CN108203778B - Zr-based biomedical alloy and preparation method thereof - Google Patents
Zr-based biomedical alloy and preparation method thereof Download PDFInfo
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- 238000002844 melting Methods 0.000 claims abstract description 25
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- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C16/00—Alloys based on zirconium
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- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C1/00—Making non-ferrous alloys
- C22C1/02—Making non-ferrous alloys by melting
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Abstract
本发明公开了一种Zr基生物医用合金及其制备方法，Zr基生物医用合金的重量百分比组成为：铌10.5～19％，钛0％～30％，余量为锆和不可避免的杂质元素。制备方法包括以下步骤：(1)按照配比称取原料，送入真空熔炼炉的反应容器中进行混合，在惰性气体的保护下进行多次真空熔炼，得到熔融反应液；(2)对反应容器的底部持续通冷水，使熔融反应液快速冷却，至温度降至室温后，得到Zr基生物医用合金。本发明的Zr基生物医用合金具有低模量，低磁化率和优异的力学性能等优点，不仅解决了植入体金属可能会造成的应力屏蔽问题，并且有利于减小金属基生物植入材料的磁化率，减小对MRI(核磁共振检测)伪影的影响。
The invention discloses a Zr-based biomedical alloy and a preparation method thereof. The weight percentage of the Zr-based biomedical alloy is composed of: niobium 10.5-19%, titanium 0-30%, and the balance is zirconium and inevitable impurity elements . The preparation method includes the following steps: (1) weighing raw materials according to the proportion, sending them into a reaction vessel of a vacuum melting furnace for mixing, and performing vacuum melting for many times under the protection of an inert gas to obtain a molten reaction solution; (2) pairing the reaction The bottom of the container is continuously passed cold water, so that the molten reaction liquid is rapidly cooled, and after the temperature drops to room temperature, a Zr-based biomedical alloy is obtained. The Zr-based biomedical alloy of the present invention has the advantages of low modulus, low magnetic susceptibility and excellent mechanical properties, which not only solves the problem of stress shielding that may be caused by the implant metal, but also helps to reduce the metal-based bio-implant material. Magnetic susceptibility to reduce the impact on MRI (nuclear magnetic resonance detection) artifacts.
Description
Technical Field
The invention belongs to the technical field of metal-based composite materials, and particularly relates to a Zr-based biomedical alloy and a preparation method thereof.
Background
Biomedical materials are functional materials used in clinical diagnosis, treatment, repair or replacement of human tissues or organs or to enhance their functions. Biomedical materials have been an indispensable part of the material research field, and have been studied intensively by many scholars around the world, because they are associated with organs of the human body and medical instruments. General requirements for biomedical materials: (1) must meet the regulation of relevant standards, and should have the advantages of no toxicity, no pyrogen reaction, no teratogenicity, no carcinogenesis, no anaphylaxis, no interference to the immune mechanism of the organism, good blood compatibility and histocompatibility, etc. (2) Good biological stability. For biomedical materials to be implanted in the body for a long period of time, the structural properties of the material must be stable. (3) Good mechanical properties. Good mechanical properties are one of the key factors of biomaterials and also one of the important factors impeding the development of biomaterials. The mechanical properties generally include strength, elasticity, fatigue resistance, wear resistance, dimensions, forming processability, etc. of the material.
At present, Ti and Ti alloy are widely applied in the biomedical field, and especially the research and application of beta-Ti alloy are prominent. Although the beta-Ti alloy has lower elastic modulus, most of the beta-Ti alloy is still higher than the modulus range of human bones (10-30GPa), which easily causes stress shielding effect and is not beneficial to bone healing. In addition, with the continuous development of medical detection technology, especially the rapid development of nuclear magnetic resonance technology, higher performance requirements are put on implant materials, and although Ti is a paramagnetic material and has relatively low magnetism, there are many reports that titanium alloy implants affect the quality of nuclear magnetic resonance images and form artifact areas. Therefore, it is more important to design a biomedical material with mechanical properties more matched with the natural skeleton of human body, good biocompatibility and low magnetic susceptibility.
