10-20 g / L CuSO4·5H2O, 20-30 g / L EDTA-2Na, 5-20 mL / L 37% formaldehyde solution, and 0.01-0.05 g / L 2,2-bipyridine.

[0018] Preferably, the alloy surface is degreased, sensitized, and activated before the electroless copper plating;

[0019] More specifically, after degreasing, the product is washed with water, dried, and then immersed in a sensitizer for sensitization; after washing with water, dried, and then immersed in an activator for activation; and after washing with water, dried, and then immersed in a plating solution for chemical copper plating.

[0020] The degreasing agent used is a solution prepared with 30-50 g / L NaOH, 5-20 g / L NaCO3 and water. The degreasing conditions are a water bath at 40-60℃ for 10-20 min.

[0021] The sensitizing agent used is a solution prepared with 30-60 mL / L 37% HCl, 5-15 g / L SnCl2 and water, and the sensitization time is 10-20 min;

[0022] The activating agent used is 1-3 g / L AgNO3 solution, and the activation time is 5-20 min.

[0023] Preferably, the titanium alloy is a near-β type titanium alloy TLM (Ti-3Zr-2Sn-3Mo-25Nb), TAI (Ti), or TC4 (Ti6Al4V);

[0024] Before preparing the crisscrossing elliptical microtexture on the surface of the titanium alloy, it is also sanded with 500#, 1000# and 2500# sandpaper in sequence.

[0025] A friction-reducing and antibacterial titanium alloy coating is prepared by the method described above.

[0026] The application of the above-mentioned friction-reducing and antibacterial titanium alloy coating in the preparation of surgical implants.

[0027] The preferred material is the friction interface used to prepare the hip joint prosthesis, namely the contact interface between the femoral head and the acetabular cup.

[0028] Compared with the prior art, the present invention has the following advantages and beneficial effects:

[0029] (1) This invention utilizes a picosecond ultraviolet laser to fabricate a longitudinal and transverse elliptical texture. The interlacing of the ellipses ensures symmetry in the sliding of the friction interface, maximizing lubrication performance in all directions. The unique surface texture can support at least one year's worth of human activity. The microtexture fabricated by the picosecond ultraviolet laser exhibits minimal sputtering, and the process is mature and refined, maximizing the uniformity of the friction interface.

[0030] (2) High-energy ion nitrogen implantation generates harder TiN on the textured alloy surface, which improves lubrication performance; the implantation depth of the metallic element copper is about tens of nanometers, the implantation is uniform and the bonding force is good, the performance is stable, and it provides nano nucleation sites for subsequent electroless copper plating.

[0031] (3) Chemical copper plating is carried out on the basis of ion implantation. The method is simple and easy to operate, and the coating thickness is controllable. The coating thickness is controlled by controlling the time the sample is immersed in the plating solution. If the coating is too thin, it cannot support the shear force generated during the friction process. If it is too thick, it will deteriorate its adhesion to the substrate. The coating thickness of this invention is 2-3 μm.

[0032] (4) The textured surface prepared by this invention is combined with the copper layer, which makes the protein adhesion performance of the sample surface better, and the lubrication and antibacterial properties are significantly improved. The friction coefficient in the atmosphere is 0.362-0.483, the friction coefficient in simulated body fluid is 0.222-0.326, the friction coefficient in serum is 0.196-0.236, and the antibacterial rate can reach 98%-100%. Attached Figure Description

[0033] The accompanying drawings, which are included to provide a further understanding of the invention and form part of this application, illustrate exemplary embodiments of the invention and are used to explain the invention, but do not constitute an undue limitation of the invention.

[0034] Figure 1 These are the texture metallographic images of three different texture densities prepared in Example 1: (a)(a1) is TT5, (b)(b1) is TT15, and (c)(c1) is TT40.

[0035] Figure 2 This is a SEM image of the copper plating thickness on the surface of the TT-NCuII / Cu sample in Example 1.

[0036] Figure 3 The antibacterial rate of a series of modified samples prepared in Example 1 is given by TT, where TT represents the sample with a texture density of 15%, TT-NII represents the sample after texturing and nitrogen injection, TT-NCuII represents the sample after texturing and nitrogen injection and copper injection, and TT-NCuII / Cu represents the sample after texturing, nitrogen injection and copper injection and copper plating. Detailed Implementation

[0037] The present invention will be further described in detail below with reference to embodiments, but the implementation of the present invention is not limited thereto.

