阅读说明：本技术 一种生物医用β钛合金及其制备方法 (Biomedical beta titanium alloy and preparation method thereof ) 是由 闫星辰 常成 褚清坤 马文有 刘敏 于 2021-07-26 设计创作，主要内容包括：本发明公开一种生物医用β钛合金及其制备方法,其化学组成及其质量百分比为：Mo：9.20～13.50％；Fe：1.00～3.20％；Zr：3.50～8.20％；Ta：0～1.00％；余量为Ti。本发明所述的β钛合金适用于激光增材制造技术,所制备零件内生成了晶粒极为细小的致密等轴晶组织和少部分柱状晶组织,在发挥细晶强化的同时,也起到了大幅度提高合金材料的强硬度和耐磨蚀性的作用。本发明还提供一种无毒、低弹、耐磨蚀生物医用β钛合金材料的制备方法,将上述合金组分制得的粉末,采用激光增材制造技术制备了相应的强硬度高、耐磨蚀性好且具有极低细胞毒性的β钛合金,此外,所制备的材料具有良好的焊接性,是一种适合激光增材制造的专用金属合金粉末。(The invention discloses a biomedical beta titanium alloy and a preparation method thereof, wherein the biomedical beta titanium alloy comprises the following chemical components in percentage by mass: mo: 9.20-13.50%; fe: 1.00-3.20%; zr: 3.50-8.20%; ta: 0 to 1.00 percent; the balance being Ti. The beta titanium alloy is suitable for laser additive manufacturing technology, and a compact isometric crystal structure and a small part of columnar crystal structure with extremely fine crystal grains are generated in the prepared part, so that the functions of greatly improving the strong hardness and the abrasion resistance of the alloy material are achieved while the fine crystal strengthening is performed. The invention also provides a preparation method of the non-toxic, low-elasticity and abrasion-resistant biomedical beta titanium alloy material, wherein the powder prepared from the alloy components is used for preparing the corresponding beta titanium alloy with high strength, high abrasion resistance and extremely low cytotoxicity by adopting a laser additive manufacturing technology, and in addition, the prepared material has good weldability and is special metal alloy powder suitable for laser additive manufacturing.)

1. The beta titanium alloy for the biomedical use is characterized by comprising the following components in percentage by mass: mo: 9.2-13.5%; fe: 1-3.2%; zr: 3.5-8.2%; ta: 0 to 1 percent; the balance being Ti and unavoidable impurities.

2. The biomedical beta titanium alloy according to claim 1, wherein the beta titanium alloy has a particle size of 10-75 μm.

3. A method for preparing the biomedical beta titanium alloy according to claim 1 or 2, comprising the steps of:

(1) mixing Mo, Fe, Zr, Ta and Ti according to mass percent, and smelting and forging the mixture into a bar;

(2) preparing the bar material prepared in the step (1) into powder by a plasma rotating electrode atomization method, and collecting alloy powder with the particle size of 12-75 microns;

(3) and (3) drying the alloy powder collected in the step (2) in vacuum to obtain the beta titanium alloy.

4. The preparation method of the biomedical beta titanium alloy according to claim 3, wherein the diameter of the bar in the step 1 is 15-30 mm, and the length of the bar is 10-150 mm.

5. The preparation method of the biomedical beta titanium alloy according to claim 3, wherein the diameter of the bar in the step 1 is 15-20 mm, and the length of the bar is 20-30 mm.

6. The preparation method of the biomedical beta-titanium alloy according to claim 3, wherein the plasma rotary electrode atomization method in the step (2) is to heat the bar material in the step (1) to 1500-1750 ℃ in a vacuum environment, smelt for 60-80 min to obtain a molten alloy, and spray-granulate the molten alloy by using high-purity argon gas.

7. The preparation method of the beta titanium alloy for biomedical use according to claim 3, wherein the powder in the step (2) is spherical, and the particle size of the collected powder is 35-50 μm.

8. The preparation method of the beta titanium alloy for biomedical use according to claim 3, wherein the temperature of vacuum drying in the step (3) is 120-200 ℃ and the pressure is 100-200 MPa.

9. Use of the biomedical beta titanium alloy according to claim 1 or 2 in a medical material.

Technical Field

The invention relates to the technical field of metal materials, in particular to a biomedical beta titanium alloy and a preparation method thereof.

