Preparation method of high-toughness super-hydrophilic titanium-zirconium alloy dental implant

Abstract

A kind of preparation method of high-toughness super-hydrophilic titanium-zirconium alloy dental implant, comprising the following steps: step 01, preparation of titanium sponge and zirconium sponge;Step 02, Ti-Zr binary alloy ingot is melted by using vacuum melting furnace;Step 03, heat preservation of Ti-Zr binary alloy ingot;Step 04, Ti-Zr binary alloy ingot is opened by using free forging process;Step 05, equal-diameter angular extrusion of Ti-Zr binary alloy ingot blank;Step 06, the blank is soaked in etching liquid for 6-12 hours, and then surface finishing and cleaning are carried out;Step 07, mechanical treatment is carried out on the blank;Step 08, Ti-Zr binary alloy rod is finely ground, and the implant semi-finished product is obtained after machining by the heart machine, and then sand blasting treatment is carried out after cleaning and drying;Step 09, super-hydrophilic acid etching treatment is carried out on the implant semi-finished product after sand blasting. It has good biocompatibility, good bone bonding performance and excellent mechanical properties.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of biomaterial preparation, and particularly relates to a preparation method of a high-strength and high-toughness super-hydrophilic titanium-zirconium alloy dental implant. BACKGROUND

[0002] The existing dental implant has the following shortcomings: first, the initial stability is poor, the surface energy of the ordinary implant is small, the affinity with water, protein, sugar and the like is small, the cell adhesion is poor in the initial implantation period, the initial stability is poor, and the implantation failure is easily caused. Second, the mechanical property is poor, and the commercially available implant is mainly made of pure titanium, the tensile strength is only about 580 MPa, and the dynamic fatigue strength of 50 million times is only 200 MPa, and the poor mechanical property easily causes the implant to break. Third, the alloy has toxicity, other medical alloys, such as medical stainless steel, cobalt-based alloy, Ti-6Al-4V alloy and the like, the ions such as Ni, Cr, Co, V and Al in the alloys are separated and enter the human body, and the ions are toxic to the human body. SUMMARY

[0003] The present application provides a preparation method of a high-strength and high-toughness super-hydrophilic titanium-zirconium alloy dental implant, so as to solve the above-mentioned problems of the prior art, and the good biocompatibility, the good bone combination performance and the excellent mechanical property are achieved.

[0004] In order to achieve the purpose of the present application, the following technologies are adopted:

[0005] A preparation method of a high-strength and high-toughness super-hydrophilic titanium-zirconium alloy dental implant, comprising the following steps:

[0006] Step 01, sponge titanium and sponge zirconium are cleaned and dried for standby use.

[0007] Step 02, the Ti-Zr binary alloy ingot prepared in step 01 is melted by using a vacuum melting furnace.

[0008] Step 03, the Ti-Zr binary alloy ingot obtained in step 02 is kept at 1050±100 DEG C in a vacuum tube furnace for 4-8 hours, and is cooled to room temperature with the furnace, and the above-mentioned operation mode is to reduce the element segregation of the titanium-zirconium alloy ingot, and the homogenization treatment is needed before hot working, so as to ensure the smooth blooming. The non-equilibrium structure of the casting mainly relies on the atomic diffusion at high temperature to realize the homogenization of the composition. First, the atoms of the segregated elements are fully diffused, and the melting of the harmful phase in the homogenization process is avoided, and the “burning” phenomenon is generated, and the production cost and efficiency are considered. The thermal homogenization process is a thermal activation process, so the atomic diffusion coefficient follows the Arrhenius equation (κ = A e -Q / RT), in order to accelerate the homogenization process, the homogenization treatment temperature should be as high as possible. According to experience, the homogenization treatment temperature is usually 0.9 T 熔 ~ 0.95 T 熔 (T 熔 is the actual casting start melting temperature).

[0009] Step 04, in order to break the coarse columnar crystal of the ingot, optimize the precipitation phase homogenization process, size and morphology, and improve the cold and hot working performance of the blank. The free forging process is used for breaking down, that is, upsetting + elongation, to obtain a blank with uniform fine grain structure and avoid cracking. Therefore, the Ti-Zr binary alloy ingot obtained in step 03 is subjected to free forging process for breaking down.

