Zirconium-niobium alloy planting part and manufacturing method of zirconium-niobium alloy planting part

Abstract

The invention relates to the technical field of dental implants, in particular to a zirconium-niobium alloy implant and a manufacturing method of the zirconium-niobium alloy implant. The zirconium-niobium alloy implant comprises an implant and an abutment, connecting threads are arranged on the periphery of the implant; the outer surface layer of the implant is of a porous bone trabecula structure, the porous bone trabecula structure adopts a three-period minimal curved surface structure, and pores of the porous bone trabecula structure are communicated with one another; the outer surface of the implant is coated with zirconium-niobium alloy metal ceramic; a connecting cavity is formed in the implant, and a connecting part is arranged in the connecting cavity; the abutment is provided with a conical connecting table which is detachably connected with the connecting part, and the abutment is pressed into the implant under quantitative pressure and pulled out under quantitative tension. The porous structure design of the implant surface of the zirconium-niobium alloy implant can promote bone tissue ingrowth, firm integration of the prosthesis and a human skeleton interface is achieved, the stability of the prosthesis is improved, the service life of the prosthesis is prolonged, the implant is stably connected with the abutment, and metal anaphylaxis and metal artifacts can be reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of dental implants, and more particularly, to a zirconium-niobium alloy implant and a method for manufacturing a zirconium-niobium alloy implant. Background Art

[0002] When traditional dental implants are installed with dentures, a single threaded installation form is mostly used for installation, resulting in poor firmness of the installation of the dentures on the dental implants, which is not conducive to the installation of the dentures on the dental implants, and the implant and the abutment need to be self-locked to improve the stability of the connection. Summary of the Invention

[0003] The objectives of the present invention include providing a zirconium-niobium alloy implant and a method for manufacturing a zirconium-niobium alloy implant. The porous structure design on the surface of the implant can promote the growth of bone tissue, achieve a firm integration at the interface between the prosthesis and the human bone, improve the stability and service life of the prosthesis, and the connection between the implant and the abutment is stable. Moreover, the use of zirconium-niobium alloy material can reduce metal allergic reactions and metal artifacts.

[0004] Embodiments of the present invention may be implemented as follows:

[0005] In a first aspect, the present invention provides a zirconium-niobium alloy implant, including:

[0006] An implant, on the outer periphery of which a connection thread is provided; the outer surface layer of the implant is a porous trabecular bone structure, the porous trabecular bone structure adopts a triply periodic minimal surface structure, and its pores are interconnected; the outer surface of the implant is covered with a zirconium-niobium alloy metal ceramic; a connection cavity is arranged inside the implant, and a connection part is arranged in the connection cavity; and

[0007] An abutment, which is provided with a tapered connection platform for detachably connecting with the connection part;

[0008] wherein both the implant and the abutment are made of zirconium-niobium alloy.

[0009] In an alternative embodiment, the thickness of the porous trabecular bone structure is 2 mm, the pore diameter is 0.8 mm, and the wire diameter is 1 mm.

[0010] In an alternative embodiment, the connection part includes a wedge-shaped protrusion protruding from the inner wall of the connection cavity, and a plurality of wedge-shaped protrusions are arranged in a circumferential array around the center of the connection cavity.

[0011] In an alternative embodiment, fillers are arranged at the gaps between two adjacent wedge-shaped protrusions.

[0012] In an alternative embodiment, the filler is silica gel with an elastic modulus of 0.36 MPa.

[0013] In an alternative embodiment, the conical connecting platform is configured to be pressed into the connecting cavity under the action of a quantitative pressure; the conical connecting platform is also configured to be pulled out of the connecting cavity under the action of a quantitative tensile force.

[0014] In a second aspect, the present invention provides a method for manufacturing a zirconium niobium alloy implant, which is used to manufacture the zirconium niobium alloy implant according to any one of the foregoing embodiments, and includes:

[0015] Using zirconium niobium alloy powder as a raw material, an implant and a abutment are obtained by 3D printing;

[0016] The implant and the abutment are machined, trimmed, polished, cleaned and dried to obtain a smooth-surfaced implant and abutment;

[0017] Then, the implant is placed in a tube furnace, an inert gas is introduced, and it is heat-treated, and then taken out after being naturally cooled to below 200°C, so as to form zirconium niobium metal ceramic on the outer surface of the implant, and the surface of the trabecular bone filaments inside is also zirconium niobium metal ceramic.

[0018] In an alternative embodiment, the particle diameter of the zirconium niobium alloy powder is 50 μm.

[0019] In an alternative embodiment, the inert gas in the tube furnace is an atmospheric inert gas with an oxygen mass percentage of 5%-15%.

[0020] In an alternative embodiment, the step of heat-treating the implant in the tube furnace includes:

[0021] Heating at 5°C / min - 20°C / min to 500°C - 700°C, and then cooling at 0.4°C / min - 0.9°C / min to 400°C - 495°C.

[0022] The beneficial effects of the zirconium niobium alloy implant and the method for manufacturing the zirconium niobium alloy implant provided by the embodiments of the present invention include:

[0023] The zirconium niobium alloy implant includes an implant and an abutment; a connecting thread is arranged on the outer periphery of the implant; the outer surface layer of the implant is a porous trabecular bone structure, and the porous trabecular bone structure adopts a triply periodic minimal surface structure, and its pores are interconnected; the outer surface of the implant is covered with zirconium niobium alloy metal ceramic; a connecting cavity is arranged inside the implant, and a connecting part is arranged in the connecting cavity; the abutment is provided with a conical connecting platform for detachably connecting with the connecting part; wherein, both the implant and the abutment are made of zirconium niobium alloy. The porous structure design on the surface of the implant of the zirconium niobium alloy implant can promote the growth of bone tissue, realize the firm integration of the prosthesis and the human bone interface, improve the stability and service life of the prosthesis, and the connection between the implant and the abutment is firm, and the use of zirconium niobium alloy material can reduce metal allergic reactions and metal artifacts. Description of the Drawings

[0024] To more clearly illustrate the technical solutions of the embodiments of the present invention, the following will briefly introduce the drawings required for use in the embodiments. It should be understood that the following drawings only show certain embodiments of the present invention and should not be regarded as limiting the scope. For those of ordinary skill in the art, without creative efforts, other related drawings can also be obtained based on these drawings.

[0025] Figure 1 It is a schematic structural diagram of the zirconium-niobium alloy implant provided in this embodiment;

[0026] Figure 2 It is a schematic structural diagram of the implant and the abutment provided in this embodiment;

[0027] Figure 3 It is a photo of the surface pore diameter and wire diameter of the implant provided in this embodiment;

[0028] Figure 4 It is a relationship diagram of the total damage rate of shear stress and tensile stress on one side of the bone interface for the prostheses with different parameter combinations of the zirconium-niobium alloy implant provided in this embodiment;

[0029] Figure 5 It is a schematic structural diagram of the implant provided in this embodiment;

[0030] Figure 6 It is a stress distribution diagram of 20 kg of quantitative pressure after the zirconium-niobium alloy implant provided in this embodiment is assembled.

[0031] Icon: 100 - zirconium-niobium alloy implant; 110 - implant; 120 - abutment; 111 - connecting thread; 112 - wedge-shaped protrusion; 113 - gap; 121 - tapered connection platform. Specific Embodiments

[0032] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the following will clearly and completely describe the technical solutions in the embodiments of the present invention with reference to the drawings in the embodiments of the present invention. Obviously, the described embodiments are some, but not all, of the embodiments of the present invention. Usually, the components of the embodiments of the present invention described and shown in the drawings here can be arranged and designed in various different configurations.

[0033] Therefore, the following detailed description of the embodiments of the present invention provided in the drawings is not intended to limit the scope of the claimed present invention, but merely represents the selected embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts belong to the scope of protection of the present invention.

[0034] It should be noted that similar reference numerals and letters indicate similar items in the following drawings. Therefore, once an item is defined in one drawing, it does not need to be further defined and explained in subsequent drawings.

[0035] In the description of the present invention, it should be noted that if terms such as "upper", "lower", "inner", "outer", etc. are used to indicate the orientation or positional relationship, it is based on the orientation or positional relationship shown in the drawings, or the orientation or positional relationship in which the product of the invention is usually placed during use. This is only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation. Therefore, it should not be construed as a limitation to the present invention.

[0036] In addition, if terms such as "first", "second", etc. are used only for distinguishing descriptions, they cannot be understood as indicating or implying relative importance.

[0037] It should be noted that, without conflict, the features in the embodiments of the present invention can be combined with each other.

[0038] With the development of technology and the progress of society, the living standards and quality of life of people have gradually improved. Dental implant surgery has become more and more common, and the styles of dental implants have also become more and more diverse.

[0039] In the existing dental implant surgery, a hole is mainly prepared in the jawbone, and then a dental implant is implanted in the hole and a tooth is inlaid on the dental implant. The traditional dental implant only has inclined threads on its surface to facilitate screwing the dental implant into the hole prepared in the jawbone. This form makes the fixation of the dental implant prone to loosening. Moreover, when installing the denture on the traditional dental implant, a single thread installation form is mostly used for installation, resulting in poor firmness of the installation of the denture on the dental implant, which is not conducive to the installation of the denture on the dental implant, and the implant and the abutment need to be self-locked to improve the stability of the connection.

[0040] For the above reasons, please refer to Figures 1-4 , this embodiment provides a zirconium niobium alloy implant 100, including:

[0041] An implant 110, on the outer periphery of the implant 110 is configured a connecting thread 111; the outer surface layer of the implant 110 is a porous trabecular bone structure, the porous trabecular bone structure adopts a triply periodic minimal surface structure, and its pores are interconnected; the outer surface of the implant 110 is covered with a zirconium niobium alloy metal ceramic; a connecting cavity is configured inside the implant 110, and a connecting portion is configured in the connecting cavity; and

[0042] An abutment 120, the abutment 120 is configured with a tapered connecting platform 121 for detachably connecting with the connecting portion;

[0043] Among them, both the implant 110 and the abutment 120 are made of zirconium niobium alloy.

[0044] Please refer to Figures 1-4 , and the working principle of the zirconium niobium alloy implant 100 is as follows:

[0045] First of all, it should be noted that with the development of 3D printing technology, metal 3D printing can realize prostheses with different structures and porous trabecular bone structures, and can manufacture complex joint prosthesis structures. Its porous structure design can promote bone tissue ingrowth, achieve a firm integration of the prosthesis and the human bone interface, and improve the stability and service life of the prosthesis. For different materials, a suitable pore structure is required for good interface integration between bone and the implant 110.

[0046] Secondly, zirconium niobium alloy has become a new generation of orthopedic implants due to its excellent biocompatibility, low elastic modulus and low magnetic susceptibility, etc., and can replace Ti alloy for the manufacture of orthopedic implants. The low elastic modulus zirconium alloy helps to reduce the stress shielding phenomenon caused by the biomechanical incompatibility between the implant and the human bone. On the other hand, when performing magnetic resonance imaging (MRI) examinations on orthopedic implant patients, zirconium alloy also has a lower magnetic susceptibility, which can reduce the MRI imaging artifact phenomenon.

[0047] Among them, zirconium niobium alloy has become the main material for medical devices and implants because of its high strength, good toughness and biocompatibility, low magnetic susceptibility and elastic modulus. After the surface of the zirconium niobium alloy implant is oxidized, a ceramic layer is formed. Its ceramic surface is integrally formed with the entire metal prosthesis, avoiding the exfoliation or generation of debris on the prosthesis surface; the friction coefficient after the surface of the zirconium niobium alloy is oxidized is half of that of cobalt-chromium alloy, and it has better lubricity and corrosion resistance, so it can significantly reduce the wear rate of the joint friction interface and extend the service life of the prosthesis; the zirconium niobium alloy implant is a one-piece design of a metal prosthesis with an oxidized interface. The strength of the zirconium niobium alloy implant is twice that of cobalt-chromium alloy, avoiding the high brittleness similar to ceramics and effectively preventing the prosthesis from breaking; in addition to good mechanical properties, zirconium niobium alloy also has ideal biocompatibility, low sensitization, and is more suitable for patients with metal allergy constitution.

[0048] For the above reasons, the zirconium niobium alloy implant 100 includes an implant 110 and an abutment 120. Among them, both the implant 110 and the abutment 120 are made of zirconium niobium alloy and are obtained by 3D metal printing;

[0049] The outer periphery of the implant 110 is provided with connecting threads 111; the outer surface layer of the implant 110 is a porous trabecular bone structure, and the porous trabecular bone structure adopts a triply periodic minimal surface structure, and its pores communicate with each other; the outer surface of the implant 110 is covered with a zirconium-niobium alloy cermet; a connecting cavity is arranged inside the implant 110, and a connecting part is arranged in the connecting cavity; the abutment 120 is provided with a tapered connecting platform 121 for detachably connecting with the connecting part; wherein, both the implant 110 and the abutment 120 are made of zirconium-niobium alloy.

[0050] Through surface oxidation treatment, a zirconium-niobium alloy cermet is formed on the surface, and the surface of the implant 110 is a porous trabecular bone structure, and the abutment 120 has a tapered connecting platform 121; the outer surface of the implant 110 has connecting threads 111, and its surface layer is composed of a porous trabecular bone structure, adopting a triply periodic minimal surface structure, with pores communicating with each other, and the porous trabecular surface is beneficial to the integration of the implant 110 with the bone; the inside of the implant 110 is a solid structure, and a wedge-shaped array annular structure is manufactured by machining.

[0051] The porous structure design on the surface of the implant 110 of the zirconium-niobium alloy implant 100 can promote the growth of bone tissue into it, realize the firm integration of the prosthesis and the human bone interface, and improve the stability and service life of the prosthesis; the connection between the implant 110 and the abutment 120 can improve the connection stability, and the surface trabecular bone structure is beneficial to reducing stress concentration and is beneficial to the long-term stability after the prosthesis is implanted; the use of zirconium-niobium alloy material reduces metal allergic reactions and metal artifacts.

[0052] Further, please refer to Figures 1-4 , in this embodiment, the thickness of the porous trabecular bone structure on the surface layer of the implant 110 is 2 mm, the pore diameter is 0.8 mm, and the wire diameter is 1 mm. That is, the outer surface of the implant 110 has a threaded shape and is composed of a porous trabecular bone structure with a thickness of 2 mm, adopting a triply periodic minimal surface structure, with pores communicating with each other, a pore diameter of 0.8 mm, and a wire diameter of 1 mm; the porous trabecular surface is beneficial to the integration of the implant 110 with the bone; in other embodiments of the present invention, it can also be other parameters.

[0053] Based on the above, the surface of the implant 110 is a trabecular structure with a thickness of 2 mm, whose pores are interconnected, with a pore diameter of 0.8 mm and a wire diameter of 1 mm; this pore structure obtains a structure with better bone integration through finite element analysis; in terms of pore diameter and wire diameter, 25 different parameter combinations of zirconium-niobium alloy trabecular prostheses and solid prostheses are designed through permutation and combination. The shear stress and tensile stress of the bone-prosthesis interface with different parameter combinations are analyzed by the finite element method and compared with the damage stress threshold, and their damage rates are statistically calculated to obtain the parameter combination of the optimal porous prosthesis. The simulation shows that there are certain rules for the shear stress and tensile stress damage on the bone interface under different pore diameter and wire diameter conditions. The optimal parameter combination of the porous zirconium-niobium alloy trabecular prosthesis is the combination of a pore diameter of 0.8 mm and a wire diameter of 1 mm. The stress damage rate of its trabecular prosthesis interface (shear and tension) is 25.9%, which is better than 60% of the solid prosthesis, and the damage rate distribution is more uniform, which can reduce the occurrence of interface stress concentration damage. The relationship between the total damage rates of shear stress and tensile stress on one side of the bone interface for 26 different parameter combination prostheses Figure 3 . In addition, the trabecular structure adopts a triply periodic minimal surface (TPMS) structure. This structure is a suitable bionic structure for the bone implant 110. The TPMS surface is very smooth, without sharp turns or connection points of the lattice porous structure, and the overall structure is interconnected. It can better improve the bone integration and bonding strength of the bone implant 110, and at the same time, 3D printing technology can be realized.

[0054] Please refer to Figures 1-5 , and when configuring the connecting part, in order to improve the connection stability between the abutment 120 and the implant 110, therefore, the connecting part includes a wedge-shaped protrusion 112 protruding from the inner wall of the connecting cavity, and a plurality of wedge-shaped protrusions 112 are arranged in a circular array around the center of the connecting cavity. And while configuring the above-mentioned wedge-shaped protrusions 112, fillers are arranged at the gaps 113 between two adjacent wedge-shaped protrusions 112. Through the setting of the fillers, after the implant 110 and the abutment 120 are assembled, the gap between the connecting part and the tapered connecting platform 121 can be eliminated, and then when the abutment 120 is subjected to the biting force, this connecting part forms an elastic buffer connection. In this embodiment, the filler is silica gel with an elastic modulus of 0.36 MPa, and the silica gel is medical silica gel. In other embodiments of the present invention, it can also be other types of filling materials.

[0055] Thus, the inside of the implant 110 is a solid structure, and a wedge-shaped array annular structure is manufactured by machining; the pores between the wedge-shaped array annular structures inside the implant 110 are filled with medical silica gel, and the elastic modulus of the silica gel is 0.36 MPa, ensuring that there is no gap inside after the implant 110 and the abutment 120 are assembled, and when the abutment 120 is subjected to the biting force, the connecting part forms an elastic buffer connection;

[0056] Current research shows that the biting force of a single tooth varies due to factors such as tooth type and individual differences. Generally speaking, the biting force of incisors is relatively small, about 20 - 30 kg; the biting force of canines is around 30 - 50 kg; the biting force of molars is the largest, usually around 50 - 70 kg. Therefore, according to different tooth types, the implant 110 and the abutment 120 are connected to reach their biting force range to ensure the stability of the implanted teeth.

[0057] Therefore, please refer to Figures 1-6 , in this embodiment, the abutment 120 is connected to the implant 110 in a plug-and-play manner, and its connection method is a detachable connection. Through reasonable finite element analysis of the wedge-shaped convex structure on the inner wall of the connection cavity, the abutment 120 is pressed into the implant 110 under a quantitative pressure, and the abutment 120 is pulled out under a quantitative tensile force; based on this, the conical connection platform 121 is used to be pressed into the connection cavity under the action of a quantitative pressure; the conical connection platform 121 is also used to be pulled out of the connection cavity under the action of a quantitative tensile force.

[0058] Specifically, in order to press the abutment 120 into the implant 110 under a quantitative pressure and pull out the abutment 120 under a quantitative tensile force; through finite element calculation and experimental measurement, there are three ways to set the quantitative pressure, as follows:

[0059] The first one: the quantitative pressure is 20 kg, and the abutment 120 is pulled out under a quantitative tensile force of 30 kg for incisor implant restoration; the second one: the quantitative pressure is 30 kg, and the abutment 120 is pulled out under a quantitative tensile force of 50 kg for canine implant restoration; the third one: the quantitative pressure is 50 kg, and the quantitative tensile force is 70 kg for molar implant restoration.

[0060] Therefore, the abutment 120 is pressed into the implant 110 under a quantitative pressure and pulled out under a quantitative tensile force. The implant 110 and the abutment 120 form a self-locking structure through friction, which is beneficial to the connection stability; a special clamping device is required for the assembly and disassembly of the implant 110 and the abutment 120, and there are fixed positions on the outer surfaces of the implant 110 and the abutment 120; there are three kinds of combinations of the implant 110 and the abutment 120. One is that the abutment 120 is pressed into the implant 110 with a quantitative pressure of 20 kg and pulled out under a quantitative tensile force of 30 kg; the second is that the abutment 120 is pressed into the implant 110 with a quantitative pressure of 30 kg and pulled out under a quantitative tensile force of 50 kg; the third is that the abutment 120 is pressed into the implant 110 with a quantitative pressure of 50 kg and pulled out under a quantitative tensile force of 70 kg; through finite element design and actual experimental verification of the quantitative pressing force and pulling force, through finite element calculation, the stress distribution of the implant 110 component after assembly with a quantitative pressing pressure of 20 kg is as Figure 6 shown.

[0061] In summary, please refer to Figures 1-6, the zirconium-niobium alloy implant 100 includes an implant body 110 and an abutment 120, which are obtained by 3D metal printing and undergo surface oxidation treatment to form a zirconium-niobium alloy cermet on the surface;

[0062] The surface of the implant body 110 has a porous trabecular bone structure and the abutment 120 has a conical structure; the outer shape of the surface of the implant body 110 has a threaded shape and is composed of a porous trabecular bone structure with a thickness of 2 mm. The three-period minimal surface structure is adopted, the pores communicate with each other, the pore diameter is 0.8 mm, and the wire diameter is 1 mm; the porous trabecular surface is conducive to the integration of the implant body 110 with the bone;

[0063] The interior of the implant body 110 is a solid structure, and a wedge array annular structure is manufactured by machining; the pores between the wedge array annular structures inside the implant body 110 are filled with medical silicone, and the elastic modulus of the silicone is 0.36 MPa to ensure that there is no gap inside after the implant body 110 and the abutment 120 are assembled. When the abutment 120 is subjected to occlusal force, an elastic buffer connection is formed at the connection part;

[0064] The abutment 120 is pressed into the implant body 110 under a quantitative pressure and pulled out of the implant body 110 under a quantitative tensile force;

[0065] Through the porous structure design on the surface of its implant body 110, the zirconium-niobium alloy implant 100 can promote the ingrowth of bone tissue, realize the firm integration of the prosthesis and the human bone interface, and improve the stability and service life of the prosthesis; the self-locking structure between the implant body 110 and the abutment 120 is conducive to stable connection, and the use of zirconium-niobium alloy material reduces metal allergic reactions and metal artifacts.

[0066] Please refer to Figures 1-6 , based on the above zirconium-niobium alloy implant 100, this embodiment also provides a manufacturing method of the zirconium-niobium alloy implant 100 for manufacturing the above zirconium-niobium alloy implant 100, including:

[0067] Using zirconium-niobium alloy powder as the raw material, the implant body 110 and the abutment 120 are obtained by 3D printing;

[0068] The implant body 110 and the abutment 120 are machined, trimmed, polished, cleaned and dried to obtain a smooth-surfaced implant body 110 and abutment 120;

[0069] Then the implant body 110 is placed in a tube furnace, an inert gas is introduced, it is heat-treated, and then taken out after being naturally cooled to below 200 °C to form a zirconium niobium oxide cermet on the outer surface of the implant body 110, and the surface of the trabecular bone wire diameter inside is also zirconium niobium oxide cermet.

[0070] In this embodiment, the particle diameter of the zirconium niobium alloy powder used in manufacturing the implant 110 and the abutment 120 is 50 μm. Moreover, the inert gas in the tubular furnace is an atmospheric inert gas with an oxygen mass percentage of 5%-15%.

[0071] In addition, the steps of heat-treating the implant 110 in the tubular furnace include:

[0072] Heating at 5°C / min - 20°C / min to 500°C - 700°C, and then cooling at 0.4°C / min - 0.9°C / min to 400°C - 495°C.

[0073] In summary, the steps of the manufacturing method of the zirconium niobium alloy implant 100 are as follows:

[0074] Using zirconium niobium alloy powder as the raw material, with the particle diameter of the powder being 50 μm, the zirconium niobium alloy implant 100, which is an implant 110 with a surface porous trabecular structure and a conical connection abutment 120, is obtained through 3D printing;

[0075] The zirconium niobium alloy implant 100 is machined, trimmed, polished, cleaned, and dried to obtain a zirconium niobium alloy implant 100 with a smooth surface, namely the implant 110 and the conical connection abutment 120;

[0076] Then, the implant 110 of the zirconium niobium alloy implant 100 is placed in the tubular furnace, an atmospheric inert gas with an oxygen mass percentage of 5%-15% is introduced, heated at 5°C / min - 20°C / min to 500°C - 700°C, cooled at 0.4°C / min - 0.9°C / min to 400°C - 495°C, and then naturally cooled to below 200°C and taken out. The obtained implant 110 is the oxidized product, and a zirconium niobium metal ceramic is formed on the outer surface, and the surface of the internal trabecular wire diameter is also a zirconium niobium metal ceramic.

[0077] The above is only the specific embodiment of the present invention, but the protection scope of the present invention is not limited thereto. Any changes or substitutions that can be easily thought of by those skilled in the art within the technical scope disclosed by the present invention should be covered within the protection scope of the present invention.

Claims

1. A zirconium niobium alloy implant, characterized in that, Comprising: An implant, on the outer periphery of which a connecting thread is arranged; the outer surface layer of the implant is a porous trabecular bone structure, the porous trabecular bone structure adopts a triply periodic minimal surface structure, and its pores communicate with each other; the outer surface of the implant is covered with a zirconium-niobium alloy metal ceramic; a connecting cavity is arranged inside the implant, and a connecting part is arranged in the connecting cavity; and A abutment, which is provided with a conical connecting platform for detachably connecting with the connecting part; Wherein, both the implant and the abutment are made of zirconium-niobium alloy.

2. The zirconium-niobium alloy implant according to claim 1, wherein: The thickness of the porous trabecular bone structure is 2 mm, the pore diameter is 0.8 mm, and the wire diameter is 1 mm.

3. The zirconium-niobium alloy implant according to claim 1, wherein: The connecting part includes a wedge-shaped protrusion protruding from the inner wall of the connecting cavity, and a plurality of the wedge-shaped protrusions are arranged in a circular array around the center of the connecting cavity.

4. The zirconium-niobium alloy implant according to claim 3, wherein: Fillers are arranged at the gaps between two adjacent wedge-shaped protrusions.

5. The zirconium-niobium alloy implant according to claim 4, wherein: The filler is silica gel with an elastic modulus of 0.36 MPa.

6. The zirconium-niobium alloy implant according to claim 1, wherein: The conical connecting platform is used to be pressed into the connecting cavity under the action of a quantitative pressure; the conical connecting platform is also used to be pulled out of the connecting cavity under the action of a quantitative tension.

7. A method for manufacturing a zirconium niobium alloy implant, which is used to manufacture the zirconium niobium alloy implant according to any one of claims 1-6, characterized in that, Comprising: Using zirconium-niobium alloy powder as a raw material, the implant and the abutment are obtained by 3D printing; The implant and the abutment are machined, trimmed, polished, cleaned and dried to obtain the implant and the abutment with smooth surfaces; Then the implant is placed in a tube furnace, an inert gas is introduced, it is heat-treated, and then taken out after being naturally cooled to below 200 °C, so as to form a zirconium-niobium oxide metal ceramic on the outer surface of the implant, and the surface of the trabecular bone wire diameter inside is also a zirconium-niobium oxide metal ceramic.

8. The method for manufacturing a zirconium-niobium alloy implant according to claim 7, wherein: The particle diameter of the zirconium-niobium alloy powder is 50 μm.

9. The method for manufacturing a zirconium-niobium alloy implant according to claim 7, wherein: The inert gas in the tube furnace is an atmospheric inert gas with an oxygen mass percentage of 5%-15%.

10. The method for manufacturing a zirconium-niobium alloy implant according to claim 8, wherein: The step of heat-treating the implant in the tube furnace includes: Heating to 500 °C - 700 °C at 5 °C / min - 20 °C / min, and then cooling to 400 °C - 495 °C at 0.4 °C / min - 0.9 °C / min.

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