A method for preparing a bone-like multifunctional medical titanium alloy
By combining Ti6Al4V5Cu alloy powder with bioceramic powder, a porous medical titanium alloy was prepared, which solved the problems of elastic modulus mismatch, limited bone integration capacity and insufficient antibacterial properties of traditional titanium alloy implants, and achieved multi-functional synergy of elastic modulus matching, bone cell adhesion and antibacterial effect.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- GUANGDONG YUEGANG NEW MATERIAL TECH CO LTD
- Filing Date
- 2026-02-28
- Publication Date
- 2026-05-26
AI Technical Summary
Traditional titanium alloy implants suffer from problems such as elastic modulus mismatch, limited osseointegration capacity, and insufficient antibacterial properties, which cannot be effectively solved by existing modification methods.
By combining Ti6Al4V5Cu alloy powder with bioceramic powder, the elastic modulus is precisely controlled to form a porous medical titanium alloy, including an outer multi-level pore layer, a middle dense layer, and an inner high-porosity core layer. Combined with alkaline heat treatment, a bone-like structure is formed, which enhances bone integration capacity and antibacterial properties.
It achieves a match between the elastic modulus and human bone tissue, enhances bone cell adhesion and ingrowth, reduces the risk of infection, and satisfies the multi-functional synergistic effect of mechanical compatibility and antibacterial properties.
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Figure CN122076992A_ABST
Abstract
Description
Technical Field
[0001] This invention relates to the field of biomedical materials technology, and in particular to a method for preparing a bone-like multifunctional medical titanium alloy. Background Technology
[0002] The clinical demand for biomedical implants continues to grow. Medical titanium alloys, due to their excellent mechanical properties, corrosion resistance, and biocompatibility, are currently the mainstream material for hard tissue repair implants. Among them, TC4 (Ti6Al4V) is a medium-strength (α+β) type biphase titanium alloy containing 6% α-stabilizing element Al and 4% β-stabilizing element V, and is most widely used in artificial joints, dental implants, and bone trauma repair products.
[0003] However, traditional titanium alloy implants have revealed many technical shortcomings in long-term clinical use: Firstly, the problem of elastic modulus mismatch is prominent. The elastic modulus of Ti6Al4V alloy is about 110 GPa, which is much higher than that of human cancellous bone (1.5~4.0 GPa) and cortical bone (10~30 GPa). Due to insufficient stress over a long period of time, the bone tissue is absorbed and atrophies, which eventually leads to loosening and detachment of the implant. Secondly, the osseointegration capacity is limited. The surface of traditional titanium alloys is mostly dense and lacks porous structures that facilitate the adhesion, proliferation and ingrowth of osteocytes, resulting in insufficient bonding strength between the implant and the host bone tissue. Third, it lacks antibacterial properties. During the implantation procedure and postoperative recovery, bacteria can easily grow on the surface of the implant, leading to infectious complications.
[0004] Existing technologies often employ surface modification or porous structure designs. For example, calcification and phosphorylation modifications are used to improve the surface of titanium alloys through acid etching and hydrothermal reactions to enhance bioactivity. However, these methods only improve surface properties and cannot solve the problems of elastic modulus mismatch and overall antibacterial properties. Furthermore, adding pore-forming agents to prepare porous titanium alloys can reduce the elastic modulus, but a single porous structure cannot simultaneously achieve both mechanical load-bearing capacity and osseointegration effects.
[0005] Therefore, developing a method for preparing a multifunctional medical titanium alloy with a bone-like structure, and preparing a multifunctional medical titanium alloy that combines bone-like mechanical properties, bone integration ability, and antibacterial properties, has become a technical problem that urgently needs to be solved in this field. Summary of the Invention
[0006] The purpose of this invention is to provide a method for preparing a bone-like multifunctional medical titanium alloy. By compounding Ti6Al4V5Cu alloy powder and Ti6Al4V alloy powder, the elastic modulus of the product can be precisely controlled to avoid the problem of elastic modulus mismatch.