[0038] Unless otherwise specified in the embodiments of this invention, the conditions shall be performed according to conventional conditions or conditions recommended by the manufacturer. All raw materials and reagents used, unless otherwise specified, are commercially available conventional products.

[0039] TLM (Ti-3Zr-2Sn-3Mo-25Nb): Purchased from Northwest Nonferrous Metals Research Institute;

[0040] TA1 (Pure Ti Grade 1): Any commercially available one is acceptable;

[0041] TC4 (Ti6Al4V): Any commercially available one is acceptable;

[0042] Picosecond UV laser model: Suzhou Yinggu Laser Co., Ltd., GXP-355-30;

[0043] High-energy ion implanter model: LZD-600-G.

[0044] Degreasing agent: 30g / L NaOH, 10g / L NaCO3, water;

[0045] Sensitizer: 40 mL / L 37% hydrochloric acid, 10 g / L SnCl2, water. For example, to prepare 200 mL of sensitizer, first add 192 mL of deionized water, then add 8 mL of 37% hydrochloric acid, and then add 2 g of SnCl2.

[0046] Activator: 0.2g AgNO3, 100mL deionized water;

[0047] Chemical copper plating solution: 15 g / L CuSO4·5H2O, 25 g / L EDTA-2Na, 10 mL / L 37% formaldehyde, 0.02 g / L 2,2-bipyridine, and 3 mol / L NaOH solution to adjust the pH of the plating solution to approximately 11.

[0048] Example 1

[0049] A Φ11mm×5mm TLM (Tracked Medium Lamination) was used. The sample surface was sequentially polished with 500#, 1000#, and 2500# sandpaper. Laser-textured surfaces were prepared using a UV picosecond laser (Suzhou Yinggu Laser Co., Ltd., GXP-355-30, power: 30W, frequency: 500kHz, scanning speed: 1000mm / s). The ellipse had a major axis of 100μm, a minor axis of 50μm, and a depth of approximately 150μm. Three spacings of 280μm, 161μm, and 99μm corresponded to densities of 5%, 15%, and 40%, respectively. Figure 1 The microtextured sample was ultrasonically cleaned with anhydrous ethanol for 15 min and then dried. A high-energy ion implanter was used at a vacuum of 5 × 10⁻⁶. -3 Pa, accelerating voltage 60kV, injection dose 4×10 17 ions / cm 2 Nitrogen implantation was performed, and the nitrogen-implanted sample with a texture density of 15% was designated TT-NII. The high-energy ion implanter operated at a vacuum of 5 × 10⁻⁶. -4 Pa, accelerating voltage 50kV, injection dose 6×10 17 ions / cm 2 Ion implantation with copper was performed, and the nitrogen-implanted and copper-implanted sample with a texture density of 15% was designated TT-NCuII. The sample was then ultrasonically cleaned again in anhydrous ethanol for 15 min and dried. It was then immersed in a degreasing agent at 40℃ for 10 min to remove oil, quickly rinsed and dried, and then immersed in a sensitizing reagent for 15 min to form an easily oxidized divalent tin gel film on the surface. It was then rinsed and dried. Next, it was immersed in a 2 g / L AgNO3 solution for 10 min to reduce catalytically active Ag ions, forming metal particles on the surface as catalytic centers. It was then rinsed and dried. Finally, electroless copper plating was performed. At the start of plating, the plating solution was heated to 60℃, and the pH of the plating solution was adjusted to 12.4 with 3 mol / L NaOH solution before immersing the sample in the electroless copper plating solution for 5 min. Figure 2 A friction-reducing and antibacterial titanium alloy coating was prepared, with a texture density of 15%. The nitrogen-injected, copper-injected, and copper-plated sample was designated as TT-NCuII / Cu.