The Zr element and the Ti element belong to the same group in the periodic table of the elements, and have many similar properties, and as can be seen from a Zr-Ti binary phase diagram, the Zr and the Ti can be mutually dissolved at any temperature. The Zr simple substance has very excellent plasticity, and in the field of biomedical alloys, Zr is a metal with excellent corrosion resistance, good tissue compatibility and no toxicity, and is often used as an alloying element to be added into Ti alloy to improve the mechanical properties of the alloy. In addition, Zr has lower elastic modulus and magnetic susceptibility than Ti, so the biomedical Zr alloy has very wide application prospect and is expected to be researched to be a substitute material which better meets the requirements of human bones.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provide the Zr-based biomedical alloy with low modulus, low magnetization rate and excellent mechanical property and the preparation method thereof.
In order to solve the technical problems, the invention adopts the following technical scheme:
a Zr-based biomedical alloy, which comprises the following components in percentage by weight: 10.5 to 19 percent of niobium, 0 to 30 percent of titanium, and the balance of zirconium and inevitable impurity elements.
Preferably, the Zr-based biomedical alloy comprises the following components in percentage by weight: 14-18% of niobium, 0-16% of titanium, and the balance of zirconium and inevitable impurity elements.
When the traditional experimental method is used for alloy design, a large amount of time is consumed, materials and funds are wasted, and the success rate is low. According to the invention, a CALPHAD method is calculated by using materials science in combination with a first principle, evaluation and component prediction are carried out on a Ti-Nb-Zr ternary system, the elastic modulus of the Ti-Nb-Zr ternary system is calculated, a reliable calculation prediction result is provided, then a large number of smelting tests are carried out according to the calculation prediction result, the Zr-based biomedical alloy with the components is determined, the elastic modulus is more matched with human bones, the stress shielding effect is prevented from being generated, and the healing of the bones is facilitated; the alloy implant material has the advantages of good mechanical property, good corrosion resistance, higher stability, capability of reducing the corrosion of the physiological environment to the implant material and reducing the probability of inducing the surrounding inflammation of the implant, lower magnetic susceptibility and capability of reducing the influence of the alloy implant material on MRI imaging.
In addition, the invention adopts Zr as an alloy matrix and Nb and Ti as alloying elements. Zr, Nb and Ti belong to nontoxic, good biocompatibility and stable elements, wherein Nb belongs to beta phase stabilizing elements and can reduce the beta → alpha transition temperature, and in the process of rapid cooling, the alloy has no time to generate beta → alpha transition, so that most of beta phase is reserved. Zr and Nb elements have better plasticity, and the strength of the alloy can be improved on the premise of not influencing the plasticity of the matrix after Nb is added into the matrix. The Zr element and the Ti element belong to the same group in the periodic table of the elements, and have many similar properties, and as can be seen from a Zr-Ti binary phase diagram, the Zr and the Ti can be mutually dissolved at any temperature. The addition of Ti can improve the strength and corrosion resistance of the alloy, and has small influence on the plasticity of the alloy.
Pure Ti has a magnetic susceptibility of 3.2X 10 at room temperature-6cm3Per g, pure Zr has a magnetic susceptibility of about 1.28X 10-6cm3(ii) in terms of/g. Based on Zr element, the magnetic susceptibility of Zr alloy can be greatly reduced, the artifact area formed in the MRI detection process is reduced, and the problem that the metal-based implant material is in MRI (nuclear magnetic resonance imaging) can be solvedTest) was determined.
And rapidly cooling to room temperature, the alloy has no time for beta-alpha phase transformation to occur, and in addition, Nb is a beta phase stabilizing element, so that the beta phase at high temperature can be reserved by adding Nb, and the phase in the alloy is mainly the beta phase with low modulus.
Preferably, in the Zr-based biomedical alloy, the total content of Nb and Ti is 14-34% by weight.
Preferably, in the Zr-based biomedical alloy, the total content of Nb and Ti is 10.5-49% by weight.
Preferably, the elastic modulus of the Zr-based biomedical alloy is 10-25 GPa, the compressive yield limit is 400-800 MPa, and the Zr-based biomedical alloy is better matched with the mechanical property of human bones.
As a general inventive concept, the invention also provides a preparation method of the Zr-based biomedical alloy, which comprises the following steps:
(1) weighing raw materials according to a ratio, feeding the raw materials into a reaction vessel of a vacuum smelting furnace for mixing, and carrying out vacuum smelting for multiple times under the protection of inert gas to obtain a molten reaction solution;
(2) and continuously introducing cold water to the bottom of the reaction vessel to rapidly cool the molten reaction liquid until the temperature is reduced to room temperature, thereby obtaining the Zr-based biomedical alloy.
Preferably, in the step (1), the temperature of vacuum melting is 3000 ℃ +/-200 ℃, the melting time is 70-90 seconds each time, and the melting times are 5-7 times.