[0007] To achieve the above objectives, this invention provides a method for preparing a bone-like multifunctional medical titanium alloy, comprising the following steps: S1. Raw material pretreatment: Titanium alloy powder and bioceramic powder are mechanically mixed to obtain composite powder; the titanium alloy powder is selected from Ti6Al4V5Cu alloy powder or Ti6Al4V alloy powder. The Ti6Al4V5Cu alloy powder is prepared by electrode induction melting and inert gas atomization to obtain spherical Ti6Al4V5Cu alloy powder with a particle size of 15~20μm. The Ti6Al4V alloy powder is prepared by ball milling to obtain pointed Ti6Al4V alloy powder with a particle size of 50~53μm; the bioceramic powder is hydroxyapatite (HA) or β-tricalcium phosphate (β-TCP) powder, and the particle size of the bioceramic powder is ≤10μm. S2, Preparation of mixture a: The composite powder obtained in S1 is mixed with the pore-forming agent at a mass ratio of 12~16:4~8 to obtain mixture a; S3, Preparation of mixture b: The composite powder obtained in S1 is mixed with liquid paraffin at a ratio of 4.86~5.67g:1mL, stirred evenly under heating at 30~40℃, and cooled to room temperature to obtain mixture b; S4. Preparation of mixture c: The composite powder obtained in S1 is mixed with the pore-forming agent at a mass ratio of 10~13:7~10 to obtain mixture c; S5. Layered pressing molding: The mixture a obtained in S2 is loaded into the mold and the powder is compressed into the required shape and size by the press. Then, the mixture b obtained in S3 and the mixture c obtained in S4 are filled in sequence to form an outer layer-middle layer-inner core layer structure. The mixture is compacted at the same time and the pressure is held for 20~40 minutes before demolding to obtain the green blank. S6. Vacuum thermal degreasing: The green body obtained in S5 is placed in a vacuum sintering furnace and degreasing and high-temperature sintering are carried out in sequence, followed by programmed cooling to obtain the implant. S7. Alkali heat treatment: The implant obtained in S6 is placed in a 5-10M NaOH solution and soaked at 60-80℃ for 12-24 hours. After cleaning, it is then heat-treated at 600-700℃ for 0.5-2 hours to obtain a bone-like multifunctional medical titanium alloy.
[0008] Preferably, in S1, the mass ratio of titanium alloy powder to bioceramic powder is 1:0.6~1.5.
[0009] Preferably, in S2 and S4, the pore-forming agent is ammonium bicarbonate or urea.
[0010] Preferably, in S2, the composite powder is a mixture of Ti6Al4V alloy powder and bioceramic powder.
[0011] Preferably, in S4, the composite powder is a mixture of Ti6Al4V5Cu alloy powder and bioceramic powder.
[0012] Preferably, in S5, the pressure is increased to 20-50 MPa by a press at a rate of 1-3 kN / s, and the compaction pressure is 200-400 MPa.
[0013] Preferably, in S5, the thickness ratio of the outer layer, the middle layer, and the inner core layer of the outer layer-middle layer-inner core layer structure is 2~3:4~5:3.
[0014] Preferably, S6 is as follows: Under a vacuum of 10-25 Pa and an argon atmosphere, the temperature is increased to 200-300℃ at a rate of 2-5℃ / min and held for 1-3 hours. Then, the temperature is increased to 1100-1250℃ at a rate of 5-10℃ / min and held for 2-4 hours. Finally, the temperature is cooled to room temperature at a rate of 2-5℃ / min.
[0015] Preferably, in S7, after heat treatment, the temperature is cooled to room temperature, specifically as follows: Cool to 150-250°C at a rate of 70-90°C / min, then cool to room temperature with the furnace.
[0016] Preferably, in S7, the outer layer of the bone-like multifunctional medical titanium alloy has a multi-level porous structure with a porosity of 50-65%, the middle layer has a dense structure with a porosity of less than 10%, and the inner core layer has a multi-level porous structure with a porosity of 60-75%. The multi-level porous structure includes macropores and micropores, with macropores having a diameter of 100-600 μm and micropores having a diameter of less than 50 μm.
