A medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy, rod, its preparation method and application

Abstract

This invention discloses a high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy for medical use, its rod material, preparation method, and applications, belonging to the technical field of titanium alloy materials. The titanium alloy comprises the following mass percentage composition: Al 6.0-7.0%, Sn 1.80-2.20%, Zr 2.80-3.20%, Mo 4.80-5.20%, Nb 0.80-1.20%, Si 0.40-0.60%, C 0.03-0.05%, Fe < 0.015%, O 0.07-0.14%, with Ti as the balance. This invention uses a mixing machine to ensure the uniformity of alloy composition in the axial and radial directions of the ingot during the ingot casting process. It employs a three-stage vacuum arc remelting process to improve the uniformity and consistency of alloying elements in the titanium alloy ingot, adjusts the ingot crystallization rate, and controls the grain size and orientation of the ingot. The prepared high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy meets the requirements.

Description

Technical Field

[0001] This invention belongs to the field of titanium alloy material technology, and more specifically relates to a medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy, rod material, its preparation method and application. Background Technology

[0002] In the medical field, pure titanium with an α phase and titanium and titanium alloys based on the α+β type Ti-6Al-4V composition are widely used. Pure titanium is used more in oral medicine, while Ti-6Al-4V alloys are commonly used in artificial joints and bone fixation. In the field of medical devices, there is basically no titanium alloy material specifically developed for this purpose.

[0003] Ultrasonic bone scalpels are a relatively new surgical instrument in the medical field, widely used in bone cutting procedures due to their minimally invasive nature, shortened operation time, and lack of damage to blood vessels, nerves, and soft tissues. Generally, ultrasonic bone scalpels made of Ti-6Al-4V titanium alloy meet the material strength requirements for heat resistance around 400℃. However, in areas with high bone density, ultrasonic bone scalpel materials must not only have sufficient strength and rigidity at room temperature but also high heat resistance up to 600℃. This is because cutting high-density bone tissue generates significant heat, necessitating high thermal hardness in the ultrasonic bone scalpel material. In practical applications, the manufactured titanium alloy material for ultrasonic bone scalpels must have a heat resistance ≥600℃, a requirement that most titanium alloys currently available domestically and internationally cannot meet. Traditionally, heat-resistant titanium alloys are crucial materials in aerospace and a key area of ​​research and development for many countries. In particular, heat-resistant titanium alloys used in the manufacture of compressor discs and blades for aircraft engines have high heat resistance requirements, typically operating at temperatures between 500-550℃. However, when manufacturing medical devices requires titanium alloys with higher heat resistance, there are still no specially selected heat-resistant titanium alloy grades.

[0004] As for titanium alloy rods used to manufacture ultrasonic bone scalpel materials, due to their slender rod structure, it is necessary to consider not only that the strength is high enough, but also that the microstructure and properties of the titanium alloy material are stable and reliable. Furthermore, the manufacture of heat-resistant titanium alloys requires a high content of heat-resistant alloying elements, making it difficult to control the uniformity of the composition and hot working.

[0005] Therefore, how to develop a medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy, rod, its preparation method, and its application is a technical problem that urgently needs to be solved by those skilled in the art. Summary of the Invention

[0006] In view of this, the present invention provides a medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy, rod material, preparation method and application thereof.

[0007] To achieve the above objectives, the present invention adopts the following technical solution: A medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy, comprising the following components by mass percentage: Al: 6.0-7.0%, Sn: 1.80-2.20%, Zr: 2.80-3.20%, Mo: 4.80-5.20%, Nb: 0.80-1.20%, Si: 0.40-0.60%, C: 0.03-0.05%, Fe: <0.015%, O: 0.07-0.14%, with Ti as the balance.

[0008] The beneficial effects of this invention are: ① Heat-resistant titanium alloys must have a considerable number of alloying elements with stable α phase represented by aluminum, and at the same time, a certain number of alloying elements with stable β phase represented by molybdenum, to ensure the stability of the microstructure and avoid the formation of brittle phases, thus affecting mechanical properties.

[0009] ② High-temperature resistant titanium alloys are relatively difficult to develop both domestically and internationally because it is very difficult to improve the heat resistance to 50℃. Therefore, it is necessary to add high-melting-point molybdenum and niobium. The composition range of these two elements plays a key role in the heat-resistant titanium alloy, so it is necessary to have a different composition range from other similar titanium alloys at home and abroad.

[0010] ③ High-temperature resistant titanium alloys are mainly used in aircraft and rocket engines, where high fatigue strength is required. The material of this invention is for ultrasonic bone cutters, where fatigue strength requirements are not high, but high thermal strength is required. Therefore, silicon must be added accurately, and the carbon content range must be controlled. This is because titanium carbide, formed during the ingot smelting process, is also a high-temperature resistant compound and has a significant impact on the thermal strength of the titanium alloy. This is the reason for strictly controlling the silicon and carbon composition.

[0011] Theoretically, near-α type titanium alloys and a very small portion of solid solution-strengthened α+β type titanium alloys have the best heat resistance. This is because the aluminum content that stabilizes the α phase is relatively high. Combined with other neutral alloying elements, the contents of Al, Sn, and Zr are determined. In order to prevent the appearance of the α" brittle phase in titanium alloys, alloying elements that stabilize the β phase and elements that improve heat resistance must be added. The contents of Mo, Nb, and Si are determined.

[0012] The titanium alloy grade of the medical high-temperature resistant and high-strength ultrasonic bone scalpel of this invention is specified as Ti65321.

[0013] Furthermore, the Al equivalent is greater than 8.0, and the equivalent value is calculated using the following expression: Al equivalent=Al+Sn / 3+Zr / 6+10×O.