Preferably, in the step (1), the gas washing is repeated for 3 times in each smelting process.
Preferably, in the step (1), the vacuum degree of vacuum melting is controlled to be 2 x 10-3Pa～4×10-3Pa。
Preferably, in the step (1), the inert gas is argon.
Compared with the prior art, the invention has the advantages that:
1. compared with the prior biomedical alloy taking Ti as a substrate, the Zr-based biomedical alloy has better corrosion resistance, stronger plasticity and more stability, particularly has lower elastic modulus and lower magnetic susceptibility compared with the Zr alloy, can effectively reduce an artifact area generated to an image in the MRI process, better meets the development requirement of a metal-based biomedical material, and provides more choices of implantation materials for medical workers.
Nb is a beta phase stabilizing element, can reduce beta → alpha transition temperature, so that the alloy contains a large amount of beta phase with low elastic modulus, and simultaneously, the addition of the Nb element can improve the strength and the corrosion resistance of the alloy on the premise of less influence on the plasticity of the Zr alloy.
3. The Zr- (14-18) Nb-xTi (x is 0-16) biomedical alloy has the elastic modulus of 10-25 GPa, is more matched with the elastic modulus of human bones (10-30GPa), can relieve the influence of stress shielding of an implant material, and is beneficial to healing of the bones. The compressive yield limit is 400-800 MPa, the mechanical property is good, and the material is better matched with the mechanical property of human skeleton, so that the implant material has longer service life, and the pain of a patient in frequently replacing the implant material is relieved.
Drawings
FIG. 1 is an SEM photograph of a Zr-based biomedical alloy according to example 1 of the present invention.
FIG. 2 is a stress-strain curve of the Zr-based biomedical alloys of examples 1 to 5 of the present invention.
FIG. 3 is an XRD pattern of the Zr-based biomedical alloy of examples 1 to 5 of the present invention before compression deformation.
FIG. 4 is an XRD pattern of the Zr-based biomedical alloy of examples 1 to 5 of the present invention after compression deformation.
FIG. 5 is an SEM photograph of a Zr-based biomedical alloy according to example 2 of the present invention.
FIG. 6 is an SEM photograph of a Zr-based biomedical alloy according to example 3 of the present invention.
FIG. 7 is an SEM photograph of a Zr-based biomedical alloy according to example 4 of the present invention.
FIG. 8 is an SEM photograph of a Zr-based biomedical alloy according to example 5 of the present invention.
Detailed Description
The invention is further described below with reference to specific preferred embodiments, without thereby limiting the scope of protection of the invention.
Example 1:
the invention relates to a Zr-based biomedical alloy with low modulus and low magnetic susceptibility, which comprises the following components in percentage by weight: nb: 16% and the balance zirconium and inevitable impurity elements.
The Zr-based biomedical alloy of this example was prepared by the following method:
(1) weighing raw materials, and respectively weighing corresponding Zr grains and Nb grains according to the designed weight percentage of each raw material component, wherein the purities of the Zr grains and the Nb grains are both more than 99.99 wt%, and the grain sizes are kept consistent as much as possible.
(2) And uniformly mixing the weighed raw materials.
(3) Smelting raw materials: wiping the inside of the non-consumable vacuum melting furnace clean, keeping the inside of the furnace clean, then putting the raw materials in the step (2) into a copper crucible of the non-consumable vacuum melting furnace, starting to vacuumize, and controlling the vacuum degree to be 3 multiplied by 10-3Pa, introducing argon to remove residual air, and smelting under the protection of argon, wherein the smelting temperature is 3000 ℃; the melting time for each sample was 80 seconds, and remelting was repeated 6 times. In this process, the scrubbing was repeated 3 times.
(4) And (4) cooling the alloy smelted in the step (3) in a copper crucible, wherein in the process, the copper crucible is protected by argon to prevent the alloy from contacting with air, continuously introducing cold water to the bottom of the copper crucible to ensure the rapid cooling of the alloy, and taking out the alloy after cooling to room temperature to obtain the Zr-16Nb biomedical alloy ingot.