[0017] Therefore, the present invention employs the above-mentioned method for preparing a bone-like multifunctional medical titanium alloy, and the beneficial effects are as follows: The outer layer of this invention uses angular Ti6Al4V powder with a particle size of 50~53μm, which enhances the mechanical stability of the porous structure by relying on the interlocking effect between particles; the middle layer uses a particle size matching the design without pore-forming agents, and forms a dense layer after sintering to ensure a compressive strength of ≥610MPa; the inner core uses spherical Ti6Al4V5Cu powder, combined with a high proportion of pore-forming agents, to achieve a porosity of 60~70% to release stress, precisely control the elastic modulus to match human bone tissue (1.5~30GPa), avoid stress shielding effect, improve bone integration capacity, and meet the multi-functional synergy of mechanical compatibility, osteoconductivity and antibacterial properties.
[0018] This invention forms a bone-like biomimetic structure with porous outer and inner layers and a dense middle layer. The outer layer, combined with bioceramic powder, directly contacts bone tissue. By controlling the porosity and thickness, bone cells can adhere and grow into the bone smoothly. The middle layer, as the core mechanical load-bearing layer, has the highest thickness and ensures compressive strength. The inner core helps release stress while facilitating nutrient penetration and metabolic waste removal, reducing the risk of postoperative infection. Furthermore, Cu ions can destroy bacterial cell membranes and inhibit bacterial metabolism, further reducing the risk of postoperative infection.
[0019] The technical solution of the present invention will be further described in detail below with reference to the accompanying drawings and embodiments. Attached Figure Description
[0020] Figure 1 This is a graph showing the elastic modulus results of an embodiment of the preparation method of a bone-like multifunctional medical titanium alloy of the present invention; Figure 2 This is a diagram showing the compressive strength results of an embodiment of the preparation method of a bone-like multifunctional medical titanium alloy according to the present invention. Detailed Implementation
[0021] The technical solution of the present invention will be further described below with reference to the accompanying drawings and embodiments.
[0022] Unless otherwise defined, the technical or scientific terms used in this invention shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention pertains.
[0023] Example 1 A method for preparing a bone-like multifunctional medical titanium alloy for use in load-bearing implants (such as artificial hip joint stems) includes the following steps: S1. Raw Material Pretreatment: Titanium alloy powder and bioceramic powder are mechanically mixed to obtain composite powder. Spherical Ti6Al4V5Cu alloy powder and pointed Ti6Al4V alloy powder are selected. The Ti6Al4V5Cu alloy powder is prepared by electrode induction melting and inert gas atomization, with a particle size of 15~18μm (chemical composition: Al 6.0wt.%, V 4.0wt.%, Cu 5.0wt.%, Fe 0.20wt.%, C 0.06wt.%, N 0.02wt.%, H 0.006wt.%, O 0.10wt.%, balance Ti). The Ti6Al4V alloy powder is prepared by ball milling, with a particle size of 50~52μm (chemical composition: Al 6.2wt.%, V 4.0wt.%, Fe 0.25wt.%, C 0.06wt.%, N 0.04wt.%, H 0.012wt.%, O 0.15 wt.%, balance Ti).
[0024] S2. Mixture preparation: 1. Take 30g of Ti6Al4V alloy powder and 35g of HA powder, mix them evenly, add 35g of NH4HCO3 pore-forming agent (particle size 300~400μm, analytical grade), mix well, and obtain mixture a; 2. Take 50g of Ti6Al4V5Cu alloy powder and 50g of HA powder, mix them evenly, add 20ml of liquid paraffin, stir and mix evenly under heating at 35℃, and cool to room temperature to obtain mixture b; 3. Take 20g of Ti6Al4V5Cu alloy powder and 30g of HA powder, mix them evenly, add 50g of NH4HCO3 pore-forming agent, mix well, and obtain mixture c.
[0025] S3. Layered pressing molding: Apply petroleum jelly to the inner wall of the mold, load mixture a (outer layer) into the mold and compress the powder into the required shape and size using a press. Apply pressure at a rate of 2kN / s to 50kN, then sequentially fill mixture b (middle layer) and mixture c (inner core layer) to form an outer layer-middle layer-inner core layer structure. During the filling process, continuously hammer and compact the material at a pressure of 300MPa. After holding the pressure for 30 minutes, remove the mold. The thickness ratio of the outer layer, middle layer, and inner core layer is 2:5:3 to obtain the green blank.