[0014] This invention also provides a method for preparing the aforementioned medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy, comprising the following steps: (1) Manufacturing Al-Mo-Si ternary master alloys: A. Pure aluminum briquettes, molybdenum, and silicon are placed in a graphite crucible and smelted using the aluminothermic method to obtain intermediate alloy castings. The obtained intermediate alloy castings are then de-scaled, crushed, and mixed to obtain intermediate alloy scraps, whose composition is analyzed. B. The analyzed intermediate alloy scraps are placed in a high-purity graphite crucible in a vacuum induction furnace for vacuum melting. During the melting process, silicon is added to replenish the silicon lost during burning according to the composition of the intermediate alloy scraps. The ratio is adjusted to a suitable level, and the alloy ingot is cast. The ingot is peeled, broken, and its composition is analyzed to obtain an Al-Mo-Si ternary intermediate alloy. The mass ratio of Mo to Si is controlled to be 10:1, with Al as the balance. (2) Manufacturing Ti-Nb-Sn ternary master alloy: a. Sponge titanium and metallic niobium are melted in a vacuum electron beam furnace. The melted ingots are peeled, their composition is analyzed, and they are machined and cut to obtain Ti-Nb alloy blocks. b. Place the cut Ti-Nb alloy block into a water-cooled copper crucible induction furnace for melting. After complete melting, press the tin block into the molten pool under an argon protective atmosphere, adjust the temperature of the molten metal, pour the alloy ingot, cool it out of the furnace, peel off the ingot, analyze its composition, and mechanically crush it to obtain the Ti-Nb-Sn ternary master alloy. Control the mass ratio of Nb to Sn to be 1:2, with Ti as the balance. (3) Accurately weigh sponge titanium, Al-Mo-Si ternary master alloy, Ti-Nb-Sn ternary master alloy and sponge zirconium, put them into a mixer to mix, put the uniformly mixed material into a hydraulic extruder mold, and use a 2,000-ton hydraulic extruder to extrude it into consumable electrode blocks. Put the extruded consumable electrode blocks into a vacuum welding box to weld them into consumable electrodes. (4) The consumable electrode is placed in a vacuum consumable arc furnace for three vacuum consumable meltings and cooled to obtain a titanium alloy ingot. The titanium alloy ingot is subjected to flaw detection, riser is removed, and the surface of the titanium alloy ingot is mechanically peeled to obtain a finished titanium alloy ingot. Samples are taken from the top, middle and bottom of the finished titanium alloy ingot to analyze its composition and obtain the medical high temperature and high strength ultrasonic bone scalpel titanium alloy.

[0015] The beneficial effects of this invention are as follows: This invention relates to a high-temperature resistant, high-strength titanium alloy, requiring the addition of six alloying elements. It is a high-alloy-content titanium alloy, among which molybdenum and niobium are high-melting-point refractory metals. Niobium, in particular, if added in its pure elemental form, easily forms metallic inclusions and compositional segregation during the titanium alloy casting process. Tin and aluminum are low-melting-point metals; adding them in their pure elemental form results in significant volatilization and burning losses, failing to guarantee the compositional stability of the titanium alloy ingot. Therefore, alloying elements must be added in the form of master alloys. The composition and production method of master alloys are issues that every titanium alloy manufacturer must address. Currently, the traditional master alloy production method for titanium alloys, both domestically and internationally, is the aluminothermic process. Because this method involves melting in the atmosphere, it is difficult to control impurities such as oxygen and nitrogen, resulting in poor stability and consistency of the master alloy, which cannot meet the requirements for high-alloy-content titanium alloys. In many cases, for high-alloy-content titanium alloys, the selection of master alloy composition, process methods, and quality control are the decisive factors in the quality of the titanium alloy ingot.

[0016] This invention uses Al-Mo-Si ternary master alloy and Ti-Nb-Sn ternary master alloy to add five alloying elements: Al, Mo, Si, Nb, and Sn. Since Zr and Ti are infinitely soluble and have little difference in melting point, sponge zirconium is used to add Zr as a pure elemental metal.

[0017] The manufacture of high-quality titanium alloy ingots is the most fundamental work in high-performance processed materials, and plays a decisive role in the uniformity, consistency and stability of the properties of titanium alloy materials.

[0018] The manufacturing of the consumable electrode for the first melting is the most important and fundamental work. This invention differs from the traditional domestic intermediate alloy ladle feeding process. It uses a mixing machine to ensure the uniformity of alloy composition in the axial and radial directions of the ingot during the ingot casting process, which is a basic process to ensure the quality of the ingot.

[0019] The titanium alloy of this invention adopts a three-stage vacuum consumable melting casting process. The second and third vacuum consumable melting processes are further refined based on the first consumable casting process, which improves the uniformity and consistency of alloying elements in the titanium alloy ingot, adjusts the crystallization rate of the ingot, and controls the size and orientation of the ingot grains.

[0020] The titanium alloy rods used in the manufacture of ultrasonic bone scalpels require high uniformity of composition and consistency of performance due to the ultrasonic conduction involved. The high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy prepared by this invention meets these requirements.

[0021] Furthermore, by mass percentage, sponge zirconium contains Zr > 99.90%; The particle size of Al-Mo-Si ternary master alloy and Ti-Nb-Sn ternary master alloy is controlled at 2.0-6.0 mm. By mass percentage, the content of gaseous and impurity components in both ternary master alloys is controlled as follows: O < 0.060%, N < 0.005%, H < 0.002%, C: 0.03-0.04%. The sponge titanium is grade 0 sponge titanium, with a particle size controlled at 3.0-8.0 mm. By mass percentage, its impurity content is controlled as follows: O < 0.05%, N < 0.002%, Fe < 0.010%.

[0022] The beneficial effects of adopting the above-mentioned further technical solutions are as follows: Since the amount of alloying elements added to the titanium alloy of the present invention is relatively high, the quality of the intermediate alloy has an important influence on the quality of the titanium alloy ingot. Therefore, the gas and impurities of the Al-Mo-Si ternary intermediate alloy and the Ti-Nb-Sn ternary intermediate alloy are controlled. Only when the particle size of the Al-Mo-Si ternary intermediate alloy and the Ti-Nb-Sn ternary intermediate alloy is consistent can the uniform distribution of the intermediate alloy be guaranteed during the extrusion of the electrode.

[0023] Furthermore, in step (4), the vacuum degree of the three vacuum self-consumption melting processes is 3.0 × 10⁻⁶. -3 -1.0×10 -3 mmHg; The melting current for the first vacuum self-consumable melting is 9000A-10000A, the melting voltage is 25-40V, and the diameter of the first vacuum self-consumable ingot is 220-225mm. The melting current for the second vacuum consumable melting was 13000A-14000A, and the melting voltage was 25-42V, resulting in a second vacuum consumable ingot diameter of 310-315mm. The melting current for the third vacuum consumable melting process was 18000A-20000A, and the melting voltage was 25-45V. The diameter of the third vacuum consumable ingot was 400-405mm, and the cooling water temperature of the copper crucible was controlled to be <36℃.