Detection of the Zr-based biomedical alloy prepared in this example:
and testing the compression mechanical property of the Zr-16Nb biomedical alloy obtained through the preparation process, cutting the smelted ingot into columns with phi of 3 multiplied by 6mm by a wire cutting machine, and testing the compression mechanical property of the cut sample at room temperature by using an Shimadzu testing machine to obtain the compression elastic modulus, the compression yield strength, the ultimate compressive strength and the compression plastic deformation of the sample. As can be seen from FIG. 2, the elastic modulus of the Zr-16Nb alloy sample is 14.6494GPa, the yield limit is 629.30MPa, the maximum compressive stress is 1566.07MPa, and the plastic deformation is 58.2127%. The microstructure of the Zr-16Nb alloy observed by SEM is shown in FIG. 1. The diffraction peak distributions before and after deformation obtained by XRD are shown in FIGS. 3 and 4, respectively, and it can be seen that the Zr-16Nb phase composition before and after compression deformation is mostly the beta phase and a small amount of the alpha 'phase because the beta → alpha phase transition is not time to occur and only a small amount of the beta phase is converted into the metastable alpha' phase during rapid cooling.
Example 2:
the invention relates to a Zr-based biomedical alloy with low modulus and low magnetic susceptibility, which comprises the following components in percentage by weight: nb: 16%, Ti: 4 percent, and the balance of zirconium and inevitable impurity elements.
The Zr-based biomedical alloy of this example was prepared by the following method:
(1) weighing raw materials, and respectively weighing corresponding Zr grains, Nb grains and Ti grains according to the designed weight percentage of each raw material component, wherein the purities of the Zr grains, the Nb grains and the Ti grains are all more than 99.99 wt%, and the grain sizes are kept consistent as much as possible.
(2) And uniformly mixing the weighed raw materials.
(3) Smelting raw materials: wiping the inside of the non-consumable vacuum melting furnace clean, keeping the inside of the furnace clean, then putting the raw materials in the step (2) into a copper crucible of the non-consumable vacuum melting furnace, starting to vacuumize, and controlling the vacuum degree to be 3 multiplied by 10-3Pa, introducing argon to remove residual air, and smelting under the protection of argon, wherein the smelting temperature is 3000 ℃; the melting time for each sample was 80 seconds, and remelting was repeated 6 times. In this process, the scrubbing was repeated 3 times.
(4) And (4) cooling the alloy smelted in the step (3) in a copper crucible, wherein in the process, the copper crucible is protected by argon gas to prevent the alloy from contacting air, water is continuously introduced into the bottom of the copper crucible to ensure the rapid cooling of the alloy, and the alloy is taken out after being cooled to room temperature to obtain the Zr-16Nb-4Ti biomedical alloy ingot.
Detection of the Zr-based biomedical alloy prepared in this example:
and testing the compression mechanical property of the Zr-16Nb-4Ti biomedical alloy obtained through the preparation process, cutting the smelted ingot into cylinders with the diameter of phi 3 multiplied by 6mm by a wire cutting machine, and testing the compression mechanical property of the cut sample at room temperature by using an Shimadzu testing machine to obtain the compression elastic modulus, the compression yield strength, the ultimate compressive strength and the compression plastic deformation of the sample. As can be seen from FIG. 2, the elastic modulus of the Zr-16Nb-4Ti alloy sample was 14.9834GPa, the yield strength was 637.36MPa, the maximum compressive stress was 1229.81MPa, and the plastic deformation was 52.1188%. The possible reason for the reduction in maximum compressive stress here is due to the deviation in sample size during the cutting process. The microstructure of the Zr-16Nb-4Ti alloy observed by SEM is shown in FIG. 5. The diffraction peak distributions before and after the deformation obtained by XRD are shown in FIGS. 3 and 4, and it can be seen that the Zr-16Nb-4Ti phase composition is a major amount of the beta phase and a minor amount of the alpha' phase before and after the compression deformation.
Example 3:
the invention relates to a Zr-based biomedical alloy with low modulus and low magnetic susceptibility, which comprises the following components in percentage by weight: nb: 16%, Ti: 8 percent, and the balance of zirconium and inevitable impurity elements.
The Zr-based biomedical alloy of this example was prepared by the following method:
(1) weighing raw materials, and respectively weighing corresponding Zr grains, Nb grains and Ti grains according to the designed weight percentage of each raw material component, wherein the purities of the Zr grains, the Nb grains and the Ti grains are all more than 99.99 wt%, and the grain sizes are kept consistent as much as possible.
(2) And uniformly mixing the weighed raw materials.