[0026] S4. Vacuum thermal degreasing: The green body is placed in a vacuum sintering furnace with the vacuum degree controlled at 15 Pa. Argon gas (purity 99.99%) is continuously introduced and heated to 240°C at a rate of 5°C / min. The temperature is held for 3 hours, then heated to 1200°C at a rate of 5°C / min and held for 4 hours. The temperature is then lowered to room temperature at a rate of 5°C / min. The body is then removed to obtain the implant.
[0027] S5. Alkali heat treatment: The implant is placed in an 8M NaOH solution and soaked at 70℃ for 18 hours. After cleaning, it is heat-treated at 650℃ for 1 hour. After heat treatment, it is cooled to 200℃ at 80℃ / min and then cooled to room temperature in the furnace to obtain a bone-like multifunctional medical titanium alloy.
[0028] Testing revealed that the titanium alloy prepared in this embodiment has an outer layer porosity of 60%, an inner core porosity of 68%, an elastic modulus of 10.5 GPa, a compressive strength of 630 MPa, and an antibacterial rate of ≥99.0% against Escherichia coli.
[0029] Example 2 A method for preparing a bone-like multifunctional medical titanium alloy for use in load-bearing implants (such as artificial hip joint stems) differs from Example 1 in that: S2. Mixture preparation: 1. Take 35g of Ti6Al4V alloy powder and 35g of HA powder, mix them evenly, add 30g of NH4HCO3 pore-forming agent (particle size 300~400μm, analytical grade), mix well, and obtain mixture a; 2. Take 50g of Ti6Al4V5Cu alloy powder and 50g of HA powder, mix them evenly, add 19ml of liquid paraffin, stir and mix evenly under heating at 35℃, and cool to room temperature to obtain mixture b; 3. Take 25g of Ti6Al4V5Cu alloy powder and 30g of HA powder, mix them evenly, add 45g of NH4HCO3 pore-forming agent, mix well, and obtain mixture c.
[0030] The remaining steps are exactly the same as in Example 1.
[0031] Testing revealed that the titanium alloy prepared in this embodiment has an outer layer porosity of 58%, an inner core porosity of 60%, an elastic modulus of 11.2 GPa, a compressive strength of 620 MPa, and an antibacterial rate of ≥99.5% against Staphylococcus aureus.
[0032] Example 3 A method for preparing a bone-like multifunctional medical titanium alloy for use in non-load-bearing implants (such as cranial repair scaffolds) differs from Example 1 in that: S2. Mixture preparation: 1. Take 35g of Ti6Al4V alloy powder and 40g of HA powder, mix them evenly, add 25g of NH4HCO3 pore-forming agent (particle size 300~400μm, analytical grade), mix well, and obtain mixture a; 2. Take 50g of Ti6Al4V5Cu alloy powder and 50g of HA powder, mix them evenly, add 18ml of liquid paraffin, stir and mix evenly under heating at 35℃, and cool to room temperature to obtain mixture b; 3. Take 30g of Ti6Al4V5Cu alloy powder and 35g of HA powder, mix them evenly, add 35g of NH4HCO3 pore-forming agent, mix well, and obtain mixture c.
[0033] The remaining steps are exactly the same as in Example 1.
[0034] Testing revealed that the titanium alloy prepared in this embodiment has an outer layer porosity of 58%, an inner core porosity of 60%, an elastic modulus of 15.9 GPa, a compressive strength of 610 MPa, and an antibacterial rate of ≥98.5% against Staphylococcus aureus.
[0035] Example 4 A method for preparing a bone-like multifunctional medical titanium alloy for use in non-load-bearing implants (such as cranial repair scaffolds) differs from Example 1 in that: S3. Layered pressing molding: Apply petroleum jelly to the inner wall of the mold, load mixture a (outer layer) into the mold and compress the powder into the required shape and size using a press. Apply pressure at a rate of 2kN / s to 50kN, then sequentially fill mixture b (middle layer) and mixture c (inner core layer) to form an outer layer-middle layer-inner core layer structure. During the filling process, continuously hammer and compact the material at a pressure of 400MPa. After holding the pressure for 30 minutes, remove the mold. The thickness ratio of the outer layer, middle layer, and inner core layer is 3:4:3 to obtain the green blank.
[0036] The remaining steps are exactly the same as in Example 1.