[0024] The beneficial effects of adopting the above-mentioned further technical solutions are as follows: The first vacuum self-consumable melting process has a significant impact on the ingot quality. Due to the large variations in melting power during the melting process, the arc length and vacuum degree are unstable. Different melting process variations must be adopted according to the different elemental compositions of the titanium alloy. In the titanium alloy of this invention, due to the presence of the volatile element tin, the vacuum degree changes drastically at different stages of melting. In the initial stage of melting, measures such as arc stabilization and high pumping rate must be taken to improve the vacuum degree and ensure the purity of the titanium alloy molten metal. During the melting process, the melting current goes from low to high, then stabilizes, and then decreases again.

[0025] The third vacuum self-consumption smelting process must also consider the ingot cooling intensity, solidification rate, ingot feeding, and improve the ingot yield. The water-cooled copper crucible has a moderate cooling intensity to ensure that the refractory metal is evenly distributed in the ingot.

[0026] The size of the vacuum consumable ingot can be selected according to the size of the melting furnace crucible and the alloy content in the titanium alloy. Since the titanium alloy of this patent has a high content of refractory metals, the molten pool needs a long electromagnetic stirring time. The ingot size of this invention is determined by taking into account various factors.

[0027] Furthermore, in step (4), the components in the titanium alloy finished ingot are controlled within the following tolerances based on mass percentage: Al < 0.02%, Sn < 0.02%, Zr < 0.01%, Mo < 0.01%, Nb < 0.01%, Si < 0.001%, C < 0.010%.

[0028] The beneficial effects of adopting the above-mentioned further technical solutions are as follows: the uniformity, accuracy, and consistency of composition have a significant impact on the performance of titanium alloys. Large deviations in the axial direction (top, middle, and bottom) and radial direction (surface and center) of the ingot indicate substantial compositional segregation, which is the fundamental reason why the performance of Chinese titanium alloys has consistently lagged behind imported products. The compositional error value of this invention is far superior to the standards and actual production control values ​​for titanium alloy ingots both domestically and internationally.

[0029] This invention also provides a method for preparing a high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod, comprising the following steps: ① Titanium alloy ingot blanking: The medical high temperature and high strength ultrasonic bone knife titanium alloy is heated and forged into blanks using a 3000-ton hydraulic high-speed forging machine and a 120KW high temperature resistance furnace. The blanks are then ground, machined to remove oxide scale and forging defects, and sawn into blanks. ② Precision forged bars: The bars are heated and forged using an 800-ton hydraulic high-speed forging machine and a 75KW resistance furnace. After machining, the surface oxide scale is removed, and the bars are sawn to obtain hot-rolled billets. ③ Hot rolling: The hot-rolled billet is heated and hot-rolled using a 460-type high-speed wire rod hot rolling mill and a 75KW box-type resistance furnace, followed by water cooling; ④ Hot drawing: Hot drawing is performed using an 80-ton adjustable speed flat drawing and stretching machine and a 10-meter horizontal high-temperature alloy tubular resistance heating furnace with a power of 85KW, followed by air cooling. ⑤ Heat treatment: Heating is carried out using a 75KW resistance furnace, followed by solution treatment, air cooling, aging treatment, and air cooling in sequence; ⑥ Hot straightening: Hot straightening is performed using a 45KW electric heating straightening machine; ⑦ Peeling, polishing, and flaw detection: Rough machining is performed using a centerless grinder, fine grinding is performed using a high-precision grinder, and polishing is performed using a polishing machine. The resulting rod is then tested with an ultrasonic flaw detector to obtain the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod.

[0030] The beneficial effects of this invention are as follows: The titanium alloy of this invention is a heat-resistant, high-strength titanium alloy. Due to its high thermal strength and large deformation resistance, the hot working of titanium alloy ingots, bars, and stretching is much more difficult than that of other α-phase, near-α-phase, and α+β two-phase titanium alloys, and generally requires processing equipment with greater capacity. Heat treatment further improves the stability and consistency of the mechanical properties of the bars.

[0031] Furthermore, in step ①, the heating temperature is 1190℃, the holding time is 1.5 hours, the forging temperature is 1050-1180℃, the deformation rate in one pass is 30-45%, and the cross-section of the billet is a square with a side length of 230mm. In step ②, the heating temperature is 1120℃, the forging temperature is 1020-1120℃, the deformation rate in one pass is 30-50%, and the bar diameter is 85-87mm. In step ③, the heating temperature is 1120℃, the hot rolling temperature is 1000-1120℃, the hot rolling line speed is 3-6 m / s, the deformation rate per pass is 20-30%, and the finished product diameter is 12mm. In step ④, the hot stretching temperature is 950-1050℃, the deformation rate per pass is 15-25%, emulsified graphite is used as a lubricant, and the diameter of the finished product is 3.0-5.0mm; In step ⑤, the solution treatment temperature is 980-1030℃±10℃, and the holding time is 30 minutes; the aging treatment temperature is 650-690℃, and the holding time is 45-60 minutes. In step ⑥, the heat straightening temperature is 580-600℃, and the diameter shrinkage error is 0.01mm.

[0032] Furthermore, in step ①, the forging deformation speed changes from low speed to medium speed to high speed to low speed, and the deformation amount changes from high to low to low to high. In step ②, the forging deformation speed changes from medium speed to fast speed, and the deformation amount changes from high to low.

[0033] The present invention also provides a medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod prepared by the method described above.

[0034] The beneficial effects of this invention are as follows: The physical properties of the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod prepared by this invention are: ① Density: ρ = 4.6-4.62 g / cm³; ② Elastic modulus E: 118-121 GPa at 20℃; 90-94 GPa at 600℃; ③ Thermal conductivity: 6.18-6.22 W / m.℃ at 100℃; 11.20-11.60 W / m.℃ at 600℃; ④ Linear thermal expansion: 0.49-0.53% at 20-600℃; Mechanical properties (after solution treatment and aging): ① Tensile properties at room temperature: σb 1080-1150MPa, σ0.2 980-1020MPa, δ12-14%, Ψ22-25%; ②Tensive properties at 600℃: σb 660-700MPa, σ0.2 550-600MPa, δ16-18%, Ψ35-37%.

[0035] The present invention also provides the application of the aforementioned high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod in the preparation of a high-temperature resistant and high-strength ultrasonic bone scalpel. Attached Figure Description

[0036] Figure 1 This is a metallographic image of the titanium alloy rod for medical high-temperature resistant and high-strength ultrasonic bone scalpel in solid solution state, as described in Embodiment 1 of the present invention. Detailed Implementation

[0037] The technical solutions in the embodiments of the present invention will be clearly and completely described below. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention. Example 1

[0038] The medical-grade high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy comprises the following components by weight percentage: Al: 6.50%, Sn: 2.10%, Zr: 3.20%, Mo: 4.95%, Nb: 1.20%, Si: 0.47%, C: 0.03%, Fe: 0.012%, O: 0.070%, N: 0.0015%, H: 0.0010%, with Ti as the balance.