(3) Smelting raw materials: wiping the inside of the non-consumable vacuum melting furnace clean, keeping the inside of the furnace clean, then putting the raw materials in the step (2) into a copper crucible of the non-consumable vacuum melting furnace, starting to vacuumize, and controlling the vacuum degree to be 3 multiplied by 10-3Pa, introducing argon to remove residual air, and smelting under the protection of argon, wherein the smelting temperature is 3000 ℃; the melting time for each sample was 80 seconds, and remelting was repeated 6 times. In this process, the scrubbing was repeated 3 times.
(4) And (4) cooling the alloy smelted in the step (3) in a copper crucible, wherein in the process, the copper crucible is protected by argon gas to prevent the alloy from contacting air, water is continuously introduced into the bottom of the copper crucible to ensure the rapid cooling of the alloy, and the alloy is taken out after being cooled to room temperature to obtain the Zr-16Nb-8Ti biomedical alloy ingot.
Detection of the Zr-based biomedical alloy prepared in this example:
and testing the compression mechanical property of the Zr-16Nb-8Ti biomedical alloy obtained through the preparation process, cutting the smelted ingot into cylinders with the diameter of phi 3 multiplied by 6mm by a wire cutting machine, and testing the compression mechanical property of the cut sample at room temperature by using an Shimadzu testing machine to obtain the compression elastic modulus, the compression yield strength, the ultimate compressive strength and the compression plastic deformation of the sample. As can be seen from FIG. 2, the elastic modulus of the Zr-16Nb-8Ti alloy sample was 19.6897GPa, the yield strength was 638.56MPa, the maximum compressive stress was 1546.23MPa, and the plastic deformation was 54.5056%. The microstructure of the Zr-16Nb-8Ti alloy observed by SEM is shown in FIG. 6. The diffraction peak distributions before and after the deformation obtained by XRD are shown in FIGS. 3 and 4, respectively, and it can be seen that the Zr-16Nb-8Ti phase composition is a major beta phase and a minor alpha' phase before and after the compression deformation.
Example 4:
the invention relates to a Zr-based biomedical alloy with low modulus and low magnetic susceptibility, which comprises the following components in percentage by weight: nb: 16%, Ti: 12% and the balance zirconium and inevitable impurity elements.
The Zr-based biomedical alloy of this example was prepared by the following method:
(1) weighing raw materials, and respectively weighing corresponding Zr grains, Nb grains and Ti grains according to the designed weight percentage of each raw material component, wherein the purities of the Zr grains, the Nb grains and the Ti grains are all more than 99.99 wt%, and the grain sizes are kept consistent as much as possible.
(2) And uniformly mixing the weighed raw materials.
(3) Smelting raw materials: wiping the inside of the non-consumable vacuum melting furnace clean, keeping the inside of the furnace clean, then putting the raw materials in the step (2) into a copper crucible of the non-consumable vacuum melting furnace, starting to vacuumize, and controlling the vacuum degree to be in3×10-3Pa, introducing argon to remove residual air, and smelting under the protection of argon, wherein the smelting temperature is 3000 ℃; the melting time for each sample was 80 seconds, and remelting was repeated 6 times. In this process, the scrubbing was repeated 3 times.
(4) And (4) cooling the alloy smelted in the step (3) in a copper crucible, wherein in the process, the copper crucible is protected by argon gas to prevent the alloy from contacting air, water is continuously introduced into the bottom of the copper crucible to ensure the rapid cooling of the alloy, and the alloy is taken out after being cooled to room temperature to obtain the Zr-16Nb-12Ti biomedical alloy ingot.
Detection of the Zr-based biomedical alloy prepared in this example:
and testing the compression mechanical property of the Zr-16Nb-12Ti biomedical alloy obtained through the preparation process, cutting the smelted ingot into columns with the diameter of phi 3 multiplied by 6mm by a wire cutting machine, and testing the compression mechanical property of the cut sample at room temperature by using an Shimadzu testing machine to obtain the compression elastic modulus, the compression yield strength, the ultimate compressive strength and the compression plastic deformation of the sample. As can be seen from FIG. 2, the elastic modulus of the Zr-16Nb-12Ti alloy sample was 20.5665GPa, the yield strength was 641.38MPa, the maximum compressive stress was 1740.91MPa, and the plastic deformation was 54.1317%. The microstructure of the Zr-16Nb-12Ti alloy observed by SEM is shown in FIG. 7. The diffraction peak distributions before and after the deformation obtained by XRD are shown in FIGS. 3 and 4, and it can be seen that the Zr-16Nb-12Ti phase composition is mostly the β phase and a very small amount of the α' phase before and after the compression deformation.