[0010] Step 05, the Ti-Zr binary alloy ingot after forging obtained in step 04 is subjected to equal angle extrusion at 300℃≤T≤450℃, at least 4 times, and each time rotating 30~150° around the longitudinal axis. The equal angle extrusion needs to be in the α phase zone to reduce internal stress, but still retains the strength and toughness of the material after cold work hardening.

[0011] Step 06, the blank obtained in step 04 is soaked in etching liquid for 6~12 hours, and then subjected to surface finishing and cleaning after taking out.

[0012] Step 07, the blank obtained in step 06 is subjected to mechanical treatment at a temperature lower than 450℃, a strain rate of 10 -2 ~10 -4 , and a strain degree of 30~80%. The final forming of the material still needs to be in the α phase zone to reduce internal stress, and still retains the strength and toughness of the material after cold work hardening.

[0013] Step 08, the Ti-Zr binary alloy rod processed in step 07 is subjected to fine grinding, and the implant semi-finished product is obtained by machining through a lathe. After cleaning and drying, the implant semi-finished product is subjected to sand blasting treatment.

[0014] Step 09, the implant semi-finished product obtained in step 08 is subjected to super-hydrophilic acid etching treatment after sand blasting.

[0015] Step 10, the implant semi-finished product after step 09 treatment is subjected to ultrasonic cleaning with ultrapure water and then stored in physiological saline or CaCl2 aqueous solution at room temperature.

[0016] The titanium-zirconium alloy prepared has a grain size of 14, which is ultra-fine grain. The tensile strength can reach 1000 MPa, and the 50 million fatigue strength is more than 500 MPa. The surface roughness is significantly increased, and has micro-nano multi-level pores. The contact angle with water is less than 5°, which is a super-hydrophilic surface. The biocompatibility is good, which can promote early cell adhesion and late osteogenic differentiation.

[0017] Further, in step 02, the mass ratio of the Ti-Zr binary alloy is Ti:Zr = 10:90 ~ 90:10.

[0018] Further, in step 02, in order to ensure the uniformity of the ingot composition, the smelting furnace needs to be turned over by 180° during smelting, and the turning over is performed 3~6 times.

[0019] Further, in order to break the coarse columnar crystals of the ingot, optimize the uniformization process, size and morphology of the precipitated phase, and improve the cold and hot working performance of the blank, according to the Ti-Zr binary alloy phase diagram, the blanking forging is performed in the β phase region. Therefore, in step 04, when blanking, a high-temperature antioxidant is coated on the surface of the ingot, and the blanking forging is performed after heating to 1050±50℃ in a vacuum furnace for 1~3 hours. The final forging temperature is 850±100℃, and the final forging temperature also needs to be in the β phase region.

[0020] Finally, the obtained titanium alloy ingot is water quenched, and the surface oxides are removed and cleaned and dried.

[0021] Further, in order to ensure better grain refinement effect and smooth extrusion, in step 05, the intersection angle of the channel of the extruder is 90°≤ψ≤160°.

[0022] Further, in step 06, the etching liquid is a mixed aqueous solution of two or more of H2SO4, HCl, HF and HNO3, and the concentration of each acid solution is less than 50%.

[0023] Further, in order to form rough depressions with a size of about 100 μm and a depth of about several microns on the surface of the alloy, which is beneficial for cell adhesion. Therefore, in step 08, the sandblasting treatment conditions are 120~180 # white corundum, pressure 0.35~0.55 MPa, moving speed 1~3 mm / s, spindle speed 1~5 revolutions / s, distance 10~30 mm.

[0024] Further, in order to ensure that the sand on the surface of the alloy is completely removed and accelerate the acid etching reaction, in step 09, when performing the etching treatment, in the mixed aqueous solution of two or more of H2SO4, HNO3, HF and HCl, and the concentration of each acid solution is less than 50%, and heated to 60~110℃, and etched for 5~30min.