[0039] If the Al equivalent is greater than 8.0, the equivalent value is calculated using the following expression: Al equivalent=Al+Sn / 3+Zr / 6+10×O.

[0040] The preparation method of medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy includes the following steps: (1) Manufacturing Al-Mo-Si ternary master alloys: A. Pure aluminum briquettes, molybdenum, and silicon were placed in a graphite crucible and smelted using the aluminothermic method to obtain intermediate alloy castings at a smelting temperature of 2700℃. The obtained intermediate alloy castings were then de-scaled, crushed, and mixed to obtain intermediate alloy scraps, whose composition was analyzed. B. The analyzed intermediate alloy scraps were placed in a high-purity graphite crucible in a vacuum induction furnace for vacuum melting at a temperature of 2200℃. During the melting process, silicon was added to replenish the silicon lost during burning according to the composition of the intermediate alloy scraps. The ratio was adjusted to a suitable level, and the alloy ingot was cast. The ingot was peeled, broken, and its composition was analyzed to obtain an Al-Mo-Si ternary intermediate alloy. The mass ratio of Mo to Si was controlled to be 10:1, with Al as the balance. (2) Manufacturing Ti-Nb-Sn ternary master alloy: a. Sponge titanium and metallic niobium are melted in a vacuum electron beam furnace at a melting temperature of 2600℃. The melted ingots are peeled, their composition is analyzed, and they are machined and cut to obtain Ti-Nb alloy blocks. b. Place the cut Ti-Nb alloy block into a water-cooled copper crucible induction furnace for melting. After complete melting, press the tin block into the molten pool under an argon protective atmosphere, adjust the temperature of the molten metal to 1700℃, pour the alloy ingot, cool it out of the furnace, peel off the ingot, analyze its composition, and mechanically crush it to obtain the Ti-Nb-Sn ternary master alloy. Control the mass ratio of Nb to Sn to be 1:2, with Ti as the balance. (3) Accurately weigh sponge titanium, Al-Mo-Si ternary master alloy, Ti-Nb-Sn ternary master alloy and sponge zirconium, put them into a mixer to mix, put the uniformly mixed material into a hydraulic extruder mold, and use a 2,000-ton hydraulic extruder to extrude it into consumable electrode blocks. Put the extruded consumable electrode blocks into a vacuum welding box to weld them into consumable electrodes. By mass percentage, sponge zirconium comprises Zr: 99.91%; The particle size of the Al-Mo-Si ternary master alloy and the Ti-Nb-Sn ternary master alloy is controlled at 2.0-6.0 mm. By mass percentage, the gas and impurity content of the Al-Mo-Si ternary master alloy is: O: 0.050%, N: 0.003%, H: 0.001%, C: 0.035%, and that of the Ti-Nb-Sn ternary master alloy is: O: 0.04%, N: 0.002%, H: 0.001%, C: 0.03%. The sponge titanium is grade 0 sponge titanium, with a particle size controlled at 3.0-8.0 mm. By mass percentage, its impurity content is: O: 0.04%, N: 0.001%, Fe: 0.009%.

[0041] (4) The self-consuming electrode is placed in a vacuum self-consuming arc furnace for three vacuum self-consuming melting processes. The melting temperature of the first vacuum self-consuming melting process is 1800℃, the melting current is 9500A, and the melting voltage is 30V. The diameter of the first vacuum self-consuming ingot is 220-225mm. The melting temperature of the second vacuum consumable melting was 1850℃, the melting current was 13500A, and the melting voltage was 32V, resulting in a diameter of 310-315mm for the second vacuum consumable ingot. The third vacuum consumable melting process was carried out at a melting temperature of 1900℃, a melting current of 19000A, and a melting voltage of 34V, resulting in a third vacuum consumable ingot with a diameter of 400-405mm. The cooling water temperature of the copper crucible was controlled at 34℃ to obtain a titanium alloy ingot. The titanium alloy ingot was subjected to flaw detection, riser removal, and surface peeling by mechanical processing to obtain a finished titanium alloy ingot. Samples were taken from three points (top, middle, and bottom) of the finished titanium alloy ingot to analyze its composition, thus obtaining the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy.

[0042] The composition of the titanium alloy finished ingot, by mass percentage, is as follows: Al: 0.01%, Sn: 0.01%, Zr: 0.007%, Mo: 0.008%, Nb: 0.005%, Si: 0.0008%, C: 0.005%.

[0043] The preparation method of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod includes the following steps: ① Titanium alloy ingot blanking: A 3000-ton hydraulic high-speed forging machine and a 120KW high-temperature resistance furnace are used to heat and forge the Φ390mm medical high-temperature resistant and high-strength ultrasonic bone knife titanium alloy blank. The blank is then ground, machined to remove oxide scale and forging defects, and sawn into blanks. The heating temperature is 1190℃, the holding time is 1.5 hours, the initial forging temperature is 1170℃, the final forging temperature is 1050℃, the deformation rate in one pass is 35%, and the billet size is 230×230×2000mm. Forging deformation speed variation: low speed → medium speed → high speed → low speed; Deformation amount variation: high → low → low → high. ② Precision forged bars: The bars are heated and forged using an 800-ton hydraulic high-speed forging machine and a 75KW resistance furnace. After machining, the surface oxide scale is removed, and the bars are sawn to obtain hot-rolled billets. The heating temperature is 1120℃, the initial forging temperature is 1120℃, the final forging temperature is 1020℃, the deformation rate in one forging is 30%, and the bar size is Φ85-87mm×1500mm. Forging deformation speed change: medium speed → fast speed; Deformation amount change: high → low. ③ Hot rolling: The hot-rolled billet is heated and hot-rolled using a 460-type high-speed wire rod hot rolling mill and a 75KW box-type resistance furnace, followed by water cooling; Heating temperature: 1120℃, rolling temperature: 1120℃, final rolling temperature: 1010℃, hot rolling line speed: 5 m / s, pass deformation rate: 25%, finished product diameter: 12 mm; ④ Hot drawing: Hot drawing is performed using an 80-ton adjustable speed flat drawing and stretching machine and a 10-meter horizontal high-temperature alloy tubular resistance heating furnace with a power of 85KW, followed by air cooling. The hot stretching temperature is 980℃, the deformation rate per pass is 18%, emulsified graphite is used as a lubricant, and the finished product size is Φ3.2mm×5000mm. ⑤ Heat treatment: Heating is carried out using a 75KW resistance furnace, followed by solution treatment, air cooling, aging treatment, and air cooling in sequence; The solution treatment temperature is 980℃ and the holding time is 30 minutes; the aging treatment temperature is 680℃ and the holding time is 45 minutes. ⑥ Hot straightening: Hot straightening is performed using a 45KW electric heating straightening machine; The heat straightening temperature is 580℃, and the diameter reduction error is 0.01mm; ⑦ Peeling, polishing, and flaw detection: Rough machining is performed using a centerless grinder, fine grinding is performed using a high-precision grinder, and polishing is performed using a polishing machine. The resulting rod is then inspected using an ultrasonic flaw detector to obtain a finished medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod with dimensions of Φ2.5+0.010mm×1500mm.