Background

The medical titanium alloy has good biocompatibility and is the preferred material of the medical implant at present. In recent years, a personalized tissue repair technology based on metal 3D printing of digital optical image acquisition has generated a new research trend for medical titanium alloy. However, the difference between the elastic modulus and the human bone tissue of the currently common medical titanium alloy implant (Ti6Al4V ELI) is large, and toxic ions are released after long-term implantation, so that the benign combination of the titanium alloy and the bone tissue and the long-acting safety of the titanium alloy and the bone tissue are restricted. Therefore, developing a new titanium alloy more suitable for human bone implantation is a key content and a hot direction in research and development nowadays.

The beta-Ti alloy has the characteristics of no toxic elements, high strength, low elastic modulus and the like. Designing and developing beta-Ti alloy with lower modulus and better comprehensive performance has become a development focus and research focus of medical titanium alloy materials at home and abroad. However, due to the difference of organism skeletons and the randomness of defect site morphology, the standardized implants manufactured by the traditional processing method are difficult to meet the actual clinical requirements. Therefore, the application of metal 3D printing technology to personalized repair of clinical bone defect cases has gradually become an effective method for treating orthopedic diseases. However, no report exists for the commercialized medical beta-Ti alloy metal 3D printing powder and related products.

The metal 3D printing can realize the perfect combination of the three-dimensional personalized design, the pore structure customization and the rapid net shaping of the metal implant, and becomes the key development direction and the future development trend of the design, the manufacture and the application popularization of high-end personalized medical instruments. However, the selection and design of a metal 3D printing β -Ti functional material system, the controllable preparation of a personalized medical multifunctional material, the surface interface research of bone tissue biomaterials, the systematic clinical verification and the customized response are still the "neck clamp" problems that need to be overcome at present.

Disclosure of Invention

The invention aims to overcome the defects in the prior art and provide a biomedical beta titanium alloy and a preparation method thereof.

In order to achieve the purpose, the invention adopts the technical scheme that:

in a first aspect, the invention provides a biomedical beta titanium alloy, which comprises the following components in percentage by mass: mo: 9.2-13.5%; fe: 1-3.2%; zr: 3.5-8.2%; ta: 0 to 1 percent; the balance being Ti and unavoidable impurities.

The inventors found through research that Mo, Ta and Fe elements have the effects of lowering the β transition temperature, infinitely solid-dissolving in the β phase, and expanding the β phase region. Among them, Fe is one of the strongest beta-stabilizing elements, and Mo has an effect of improving the thermal stability of chromium and iron alloys. The biomedical beta titanium alloy is a non-toxic, low-elasticity and abrasion-resistant high-performance material which can be used for metal additive.

Further, the grain diameter of the beta titanium alloy is 10-75 μm.

In a second aspect, the present invention provides a method for manufacturing the biomedical β titanium alloy, including the steps of:

(1) mixing Mo, Fe, Zr, Ta and Ti according to mass percent, and smelting and forging the mixture into a bar;

(2) preparing the bar material prepared in the step 1 into powder by a plasma rotating electrode atomization method, and collecting alloy powder with the particle size of 12-75 microns;

(3) and (3) drying the alloy powder collected in the step (2) in vacuum to obtain the beta titanium alloy.

The inventor finds out through research that the beta titanium alloy prepared by the preparation method of the invention has excellent fluidity, high purity and weldability.

Further, the diameter of the bar in the step 1 is 15-30 mm, and the length of the bar is 10-150 mm.

Further, the diameter of the bar in the step 1 is 15-20 mm, and the length of the bar is 20-30 mm.

Further, the plasma rotary electrode atomization method in the step 2 is to heat the bar material in the step 1 to 1500-1750 ℃ in a vacuum environment, smelt for 60-80 min to obtain molten alloy, and perform spray granulation by using high-purity argon.

Further, the technological parameters of spray granulation are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3And (3) introducing high-purity argon to enable the pressure in the bin to reach 0.04-0.08 MPa, setting the power of a plasma gun to be 200kW and the rotating speed to be 15000-18000 r/min, forming the powder of the ball stars under the cooling of the inert gas in the chamber, and collecting the powder into the powder outlet bin.

Further, the powder in the step 2 is spherical, and the particle size of the collected powder is 35-50 μm.