[0050] This embodiment uses a multifunctional tribometer (Rtec MFT-5000tribometer, Rtec Instruments, America) to test the reciprocating tribological performance. Preliminary tribological evaluations were performed on the microtextured samples in atmospheric, simulated body fluid, and 30 g / L fetal bovine serum environments. A polytetrafluoroethylene (PTFE) bath was selected for the tests in a liquid environment, and ZrO2 balls with a diameter of 6 mm were used as the grinding balls. All tests were conducted at room temperature (20–25 °C) for 30 min. The contact load was 1 N, the sliding frequency was 1 Hz, and the reciprocating sliding distance was 5 mm. Before the tests, the mating materials and samples were ultrasonically cleaned with deionized water and ethanol. The three samples with spacings of 280 μm, 161 μm, and 99 μm were designated TT5, TT15, and TT40, respectively. The coefficients of friction in fetal bovine serum were 0.236, 0.196, and 0.210, respectively. Tribological tests were conducted on samples with a spacing of 161 μm, i.e., a texture density of 15%. The results showed a friction coefficient of 0.362 in the atmosphere, 0.320 in simulated body fluids, and 0.196 in serum.

[0051] The samples were co-cultured with Staphylococcus aureus for 3 hours, and the antibacterial performance was evaluated using the plate spread method, with an antibacterial rate of 99.41%. Specifically, Gram-positive Staphylococcus aureus ATCC 6538 was selected as the experimental bacteria. Before the experiment, the samples were immersed in 75% ethanol solution and exposed to ultraviolet light for 30 minutes for sterilization. The samples were then washed with PBS solution and transferred to 24-well plates. The bacterial suspension was diluted to 5 × 10⁻⁶. 5 A concentration of CFU / mL was used to add 100 μL of bacterial suspension to the surface of each sample, followed by incubation at 37°C for 3 h. The bacterial suspension was then collected from the sample surface and appropriately diluted with PBS solution. 100 μL of the bacterial suspension was spread onto an agar plate and incubated at 37°C for 12 h. The antibacterial rate (AR) was calculated as follows: AR = (Nc - Nt) / Nc × 100%, where Nc and Nt represent the average colony counts of the control and test samples, respectively. Figure 3 The antibacterial rate of TT-NCuII / Cu can reach 99.41%.

[0052] Example 2

[0053] A 15mm × 5mm TA1 abrasive was used. The sample surface was sequentially polished with 500#, 1000#, and 2500# sandpaper. Laser texturing was then performed at 30W picosecond UV light. The ellipse had a major axis of 100μm, a minor axis of 50μm, and a depth of approximately 150μm. Three spacings of 280μm, 161μm, and 99μm corresponded to densities of 5%, 15%, and 40%, respectively. The textured sample was ultrasonically cleaned with anhydrous ethanol for 15 minutes and then dried. A high-energy ion implanter was used at a vacuum of 6 × 10⁻⁶.-3 Pa, accelerating voltage 60kV, injection dose 6×10 17 ions / cm 2 Nitrogen ion implantation was performed. The high-energy ion implanter operated at a vacuum level of 5 × 10⁻⁶. -4 Pa, accelerating voltage 50kV, injection dose 8×10 17 ions / cm 2 Ion implantation with copper was performed. The sample was ultrasonically cleaned again in anhydrous ethanol for 10 min and then dried. It was then immersed in a degreasing agent at 40℃ for 10 min to remove oil, followed by rapid rinsing and drying. Immersion in a sensitizing reagent for 15 min formed an easily oxidizable divalent tin gel film on the surface, followed by rinsing and drying. Immersion in a 2 g / L AgNO3 solution reduced catalytically active Ag ions, forming metal particles on the surface as catalytic centers, followed by rinsing and drying. Finally, electroless copper plating was performed. At the start of plating, the plating solution was heated to 60℃, and the pH of the plating solution was adjusted to 12.4 with 3 mol / L NaOH solution. The sample was then immersed in the electroless copper plating solution for 10 min to obtain a friction-reducing and antibacterial titanium alloy coating.

[0054] The friction coefficients of samples with spacings of 280 μm, 161 μm, and 99 μm in fetal bovine serum were 0.336, 0.210, and 0.310, respectively. The sample with a spacing of 161 μm underwent a series of modifications and tribological tests, showing a friction coefficient of 0.338 in atmosphere, 0.222 in simulated body fluid, and 0.210 in serum. The antibacterial properties of the sample were evaluated using the plate coating method after co-culturing with Staphylococcus aureus for 3 hours, achieving an antibacterial rate of 100%.