[0044] Mechanical properties of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rods for medical use: Physical properties: ① Density: ρ = 4.61 g / cm³; ② Elastic modulus E: 119 GPa at 20℃; 92 GPa at 600℃; ③ Thermal conductivity: 6.20 W / m·℃ at 100℃; 11.50 W / m·℃ at 600℃; ④ Linear thermal expansion: 0.51% at 20-600℃; Mechanical properties (after solution treatment and aging): ① Tensile properties at room temperature: σb 1150MPa, σ0.2 1020MPa, δ 13%, Ψ 23%; ②Tensive properties at 600℃: σb 690MPa, σ0.2 585MPa, δ18%, Ψ37%. Example 2

[0045] The medical-grade high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy comprises the following components by weight percentage: Al: 6.0%, Sn: 1.80%, Zr: 2.80%, Mo: 4.80%, Nb: 0.80%, Si: 0.40%, C: 0.04%, Fe: 0.012%, O: 0.11%, N: 0.0015%, H: 0.0010%, with Ti as the balance.

[0046] If the Al equivalent is greater than 8.0, the equivalent value is calculated using the following expression: Al equivalent=Al+Sn / 3+Zr / 6+10×O.

[0047] The preparation method of medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy includes the following steps: (1) Manufacturing Al-Mo-Si ternary master alloys: A. Pure aluminum briquettes, molybdenum, and silicon were placed in a graphite crucible and smelted using the aluminothermic method to obtain intermediate alloy castings at a smelting temperature of 2700℃. The obtained intermediate alloy castings were then de-scaled, crushed, and mixed to obtain intermediate alloy scraps, whose composition was analyzed. B. The analyzed intermediate alloy scraps were placed in a high-purity graphite crucible in a vacuum induction furnace for vacuum melting at a temperature of 2200℃. During the melting process, silicon was added to replenish the silicon lost during burning according to the composition of the intermediate alloy scraps. The ratio was adjusted to a suitable level, and the alloy ingot was cast. The ingot was peeled, broken, and its composition was analyzed to obtain an Al-Mo-Si ternary intermediate alloy. The mass ratio of Mo to Si was controlled to be 10:1, with Al as the balance. (2) Manufacturing Ti-Nb-Sn ternary master alloy: a. Sponge titanium and metallic niobium are melted in a vacuum electron beam furnace at a melting temperature of 2600℃. The melted ingots are peeled, their composition is analyzed, and they are machined and cut to obtain Ti-Nb alloy blocks. b. Place the cut Ti-Nb alloy block into a water-cooled copper crucible induction furnace for melting. After complete melting, press the tin block into the molten pool under an argon protective atmosphere, adjust the temperature of the molten metal to 1700℃, pour the alloy ingot, cool it out of the furnace, peel off the ingot, analyze its composition, and mechanically crush it to obtain the Ti-Nb-Sn ternary master alloy. Control the mass ratio of Nb to Sn to be 1:2, with Ti as the balance. (3) Accurately weigh sponge titanium, Al-Mo-Si ternary master alloy, Ti-Nb-Sn ternary master alloy and sponge zirconium, put them into a mixer to mix, put the uniformly mixed material into a hydraulic extruder mold, and use a 2,000-ton hydraulic extruder to extrude it into consumable electrode blocks. Put the extruded consumable electrode blocks into a vacuum welding box to weld them into consumable electrodes. By mass percentage, sponge zirconium comprises Zr: 99.92%; The particle size of the Al-Mo-Si ternary master alloy and the Ti-Nb-Sn ternary master alloy is controlled at 2.0-6.0 mm. By mass percentage, the gas and impurity content of the Al-Mo-Si ternary master alloy is: O: 0.040%, N: 0.003%, H: 0.001%, C: 0.03%; and the gas and impurity content of the Ti-Nb-Sn ternary master alloy is: O: 0.050%, N: 0.004%, H: 0.001%, C: 0.04%. The sponge titanium is grade 0 sponge titanium, with a particle size controlled at 3.0-8.0 mm. By mass percentage, its impurity content is: O: 0.04%, N: 0.001%, Fe: 0.009%.

[0048] (4) The self-consuming electrode is placed in a vacuum self-consuming arc furnace for three vacuum self-consuming melting processes. The melting temperature of the first vacuum self-consuming melting process is 1800℃, the melting current is 9500A, and the melting voltage is 30V. The diameter of the first vacuum self-consuming ingot is 220-225mm. The melting temperature of the second vacuum consumable melting was 1850℃, the melting current was 13500A, and the melting voltage was 32V, resulting in a diameter of 310-315mm for the second vacuum consumable ingot. The third vacuum consumable melting process was carried out at a melting temperature of 1900℃, a melting current of 19000A, and a melting voltage of 34V, resulting in a third vacuum consumable ingot with a diameter of 400-405mm. The cooling water temperature of the copper crucible was controlled at 35℃ to obtain a titanium alloy ingot. The titanium alloy ingot was then subjected to flaw detection, riser removal, and surface peeling by mechanical processing to obtain a finished titanium alloy ingot. Samples were taken from three points (top, middle, and bottom) of the finished titanium alloy ingot to analyze its composition, thus obtaining the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy.

[0049] The composition of the titanium alloy finished ingot, by mass percentage, is as follows: Al: 0.01%, Sn: 0.01%, Zr: 0.007%, Mo: 0.008%, Nb: 0.005%, Si: 0.0008%, C: 0.005%.