[0025] The above technical solution has the following advantages:

[0026] The dental implant prepared by the application has the following advantages: first, the dental implant is non-toxic to human body and does not cause inflammation or allergic reaction in the body; second, the surface chemistry, roughness, morphology and hydrophilicity of the implant play a major role in bone combination, so that the implant can be well combined with the bone; third, the dental implant prepared by the application has high strength and mechanical properties such as fatigue resistance, so that the contact point between the natural tooth and the implant tooth will not rub, the implant will not loosen and produce wear debris, and the dissolved ions will not cause allergic reactions and toxic reactions in the human body. BRIEF DESCRIPTION OF DRAWINGS

[0027] In order to make the purpose, technical scheme and advantages of the application more clear, the application will be further described in detail below with reference to the drawings.

[0028] Figure 1 The figure shows the finished product of titanium-zirconium alloy.

[0029] Figure 2 The figure shows the microstructure morphology of titanium-zirconium alloy.

[0030] Figure 3 The figure shows the microstructure morphology of titanium-zirconium alloy at 200 times.

[0031] Figure 4 The figure shows the microstructure morphology of titanium-zirconium alloy at 1000 times.

[0032] Figure 5 The figure shows the microstructure morphology of titanium-zirconium alloy at 2000 times.

[0033] Figure 6 The figure shows the hydrophilicity test result of titanium-zirconium alloy.

[0034] Figure 7 The figure shows the relationship between the proliferation of rat bone marrow stromal cells and the affinity effect of cells and days in titanium-zirconium alloy, titanium-zirconium alloy and commercial medical pure titanium sheet after surface treatment.

[0035] Figure 8 The figure shows the effect of rat bone marrow stromal cells spreading on the surface of titanium-zirconium alloy and cell affinity surface after surface treatment.

[0036] Figure 9 The figure shows the effect of rat bone marrow stromal cells spreading on the surface of titanium-zirconium alloy and cell affinity surface.

[0037] Figure 10 The figure shows the effect of rat bone marrow stromal cells spreading on the surface of commercial medical pure titanium sheet (control).

[0038] Figure 11Magnified images showing the affinity effect of titanium-zirconium alloy, titanium-zirconium alloy and cells after surface treatment on rat bone marrow stromal stem cells, mineralization effect diagram after 14 days of culture on commercial medical pure titanium sheet.

[0039] Figure 12 Magnified images showing the expression of angiogenesis and osteogenesis-related proteins of rat bone marrow stromal stem cells after 4 days of culture on titanium-zirconium alloy, titanium-zirconium alloy and commercial medical pure titanium sheet after surface treatment.

[0040] Figure 13 Magnified images showing the inflammatory response of titanium-zirconium alloy, titanium-zirconium alloy and commercial medical pure titanium sheet after surface treatment after 1 week of subcutaneous implantation in SD rats. DETAILED DESCRIPTION

[0041] Example 1

[0042] A method for preparing a high-toughness super-hydrophilic titanium-zirconium alloy dental implant, comprising the steps of:

[0043] Step 01, the sponge titanium and sponge zirconium are cleaned and dried for standby, wherein the purity of the sponge titanium is at least 99.99%, and the purity of the sponge zirconium is at least 99.95%.

[0044] Step 02, the Ti-Zr binary alloy ingot prepared in step 01 is melted by using a vacuum melting furnace, wherein the mass ratio of Ti to Zr is 85:15. During melting, the melting furnace needs to be turned over by 180° and turned over 3 times.

[0045] Step 03, the Ti-Zr binary alloy ingot obtained in step 02 is kept in a vacuum tube furnace at 1000℃ for 5 hours, and cooled to room temperature with the furnace.

[0046] Step 04, the Ti-Zr binary alloy ingot obtained in step 03 is subjected to open die forging by using a free forging process, that is, upsetting + elongation. During open die forging, a high-temperature antioxidant is coated on the surface of the ingot, heated to 1000℃ in a vacuum furnace, and kept for 3 hours for open die forging, and the final forging temperature is 900℃. After obtaining the titanium alloy ingot, water quenching, removing the surface oxide, and cleaning and drying.

[0047] Step 05, the forged Ti-Zr binary alloy ingot obtained in step 04 is extruded 4 times at 450℃, and rotated by 90° around the longitudinal axis during each extrusion, and subjected to equal-channel angular extrusion in an equal-channel angular extrusion machine with a channel intersection angle of 90°.