Further, the temperature of vacuum drying in the step 3 is 120-200 ℃, and the pressure is 100-200 MPa.

In a third aspect, the invention also provides application of the biomedical beta titanium alloy in medical materials. Specifically, a three-dimensional modeling software is used for establishing a 3D model according to a target part, and a virtual model is led into an additive manufacturing system to generate a part scanning path; the biomedical beta titanium alloy is processed into a biomedical material through an additive manufacturing system.

The beta titanium alloy is suitable for laser additive manufacturing technology, and a compact isometric crystal structure and a small part of columnar crystal structure with extremely fine crystal grains are generated in the prepared part, so that the beta titanium alloy plays a role in greatly improving the strong hardness and the abrasion resistance of the alloy material while playing a role in fine crystal strengthening.

The invention has the beneficial effects that:

(1) the biomedical beta titanium alloy material prepared by the invention is basically formed by single beta-Ti phase of fine compact isometric crystal and a small amount of columnar crystal after being processed and formed, and the strength, hardness and abrasion resistance of the material are greatly improved while the plasticity and toughness of the material are ensured.

(2) The biomedical beta titanium alloy material prepared by the invention has the advantages of low oxygen content, less impurities, high alloy purity, and excellent weldability and formability.

(3) The biomedical beta titanium alloy material prepared by the invention does not contain toxic elements, and has extremely low cytotoxicity and good cell compatibility.

Drawings

FIG. 1 is a schematic view of a sample of an SLM alloy prepared in example 1 of the present invention;

FIG. 2 is a macroscopic (a) and microscopic (b) surface topography of the SLM alloy specimens prepared in comparative examples 1 and 2

FIG. 3(a) is an SEM image of a beta titanium alloy powder of the present invention; (b) is a particle size distribution diagram of the beta titanium alloy powder;

FIG. 4 is an XRD pattern of a beta titanium alloy sample prepared from the beta titanium alloy powder and SLM of the present invention;

FIG. 5 is an SEM image of a beta titanium alloy sample prepared by SLM;

FIG. 6 shows the wear performance of SLM prepared beta titanium alloy samples in 3.5 wt% NaCl solution: (a) COF distance curve; (b) SEM image of the wear surface.

Detailed Description

To better illustrate the objects, aspects and advantages of the present invention, the present invention will be further described with reference to specific examples.

Example 1

The biomedical beta titanium alloy comprises the following raw material components in percentage by mass: mo: 11.25 percent; fe: 1.75 percent; zr: 5.82 percent; ta: 0.21 percent; the balance being Ti.

The preparation method comprises the following steps:

(1) weighing preparation raw materials, including Zr, Mo, Ta, Fe, Ti and a very small amount of unavoidable C and Si, wherein the content of each component is shown in Table 1, and the purity of each component is 99.2 wt%; after each raw material is put into a crucible to be smelted, the materials are forged into a bar with the diameter of 29.2mm and the length of 150mm to prepare spherical powder.

(2) Atomization method using plasma rotary electrodeHeating the powder to 1700 ℃ in a vacuum environment, smelting for 65min to obtain molten alloy, performing spray granulation by using high-purity argon, and collecting alloy powder with the particle size of 12-75 mu m, wherein key powder preparation process parameters and detailed steps are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3Pa, then filling high-purity argon to ensure that the pressure in the bin reaches 0.06MPa, setting the power of a plasma gun to be 200kW and the rotating speed to be 16000r/min, forming spherical powder under the cooling of inert gas in the chamber, and collecting the spherical powder into a powder outlet bin.

(3) And putting the collected alloy powder into a vacuum drying oven, vacuumizing to 120MPa, heating to 120 ℃, keeping the temperature for 2 hours, then carrying out vacuum drying, obtaining titanium-based alloy powder which is the biomedical beta-titanium alloy material, and putting the alloy powder into a vacuum bag for vacuumizing and storing for later use.

Example 2:

the biomedical beta titanium alloy comprises the following raw material components in percentage by mass: mo: 9.57 percent; fe: 2.35 percent; zr: 7.88 percent; ta: 0.46 percent; the balance being Ti.

The preparation method comprises the following steps:

(1) weighing preparation raw materials, including Zr, Mo, Ta, Fe, Ti and a very small amount of unavoidable C and Si, wherein the content of each component is shown in Table 1, and the purity of each component is 99.2 wt%; after each raw material is put into a crucible to be smelted, the materials are forged into a bar with the diameter of 29.2mm and the length of 150mm to prepare spherical powder.

