CN118948500A

CN118948500A - A titanium alloy artificial bone joint with low friction coefficient and its preparation method

Info

Publication number: CN118948500A
Application number: CN202411035183.0A
Authority: CN
Inventors: 唐洁
Original assignee: Hunan Pengdeng Biotechnology Co ltd
Current assignee: Hunan Pengdeng Biotechnology Co ltd
Priority date: 2024-07-31
Filing date: 2024-07-31
Publication date: 2024-11-15

Abstract

The present invention discloses a titanium alloy artificial bone joint with a low friction coefficient, including a joint part and a lining structure arranged at the connection of adjacent joint parts, the joint part includes an action part and a connection part, the action part and the lining structure are matched and combined, and the connection part is fixedly connected to the natural bone or artificial bone; the action part and the connection part both include a base structure arranged on the inner side, the action part also includes an intermediate layer attached to the outer side of the base structure and a surface layer attached to the outer side of the intermediate layer; the connection part also includes a fusion layer attached to the outer side of the base structure. The preparation method of a titanium alloy artificial bone joint with a low friction coefficient disclosed by the present invention can significantly improve the mechanical properties, biocompatibility and low friction coefficient of the titanium alloy artificial bone joint, overcome the shortcomings of the prior art, and provide a better solution for the clinical application of artificial bone joints.

Description

Titanium alloy artificial bone joint with low friction coefficient and preparation method thereof

Technical Field

The invention relates to the technical field of bone joints, in particular to a titanium alloy artificial bone joint with a low friction coefficient and a preparation method thereof.

Background

The development and application of artificial bone joints is one of the important directions in the field of modern medicine, and especially in orthopedics surgery, the application of artificial joints greatly improves the quality of life of patients. Titanium alloy is an important material for preparing artificial bone joints due to good mechanical property, biocompatibility and corrosion resistance. However, existing titanium alloy artificial bone joints still have some significant drawbacks in terms of mechanical properties, biocompatibility and low coefficient of friction.

Titanium alloys have higher strength and lower density, which makes it one of the ideal artificial bone joint materials. However, the existing titanium alloy artificial bone joint often has fatigue damage and abrasion problems in the long-time use process. Since human joints are subjected to repeated stress and strain in daily activities, this requires that the artificial joint material have excellent tensile strength and yield strength. The performance of the existing titanium alloy artificial bone joint in the aspect is not ideal, and the mechanical performance of the material can be reduced after long-term use, so that the service life and the functions of the joint are affected.

Biocompatibility is one of important indexes for evaluating the quality of artificial bone joint materials. Existing titanium alloy artificial bone joints, after implantation into the human body, although generally exhibiting good biocompatibility, still present some problems. For example, certain titanium alloy materials may trigger a localized inflammatory response, resulting in rejection of the implant by the tissue. In addition, existing titanium alloy surface treatment techniques are limited, and it is difficult to achieve good bonding with surrounding bone tissue, affecting bone healing and long-term stability of the joint. The problem of cytotoxicity also limits the wide application of the existing titanium alloy artificial bone joint to a certain extent.

The proper functioning of the joint depends on low friction and high lubricity between the articular surfaces. The existing titanium alloy artificial bone joints are still not fully satisfactory in this regard. The surface friction coefficient of titanium alloys is high, which means that frictional wear is exacerbated during articulation, thereby affecting the function and durability of the joint. The high friction coefficient not only causes discomfort to the patient in the use process, but also can cause abrasion and inflammation of tissues around the joint, thereby further reducing the service life of the artificial joint.

In summary, there is a great room for improvement in the mechanical properties, biocompatibility and low friction coefficient of the existing titanium alloy artificial bone joint. These drawbacks limit the wide clinical application and popularization of artificial bone joints. In view of these problems, it is particularly important to develop a titanium alloy artificial bone joint with higher mechanical properties, better biocompatibility and lower coefficient of friction.

Disclosure of Invention

Aiming at the defects in the prior art, the invention aims to provide the titanium alloy artificial bone joint with low friction coefficient and the preparation method thereof, which remarkably improve the mechanical property, biocompatibility and low friction coefficient of the titanium alloy artificial bone joint, overcome the defects in the prior art and provide a better solution for clinical application of the artificial bone joint.

The technical scheme adopted by the invention for achieving the purpose is as follows: the utility model provides a low coefficient of friction's titanium alloy artificial bone joint, includes joint spare and sets up in the liner structure of adjacent joint spare junction, the joint spare includes effect portion, connecting portion, the supporting combination of effect portion and liner structure, connecting portion and natural bone or artificial bone fixed connection.

The action part and the connecting part both comprise a matrix structure arranged on the inner side, and the action part also comprises an intermediate layer attached to the outer side of the matrix structure and a surface layer attached to the outer side of the intermediate layer; the connecting portion further comprises a fusion layer attached to the outer side of the base structure.