[0048] Step 06, the billet obtained in step 04 is soaked in a corrosion liquid (volume ratio of HF:HNO3:H2O=1:3:10) for 12 hours, and then subjected to surface finishing and cleaning after taking out.

[0049] Step 07, the billet obtained in step 06 is subjected to equal-channel angular extrusion at a temperature of 350~450℃ and a strain rate of 10-3 mechanically processing the blank obtained in step 06 under the condition of 80% strain degree.

[0050] Step 08, the Ti-Zr binary alloy rod processed in step 07 is finely ground, and the implant semi-finished product is obtained after processing by the lathe, and after cleaning and drying, sand blasting treatment is carried out, and the sand blasting treatment conditions are 150# white corundum, pressure 0.45MPa, moving speed 3mm / s, spindle speed 3r / s, distance 20mm, reciprocating 2 times.

[0051] Step 09, the implant semi-finished product obtained in step 08 is subjected to super-hydrophilic acid etching treatment after sand blasting, and the etching liquid is (volume ratio 98% H2SO4:37% HCl:H2O=1:1:2). And heated to 80℃, and acid etching for 20min.

[0052] Step 10, the implant semi-finished product after step 09 treatment is ultrasonically cleaned with ultrapure water and stored in physiological saline at room temperature.

[0053] As shown in Figures 1-5 , it can be seen from the figure that the surface microstructure of titanium-zirconium alloy after sandblasting super-hydrophilic acid etching treatment. The surface has micro-nano multi-level pores, and the roughness increases significantly, which helps cell adhesion and improves the biocompatibility of the material. The yield strength of the obtained mechanically treated implant semi-finished product is 815±28MPa, the tensile strength is 1021±31MPa, the deformation is 6.1±0.9%, the grain size is 14.0 grade, which is ultra-fine grain, and the fatigue strength of 5 million times can reach 515MPa.

[0054] As shown in Figure 6 , it can be seen from the figure that the hydrophilicity of Ti15Zr after sandblasting super-hydrophilic acid etching treatment is significantly enhanced compared with ordinary sandblasting acid etching treatment. The contact angle with water is less than 5°, which is a super-hydrophilic surface.

[0055] As shown in Figures 7-11 , it can be seen from the figure that the biocompatibility of Ti15Zr material after sandblasting super-hydrophilic acid etching treatment is improved, which helps cell adhesion and mineralization.

[0056] As shown in Figure 12 , Ti15Zr material after sandblasting super-hydrophilic acid etching treatment can significantly induce cell osteogenic differentiation.

[0057] As shown in Figure 13 , Ti15Zr material after sandblasting super-hydrophilic acid etching treatment has good biocompatibility in SD rats and no inflammatory reaction.

[0058] Example 2

[0059] The application discloses a preparation method of a high-toughness super-hydrophilic titanium-zirconium alloy dental implant body.

[0060] Step 01, sponge titanium and sponge zirconium are cleaned and dried for later use, wherein the purity of the sponge titanium is at least 99.99%, and the purity of the sponge zirconium is at least 99.95%.

[0061] Step 02, a Ti-Zr binary alloy ingot prepared in step 01 is smelted by using a vacuum smelting furnace, wherein the mass ratio of Ti to Zr is 50:50. The smelting furnace needs to be turned over by 180 degrees and turned over for 5 times.

[0062] Step 03, the Ti-Zr binary alloy ingot obtained in step 02 is kept in a 1050 DEG C vacuum tube furnace for 6 hours, and is cooled to room temperature along with the furnace.

[0063] Step 04, a free forging process is used to break down the Ti-Zr binary alloy ingot obtained in step 03, that is, upsetting + elongation. When breaking down, a high-temperature antioxidant is coated on the surface of the ingot, the ingot is heated to 1100 DEG C in a vacuum furnace, and is kept for 2 hours for breaking down forging, and the final forging temperature is 950 DEG C. After the titanium alloy ingot is obtained, the ingot is water quenched, the surface oxide is removed, and the ingot is cleaned and dried.

[0064] Step 05, the forged Ti-Zr binary alloy ingot obtained in step 04 is extruded for 6 times at 400 DEG C, and is rotated by 60 degrees around the longitudinal axis at each time of extrusion, and is subjected to equal-channel angular extrusion in an equal-channel angular extrusion machine with a channel intersection angle of 120 degrees.

[0065] Step 06, the blank obtained in step 04 is soaked in an etching liquid (HF:HNO3:H2O=1:3:10 in volume ratio) for 12 hours, and is subjected to surface finishing and cleaning after being taken out.

[0066] Step 07, the blank obtained in step 06 is subjected to mechanical treatment under the conditions that the temperature is 400-450 DEG C, the strain rate is 2*10 -3 , and the strain degree is 60%.

[0067] Step 08, the Ti-Zr binary alloy rod processed in step 07 is subjected to fine grinding, and an implant body semi-finished product is obtained through a lathe, and the implant body semi-finished product is subjected to sand blasting treatment after being cleaned and dried, wherein the sand blasting treatment is performed under the conditions that the white corundum is 180 #, the pressure is 0.55 MPa, the moving speed is 2 mm / s, the spindle rotating speed is 3 revolutions / s, the distance is 15 mm, and the reciprocation is 3 times.

[0068] Step 09, the implant body semi-finished product obtained in step 08 is subjected to super-hydrophilic acid etching treatment after being subjected to sand blasting, and the etching liquid is 98% H2SO4:37% HCl:H2O=1:1:2 in volume ratio. The etching liquid is heated to 100 DEG C, and the acid etching is performed for 15 minutes.

[0069] Step 10, after ultrasonic cleaning with ultrapure water, the implant semi-finished product treated in step 09 is stored in a CaCl2 aqueous solution at room temperature.

[0070] Example 3

[0071] A method for preparing a high-toughness super-hydrophilic titanium-zirconium alloy dental implant, comprising the steps of:

[0072] Step 01, sponge titanium and sponge zirconium are cleaned and dried for standby use, wherein the purity of the sponge titanium is at least 99.99%, and the purity of the sponge zirconium is at least 99.95%.

[0073] Step 02, a Ti-Zr binary alloy ingot prepared in step 01 is melted by using a vacuum melting furnace, wherein the mass ratio of Ti to Zr is 30:70. During melting, the melting furnace needs to be turned over by 180° and turned over 3 times.

[0074] Step 03, the Ti-Zr binary alloy ingot obtained in step 02 is kept in a vacuum tube furnace at 1000℃ for 5 hours, and cooled to room temperature with the furnace.

[0075] Step 04, the Ti-Zr binary alloy ingot obtained in step 03 is subjected to open-die forging by using a free forging process, i.e. upsetting + elongation. During open-die forging, a high-temperature antioxidant is coated on the surface of the ingot, heated to 1000℃ in a vacuum furnace, and kept for 3 hours for open-die forging, and the final forging temperature is 900℃. After obtaining the titanium alloy ingot, it is water quenched, the surface oxide is removed, and then cleaned and dried.

[0076] Step 05, the forged Ti-Zr binary alloy ingot obtained in step 04 is subjected to equal-channel angular extrusion in an equal-channel angular extrusion machine with a pass number of 4 at 450℃, and rotated by 90° around the longitudinal axis during each extrusion, and the intersection angle of the channels is 90°.

[0077] Step 06, the billet obtained in step 04 is soaked in an etching liquid (volume ratio of HF:HNO3:H2O=1:3:10) for 12 hours, and then subjected to surface finishing and cleaning after being taken out.

[0078] Step 07, the billet obtained in step 06 is subjected to mechanical treatment at a temperature of 350~450℃, a strain rate of 10 -3 , and a strain degree of 80%.

[0079] Step 08, the Ti-Zr binary alloy rod processed in step 07 is subjected to fine grinding, and an implant semi-finished product is obtained after being processed by a lathe. After cleaning and drying, the implant semi-finished product is subjected to sandblasting treatment, and the sandblasting treatment conditions are as follows: 150# white corundum, pressure 0.45MPa, moving speed 3mm / s, spindle speed 3r / s, distance 20mm, and reciprocation 2 times.

[0080] Step 09: The implant semi-finished product obtained in step 08 is subjected to super-hydrophilic acid etching treatment after sand blasting, and the etching liquid is (volume ratio of 98% H2SO4: 37% HCl: H2O = 1:1:2). The etching liquid is heated to 80°C and etched for 20 min.

[0081] Step 10: The implant semi-finished product obtained in step 09 is subjected to ultrasonic cleaning with ultrapure water and then stored in physiological saline or a CaCl2 aqueous solution at room temperature.

[0082] The yield strength of the obtained implant semi-finished product is 850±32 MPa, the tensile strength is 1034±37 MPa, the deformation is 7.1±0.8%, and the grain size is 14.0. The contact angle between the implant semi-finished product and water is less than 5°.

[0083] The above description is merely preferred embodiments of the present application and is not intended to limit the present application. Obviously, one of ordinary skill in the art can make various modifications and variations to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalent technologies, they are also intended to be included in the present application.

Claims

1. A method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant, characterized in that, Including the following steps: Step 01: Clean and dry the sponge titanium and sponge zirconium for later use; Step 02: Melt the Ti-Zr binary alloy ingot prepared in step 01 using a vacuum melting furnace; Step 03: Hold the Ti-Zr binary alloy ingot obtained in Step 02 in a vacuum tube furnace at 1050±100℃ for 4~8 hours, and then cool it to room temperature in the furnace. Step 04: The Ti-Zr binary alloy ingot obtained in Step 03 is blanked using a free forging process; Step 05: The forged Ti-Zr binary alloy ingot obtained in step 04 is extruded at 300℃≤T≤450℃ at least 4 times, and the billet is rotated 30~150° around the longitudinal axis each time to perform equal diameter angular extrusion. Step 06: Immerse the billet obtained in step 04 in the etching solution for 6 to 12 hours, then remove it and perform surface finishing and cleaning. Step 07, at a temperature below 450°C and a strain rate of 10 -2 ~10 -4 The billet obtained in step 06 is mechanically processed under a strain degree of 30-80%. Step 08: The Ti-Zr binary alloy rod processed in Step 07 is finely ground and processed by a Swiss-type lathe to obtain a semi-finished implant. After cleaning and drying, it is sandblasted. Step 09: After sandblasting, the semi-finished implant obtained in step 08 is subjected to superhydrophilic acid etching treatment. Step 10: After ultrasonic cleaning with ultrapure water, the semi-finished implant product processed in step 09 is stored at room temperature in physiological saline or CaCl2 aqueous solution. The prepared titanium-zirconium alloy has a grain size of 14, which is ultrafine. The tensile strength of the prepared titanium-zirconium alloy can reach 1000 MPa; The prepared titanium-zirconium alloy has a fatigue strength exceeding 500 MPa after 5 million cycles. The prepared titanium-zirconium alloy surface has micro-nano hierarchical pores; The prepared titanium-zirconium alloy has a contact angle with water of less than 5°, making it a superhydrophilic surface.

2. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 02, the mass ratio of the Ti-Zr binary alloy is Ti:Zr = 10:90 ~ 90:

10.

3. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 02, the smelting furnace needs to be rotated 180° during smelting, and rotated 3 to 6 times.

4. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 04, when the billet is being forged, a high-temperature antioxidant is coated on the surface of the ingot, and it is heated to 1050±50℃ in a vacuum furnace and held for 1~3 hours before forging. Final forging temperature: 850±100℃; Finally, the obtained titanium alloy ingot is water-quenched to remove surface oxides, and then cleaned and dried.

5. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 05, the cross angle of the extruder channel is 90°≤ψ≤160°.

6. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 06, the corrosive solution is a mixed aqueous solution of two or more of H2SO4, HCl, HF and HNO3, and the concentration of each acid solution is less than 50%.

7. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 08, the sandblasting conditions are 120~180# white corundum, pressure 0.35~0.55 MPa, moving speed 1~3 mm / s, spindle speed 1~5 rpm, and distance 10~30 mm.

8. The method for preparing a high-strength, high-toughness, superhydrophilic titanium-zirconium alloy dental implant according to claim 1, characterized in that, In step 09, during the corrosion treatment, the solution is prepared in a mixed aqueous solution of two or more of H2SO4, HNO3, HF, and HCl, with the concentration of each acid solution being less than 50%, and heated to 60-110°C for 5-30 minutes.

Images