[0050] The preparation method of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod includes the following steps: ① Titanium alloy ingot blanking: A 3000-ton hydraulic high-speed forging machine and a 120KW high-temperature resistance furnace are used to heat and forge the titanium alloy for medical high-temperature resistant and high-strength ultrasonic bone scalpel. The blank is then ground, machined to remove oxide scale and forging defects, and sawn into blanks. The heating temperature is 1190℃, the holding time is 1.5 hours, the initial forging temperature is 1170℃, the final forging temperature is 1050℃, the deformation rate in one pass is 30%, and the billet size is 230×230×2000mm. Forging deformation speed variation: low speed → medium speed → high speed → low speed; Deformation amount variation: high → low → low → high. ② Precision forged bars: The bars are heated and forged using an 800-ton hydraulic high-speed forging machine and a 75KW resistance furnace. After machining, the surface oxide scale is removed, and the bars are sawn to obtain hot-rolled billets. The heating temperature is 1120℃, the initial forging temperature is 1120℃, the final forging temperature is 1020℃, the deformation rate in one pass is 40%, and the bar diameter is 85-87mm. Forging deformation speed change: medium speed → fast speed; Deformation amount change: high → low. ③ Hot rolling: The hot-rolled billet is heated and hot-rolled using a 460-type high-speed wire rod hot rolling mill and a 75KW box-type resistance furnace, followed by water cooling; Heating temperature: 1120℃, rolling temperature: 1120℃, final rolling temperature: 1010℃, hot rolling speed: 4 m / s, pass deformation rate: 25%, finished product diameter: 12 mm. ④ Hot drawing: Hot drawing is performed using an 80-ton adjustable speed flat drawing and stretching machine and a 10-meter horizontal high-temperature alloy tubular resistance heating furnace with a power of 85KW, followed by air cooling. The hot stretching temperature is 950℃, the deformation rate per pass is 20%, emulsified graphite is used as a lubricant, and the finished product size is Φ3.2mm×5000mm. ⑤ Heat treatment: Heating is carried out using a 75KW resistance furnace, followed by solution treatment, air cooling, aging treatment, and air cooling in sequence; The solution treatment temperature was 980℃ and the holding time was 30 minutes; the aging treatment temperature was 650℃ and the holding time was 45 minutes. ⑥ Hot straightening: Hot straightening is performed using a 45KW electric heating straightening machine; The heat straightening temperature is 580℃, and the diameter reduction error is 0.01mm; ⑦ Peeling, polishing, and flaw detection: Rough machining is performed using a centerless grinder, fine grinding is performed using a high-precision grinder, and polishing is performed using a polishing machine. The resulting rod is then inspected using an ultrasonic flaw detector to obtain a finished medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod with dimensions of Φ2.5+0.010mm×1500mm.

[0051] Mechanical properties of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rods for medical use: Physical properties: ① Density: ρ = 4.60 g / cm³; ② Elastic modulus E: 118 GPa at 20℃; 90 GPa at 600℃; ③ Thermal conductivity: 6.18 W / m·℃ at 100℃; 11.20 W / m·℃ at 600℃; ④ Linear thermal expansion: 0.49% at 20-600℃; Mechanical properties (after solution treatment and aging): ① Tensile properties at room temperature: σb 1150MPa, σ0.2 1020MPa, δ 14%, Ψ 25%; ②Tensive properties at 600℃: σb 700MPa, σ0.2 600MPa, δ18%, Ψ37%. Example 3

[0052] The medical-grade high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy comprises the following components by weight percentage: Al: 7.0%, Sn: 2.20%, Zr: 3.0%, Mo: 5.20%, Nb: 1.0%, Si: 0.60%, C: 0.05%, Fe: 0.012%, O: 0.14%, N: 0.0015%, H: 0.0010%, with Ti as the balance.

[0053] If the Al equivalent is greater than 8.0, the equivalent value is calculated using the following expression: Al equivalent=Al+Sn / 3+Zr / 6+10×O.

[0054] The preparation method of medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy includes the following steps: (1) Manufacturing Al-Mo-Si ternary master alloys: A. Pure aluminum briquettes, molybdenum, and silicon were placed in a graphite crucible and smelted using the aluminothermic method to obtain intermediate alloy castings at a smelting temperature of 2700℃. The obtained intermediate alloy castings were then de-scaled, crushed, and mixed to obtain intermediate alloy scraps, whose composition was analyzed. B. The analyzed intermediate alloy scraps were placed in a high-purity graphite crucible in a vacuum induction furnace for vacuum melting at a temperature of 2200℃. During the melting process, silicon was added to replenish the silicon lost during burning according to the composition of the intermediate alloy scraps. The ratio was adjusted to a suitable level, and the alloy ingot was cast. The ingot was peeled, broken, and its composition was analyzed to obtain an Al-Mo-Si ternary intermediate alloy. The mass ratio of Mo to Si was controlled to be 10:1, with Al as the balance. (2) Manufacturing Ti-Nb-Sn ternary master alloy: a. Sponge titanium and metallic niobium are melted in a vacuum electron beam furnace at a melting temperature of 2600℃. The melted ingots are peeled, their composition is analyzed, and they are machined and cut to obtain Ti-Nb alloy blocks. b. Place the cut Ti-Nb alloy block into a water-cooled copper crucible induction furnace for melting. After complete melting, press the tin block into the molten pool under an argon protective atmosphere, adjust the temperature of the molten metal to 1700℃, pour the alloy ingot, cool it out of the furnace, peel off the ingot, analyze its composition, and mechanically crush it to obtain the Ti-Nb-Sn ternary master alloy. Control the mass ratio of Nb to Sn to be 1:2, with Ti as the balance. (3) Accurately weigh sponge titanium, Al-Mo-Si ternary master alloy, Ti-Nb-Sn ternary master alloy and sponge zirconium, put them into a mixer to mix, put the uniformly mixed material into a hydraulic extruder mold, and use a 2,000-ton hydraulic extruder to extrude it into consumable electrode blocks. Put the extruded consumable electrode blocks into a vacuum welding box to weld them into consumable electrodes. By mass percentage, sponge zirconium comprises Zr: 99.93%; The particle size of Al-Mo-Si ternary master alloy and Ti-Nb-Sn ternary master alloy is controlled at 2.0-6.0 mm. By mass percentage, the gas and impurity content of Al-Mo-Si ternary master alloy is: O: 0.050%, N: 0.004%, H: 0.001%, C: 0.04%. The gaseous and impurity composition of the Ti-Nb-Sn ternary master alloy is as follows: O: 0.040%, N: 0.003%, H: 0.001%, C: 0.03%; The sponge titanium is grade 0 sponge titanium, with a particle size controlled at 3.0-8.0 mm. By mass percentage, its impurity content is: O: 0.04%, N: 0.001%, Fe: 0.009%.