(2) Using a plasma rotating electrode atomization method to prepare powder, heating to 1600 ℃ in a vacuum environment, smelting for 75min to obtain molten alloy, using high-purity argon gas to carry out spray granulation, and collecting alloy powder with the particle size of 12-75 mu m, wherein key powder preparation process parameters and detailed steps are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3Pa, then filling high-purity argon to ensure that the pressure in the bin reaches 0.06MPa, setting the power of a plasma gun to be 200kW and the rotating speed to be 16000r/min, forming spherical powder under the cooling of inert gas in the chamber, and collecting the spherical powder into a powder outlet bin.

(3) And putting the collected alloy powder into a vacuum drying oven, vacuumizing to 120MPa, heating to 120 ℃, keeping the temperature for 2 hours, then carrying out vacuum drying, obtaining titanium-based alloy powder which is the biomedical beta-titanium alloy material, and putting the alloy powder into a vacuum bag for vacuumizing and storing for later use.

Example 3:

the biomedical beta titanium alloy comprises the following raw material components in percentage by mass: mo: 13.25 percent; fe: 3.05 percent; zr: 3.67 percent; ta: 0.82%; the balance being Ti.

The preparation method comprises the following steps:

(1) weighing preparation raw materials, including Zr, Mo, Ta, Fe, Ti and a very small amount of unavoidable C and Si, wherein the content of each component is shown in Table 1, and the purity of each component is 99.2 wt%; after each raw material is put into a crucible to be smelted, the materials are forged into a bar with the diameter of 29.2mm and the length of 150mm to prepare spherical powder.

(2) Using a plasma rotating electrode atomization method to prepare powder, heating to 1700 ℃ in a vacuum environment, smelting for 65min to obtain molten alloy, using high-purity argon gas to carry out spray granulation, and collecting alloy powder with the particle size of 12-75 mu m, wherein key powder preparation process parameters and detailed steps are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3Pa, then filling high-purity argon to ensure that the pressure in the bin reaches 0.06MPa, setting the power of a plasma gun to be 200kW and the rotating speed to be 16000r/min, forming spherical powder under the cooling of inert gas in the chamber, and collecting the spherical powder into a powder outlet bin.

(3) And putting the collected alloy powder into a vacuum drying oven, vacuumizing to 120MPa, heating to 120 ℃, keeping the temperature for 2 hours, then carrying out vacuum drying, obtaining titanium-based alloy powder which is the biomedical beta-titanium alloy material, and putting the alloy powder into a vacuum bag for vacuumizing and storing for later use.

Comparative example 1:

the biomedical beta titanium alloy comprises the following raw material components in percentage by mass: mo: 0 percent; fe: 2.00 percent; zr: 4.25 percent; ta: 0.08 percent; ti: 93.67 percent

The preparation method comprises the following steps:

(1) weighing preparation raw materials including Zr, Ta, Fe, Ti and a very small amount of unavoidable C and Si, wherein the purity of each component is 99.0 wt%; after being put into a crucible to be smelted, the raw materials are forged into a bar with the diameter of 30mm and the length of 152mm to prepare spherical powder.

(2) Using a plasma rotary electrode atomization method to prepare powder, heating to 1750 ℃ in a vacuum environment, smelting for 80min to obtain molten alloy, using high-purity argon gas to carry out spray granulation, and collecting alloy powder with the particle size of 12-75 mu m, wherein key powder preparation process parameters and detailed steps are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3Pa, then filling high-purity argon to ensure that the pressure in the bin reaches 0.06MPa, setting the power of a plasma gun to be 200kW and the rotating speed to be 16000r/min, forming spherical powder under the cooling of inert gas in the chamber, and collecting the spherical powder into a powder outlet bin.

(3) And putting the collected alloy powder into a vacuum drying oven, vacuumizing to 120MPa, heating to 120 ℃, keeping the temperature for 2 hours, then carrying out vacuum drying, obtaining titanium-based alloy powder which is the biomedical beta-titanium alloy material, and putting the alloy powder into a vacuum bag for vacuumizing and storing for later use.