[0037] Testing revealed that the titanium alloy prepared in this embodiment has an outer layer porosity of 55%, an inner core porosity of 60%, an elastic modulus of 18.4 GPa, a compressive strength of 610 MPa, and an antibacterial rate of ≥98.5% against Staphylococcus aureus.
[0038] Comparative Example 1 A conventional Ti6Al4V alloy has the following chemical composition: Al 6.2wt.%, V 4.0wt.%, Fe 0.25wt.%, C 0.06wt.%, N 0.04wt.%, H 0.012wt.%, O 0.15wt.%, with the balance being Ti.
[0039] The titanium alloy in this comparative example has an elastic modulus of 115 GPa, a compressive strength of 910 MPa, and an antibacterial rate of ≤10.0% against Staphylococcus aureus, as tested.
[0040] Test 1. Osteocyte adhesion and bone tissue ingrowth depth were analyzed in Examples 1-3 and Comparative Example 1. The results are shown in Table 1.
[0041] Bone cell adhesion quantity assay: The sample was placed in a culture medium containing rat BMSCs (cell concentration 1×10⁻⁶). 5 After culturing for 24 hours, the cells were stained with DAPI, and five fields of view were randomly selected under a 200× fluorescence microscope for counting. The average value was then taken.
[0042] Bone ingrowth depth test: The sample was implanted into the femoral condyle defect of New Zealand white rabbits (defect diameter 4mm, depth 6mm). After 12 weeks, bone tissue was taken from the implantation site, decalcified, paraffin embedded, sectioned (5μm), and stained with HE. The maximum depth of bone tissue ingrowth from the sample surface into the interior was measured under an optical microscope, and the average value of 3 experimental animals was taken.
[0043] Table 1. Data on osteoblast adhesion and bone ingrowth depth
[0044] As shown in Table 1, the traditional Ti6Al4V alloy has a dense structure with extremely low porosity, which cannot provide space for osteocyte adhesion, proliferation, and ingrowth, resulting in poor osteointegration. Example 1 showed a 40% improvement in osteocyte adhesion compared to the traditional Ti6Al4V alloy, exhibiting the best adhesion ability. Examples 2 and 3 showed slightly reduced adhesion numbers, but still significantly higher than the traditional alloy. Furthermore, Example 1 showed a 275% increase in bone ingrowth depth compared to the traditional Ti6Al4V alloy, and Example 2 showed a 35% increase. This indicates that high porosity improves bone ingrowth, but excessive porosity can lead to decreased mechanical properties. The gradient porosity structure of Example 2 ensures both osteocyte adhesion on the material surface (outer layer porosity) and provides a smooth channel for bone tissue ingrowth, while simultaneously meeting the mechanical requirements of load-bearing implants (such as artificial hip joint stems).
[0045] 2. Mechanical property analysis was performed on Examples 1, 3-4, and Comparative Example 1. The elastic modulus results are as follows: Figure 1 As shown, the compressive strength results are as follows: Figure 2 As shown.
[0046] Depend on Figures 1-2 It is evident that, to further clarify the mechanical compatibility of multifunctional medical titanium alloys with bone-like structures under different implantation scenarios, Comparative Example 1 (traditional Ti6Al4V alloy) has an elastic modulus as high as 115 GPa, far exceeding the elastic modulus of human cortical bone (10~30 GPa). After implantation, it is prone to "stress shielding effect," leading to absorption and atrophy of surrounding bone tissue, resulting in poor long-term implantation stability. Example 1 (for load-bearing implants) has an elastic modulus of 10.5 GPa, perfectly matching the range of human bone elastic modulus, effectively avoiding the stress shielding effect. Examples 3 and 4 (for non-load-bearing implants) have elastic moduli of 15.9 GPa and 18.4 GPa, respectively, also within the range of human bone elastic modulus, balancing mechanical support and biocompatibility. Furthermore, Examples 3 and 4 have a compressive strength of 610 MPa, lower than Example 1, meeting the mechanical requirements of non-load-bearing implants such as cranioplasty scaffolds, and providing another process option for non-load-bearing implants.
[0047] Therefore, the present invention adopts the above-mentioned preparation method of a bone-like structure multifunctional medical titanium alloy, and precisely controls the elastic modulus of the product by compounding Ti6Al4V5Cu alloy powder and Ti6Al4V alloy powder to avoid the problem of elastic modulus mismatch.