[0055] Example 3

[0056] A 10mm × 10mm × 5mm Ti6Al4V (TC4) abrasive was used, and the sample surface was successively polished with 500#, 1000#, and 2500# sandpaper. Laser texturing of the surface was performed using a 15W picosecond UV laser. The major axis of the ellipse was 100μm, the minor axis was 50μm, and the depth was approximately 150μm. Three spacings of 280μm, 161μm, and 99μm corresponded to densities of 5%, 15%, and 40%, respectively. After texturing, the sample was ultrasonically cleaned with anhydrous ethanol for 10 min and then dried. A high-energy ion implanter was used at a vacuum of 5 × 10⁻⁶. -3 Pa, accelerating voltage 60kV, injection dose 4×10 17 ions / cm 2 Nitrogen ion implantation was performed. The high-energy ion implanter operated at a vacuum level of 5 × 10⁻⁶. -4 Pa, accelerating voltage 50kV, injection dose 6×10 17 ions / cm 2Ion implantation of copper was performed. The sample was ultrasonically cleaned again in anhydrous ethanol for 10 min and then dried. It was then immersed in a degreasing agent at 60°C for 10 min to remove oil, followed by rapid rinsing and drying. Immersion in a sensitizing reagent for 15 min formed an easily oxidizable divalent tin gel film on the surface, followed by rinsing and drying. Immersion in a 2 g / L AgNO3 solution for 10 min reduced catalytically active Ag ions, forming metal particles on the surface as catalytic centers, followed by rinsing and drying. Finally, electroless copper plating was performed. At the start of plating, the plating solution was heated to 60°C, and the pH of the plating solution was adjusted to 12.4 with 3 mol / L NaOH solution before immersion in the electroless copper plating solution for 15 min.

[0057] The friction coefficients of samples with spacings of 280 μm, 161 μm, and 99 μm in fetal bovine serum were 0.315, 0.236, and 0.223, respectively. The sample with a spacing of 161 μm underwent a series of modifications and tribological tests, showing a friction coefficient of 0.483 in atmosphere, 0.362 in simulated body fluid, and 0.236 in serum. The antibacterial properties of the sample were evaluated using the plate coating method after co-culturing with Staphylococcus aureus for 3 hours, achieving an antibacterial rate of 98%.

[0058] Comparative Example 1

[0059] A 10mm × 10mm × 5mm Ti6Al4V (TC4) abrasive was used, and the sample surface was successively polished with 500#, 1000#, and 2500# sandpaper. Laser texturing of the surface was performed using a 30W UV picosecond laser, with an ellipse major axis of 100μm, a minor axis of 50μm, and a depth of approximately 150μm. Three spacings of 280μm, 161μm, and 99μm corresponded to densities of 5%, 15%, and 40%, respectively. The textured sample was ultrasonically cleaned with anhydrous ethanol for 15 minutes and then dried. A high-energy ion implanter was used at a vacuum of 5 × 10⁻⁶. -3 Pa, accelerating voltage 60kV, injection dose 4×10 17 ions / cm 2 Nitrogen ion implantation was performed. The high-energy ion implanter operated at a vacuum level of 5 × 10⁻⁶. -4 Pa, accelerating voltage 50kV, injection dose 6×10 17 ions / cm 2 Copper ion implantation was performed. The sample was then ultrasonically cleaned again in anhydrous ethanol for 15 minutes and dried. Roughness and coefficient of friction were then measured.

[0060] According to the test method of Example 3, the friction coefficient of the sample prepared in Comparative Example 1 was 0.4829 in the atmosphere, 0.4624 in the simulated body fluid, and 0.3356 in the serum. The friction coefficient of the coating in Comparative Example 1 was significantly greater than that of the coating in Example 3. The roughness and friction coefficient were higher than those of the copper-plated sample. In Example 3, the soft phase metallic copper layer prepared by chemical copper plating played a good role in reducing friction as a lubricant, thus reducing the friction coefficient.

[0061] The sample was co-cultured with Staphylococcus aureus for 3 hours, and its antibacterial properties were evaluated using the plate coating method. The antibacterial rate was 62.5%. The antibacterial performance was not significant when the copper content of the ion implantation was low.