[0055] (4) The self-consuming electrode is placed in a vacuum self-consuming arc furnace for three vacuum self-consuming melting processes. The melting temperature of the first vacuum self-consuming melting process is 1800℃, the melting current is 9500A, and the melting voltage is 30V. The diameter of the first vacuum self-consuming ingot is 220-225mm. The melting temperature of the second vacuum consumable melting was 1850℃, the melting current was 13500A, and the melting voltage was 32V, resulting in a diameter of 310-315mm for the second vacuum consumable ingot. The third vacuum consumable melting process was carried out at a melting temperature of 1900℃, a melting current of 19000A, and a melting voltage of 34V, resulting in a third vacuum consumable ingot with a diameter of 400-405mm. The cooling water temperature of the copper crucible was controlled at 35℃ to obtain a titanium alloy ingot. The titanium alloy ingot was then subjected to flaw detection, riser removal, and surface peeling by mechanical processing to obtain a finished titanium alloy ingot. Samples were taken from three points (top, middle, and bottom) of the finished titanium alloy ingot to analyze its composition, thus obtaining the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy.

[0056] The composition of the titanium alloy finished ingot, by mass percentage, is as follows: Al: 0.01%, Sn: 0.01%, Zr: 0.007%, Mo: 0.008%, Nb: 0.005%, Si: 0.0008%, C: 0.005%.

[0057] The preparation method of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod includes the following steps: ① Titanium alloy ingot blanking: A 3000-ton hydraulic high-speed forging machine and a 120KW high-temperature resistance furnace are used to heat and forge the titanium alloy for medical high-temperature resistant and high-strength ultrasonic bone scalpel. The blank is then ground, machined to remove oxide scale and forging defects, and sawn into blanks. The heating temperature is 1190℃, the holding time is 1.5 hours, the initial forging temperature is 1170℃, the final forging temperature is 1050℃, the deformation rate in one pass is 45%, and the cross-section of the billet is a square with a side length of 230mm. Forging deformation speed variation: low speed → medium speed → high speed → low speed; Deformation amount variation: high → low → low → high. ② Precision forged bars: The bars are heated and forged using an 800-ton hydraulic high-speed forging machine and a 75KW resistance furnace. After machining, the surface oxide scale is removed, and the bars are sawn to obtain hot-rolled billets. The heating temperature is 1120℃, the initial forging temperature is 1120℃, the final forging temperature is 1020℃, the deformation rate in one forging is 50%, and the bar diameter is 85-87mm. Forging deformation speed change: medium speed → fast speed; Deformation amount change: high → low. ③ Hot rolling: The hot-rolled billet is heated and hot-rolled using a 460-type high-speed wire rod hot rolling mill and a 75KW box-type resistance furnace, followed by water cooling; Heating temperature: 1120℃, rolling temperature: 1120℃, final rolling temperature: 1010℃, hot rolling line speed: 6 m / s, pass deformation rate: 30%, finished product diameter: 12 mm; ④ Hot drawing: Hot drawing is performed using an 80-ton adjustable speed flat drawing and stretching machine and a 10-meter horizontal high-temperature alloy tubular resistance heating furnace with a power of 85KW, followed by air cooling. The hot stretching temperature is 1050℃, the deformation rate per pass is 25%, emulsified graphite is used as a lubricant, and the diameter is Φ5mm×5000mm. ⑤ Heat treatment: Heating is carried out using a 75KW resistance furnace, followed by solution treatment, air cooling, aging treatment, and air cooling in sequence; The solution treatment temperature was 1030℃ and the holding time was 30 minutes; the aging treatment temperature was 690℃ and the holding time was 60 minutes. ⑥ Hot straightening: Hot straightening is performed using a 45KW electric heating straightening machine; The heat straightening temperature is 600℃, and the diameter reduction error is 0.01mm; ⑦ Peeling, polishing, and flaw detection: Rough machining is performed using a centerless grinder, fine grinding is performed using a high-precision grinder, and polishing is performed using a polishing machine. The resulting rod is then inspected using an ultrasonic flaw detector to obtain a finished medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod with dimensions of Φ2.5+0.010mm×1500mm.

[0058] Mechanical properties of high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rods for medical use: Physical properties: ① Density: ρ = 4.62 g / cm³; ② Elastic modulus E: 121 GPa at 20℃; 94 GPa at 600℃; ③ Thermal conductivity: 6.22 W / m·℃ at 100℃; 11.60 W / m·℃ at 600℃; ④ Linear thermal expansion: 0.53% at 20-600℃; Mechanical properties (after solution treatment and aging): ① Room temperature tensile properties: σb 1080MPa, σ0.2 980MPa, δ 12%, Ψ 22%; ②Tensive properties at 600℃: σb 660MPa, σ0.2 550MPa, δ16%, Ψ35%.