In some of these embodiments, the following solutions are provided for ensuring that the matrix structure in the active part, the connection part, exhibits good mechanical properties.

The matrix structure comprises the following raw material components in parts by weight:

Titanium: more than or equal to 85 percent,

Nitrogen: 5 to 10 percent,

Aluminum: 2 to 8 percent,

Vanadium: 1-2%.

In some of these implementations, the following technical solutions are provided for further improving the structural strength, biocompatibility, processability and corrosion resistance of the matrix structure.

The matrix structure also comprises the following raw material components in parts by weight:

Iron: less than or equal to 0.25 percent,

Zirconium: less than or equal to 0.3 percent,

Molybdenum: less than or equal to 1.5 percent.

In some implementations, in order to ensure that the fusion layer can be stably attached and attached on the substrate structure of the connecting part to form a unified whole, ensure that the fusion layer is formed by good biocompatibility, realize effective fusion with natural bones, and improve the combination stability of the artificial bone joint and the natural bones, the following technical scheme is provided.

The fusion layer comprises the following raw material components in parts by weight:

Titanium: 85-90 percent,

Bioactive glass: 10-15%;

the bioactive glass comprises the following raw material components in parts by weight:

Silica: 45-52%,

Calcium oxide: 25 to 30 percent,

Sodium oxide: 10 to 15 percent,

Phosphorus oxide: 2-6%.

In some implementations, the middle layer can be stably attached and attached on the substrate structure of the acting part to form a unified whole, meanwhile, the strength and rigidity of the whole acting part can be further improved, the impact resistance and fatigue resistance of the acting part are enhanced, long-term stable use is ensured, and the functions of bearing and dispersing stress are achieved.

Anchor holes are uniformly formed in one side, facing the pad structure, of the middle layer, and the middle layer comprises the following raw material components in parts by weight:

titanium: 85-95 percent,

Tantalum: 5 to 10 percent,

Niobium: 1 to 5 percent,

Ceramic matrix composite: less than or equal to 5 percent;

the ceramic matrix composite comprises the following raw material components in parts by weight:

alumina: 70-80 percent,

Zirconia: 20-30%,

Additive: less than or equal to 5 percent;

The additive comprises one or more of silicon dioxide, titanium oxide and rare earth oxide.

In some implementations, in order to ensure that the surface layer can be stably attached to the outer surface of the intermediate layer and form a unified whole, and simultaneously ensure that the surface layer has an extremely low friction coefficient and stably operates in cooperation with the liner structure, the following technical scheme is provided.

The surface layer adopts a nitrogen-containing high-carbon nanocrystalline titanium alloy coating, and the nitrogen-containing high-carbon nanocrystalline titanium alloy coating comprises the following raw material components in parts by weight:

Nanocrystalline titanium: more than or equal to 80 percent,

Nitrogen: 4 to 8 percent,

And (3) charcoal: 2-5%.

In some of these implementations, in order to reduce the friction of the pad structure with the active portion surface layer, the following technical solution is provided.

The pad structure comprises the following raw material components in parts by weight:

polyetheretherketone: 90-95 percent,

Tetrafluoroethylene fiber: 5-10%.

A method for preparing a titanium alloy artificial bone joint with a low friction coefficient, which is used for preparing the titanium alloy artificial bone joint with the low friction coefficient, and comprises the following steps of:

S1-1, preparing a matrix structure:

S1-1-1: preparing a blank by adopting a melting casting method;

S1-1-2: sequentially carrying out cutting finish machining, angular position polishing treatment, sand blasting treatment and cleaning on the surface of the blank to obtain a matrix structure presenting a connecting part and an acting part;

S1-2, preparation of a fusion layer:

S1-2-1: coating the substrate structure of the action part, additionally arranging a coating shell outside the action part, and manufacturing a fusion layer on the outer surface of the substrate structure of the connection part by adopting a vapor deposition method;

s1-2-2: removing the coating shell outside the acting part, and cleaning the substrate structure of the acting part;

S1-3, preparation of an intermediate layer:

s1-3-1: cladding the fusion layer of the connecting part, additionally arranging a cladding shell outside the fusion layer, and manufacturing an intermediate layer on the outer surface of the substrate structure of the acting part by adopting a vapor deposition method;

s1-3-2: drilling a hole on one side of the middle layer facing the pad structure, processing the anchor hole, and adopting a spraying process to manufacture a surface layer on the outer surface of the middle layer, so that the surface layer enters the anchor hole to enhance the combination stability of the surface layer and the middle layer.

S1-3-3: removing the cladding shell outside the fusion layer, and cleaning the whole joint part to finish the preparation work of the joint part;

the method further comprises the following preparation steps of the gasket structure:

S2: and processing the integrated liner structure by adopting a melting pouring mode.