[0048] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit them. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can still be made to the technical solutions of the present invention, and these modifications or equivalent substitutions cannot cause the modified technical solutions to deviate from the spirit and scope of the technical solutions of the present invention.
Claims
1. A method for preparing a bone-like multifunctional medical titanium alloy, characterized in that, Includes the following steps: S1. Raw material pretreatment: Titanium alloy powder and bioceramic powder are mechanically mixed to obtain composite powder; the titanium alloy powder is selected from Ti6Al4V5Cu alloy powder or Ti6Al4V alloy powder. The Ti6Al4V5Cu alloy powder is prepared by electrode induction melting and inert gas atomization to obtain spherical Ti6Al4V5Cu alloy powder with a particle size of 15~20μm. The Ti6Al4V alloy powder is prepared by ball milling to obtain pointed Ti6Al4V alloy powder with a particle size of 50~53μm; the bioceramic powder is hydroxyapatite or β-tricalcium phosphate powder, and the particle size of the bioceramic powder is ≤10μm. S2, Preparation of mixture a: The composite powder obtained in S1 is mixed with the pore-forming agent at a mass ratio of 12~16:4~8 to obtain mixture a; S3, Preparation of mixture b: The composite powder obtained in S1 is mixed with liquid paraffin at a ratio of 4.86~5.67g:1mL, stirred evenly under heating at 30~40℃, and cooled to room temperature to obtain mixture b; S4. Preparation of mixture c: The composite powder obtained in S1 is mixed with the pore-forming agent at a mass ratio of 10~13:7~10 to obtain mixture c; S5. Layered pressing molding: The mixture a obtained in S2 is loaded into the mold and the powder is compressed into the required shape and size by the press. Then, the mixture b obtained in S3 and the mixture c obtained in S4 are filled in sequence to form an outer layer-middle layer-inner core layer structure. The mixture is compacted at the same time and the pressure is held for 20~40 minutes before demolding to obtain the green blank. S6. Vacuum thermal degreasing: The green body obtained in S5 is placed in a vacuum sintering furnace and degreasing and high-temperature sintering are carried out in sequence, followed by programmed cooling to obtain the implant. S7. Alkali heat treatment: The implant obtained in S6 is placed in a 5-10M NaOH solution and soaked at 60-80℃ for 12-24 hours. After cleaning, it is then heat-treated at 600-700℃ for 0.5-2 hours to obtain a bone-like multifunctional medical titanium alloy.
2. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S1, the mass ratio of titanium alloy powder to bioceramic powder is 1:0.6~1.
5.
3. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S2 and S4, the pore-forming agent is ammonium bicarbonate or urea.
4. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S2, the composite powder is a mixture of Ti6Al4V alloy powder and bioceramic powder.
5. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S4, the composite powder is a mixture of Ti6Al4V5Cu alloy powder and bioceramic powder.
6. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S5, the press increases the pressure to 20-50 MPa at a rate of 1-3 kN / s, and the compaction pressure is 200-400 MPa.
7. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S5, the thickness ratio of the outer layer, intermediate layer, and inner core layer in the outer layer-intermediate layer-inner core layer structure is 2~3:4~5:
3.
8. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, S6 specifically refers to: Under a vacuum of 10-25 Pa and an argon atmosphere, the temperature is increased to 200-300℃ at a rate of 2-5℃ / min and held for 1-3 hours. Then, the temperature is increased to 1100-1250℃ at a rate of 5-10℃ / min and held for 2-4 hours. Finally, the temperature is cooled to room temperature at a rate of 2-5℃ / min.
9. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S7, after heat treatment, the material is cooled to room temperature, specifically as follows: Cool to 150-250°C at a rate of 70-90°C / min, then cool to room temperature with the furnace.
10. The method for preparing a bone-like multifunctional medical titanium alloy according to claim 1, characterized in that, In S7, the outer layer of the bone-like multifunctional medical titanium alloy has a multi-level porous structure with a porosity of 50-65%, the middle layer has a dense structure with a porosity of less than 10%, and the inner core layer has a multi-level porous structure with a porosity of 60-75%. The multi-level porous structure includes macropores and micropores, with macropores having a diameter of 100-600 μm and micropores having a diameter of less than 50 μm.