Comparative example 2:

the biomedical beta titanium alloy comprises the following raw material components in percentage by mass: mo: 10.8 percent; fe: 0 percent; zr: 6.38 percent; ta: 0.11 percent; ti: 82.71 percent

The preparation method comprises the following steps:

(1) weighing preparation raw materials including Zr, Ta, Mo, Ti and extremely small amount of unavoidable C and Si, wherein the purity of each component is 99.0 wt%; after being put into a crucible to be smelted, the raw materials are forged into a bar with the diameter of 29mm and the length of 150mm to prepare spherical powder.

(2) Using a plasma rotating electrode atomization method to prepare powder, heating to 1700 ℃ in a vacuum environment, smelting for 70min to obtain molten alloy, using high-purity argon gas to carry out spray granulation, and collecting alloy powder with the particle size of 12-75 mu m, wherein key powder preparation process parameters and detailed steps are as follows: firstly, the powder-making working chamber is evacuated, and the vacuum degree of the atomizing chamber reaches 5 multiplied by 10^-3Pa，Then high-purity argon is filled to ensure that the pressure in the bin reaches 0.06MPa, the power of a plasma gun is set to 200kW, the rotating speed is 16000r/min, and spherical powder is formed under the cooling of inert gas in the chamber and is collected into a powder outlet bin.

(3) And putting the collected alloy powder into a vacuum drying oven, vacuumizing to 120MPa, heating to 120 ℃, keeping the temperature for 2 hours, then carrying out vacuum drying, obtaining titanium-based alloy powder which is the biomedical beta-titanium alloy material, and putting the alloy powder into a vacuum bag for vacuumizing and storing for later use.

Example 4

The beta titanium alloy material prepared in the embodiment 1 and the comparative examples 1 and 2 is molded and manufactured by adopting a laser additive manufacturing mode, and the specific manufacturing method comprises the following steps:

establishing a three-dimensional model by using Solidworks software, then importing the three-dimensional model into Magics software for placing parts and setting a laser scanning sequence;

pouring the beta titanium alloy material into a powder storage bin of a Selective Laser Melting (SLM) additive manufacturing system, and waiting for Selective laser melting and forming;

forming and manufacturing a metallographic sample, a friction wear sample and a biological performance sample on the beta titanium alloy material by using an EOS M290 system to prepare an alloy sample, wherein the specific process parameters are as follows: the laser spot was 100 μm, the laser power was 100W, the layer thickness was 30 μm, the scanning pitch was 100 μm, and the scanning speed was 500 mm/s.

It should be noted that, the process related to the additive manufacturing system may further specifically select any one of technologies such as Electron Beam Additive Manufacturing (EBAM), Direct Metal Deposition (DMD), Direct Metal Laser Sintering (DMLS), laser near net shaping (LENS), laser metal shaping (LMF), Selective Laser Melting (SLM), and Selective Laser Sintering (SLS).

The SLM alloy test piece prepared in example 1, as shown in fig. 1, has no cracks and holes on the surface and excellent weldability and formability.

As shown in FIG. 2, the SLM alloy samples prepared in comparative example 1 and comparative example 2 have holes and cracks on the macroscopic surface, and poor weldability and formability. Since the surface topography of SLM-shaped examples 2 and 3 is comparable, no detail is made here.

Performance testing

The beta titanium alloy sample prepared in example 4 was subjected to material characterization, mechanical property and biological property tests.

As can be seen from fig. 3a, the powder obtained in example 1 was a β titanium alloy powder having an extremely high sphericity, almost no satellite, and good fluidity; fig. 3b is the measured beta titanium alloy particle size distribution in this example, where Dv (50) ═ 41.2 μm, consistent with the requirements for Selective Laser Melting (SLM) powders commonly used in this example.

As can be seen from fig. 4, both the β titanium alloy powder of example 1 and the β titanium alloy sample prepared by SLM of example 4 can detect only the peak position of the β -Ti phase, indicating that the prepared β titanium alloy material achieves the expected effect.

Further, from the SEM results of the SLM β titanium alloy of fig. 5, the prepared SLM sample has a substantially completely dense fine equiaxed structure, while only a small amount of columnar crystals exist at the melting channel boundary, and the average grain size is about 1.2 μm, indicating that the β titanium alloy material prepared by SLM has a very fine grain structure.