In some implementations, in order to ensure that the fusion layer of the base structure of the acting part and the connecting part is subjected to cladding treatment so as to ensure that the vapor deposition operation of the exposed part is stably performed, the following technical scheme is provided.

The cladding shell is made of high-temperature resistant materials, and the steps of cladding treatment and dismantling the cladding shell comprise:

S3-1: the coating shell is assembled on the outer side of the basal body structure of the action part or the outer side of the fusion layer of the connecting part in a detachable mode;

s3-2: and removing the cladding shell outside the basal body structure of the action part or outside the fusion layer of the connecting part.

The invention has the beneficial effects that:

1. The application prepares the titanium alloy blank by adopting a melting casting method, and carries out fine processing, such as cutting, polishing and sand blasting, so that the substrate structure has higher smoothness and geometric accuracy, and a solid foundation is laid for the subsequent adhesion of the fusion layer and the intermediate layer. The preparation of the fusion layer and the middle layer adopts a vapor deposition method, so that the structural strength of the material is enhanced, and the tensile strength and the yield strength are also obviously improved. Experimental results show that the tensile strength of the titanium alloy artificial bone joint provided by the application reaches 950MPa, and the yield strength reaches 920MPa, which are obviously superior to the existing 850MPa and 800MPa. The improvement of the overall mechanical properties ensures the stability and durability of the joint in long-term use.

In terms of biocompatibility, the application obviously reduces cytotoxicity and achieves a cell proliferation rate of 95% by preparing the fusion layer and the intermediate layer with low toxicity on the surface of the titanium alloy. The surface treatment process of the application enables the titanium alloy material to be combined with surrounding bone tissue more tightly, and reduces the risks of inflammatory reaction and tissue rejection. Cell culture experiments prove that the titanium alloy artificial bone joint provided by the application has obvious advantages in terms of biocompatibility, and is beneficial to healing of bone tissues and long-term stability of the artificial joint.

3. According to the application, the nitrogen-containing high-carbon nanocrystalline coating is prepared on the surface of the titanium alloy by adopting a spraying process, and the anchor holes are drilled on the intermediate layer, so that the surface layer material enters the anchor holes, and the bonding stability between the surface layer and the intermediate layer is enhanced. Through friction and wear tests, the friction coefficient of the titanium alloy artificial bone joint provided by the application is only 0.20, which is obviously lower than 0.35 of the existing titanium alloy artificial bone joint. The realization of low friction coefficient not only reduces the abrasion and energy consumption in the joint movement, but also improves the comfort level of the patient and the service life of the joint.

In conclusion, the mechanical property, biocompatibility and low friction coefficient of the titanium alloy artificial bone joint are remarkably improved through the innovative preparation method and the surface treatment process, the defects in the prior art are overcome, and a better solution is provided for clinical application of the artificial bone joint.

Drawings

FIG. 1 is a schematic view of a titanium alloy bone joint according to the present invention in a sectioned state;

Fig. 2 is a schematic structural diagram of the intermediate layer and the surface layer in a disassembled state.

In the figure: 1 joint part, 101 acting part, 102 connecting part, 11 basal body structure, 12 middle layer, 121 anchor hole, 13 surface layer, 14 fusion layer and 2 lining structure.

Detailed Description

The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.

Referring to fig. 1-2, various technical schemes provided by the low friction coefficient titanium alloy artificial bone joint and the preparation method thereof provided by the invention are described in detail by action mechanisms in combination with the following embodiments.

Example 1

The utility model provides a low coefficient of friction's titanium alloy artificial bone joint, includes joint spare 1 and sets up in the liner structure 2 of adjacent joint spare 1 junction, and joint spare 1 includes effect portion 101, connecting portion 102, and effect portion 101 and liner structure 2 are supporting to be combined, connecting portion 102 and natural bone or artificial bone fixed connection.

The acting part 101 and the connecting part 102 both comprise a base structure 11 arranged on the inner side, and the acting part 101 also comprises an intermediate layer 12 attached to the outer side of the base structure 11 and a surface layer 13 attached to the outer side of the intermediate layer 12; the connection 102 further comprises a fusion layer 14 attached to the outside of the base structure 11.

The titanium alloy artificial bone joint with low friction coefficient provided by the invention has reasonable design, and the coordination among the related structures is strong, so that the functions of the titanium alloy artificial bone joint can be fully exerted. Specifically:

The joint element 1 comprises an active part 101 and a connecting part 102, the function is clear, the active part 101 is matched with the pad structure 2 to provide a low friction surface required by joint movement, and the connecting part 102 is fixedly connected with natural bone or artificial bone to provide stable support for the joint.

In the structural design of the acting part 101, the base structure 11 provides structural support, bears main load, has good mechanical properties, and ensures the stability of the structure in the process of joint movement; the middle layer 12 can further improve the strength and rigidity of the whole acting part 101, strengthen the impact resistance and fatigue resistance of the acting part, ensure long-term stable use, play a role in bearing and dispersing stress, ensure that the base structure 11, the surface layer 13 and the middle layer 12 can be stably attached together to form an integral structure, avoid the problems of delamination, cracking and the like, and prolong the service life of the joint; the surface layer 13 has an extremely low coefficient of friction and excellent wear resistance, and acts directly on the spacer structure 2, acting as an articulating effect.

In the structural design of the connecting part 102, the base structure 11 is the same as the base structure 11 in the acting part 101, and has good compatibility with human bone tissue, so that the connecting part 102 can be stably connected with natural bone; the fusion layer 14 can further increase good fusion with natural or artificial bone, ensure firm connection, and avoid loosening.

The pad structure 2 is arranged at the joint of the adjacent joint parts 1, buffers impact force generated during joint movement, reduces stress concentration, protects joints and surrounding tissues, and is matched with the action part 101 at the same time, so that the low friction characteristic of the joint is further optimized.

The design of each structure is carried out around key targets such as friction reduction, stress dispersion, stability improvement and the like, and long-term stable and reliable operation of the artificial joint can be realized through mutual cooperation.

Example 2

In order to ensure that the base structure 11 in the active part 101, the connection part 102 exhibits excellent mechanical properties, the following technical solutions are provided.

The matrix structure 11 comprises the following raw material components in parts by weight:

Titanium: more than or equal to 85 percent,

Nitrogen: 5 to 10 percent,

Aluminum: 2 to 8 percent,

Vanadium: 1-2%.

Among the titanium alloy components used in the base structure 11, titanium is a main component, has good biocompatibility and mechanical properties, and nitride can improve the hardness and wear resistance of metal and also improve the compatibility with human tissues. The strength and hardness of the titanium alloy can be improved by the aluminum, the mechanical property of the titanium alloy is ensured, and the corrosion resistance of the vanadium can be improved on the basis of improving the strength of the titanium alloy.

In order to further improve the structural strength, biocompatibility, processability and corrosion resistance of the base structure 11, the following technical scheme is provided.

The matrix structure 11 also comprises the following raw material components in parts by weight:

Iron: less than or equal to 0.25 percent,

Zirconium: less than or equal to 0.3 percent,

Molybdenum: less than or equal to 1.5 percent.

Iron can be selectively added, and the heat treatment performance of the titanium alloy can be improved when the strength of the titanium alloy is improved; zirconium can be selectively added, so that the processability and biocompatibility of the titanium alloy can be improved; molybdenum is selectively added to improve the corrosion resistance and strength of the titanium alloy.

Example 3

In order to ensure that the fusion layer 14 can be stably attached and attached to the base structure 11 of the connecting part 102 to form a unified whole, ensure that the fusion layer 14 is formed by good biocompatibility, realize effective fusion with natural bones, and improve the combination stability of the artificial bone joint and the natural bones, the following technical scheme is provided.

The fusion layer 14 comprises the following raw material components in parts by weight:

Titanium: 85-90 percent,

Bioactive glass: 10-15%;

Silica: 45-52%,

Calcium oxide: 25 to 30 percent,

Sodium oxide: 10 to 15 percent,

Phosphorus oxide: 2-6%.

Silica is a network former of bioactive glass, imparting good mechanical strength and chemical stability to bioactive glass. In vivo, silica can hydrolyze to release Si ions, stimulate surrounding cells to produce silicate and phosphate precipitates, and promote the formation of new bone tissues.

Calcium oxide can increase the bioactivity and dissolution rate of bioactive glass. The release of calcium ions is beneficial to cell adhesion and proliferation, and can be combined with phosphate ions to form hydroxyapatite, so that chemical bonding with natural bones is formed.

Sodium oxide can regulate the dissolution rate of glass so that it maintains proper bioactive reaction kinetics in vivo. The release of sodium ions aids in extracellular matrix mineralization and new bone formation.

The phosphorus oxide can further enhance the biological activity of the bioactive glass and promote the formation of hydroxyapatite. At the same time, the release of phosphate ions is beneficial to the cell differentiation and bone mineralization process.

The components in the bioactive glass can generate a series of complex chemical-biological reactions in vivo, and play roles in promoting bone tissue regeneration and fusion together. After the titanium is added, the fusion layer 14 can be stably attached to the outer surface of the base structure 11 and form a unified whole.

Example 4

The following technical scheme is provided for the purpose that the middle layer 12 can be stably attached and attached on the base structure 11 of the acting part 101 to form a unified whole, meanwhile, the strength and rigidity of the whole acting part 101 can be further improved, the impact resistance and fatigue resistance of the acting part are enhanced, long-term stable use is ensured, and the functions of bearing and dispersing stress are achieved.

Anchor holes 121 are uniformly formed in one side, facing the pad structure 2, of the middle layer 12, and the middle layer 12 comprises the following raw material components in parts by weight:

titanium: 85-95 percent,

Tantalum: 5 to 10 percent,

Niobium: 1 to 5 percent,

Ceramic matrix composite: less than or equal to 5 percent;

alumina: 70-80 percent,

Zirconia: 20-30%,

Additive: less than or equal to 5 percent;

Titanium is used as a main component, has excellent performances of high strength, light weight, corrosion resistance and the like, tantalum is a metal element with high density, corrosion resistance and good biocompatibility, and the strength, the hardness and the wear resistance of the alloy can be improved by adding the tantalum into the titanium alloy. Niobium is a metal element with good biocompatibility, can improve the mechanical property of the alloy, and can increase the strength, toughness and fatigue resistance of the alloy by adding a proper amount of niobium into the titanium alloy, and is also beneficial to improving the corrosion resistance of the alloy and ensuring the long-term stability of the joint prosthesis in a physiological environment.

Alumina is a ceramic material with high strength and high hardness, and can greatly improve the mechanical strength and rigidity of the composite material. The composite material has excellent wear resistance and corrosion resistance, can obviously enhance the durability of the composite material, has good thermal stability at high temperature, and is beneficial to improving the fatigue resistance of the composite material.

The zirconia has higher fracture toughness, can effectively inhibit crack growth and improves the impact resistance of the composite material. The volume expansion in the phase transformation process can generate compressive stress, prevent crack propagation and enhance wear resistance, and when the anchor holes 121 are formed in the side, facing the liner structure 2, of the middle layer 12, the crack phenomenon around the anchor holes 121 can be effectively avoided. The chemical stability of zirconia also helps to promote durability of the composite in biological environments.

Among other things, silica can improve the compactness and strength of the ceramic, titania can improve the thermal shock resistance and wear resistance of the ceramic, and rare earth oxides (e.g., yttria) can improve the fracture toughness and creep resistance of the ceramic.

The anchor holes 121 can improve the effective adhesion and lamination of the surface layer 13 on the outer surface of the intermediate layer 12, improve the lamination effect of the surface layer and the intermediate layer, ensure that the intermediate layer 12 and the surface layer 13 can be stably laminated together to form an integral structure, and avoid the problems of delamination, cracking and the like.

In order to ensure that the surface layer 13 can be stably attached to the outer surface of the intermediate layer 12 and form a unified whole, and simultaneously ensure that the surface layer 13 has an extremely low friction coefficient and stably operates in cooperation with the pad structure 2, the following technical scheme is provided.

The surface layer 13 adopts a nitrogen-containing high-carbon nanocrystalline titanium alloy coating, and the nitrogen-containing high-carbon nanocrystalline titanium alloy coating comprises the following raw material components in parts by weight:

Nanocrystalline titanium: more than or equal to 80 percent,

Nitrogen: 4 to 8 percent,

And (3) charcoal: 2-5%.

The nano-scale grain size of the nanocrystalline titanium can obviously improve the hardness and strength of the titanium alloy, so that the wear resistance of the surface layer 13 is enhanced, the nanocrystalline structure can also improve the thermal stability and chemical stability of the material, and the durability of the surface layer 13 is improved.

The nitrogen element can form TiN phase in the nanocrystalline titanium matrix, so that the hardness and wear resistance of the surface layer 13 are further improved, the lubricating property of the surface layer 13 can be improved by the existence of the TiN phase, and the friction coefficient with the corresponding liner structure 2 is reduced.

The carbon element can form TiC phase in the nanocrystalline titanium, so that the strength and toughness of the surface layer 13 are further enhanced, and the existence of the TiC phase can also improve the chemical stability of the surface layer 13 and improve the corrosion resistance and wear resistance.

Other microelements, specifically a small amount of Al, V, fe and the like, can be added on the basis of the method, so that the performances of the surface layer 13, such as corrosion resistance, oxidation resistance and the like, are further optimized.

During the bonding of the surface layer 13 to the intermediate layer 12, a portion of the surface layer 13 material may penetrate into the anchor holes 121 of the intermediate layer 12 to form a stable anchoring structure to enhance the stability and uniformity of the combination of the two.

Example 5

In order to reduce the friction force of the pad structure 2 with the surface layer 13 of the acting portion 101, the following technical solution is provided.

The gasket structure 2 comprises the following raw material components in parts by weight:

polyetheretherketone: 90-95 percent,

Tetrafluoroethylene fiber: 5-10%.

Polyetheretherketone (PEEK) is a high-performance engineering plastic with excellent mechanical strength, rigidity and high-temperature resistance. Its good chemical resistance and biocompatibility, being able to ensure the stability and safety of the pad structure 2 in biological environments, its low friction factor and excellent self-lubricity, favouring low friction movements with the surface layer 13.

Tetrafluoroethylene (PTFE) fiber has an extremely low friction factor and excellent abrasion resistance, and can further reduce the friction coefficient with the surface layer 13. In addition, the addition of PTFE fiber can also enhance the crack resistance of the PEEK matrix and improve the reliability and durability of the whole. The synergy between the PTFE fiber and the PEEK matrix can realize more stable low friction characteristics.

The PEEK matrix provides excellent mechanical strength and rigidity, and is capable of withstanding high loads during articulation.

Example 6

A method for preparing a low friction coefficient titanium alloy artificial bone joint, which is used for preparing the low friction coefficient titanium alloy artificial bone joint, and comprises the following preparation steps of a joint part 1:

S1-1, preparation of a matrix structure 11:

S1-1-1: preparing a blank by adopting a melting casting method;

S1-1-2: sequentially performing cutting finish machining, angular position polishing treatment, sand blasting treatment and cleaning on the surface of the blank to obtain a substrate structure 11 presenting a connecting part 102 and an acting part 101;

s1-2, preparation of a fusion layer 14:

S1-2-1: coating the base structure 11 of the acting part 101, adding a coating shell outside the acting part 101, and manufacturing a fusion layer 14 on the outer surface of the base structure 11 of the connecting part 102 by adopting a vapor deposition method;

s1-2-2: removing the coating shell outside the action part 101 and cleaning the substrate structure 11 of the action part 101;

s1-3, preparation of an intermediate layer 12:

S1-3-1: cladding the fusion layer 14 of the connecting part 102, adding a cladding shell outside the fusion layer 14, and manufacturing an intermediate layer 12 on the outer surface of the base structure 11 of the acting part 101 by adopting a vapor deposition method;

S1-3-2: and drilling a hole on one side of the middle layer 12 facing the pad structure 2, machining an anchor hole 121, manufacturing a surface layer 13 on the outer surface of the middle layer 12 by adopting a spraying process, and enabling the surface layer 13 to enter the anchor hole 121 so as to enhance the combination stability of the surface layer 13 and the middle layer 12.

S1-3-3: removing the cladding shell outside the fusion layer 14, and cleaning the whole joint part 1 to finish the preparation work of the joint part 1;

The following steps are also included in relation to the preparation of the liner structure 2:

s2: the integrally formed liner structure 2 is fabricated by means of melt casting.

The titanium alloy blank is prepared by adopting a melt casting method, a foundation is laid for subsequent processing, the blank is subjected to cutting finish machining to process the structures of the upper acting part 101 and the connecting part 102, then the corner part is subjected to polishing treatment to remove impurities and burrs on the corner part, and finally the whole structure is subjected to spraying treatment to roughen the surface, so that the fusion layer 14 and the middle layer 12 are conveniently and stably attached on the surface and form a unified whole.

When the molten layer is generated, the action part 101 is coated by a coating treatment mode, the influence of the falling of the molten layer material on the action part 101 on the structural stability of the action part 101 is avoided, the fusion layer 14 is prepared on the surface of the substrate of the connecting part 102 by adopting a vapor deposition method, then the coating shell outside the action part 101 is removed, and the residual coating shell on the surface of the substrate is cleaned.

When the intermediate layer 12 is generated, firstly, the fusion layer 14 is coated in a coating treatment mode, the materials of the intermediate layer 12 and the surface layer 13 are prevented from falling on the fusion layer 14 to affect the normal exertion of the design function, the intermediate layer 12 is prepared by adopting a vapor deposition method, the overall structural strength is improved, the anchor holes 121 are drilled in the intermediate layer 12 to improve the combination effect of the intermediate layer 12 and the surface layer 13, the surface layer 13 is prepared by adopting a spraying process, the anchor holes 121 are made to enhance combination, finally, the coating shell outside the connecting part 102 is removed, and the whole joint part 1 is cleaned to remove surface impurities.

The lining structure 2 adopts a melting pouring mode to prepare the integrated composite lining structure 2.

The fusion layer 14 and the intermediate layer 12 are prepared by a vapor deposition method, so that stable adhesion on the surface of the substrate can be realized.

The finish machining processes such as cutting, polishing, sand blasting and the like can ensure the surface smoothness and geometric accuracy of the substrate, lay a foundation for the preparation of subsequent adhesion layers, and the series of surface treatment processes are beneficial to improving the binding force between the substrate structure 11 and the adhesion layers.

The spraying of the surface layer 13 and the design of the anchor holes 121 can prepare a low-friction nitrogen-containing high-carbon nanocrystalline coating on the surface of the intermediate layer 12, and the anchor holes 121 are drilled on the intermediate layer 12, so that the surface layer 13 material enters the intermediate layer, and the bonding stability between the intermediate layer 12 and the intermediate layer is enhanced.

In order to ensure that the fusion layer 14 of the base structure 11 of the acting portion 101 and the connecting portion 102 is subjected to cladding treatment so as to ensure that the vapor deposition operation of the exposed portion is stably performed, the following technical scheme is provided.

S3-1: the cladding shell is detachably assembled outside the basal body structure 11 of the action part 101 or outside the fusion layer 14 of the connecting part 102;

S3-2: the coating shell outside the base structure 11 of the acting part 101 or outside the fusion layer 14 of the connecting part 102 is removed.

The protective shell is additionally arranged in a detachable mode, so that the inner structure can be effectively protected, and meanwhile, the protective shell is conveniently detached to carry out vapor deposition on the inner structure and prepare the outer layer structure.

Example 7

In order to verify the superiority of the low friction coefficient titanium alloy artificial bone joint in the scheme of the application in the aspects of mechanical property, biocompatibility and low friction coefficient, the following comparative experiment is designed, the detailed test is carried out on the conventional titanium alloy artificial bone joint and the artificial bone joint provided by the application, and the specific experimental flow, namely test data, are shown as follows:

group a samples: the titanium alloy artificial bone joint which is common in the market is adopted as a control group sample.

Group B samples: the titanium alloy artificial bone joint with low friction coefficient provided by the invention is adopted, wherein:

Titanium: 85%, nitrogen: 6%, aluminum: 5%, vanadium: 2%, iron: 0.25%, zirconium: less than or equal to 0.25 percent, molybdenum: 1.5%.

titanium: 85%, bioactive glass: 15%;

silica: 50%, calcium oxide: 30%, sodium oxide: 15%, phosphorus oxide: 5%.

The intermediate layer comprises the following raw material components in parts by weight:

titanium: 90%, tantalum: 5%, niobium: 3%, ceramic matrix composite: 2%.

Alumina: 75%, zirconia: 20%, additive: 5%. The additive adopts silicon dioxide.

Nanocrystalline titanium: 90%, nitrogen: 7%, charcoal: 3%.

The gasket structure comprises the following raw material components in parts by weight:

polyetheretherketone: 90%, tetrafluoroethylene fiber: 10%.

The complete joint and spacer structure was fabricated according to the preparation method provided in example 6.

The following experiments were performed on group a samples, group B samples:

1. mechanical property test: the tensile strength, yield strength and hardness of the two titanium alloy artificial bone joints are tested by adopting a universal testing machine.

2. Biocompatibility testing: and evaluating cytotoxicity and cell proliferation of the two titanium alloy artificial bone joints by adopting an in-vitro cell culture method.

3. Low coefficient of friction test: and testing the friction coefficients of the two titanium alloy artificial bone joints by adopting a friction and wear testing machine.

Comparison of detection data for group a samples, group B samples:

analysis is carried out on detection data of the A group sample and the B group sample:

1. Mechanical properties:

The tensile strength of the titanium alloy artificial bone joint provided by the application is 950MPa, which is improved by about 12% compared with the existing 850 MPa.

The yield strength of the titanium alloy artificial bone joint provided by the application is 920MPa, which is improved by about 15% compared with the existing 800 MPa.

The hardness of the titanium alloy artificial bone joint provided by the application is 380HV, which is improved by about 19% compared with the existing 320 HV.

2. Biocompatibility:

the titanium alloy artificial bone joint provided by the application shows low toxicity in cytotoxicity test, while the existing titanium alloy artificial bone joint shows medium toxicity.

In terms of cell proliferation rate, the titanium alloy artificial bone joint provided by the application is 95%, and is improved by about 27% compared with the existing 75%.

3. Low coefficient of friction:

The friction coefficient of the titanium alloy artificial bone joint provided by the application is 0.20, which is obviously lower than 0.35 of the existing titanium alloy artificial bone joint, and is reduced by about 43%.

4. Conclusion:

the comparison experiment shows that the low friction coefficient titanium alloy artificial bone joint provided by the application is superior to the existing titanium alloy artificial bone joint in mechanical property, biocompatibility and low friction coefficient, and the scheme of the application has obvious advantages.

It will be evident to those skilled in the art that the invention is not limited to the details of the foregoing illustrative embodiments, and that the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The present embodiments are, therefore, to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein. Any reference sign in a claim should not be construed as limiting the claim concerned.

Furthermore, it should be understood that although the present disclosure describes embodiments, not every embodiment is provided with a separate embodiment, and that this description is provided for clarity only, and that the disclosure is not limited to the embodiments described in detail below, and that the embodiments described in the examples may be combined as appropriate to form other embodiments that will be apparent to those skilled in the art.

Claims

1. A low coefficient of friction titanium alloy artificial bone joint, characterized in that: the joint comprises joint pieces (1) and liner structures (2) arranged at the joints of the adjacent joint pieces (1), wherein each joint piece (1) comprises an acting part (101) and a connecting part (102), the acting parts (101) are matched and combined with the liner structures (2), and the connecting parts (102) are fixedly connected with natural bones or artificial bones;

The action part (101) and the connecting part (102) both comprise a base structure (11) arranged on the inner side, and the action part (101) also comprises an intermediate layer (12) attached to the outer side of the base structure (11) and a surface layer (13) attached to the outer side of the intermediate layer (12); the connection portion (102) further comprises a fusion layer (14) attached to the outside of the base structure (11).

2. The low friction titanium alloy artificial bone joint according to claim 1, wherein the matrix structure (11) comprises the following raw material components in parts by weight:

Titanium: more than or equal to 85 percent,

Nitrogen: 5 to 10 percent,

Aluminum: 2 to 8 percent,

Vanadium: 1-2%.

3. The low friction titanium alloy artificial bone joint according to claim 2, wherein the base structure (11) further comprises the following raw material components in parts by weight:

Iron: less than or equal to 0.25 percent,

Zirconium: less than or equal to 0.3 percent,

Molybdenum: less than or equal to 1.5 percent.

4. A low coefficient of friction titanium alloy artificial bone joint according to claim 3, wherein the fusion layer (14) comprises the following raw material components in parts by weight:

Titanium: 85-90 percent,

Bioactive glass: 10-15%;

Silica: 45-52%,

Calcium oxide: 25 to 30 percent,

Sodium oxide: 10 to 15 percent,

Phosphorus oxide: 2-6%.

5. The low friction coefficient titanium alloy artificial bone joint according to claim 4, wherein the middle layer (12) is uniformly provided with anchor holes (121) towards one side of the pad structure (2), and the middle layer (12) comprises the following raw material components in parts by weight:

titanium: 85-95 percent,

Tantalum: 5 to 10 percent,

Niobium: 1 to 5 percent,

Ceramic matrix composite: less than or equal to 5 percent;

alumina: 70-80 percent,

Zirconia: 20-30%,

Additive: less than or equal to 5 percent;

6. The low friction coefficient titanium alloy artificial bone joint according to claim 5, wherein the surface layer (13) adopts a nitrogen-containing high carbon nanocrystalline titanium alloy coating, and the nitrogen-containing high carbon nanocrystalline titanium alloy coating comprises the following raw material components in parts by weight:

Nanocrystalline titanium: more than or equal to 80 percent,

Nitrogen: 4 to 8 percent,

And (3) charcoal: 2-5%.

7. The low coefficient of friction titanium alloy artificial bone joint according to claim 6, wherein the spacer structure (2) comprises the following raw material components in parts by weight:

polyetheretherketone: 90-95 percent,

Tetrafluoroethylene fiber: 5-10%.

8. A low coefficient of friction titanium alloy artificial bone joint according to claim 7 provides a method of preparation comprising the following steps with respect to the preparation of the joint member (1):

s1-1, preparation of a matrix structure (11):

S1-1-1: preparing a blank by adopting a melting casting method;

S1-1-2: sequentially performing cutting finish machining, angular position polishing treatment, sand blasting treatment and cleaning on the surface of the blank to obtain a matrix structure (11) presenting a connecting part (102) and an acting part (101);

S1-2, preparation of a fusion layer (14):

S1-2-1: coating the substrate structure (11) of the acting part (101), additionally arranging a coating shell outside the acting part (101), and manufacturing a fusion layer (14) on the outer surface of the substrate structure (11) of the connecting part (102) by adopting a vapor deposition method;

S1-2-2: removing the coating shell outside the action part (101) and cleaning the substrate structure (11) of the action part (101);

s1-3, preparing an intermediate layer (12):

s1-3-1: cladding the fusion layer (14) of the connecting part (102), additionally arranging a cladding shell outside the fusion layer (14), and manufacturing an intermediate layer (12) on the outer surface of the base structure (11) of the acting part (101) by adopting a vapor deposition method;

S1-3-2: drilling a hole on one side of the middle layer (12) facing the pad structure (2), machining an anchor hole (121), manufacturing a surface layer (13) on the outer surface of the middle layer (12) by adopting a spraying process, and enabling the surface layer (13) to enter the anchor hole (121) so as to enhance the combination stability of the surface layer (13) and the middle layer (12);

S1-3-3: removing the cladding shell outside the fusion layer (14), and cleaning the whole joint part (1) to finish the preparation work of the joint part (1);

the method further comprises the following preparation steps for the liner structure (2):

S2: and processing the integrated gasket structure (2) by adopting a melting pouring mode.

9. The method of claim 8, wherein the coating is a high temperature resistant material, and wherein the steps of coating and removing the coating comprise:

S3-1: the coating shell is assembled on the outer side of the basal body structure (11) of the action part (101) or the outer side of the fusion layer (14) of the connecting part (102) in a detachable mode;

S3-2: the coating shell outside the base structure (11) of the action part (101) or outside the fusion layer (14) of the connecting part (102) is removed.