Example 5:
the invention relates to a Zr-based biomedical alloy with low modulus and low magnetic susceptibility, which comprises the following components in percentage by weight: nb: 16%, Ti: 16 percent and inevitable impurity elements, wherein the purities of Zr, Nb and Ti are all more than 99.99wt percent.
The Zr-based biomedical alloy of this example was prepared by the following method:
(1) weighing raw materials, and respectively weighing corresponding Zr grains, Nb grains and Ti grains according to the designed weight percentage of each raw material component, wherein the purities of the Zr grains, the Nb grains and the Ti grains are all more than 99.99 wt%, and the grain sizes are kept consistent as much as possible.
(2) And uniformly mixing the weighed raw materials.
(3) Smelting raw materials: wiping the inside of the non-consumable vacuum melting furnace clean, keeping the inside of the furnace clean, then putting the raw materials in the step (2) into a copper crucible of the non-consumable vacuum melting furnace, starting to vacuumize, and controlling the vacuum degree to be 3 multiplied by 10-3Pa, introducing argon to remove residual air, and smelting under the protection of argon, wherein the smelting temperature is 3000 ℃; the melting time for each sample was 80 seconds, and remelting was repeated 6 times. In this process, the scrubbing was repeated 3 times.
(4) And (4) cooling the alloy smelted in the step (3) in a copper crucible, wherein in the process, the copper crucible is protected by argon gas to prevent the alloy from contacting air, water is continuously introduced into the bottom of the copper crucible to ensure the rapid cooling of the alloy, and the alloy is taken out after being cooled to room temperature to obtain the Zr-16Nb-16Ti biomedical alloy ingot.
Detection of the Zr-based biomedical alloy prepared in this example:
and testing the compression mechanical property of the Zr-16Nb-16Ti biomedical alloy obtained through the preparation process, cutting the smelted ingot into columns with the diameter of phi 3 multiplied by 6mm by a wire cutting machine, and testing the compression mechanical property of the cut sample at room temperature by using an Shimadzu testing machine to obtain the compression elastic modulus, the compression yield strength, the ultimate compressive strength and the compression plastic deformation of the sample. As can be seen from FIG. 2, the elastic modulus of the Zr-16Nb-16Ti alloy sample was 20.4661GPa, the yield strength was 642.82MPa, the maximum compressive stress was 1784.34MPa, and the plastic deformation was 54.0206%. The microstructure of the Zr-16Nb-16Ti alloy observed by SEM is shown in FIG. 8. The diffraction peak distributions before and after the deformation obtained by XRD are shown in FIGS. 3 and 4, and it can be seen that the Zr-16Nb-16Ti phase composition before and after the compression deformation is a majority of the β phase and a very small amount of the α' phase.
Finally, it must be said here that: the above embodiments are only used for further detailed description of the technical solutions of the present invention, and should not be understood as limiting the scope of the present invention, and the insubstantial modifications and adaptations made by those skilled in the art according to the above descriptions of the present invention are within the scope of the present invention. Finally, it must be said here that: the above embodiments are only used for further detailed description of the technical solutions of the present invention, and should not be understood as limiting the scope of the present invention, and the insubstantial modifications and adaptations made by those skilled in the art according to the above descriptions of the present invention are within the scope of the present invention.
Claims (1)
1. The Zr-based biomedical alloy is characterized by comprising the following components in percentage by weight: 16% of niobium, 12% of titanium, and the balance of zirconium and inevitable impurity elements;
the elastic modulus of the Zr-based biomedical alloy is 19.6897-20.5665 GPa, and the compressive yield limit is 641.38-800 MPa;
the preparation method of the Zr-based biomedical alloy comprises the following steps:
(1) weighing raw materials according to a ratio, feeding the raw materials into a reaction vessel of a vacuum smelting furnace for mixing, and carrying out vacuum smelting for multiple times under the protection of inert gas to obtain a molten reaction solution;
(2) continuously introducing cold water to the bottom of the reaction container to rapidly cool the molten reaction liquid until the temperature is reduced to room temperature, thereby obtaining the Zr-based biomedical alloy;
in the step (1), the temperature of vacuum melting is 3000 +/-200 ℃, the melting time is 70-90 seconds each time, and the melting times are 5-7 times; repeatedly washing gas for 3 times in each smelting process; the vacuum degree of vacuum melting is controlled to be 2 x 10-3Pa～4×10- 3Pa; the inert gas is argon.
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