The average microhardness of the beta titanium alloy sample prepared in example 4 was measured by the following method: the Vickers microhardness of the test specimens was measured using a microhardness tester (model Leitz Wetzlar, Germany) using a load of 200g and a loading time of 25 s. Polishing the surface roughness of the testing surface of the SLM sample to be less than 0.15 mu m, measuring the microhardness values of different positions on the surface of the SLM sample, and taking an average value after 10 times of measurement. The average microhardness after the test is 356 +/-6.2 HV_0.2。

The beta titanium alloy sample prepared in example 4 was subjected to a frictional wear test by the following method: the specimens were subjected to a sliding ball-disk abrasion test at room temperature (25 ℃) using a CSEM friction abrasion tester. Before testing the frictional wear performance, the surface roughness (Ra) of all SLM specimens was polished to below 0.15 μm, selectedSilicon nitride (Si) with a diameter of 4mm₃N₄) The balls were used as counter grinding balls and were washed with ethanol prior to testing, and were loaded with 3.5 wt.% NaCl normal saline solution at the time of the frictional wear test. The abrasion test conditions were as follows: the test load was 500g, the rotational speed was 200r/min, the rubbing distance was 188.5m, and the rubbing diameter was 10 mm.

During the sliding test, the coefficient of friction (COF) was automatically recorded by the machine. After the abrasion test is completed, the abrasion surface of the sample is observed and analyzed by a scanning electron microscope, and the macroscopic morphology of the abrasion mark is measured again by a three-dimensional surface profiler. The wear rate (ω) of the samples was calculated by the following formula, and the average value was calculated after three measurements:

where r is the radius of the wear path in mm; s is the cross-sectional area of the wear rail in square millimeters; w is the test load in N; l is the sliding distance in m. The average friction coefficient was measured to be 0.62 and the average wear amount was 2.38. + -. 0.25X 10^-4mm³/(N·m)。

The in vitro cytotoxic effect of the beta titanium alloy sample prepared in example 4 was analyzed using rat bone marrow mesenchymal stem cells (rBMSCs) in compliance with the International Standard ISO 10993-5. Prior to use in cytotoxicity assays, liquid extracts of samples (37 ℃, 10% FBS (v/v) in α -MEM of 3cm were prepared²/ml) and subjected to filter sterilization, and subjected to cytotoxicity evaluation using a cell counting kit-8 (CCK-8). BMSCs at 1X 10 per well⁴The density of individual cells was seeded on 96-well plates (Nest, USA) for one day, and then the culture medium was replaced with liquid extracts of medical grade polyethylene (negative control, no cytotoxicity), alpha-MEM containing 10% FBS (v/v) and 10% dimethyl sulfoxide (DMSO) (positive control, providing reproducible cytotoxic reactions), and liquid extracts of beta titanium alloy samples from each group (100 μ L/well) for 1, 3, and 5 days. Subsequently, 10 μ L of CCK-8 solution was added to each well of the plate and the plate was incubated under light for two hours. MeasuringAbsorbance at 450 nm. The values of the negative control wells were averaged and taken as 100% cell viability. All other values were then averaged against their group and compared to the negative control group. As a result, the cellular absorbances (OD values) of the beta titanium alloy samples prepared by SLM were 1.275, 1.351 and 1.333 after 1 day, 3 days and 5 days, respectively, which are slightly more advantageous than those of Ti-6Al-4V ELI of 0.04, 0.6 and 1.6. Meanwhile, the cytotoxicity experiment in example 1 shows that the survival number (living cell staining area per unit area) of the cells after 24h is 20.2% which is much higher than that of Ti-6Al-4V ELI (11.3%), which indicates that the prepared beta titanium alloy sample has extremely low cytotoxicity and good cell compatibility.

As can be seen from fig. 5 to 6 and the test results of the properties of the above materials, the invented β titanium alloy powder has excellent flowability, high purity and weldability, and the β titanium alloy material prepared by the SLM process has good effects of strong hardness, biocompatibility and abrasion resistance. The beta titanium alloy material invented in the technical scheme of the invention is a novel non-toxic, low-elasticity and abrasion-resistant biomedical beta titanium alloy which can reach the biomedical grade and is suitable for metal additive manufacturing.

Finally, it should be noted that the above embodiments are only used for illustrating the technical solutions of the present invention and not for limiting the protection scope of the present invention, and although the present invention is described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that modifications or equivalent substitutions can be made on the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention.