Dental implant material, method for preparing the same and use thereof

Abstract

This invention provides a dental implant material, its preparation method, and its application, relating to the field of biomedical materials technology. The preparation method of the dental implant material includes: mixing α-silicon nitride powder, a sintering aid, and a pore-forming agent, followed by ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic framework; placing the porous silicon nitride ceramic framework in molten ZK60 magnesium alloy for gas pressure infiltration, and cooling to room temperature to obtain a bicontinuous phase composite material; subjecting the bicontinuous phase composite material to a first heat treatment followed by water quenching to obtain a preform; subjecting the preform to a second heat treatment and air cooling to room temperature to obtain the dental implant material. The dental implant material prepared using this method exhibits superior corrosion resistance, dynamic stability, impact resistance, biocompatibility, and an elastic modulus matching alveolar bone tissue.

Description

Technical Field

[0001] This invention relates to the field of biomedical materials technology, and more specifically, to a dental implant material, its preparation method, and its application. Background Technology

[0002] Dental implant restoration has become the gold standard for treating missing teeth, with millions of implant surgeries performed globally each year. Although modern dental implants have high clinical success rates under static loads, mechanical complications under dynamic functional loads and accidental impacts (such as biting hard objects, sports injuries, falls, etc.) still pose significant clinical challenges. The oral environment is a complex biomechanical system, and implants must withstand various dynamic loading modes, including cyclic masticatory forces, occlusal overloads, and impact loads. These loads can induce significant stress concentration at the implant-bone interface, leading to marginal bone resorption, implant loosening, and even catastrophic fracture of the superstructure or the implant itself. Therefore, the dynamic stability and impact resistance of dental implant materials have become key factors determining long-term clinical success.

[0003] Currently, commercially available pure titanium (cp-Ti) and Ti-6Al-4V alloys dominate dental implants due to their excellent biocompatibility, corrosion resistance, and osseointegration properties. However, the elastic modulus of titanium alloys (approximately 110 GPa) differs significantly from that of human bone (15 GPa to 20 GPa), easily leading to stress shielding effects, resulting in bone resorption and decreased long-term stability. While ceramic implants, represented by zirconia (Y-TZP), offer good aesthetics and biocompatibility, their inherent brittleness and low fracture toughness make them highly susceptible to spalling, crack propagation, and even catastrophic fracture under impact loads. Polyetheretherketone (PEEK) and its composites, although having a lower modulus and better stress distribution, suffer from insufficient strength and wear resistance. Magnesium and its alloys, as biodegradable biometals, have the advantage of an elastic modulus closer to that of human bone, but their mechanical strength is insufficient and they corrode too quickly in the oral cavity environment. Therefore, how to obtain dental implant materials with better corrosion resistance, better dynamic stability, better impact resistance, better biocompatibility, and an elastic modulus that matches alveolar bone tissue has become an urgent technical problem to be solved. Summary of the Invention

[0004] The problem solved by this invention is: how to obtain dental implant materials with better corrosion resistance, better dynamic stability, better impact resistance, better biocompatibility, and an elastic modulus that matches alveolar bone tissue.

[0005] To address the above problems, the present invention provides a method for preparing a dental implant material, comprising: Step S1: After mixing α-silicon nitride powder, sintering aid, and pore-forming agent, the mixture is subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic skeleton. Step S2: The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material. Step S3: After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain the preform; wherein the temperature of the first heat treatment is 510℃ to 520℃ and the time is 1.5h to 2.5h. Step S4: The preform is subjected to a second heat treatment and air-cooled to room temperature to obtain a dental implant material; wherein the temperature of the second heat treatment is 155°C to 165°C and the time is 22h to 26h.

[0006] Optionally, in step S2, before placing the porous silicon nitride ceramic skeleton in the molten ZK60 magnesium alloy for gas pressure infiltration, a Ti layer is deposited on the surface of the porous silicon nitride ceramic skeleton; the thickness of the Ti layer is 1.5 μm to 2.5 μm.

[0007] Optionally, in step S1, the mass ratio of the α-silicon nitride powder, the sintering aid, and the pore-forming agent is (92 to 94): (5 to 8): (10 to 90).

[0008] Optionally, in step S1, the sintering aid includes rare earth oxides and alumina; the pore-forming agent includes at least one of starch, graphite and PMMA microspheres.

[0009] Optionally, in step S1, the ball milling process uses alcohol as the milling medium, the ball milling speed is 100 rpm to 200 rpm, and the time is 10 h to 14 h.

[0010] Optionally, in step S1, the pressure of the pressing is 10 MPa to 50 MPa; the temperature of the degreasing treatment is 550°C to 650°C, and the time is 1 hour to 2 hours.

[0011] Optionally, in step S1, the sintering process is carried out under a nitrogen atmosphere, and the sintering temperature is 1700°C to 1800°C for 2 hours to 3 hours.

[0012] Optionally, in step S2, the temperature of the gas pressure infiltration is 650°C to 720°C, the pressure is 1MPa to 4MPa, and the time is 20min to 40min.

[0013] The present invention also provides a dental implant material, which is prepared using the dental implant material preparation method described above.

[0014] The present invention also provides the application of the dental implant materials described above in the preparation of artificial tooth roots and artificial tooth crowns.

[0015] Compared with related technologies, this invention uses α-silicon nitride powder, sintering aids, and pore-forming agents as raw materials to prepare a porous silicon nitride ceramic framework. This retains the excellent corrosion resistance of silicon nitride ceramics while forming a bicontinuous phase structure through pressure infiltration with molten ZK60 magnesium alloy. Combined with two specific heat treatment processes, the material exhibits both a low elastic modulus (matching the elastic modulus of alveolar bone tissue) and good toughness. This significantly improves dynamic stability and impact resistance, and optimizes surface bioactivity through the synergistic effect of the biphase, effectively promoting cell proliferation and bone integration. Furthermore, the porous structure and the controllable degradation characteristics of the magnesium alloy further reduce the corrosion rate, achieving a precise balance between corrosion resistance, mechanical properties, and biocompatibility. In summary, the dental implant material prepared using the method of this invention possesses superior corrosion resistance, dynamic stability, impact resistance, biocompatibility, and an elastic modulus matching that of alveolar bone tissue. The application of this dental implant material in artificial tooth roots and crowns not only solves the inherent defects of traditional titanium alloys such as excessively high elastic modulus, magnesium alloys such as excessively rapid degradation, and ceramics such as fragility, but also achieves synergistic optimization of mechanical adaptability, bioactivity and durability, and has significant clinical application value and market prospects. Attached Figure Description

[0016] Figure 1 The images show the fracture morphology of the dental implant material prepared in Example 2 of this invention after being subjected to loads at different strain rates. Detailed Implementation

[0017] To make the above-mentioned objects, features, and advantages of the present invention more apparent and understandable, specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings. Although some embodiments of the present invention are shown in the drawings, it should be understood that the present invention can be implemented in various forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided to provide a more thorough and complete understanding of the present invention. It should be understood that the accompanying drawings and embodiments of the present invention are for illustrative purposes only and are not intended to limit the scope of protection of the present invention.

[0018] Unless otherwise defined, all technical and scientific terms used in this invention have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention.

[0019] The term "comprising" and its variations as used herein are open-ended, meaning "including but not limited to"; the term "based on" means "at least partially based on"; the term "one embodiment" means "at least one embodiment"; the term "another embodiment" means "at least one additional embodiment"; the term "some embodiments" means "at least some embodiments"; and the term "optionally" means "optional embodiments". Definitions of other terms will be given in the following description. It should be noted that the concepts of "first," "second," etc., mentioned in this invention are used to distinguish different objects, not to describe a specific order or hierarchy. Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Thus, a feature defined with "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this invention, unless otherwise stated, "a plurality of" means two or more.

[0020] This invention provides a method for preparing a dental implant material, comprising: Step S1: After mixing α-silicon nitride powder, sintering aid, and pore-forming agent, the mixture is subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic skeleton. Step S2: The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material. Step S3: After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain the preform; wherein the temperature of the first heat treatment is 510℃ to 520℃ and the time is 1.5h to 2.5h. Step S4: The preform is subjected to a second heat treatment and air-cooled to room temperature to obtain a dental implant material; wherein the temperature of the second heat treatment is 155°C to 165°C and the time is 22h to 26h.

[0021] This invention utilizes α-silicon nitride powder, sintering aids, and pore-forming agents to fabricate a porous silicon nitride ceramic framework. This framework retains the excellent corrosion resistance of silicon nitride ceramics while forming a bicontinuous phase structure through pressure infiltration with molten ZK60 magnesium alloy. Combined with two specific heat treatment processes, the material exhibits both a low elastic modulus (matching the elastic modulus of alveolar bone tissue) and excellent toughness. This significantly improves dynamic stability and impact resistance, and optimizes surface bioactivity through the synergistic effect of the biphase structure, effectively promoting cell proliferation and osseointegration. Furthermore, the porous structure and the controllable degradation characteristics of the magnesium alloy further reduce the corrosion rate, achieving a precise balance between corrosion resistance, mechanical properties, and biocompatibility. In summary, the dental implant material prepared using the method of this invention possesses superior corrosion resistance, dynamic stability, impact resistance, biocompatibility, and an elastic modulus matching that of alveolar bone tissue.

[0022] In some embodiments of the present invention, preferably, in step S2, before placing the porous silicon nitride ceramic skeleton in molten ZK60 magnesium alloy for gas pressure infiltration, a Ti layer is deposited on the surface of the porous silicon nitride ceramic skeleton; the thickness of the Ti layer is 1.5 μm to 2.5 μm. In this embodiment, after depositing a 1.5 μm to 2.5 μm Ti layer on the surface of the porous silicon nitride ceramic skeleton, when gas pressure infiltration of the molten ZK60 magnesium alloy is performed, the Ti layer can undergo a slight interfacial reaction with the magnesium alloy, forming a Mg-Ti intermetallic compound or a Ti-Si-N diffusion layer. These reaction products, as a "transition layer," effectively alleviate the residual stress caused by the difference in thermal expansion coefficients between the ceramic and the metal, and enhance the chemical bonding and mechanical interlocking force between the two phases. The Ti layer itself has a certain degree of plasticity and can absorb some energy under dynamic compressive loads (such as chewing impacts), inhibiting the rapid propagation of cracks at the ceramic / metal interface, thereby improving the fracture toughness of the interface. Meanwhile, this transition layer allows for a more uniform distribution of stress within the bicontinuous phase structure, preventing localized stress concentrations and further enhancing the overall dynamic compressive strength of the material. This modification process not only optimizes the interfacial microstructure but also strengthens the synergistic load-bearing capacity between porous silicon nitride and ZK60 magnesium alloy, making dental implant materials more fatigue-resistant and impact-resistant in complex oral mechanical environments, significantly improving long-term service stability.

[0023] In some embodiments of the present invention, in step S1, the mass ratio of the α-silicon nitride powder, the sintering aid, and the pore-forming agent is (92 to 94): (5 to 8): (10 to 90).

[0024] In some embodiments of the present invention, in step S1, the sintering aid includes rare earth oxides and alumina; the pore-forming agent includes at least one of starch, graphite and PMMA microspheres.

[0025] In some embodiments of the present invention, in step S1, the ball milling process uses alcohol as the ball milling medium, the ball milling speed is 100 rpm to 200 rpm, and the time is 10 h to 14 h.

[0026] In some embodiments of the present invention, in step S1, the pressure of the pressing molding is 10 MPa to 50 MPa.

[0027] In some embodiments of the present invention, in step S1, the degreasing treatment is carried out at a temperature of 550°C to 650°C for a time of 1 hour to 2 hours.

[0028] In some embodiments of the present invention, in step S1, the sintering process is carried out under a nitrogen atmosphere, the temperature of the sintering process is 1700°C to 1800°C, and the time is 2h to 3h.

[0029] In some embodiments of the present invention, in step S2, the temperature of the gas pressure infiltration is 650°C to 720°C, the pressure is 1 MPa to 4 MPa, and the time is 20 min to 40 min.

[0030] This invention also provides a dental implant material, which is prepared using the dental implant material preparation method described above.

[0031] The embodiments of the present invention also provide the application of the dental implant materials described above in the preparation of artificial tooth roots and artificial tooth crowns.

[0032] The dental implant materials provided in this invention, when used in artificial tooth roots and crowns, not only solve the inherent defects of traditional titanium alloys (too high elastic modulus), magnesium alloys (too fast degradation), and ceramics (fragile), but also achieve synergistic optimization of mechanical adaptability, bioactivity, and durability, possessing significant clinical application value and market prospects.

[0033] The present invention will be further described below with reference to specific embodiments.

[0034] Example 1 A1. Alpha-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres are mixed and then subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic framework. The particle size of the α-silicon nitride powder is 0.5 μm, the particle size of the PMMA microspheres is 150 μm, and the mass ratio of the α-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres is 93.46:4.67:1.87:84.3. The ball milling process uses alcohol as the milling medium, operates at 150 rpm, and lasts for 12 hours. The pressing pressure is 30 MPa. The degreasing temperature is 600°C, and the time is 1.5 hours. The sintering process is carried out under a nitrogen atmosphere at 1750°C for 2 hours.

[0035] A2. The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material; the gas pressure infiltration temperature is 720℃, the pressure is 4MPa, and the time is 30min.

[0036] A3. After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain a preform; wherein the temperature of the first heat treatment is 515℃ and the time is 2h.

[0037] A4. The preform is subjected to a second heat treatment and then air-cooled to room temperature to obtain a dental implant material; wherein the temperature of the second heat treatment is 160°C and the time is 24 hours. Testing revealed that the volume fraction of the silicon nitride ceramic phase in the dental implant material obtained in this embodiment is 30%, and the volume fraction of the magnesium alloy phase is 70%.

[0038] Example 2 A1. Alpha-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres are mixed and then subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic framework. The particle size of the α-silicon nitride powder is 0.5 μm, the particle size of the PMMA microspheres is 150 μm, and the mass ratio of the α-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres is 93.46:4.67:1.87:36.1. The ball milling process uses alcohol as the milling medium, operates at 200 rpm, and lasts for 10 hours. The pressing pressure is 30 MPa. The degreasing temperature is 550°C, and the time is 2 hours. The sintering process is carried out under a nitrogen atmosphere at 1800°C for 2 hours.

[0039] A2. The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material; the gas pressure infiltration temperature is 720℃, the pressure is 4MPa, and the time is 30min.

[0040] A3. After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain a preform; wherein the temperature of the first heat treatment is 520℃ and the time is 1.5h.

[0041] A4. The preform undergoes a second heat treatment and is then air-cooled to room temperature to obtain a dental implant material; wherein the second heat treatment is performed at a temperature of 165°C for 22 hours. Testing revealed that the dental implant material obtained in this embodiment contains 50% silicon nitride ceramic phase and 50% magnesium alloy phase by volume.

[0042] Example 3 A1. Alpha-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres are mixed and then subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic framework. The particle size of the α-silicon nitride powder is 0.5 μm, the particle size of the PMMA microspheres is 150 μm, and the mass ratio of the α-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres is 93.46:4.67:1.87:15.5. The ball milling process uses alcohol as the milling medium, operates at 100 rpm, and lasts for 14 hours. The pressing pressure is 30 MPa. The degreasing temperature is 650°C, and the time is 1 hour. The sintering process is carried out under a nitrogen atmosphere at 1700°C for 3 hours.

[0043] A2. The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material; the gas pressure infiltration temperature is 720℃, the pressure is 4MPa, and the time is 30min.

[0044] A3. After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain a preform; wherein the temperature of the first heat treatment is 510℃ and the time is 2.5h.

[0045] A4. The preform is subjected to a second heat treatment and then air-cooled to room temperature to obtain a dental implant material; wherein the temperature of the second heat treatment is 155°C and the time is 26 hours. Testing revealed that the volume fraction of the silicon nitride ceramic phase in the dental implant material obtained in this embodiment is 70%, and the volume fraction of the magnesium alloy phase is 30%.

[0046] Example 4 The difference from Example 2 is that step A2 is as follows: after depositing a Ti layer on the surface of the porous silicon nitride ceramic skeleton by magnetron sputtering, it is placed in a molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material; wherein, the thickness of the Ti layer is 2 μm, the gas pressure infiltration temperature is 720°C, the pressure is 4 MPa, and the time is 30 min.

[0047] Comparative Example 1 Alpha-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres were mixed and then subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic framework. The particle size of the α-silicon nitride powder was 0.5 μm, the particle size of the PMMA microspheres was 150 μm, and the mass ratio of the α-silicon nitride powder, yttrium oxide, alumina, and PMMA microspheres was 93.46:4.67:1.87:36.1. The ball milling process used alcohol as the milling medium at a speed of 200 rpm for 10 hours. The pressing pressure was 30 MPa. The degreasing temperature was 550°C for 2 hours. The sintering process was carried out under a nitrogen atmosphere at a temperature of 1800°C for 2 hours.

[0048] The porous silicon nitride ceramic framework was placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a dental implant material; the gas pressure infiltration temperature was 720℃, the pressure was 4MPa, and the time was 30min.

[0049] Effect Example Electron microscopy was used to characterize the fracture morphology of the dental implant material prepared in Example 2 after fracture under different strain rates. The results are shown in the figure. Figure 1 , Figure 1 Middle (a) to Figure 1 (c) shows the fracture morphology after fracture under quasi-static loading. Figure 1 Middle (a) to Figure 1 The strain rate in (c) is 0.001 s⁻¹. －1 0.01s －1 and 0.1s －1 ; Figure 1 Middle (d) to Figure 1 (f) shows the fracture morphology after fracture under dynamic impact loading; Figure 1 Middle (d) to Figure 1 The strain rates in (f) are 200 s⁻¹. －1 400s －1 and 600s －1 .

[0050] The quasi-static and dynamic impact properties of the dental implant materials prepared in Examples 2 to 4 and Comparative Example 1 were tested, and the results are shown in Table 1. Table 1 shows that the dynamic compressive strength of the dental implant materials prepared in Examples 2 to 4 is significantly higher than their quasi-static compressive strength, indicating that they not only meet the static mechanical requirements of normal chewing but also maintain structural stability under dynamic impact conditions. Compared with Comparative Example 1, the dental implant materials prepared in Examples 2 to 4 have higher dynamic compressive strength and energy absorption density, indicating better dynamic stability and impact resistance. Compared with Example 2, the dental implant material prepared in Example 4 has higher dynamic compressive strength and energy absorption density, indicating better dynamic stability and impact resistance. Furthermore, the elastic modulus of the dental implant materials prepared in Examples 2 to 4 is not significantly different from that of alveolar bone tissue, indicating good matching between their elastic moduli.

[0051] Table 1

[0052] It should be noted that the quasi-static compressive strength in Table 1 is calculated using a universal testing machine at a strain rate of 0.001 s⁻¹. －1 The dynamic compressive strength and energy absorption density in Table 1 were measured using the Split Hopkinson Bar (SHPB) test method at a strain rate of 600 s⁻¹. －1 The following measurements were taken.

[0053] The dental implant materials in Examples 2 to 4 and Comparative Example 1 were placed in simulated body fluid at 37°C to test their static corrosion rate. The results are shown in Table 2. Compared with Comparative Example 1, the static corrosion rate of the dental implant materials in Examples 2 to 4 was slower, indicating that the dental implant materials in Examples 2 to 4 have better corrosion resistance in simulated body fluid.

[0054] Table 2

[0055] MC3T3-E1 osteogenic progenitor cells were seeded onto the surfaces of dental implant materials in Example 2 and Comparative Example 1, respectively, and cultured in osteogenic induction medium. On day 3, the cell proliferation rate was detected. The results showed that, compared with Comparative Example 1, the cell proliferation rate of the corresponding MC3T3-E1 osteogenic progenitor cells in Example 2 increased by 76%, indicating that the dental implant material in Example 2 has good biocompatibility.

[0056] While the present invention has been disclosed above, its scope of protection is not limited thereto. Those skilled in the art can make various changes and modifications without departing from the spirit and scope of the present invention, and all such changes and modifications will fall within the scope of protection of the present invention.

Claims

1. A method for preparing a dental implant material, characterized in that, include: Step S1: After mixing α-silicon nitride powder, sintering aid, and pore-forming agent, the mixture is subjected to ball milling, pressing, degreasing, and sintering to obtain a porous silicon nitride ceramic skeleton. Step S2: The porous silicon nitride ceramic skeleton is placed in molten ZK60 magnesium alloy for gas pressure infiltration and cooled to room temperature to obtain a bicontinuous phase composite material. Step S3: After the first heat treatment of the bicontinuous phase composite material, water quenching is performed to obtain the preform; wherein the temperature of the first heat treatment is 510℃ to 520℃ and the time is 1.5h to 2.5h. Step S4: The preform is subjected to a second heat treatment and air-cooled to room temperature to obtain a dental implant material; wherein the temperature of the second heat treatment is 155°C to 165°C and the time is 22h to 26h.

2. The method for preparing dental implant material according to claim 1, characterized in that, In step S2, before the porous silicon nitride ceramic skeleton is placed in the molten ZK60 magnesium alloy for gas pressure infiltration, a Ti layer is deposited on the surface of the porous silicon nitride ceramic skeleton; the thickness of the Ti layer is 1.5 μm to 2.5 μm.

3. The method for preparing dental implant material according to claim 1, characterized in that, In step S1, the mass ratio of the α-silicon nitride powder, the sintering aid, and the pore-forming agent is (92 to 94): (5 to 8): (10 to 90).

4. The method for preparing dental implant material according to claim 1, characterized in that, In step S1, the sintering aid includes rare earth oxides and alumina; the pore-forming agent includes at least one of starch, graphite and PMMA microspheres.

5. The method for preparing dental implant material according to claim 1, characterized in that, In step S1, the ball milling process uses alcohol as the milling medium, and the ball milling speed is 100 rpm to 200 rpm for 10 h to 14 h.

6. The method for preparing dental implant material according to claim 1, characterized in that, In step S1, the pressure of the pressing is 10 MPa to 50 MPa; the temperature of the degreasing treatment is 550°C to 650°C, and the time is 1 hour to 2 hours.

7. The method for preparing dental implant material according to claim 1, characterized in that, In step S1, the sintering process is carried out under a nitrogen atmosphere, and the sintering temperature is 1700°C to 1800°C for 2 hours to 3 hours.

8. The method for preparing dental implant material according to claim 1, characterized in that, In step S2, the temperature of the gas pressure infiltration is 650°C to 720°C, the pressure is 1MPa to 4MPa, and the time is 20min to 40min.

9. A dental implant material, characterized in that, It is prepared using the method for preparing dental implant materials as described in any one of claims 1 to 8.

10. The application of the dental implant material as described in claim 9 in the preparation of artificial tooth roots and artificial crowns.

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