[0059] The description of the disclosed embodiments enables those skilled in the art to make or use the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the invention. Therefore, the invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy, characterized in that, The composition, by mass percentage, includes the following components: Al: 6.0-7.0%, Sn: 1.80-2.20%, Zr: 2.80-3.20%, Mo: 4.80-5.20%, Nb: 0.80-1.20%, Si: 0.40-0.60%, C: 0.03-0.05%, Fe: <0.015%, O: 0.07-0.14%, Ti balance; The preparation method of the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy includes the following steps: (1) Manufacturing Al-Mo-Si ternary master alloys: A. Pure aluminum briquettes, molybdenum, and silicon are placed in a graphite crucible and smelted using the aluminothermic method to obtain intermediate alloy castings. The obtained intermediate alloy castings are then de-scaled, crushed, and mixed to obtain intermediate alloy scraps, whose composition is analyzed. B. The analyzed intermediate alloy scraps are placed in a high-purity graphite crucible in a vacuum induction furnace for vacuum melting. During the melting process, silicon is added to replenish the silicon lost during burning according to the composition of the intermediate alloy scraps. The ratio is adjusted to a suitable level, and the alloy ingot is cast. The ingot is peeled, broken, and its composition is analyzed to obtain an Al-Mo-Si ternary intermediate alloy. The mass ratio of Mo to Si is controlled to be 10:1, with Al as the balance. (2) Manufacturing Ti-Nb-Sn ternary master alloy: a. Sponge titanium and metallic niobium are melted in a vacuum electron beam furnace. The melted ingots are peeled, their composition is analyzed, and they are machined and cut to obtain Ti-Nb alloy blocks. b. Place the cut Ti-Nb alloy block into a water-cooled copper crucible induction furnace for melting. After complete melting, press the tin block into the molten pool under an argon protective atmosphere, adjust the temperature of the molten metal, pour the alloy ingot, cool it out of the furnace, peel off the ingot, analyze its composition, and mechanically crush it to obtain the Ti-Nb-Sn ternary master alloy. Control the mass ratio of Nb to Sn to be 1:2, with Ti as the balance. (3) Accurately weigh sponge titanium, Al-Mo-Si ternary master alloy, Ti-Nb-Sn ternary master alloy and sponge zirconium, put them into a mixer to mix, put the uniformly mixed material into a hydraulic extruder mold, and use a 2,000-ton hydraulic extruder to extrude it into consumable electrode blocks. Put the extruded consumable electrode blocks into a vacuum welding box to weld them into consumable electrodes. (4) The consumable electrode is placed in a vacuum consumable arc furnace for three vacuum consumable meltings and cooled to obtain a titanium alloy ingot. The titanium alloy ingot is subjected to flaw detection, riser is removed, and the surface of the titanium alloy ingot is mechanically peeled to obtain a finished titanium alloy ingot. Samples are taken from the top, middle and bottom of the finished titanium alloy ingot to analyze its composition and obtain the medical high temperature resistant high strength ultrasonic bone scalpel titanium alloy. In step (4), the vacuum degree of the three vacuum consumable melting processes is 3.0 × 10⁻⁶. -3 -1.0×10 -3 mmHg; The melting current for the first vacuum self-consumable melting is 9000A-10000A, the melting voltage is 25-40V, and the diameter of the first vacuum self-consumable ingot is 220-225mm. The melting current for the second vacuum consumable melting was 13000A-14000A, and the melting voltage was 25-42V, resulting in a second vacuum consumable ingot diameter of 310-315mm. The melting current for the third vacuum consumable melting process is 18000A-20000A, and the melting voltage is 25-45V. The diameter of the third vacuum consumable ingot is 400-405mm. The cooling process involves controlling the temperature of the cooling water in the copper crucible to be <36℃.

2. The medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy according to claim 1, characterized in that, If the Al equivalent is greater than 8.0, the equivalent value is calculated using the following expression: Al equivalent=Al+Sn / 3+Zr / 6+10×O.

3. The medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy according to claim 1, characterized in that, By mass percentage, sponge zirconium contains Zr > 99.90%; The particle size of Al-Mo-Si ternary master alloy and Ti-Nb-Sn ternary master alloy is controlled at 2.0-6.0 mm. By mass percentage, the content of gaseous and impurity components of the two ternary master alloys is controlled as follows: O < 0.060%, N < 0.005%, H < 0.002%, C: 0.03-0.04%. The sponge titanium is grade 0 sponge titanium, with a particle size controlled at 3.0-8.0 mm. By mass percentage, its impurity content is controlled as follows: O < 0.05%, N < 0.002%, Fe < 0.010%.

4. The medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy according to claim 1, characterized in that, In step (4), the components in the titanium alloy finished ingot are controlled within the following tolerances based on mass percentage: Al < 0.02%, Sn < 0.02%, Zr < 0.01%, Mo < 0.01%, Nb < 0.01%, Si < 0.001%, C < 0.010%.

5. A method for preparing a high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod, characterized in that, Includes the following steps: ① Titanium alloy ingot blanking: The medical high temperature resistant and high strength ultrasonic bone knife titanium alloy described in claim 1 is heated and forged using a 3000-ton hydraulic high-speed forging machine and a 120KW high temperature resistance furnace. The blank is then ground, machined to remove oxide scale and forging defects, and sawn into blanks. ② Precision forged bars: The bars are heated and forged using an 800-ton hydraulic high-speed forging machine and a 75KW resistance furnace. After machining, the surface oxide scale is removed, and the bars are sawn to obtain hot-rolled billets. ③ Hot rolling: The hot-rolled billet is heated and hot-rolled using a 460-type high-speed wire rod hot rolling mill and a 75KW box-type resistance furnace, followed by water cooling; ④ Hot drawing: Hot drawing is performed using an 80-ton adjustable speed flat drawing and stretching machine and a 10-meter horizontal high-temperature alloy tubular resistance heating furnace with a power of 85KW, followed by air cooling. ⑤ Heat treatment: Heating is carried out using a 75KW resistance furnace, followed by solution treatment, air cooling, aging treatment, and air cooling in sequence; ⑥ Hot straightening: Hot straightening is performed using a 45KW electric heating straightening machine; ⑦ Peeling, polishing, and flaw detection: Rough machining is performed using a centerless grinder, fine grinding is performed using a high-precision grinder, and polishing is performed using a polishing machine. The resulting rod is then tested with an ultrasonic flaw detector to obtain the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod.

6. The method for preparing a medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod according to claim 5, characterized in that, In step ①, the heating temperature is 1190℃, the holding time is 1.5 hours, the forging temperature is 1050-1180℃, the deformation rate in one pass is 30-45%, and the cross-section of the billet is a square with a side length of 230mm. In step ②, the heating temperature is 1120℃, the forging temperature is 1020-1120℃, the deformation rate in one pass is 30-50%, and the bar diameter is 85-87mm. In step ③, the heating temperature is 1120℃, the hot rolling temperature is 1000-1120℃, the hot rolling line speed is 3-6 m / s, the deformation rate per pass is 20-30%, and the finished product diameter is 12mm. In step ④, the hot stretching temperature is 950-1050℃, the deformation rate per pass is 15-25%, emulsified graphite is used as a lubricant, and the diameter of the finished product is 3.0-5.0mm; In step ⑤, the solution treatment temperature is 980-1030℃ and the holding time is 30 minutes; the aging treatment temperature is 650-690℃ and the holding time is 45-60 minutes. In step ⑥, the heat straightening temperature is 580-600℃, and the diameter shrinkage error is 0.01mm.

7. A medical high-temperature resistant, high-strength ultrasonic bone scalpel titanium alloy rod prepared by the preparation method according to any one of claims 5-6.

8. The application of the medical high-temperature resistant and high-strength ultrasonic bone scalpel titanium alloy rod as described in claim 7 in the preparation of a medical high-temperature resistant and high-strength ultrasonic bone scalpel.

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