[0062] Comparative Example 2

[0063] A Φ11mm×5mm TLM was selected, and the sample surface was successively polished using 500#, 1000#, and 2500# sandpaper. A high-energy ion implanter was used at a vacuum degree of 5×10⁻⁶. -3 Pa, accelerating voltage 60kV, injection dose 4×10 17 ions / cm 2 Nitrogen ion implantation was performed. The high-energy ion implanter operated at a vacuum level of 5 × 10⁻⁶. -4 Pa, accelerating voltage 50kV, injection dose 6×10 17 ions / cm 2 Ion implantation of copper was performed. The sample was ultrasonically cleaned again in anhydrous ethanol for 15 min and then dried. It was then immersed in a degreasing agent at 60°C for 10 min to remove oil, followed by rapid rinsing and drying. It was then immersed in a sensitizing reagent for 15 min to form an easily oxidizable divalent tin gel film on the surface, followed by rinsing and drying. Finally, it was immersed in a 2 g / L AgNO3 solution for 10 min to reduce catalytically active Ag ions, forming metal particles on the surface as catalytic centers, followed by rinsing and drying. The pH of the plating bath was adjusted to 12.4 with a 3 mol / L NaOH solution, and the sample was then immersed in a chemical copper plating solution for 15 min.

[0064] According to the test method of Example 1, the coefficient of friction of the sample prepared in this comparative example in calf serum was 0.276.

[0065] Comparative Example 3

[0066] When using ordinary lasers to prepare surface textures, it is difficult to achieve precise preparation of textures of the above dimensions due to the low resolution of the equipment and the poor accuracy of morphology control.

[0067] The above embodiments are preferred embodiments of the present invention, but the embodiments of the present invention are not limited to the above embodiments. Any changes, modifications, substitutions, combinations, or simplifications made without departing from the spirit and principle of the present invention shall be considered equivalent substitutions and shall be included within the protection scope of the present invention.

Claims

1. A method for preparing a friction-reducing and antibacterial titanium alloy coating, characterized in that, Includes the following steps: An interlaced elliptical microtexture is prepared on the surface of titanium or titanium alloy, and then N ion implantation and Cu ion implantation are performed sequentially. After ion implantation, copper is electroless plated on the surface of the titanium alloy to finally obtain a friction-reducing and antibacterial titanium alloy coating. The major axis of the ellipse is 100±5μm, the minor axis is 50±5 μm, the depth is 150±20 μm, and the spacing of the elliptical microtexture is 99μm~280μm; The vacuum degree during N ion implantation is 1×10⁻⁶. -3 ~6×10 -3 The implantation dose of Pa and N ions is 1×10 17 ~6×10 17 ions / cm 2 The implantation dose of Cu ions is 1×10⁻⁶. 17 ~8×10 17 ions / cm 2 .

2. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The texture density is 5%~40%.

3. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The crisscrossing elliptical microtextures were fabricated using a picosecond ultraviolet laser with a power of 15W~30W, a frequency of 500±200 kHz, and a scanning speed of 1000±200 mm / s.

4. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The accelerating voltage during N-ion implantation is 30~70 kV.

5. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The vacuum degree during Cu ion implantation is 1×10⁻⁶. -4 ~5×10 -4 Pa, accelerating voltage is 30~60 kV.

6. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The chemical copper plating conditions are as follows: immerse the titanium alloy in a plating solution at 50~70℃ for 5~15 minutes; The plating solution consists of 10-20 g / L CuSO4·5H2O, 20-30 g / L EDTA-2Na, 5-20 mL / L 37% formaldehyde solution, and 0.01-0.05 g / L 2,2-bipyridine.

7. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, Before electroless copper plating, the alloy surface is degreased, sensitized, and activated; The degreasing agent used for degreasing is a solution prepared with 30~50 g / L NaOH and 5~20 g / L NaCO3; the sensitizing agent used for sensitization is a solution prepared with 30~60 mL / L 37% HCl and 5~15 g / L SnCl2; the activating agent used for activation is a 1~3 g / L AgNO3 solution.

8. The method for preparing a friction-reducing and antibacterial titanium alloy coating according to claim 1, characterized in that, The titanium alloy is either Ti-3Zr-2Sn-3Mo-25Nb or Ti-6Al-4V; Before preparing the crisscrossing elliptical microtexture on the surface of the titanium alloy, it is also sanded.

9. A friction-reducing and antibacterial titanium alloy coating, characterized in that, It is prepared by the method described in any one of claims 1 to 8.

10. The application of the anti-friction and antibacterial titanium alloy coating of claim 9 in the preparation of surgical implants.

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