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Preparation method of medical magnesium alloy capable of being evenly degraded

A magnesium alloy, uniform technology, applied in the field of preparation of biomedical degradable materials, can solve the problems of rare earth magnesium alloys that cannot meet the actual needs of biomedicine, fast corrosion speed, low strength, etc., to achieve reduced corrosion degradation rate, high mechanical strength and corrosion resistance, the effect of improving the strength of the alloy

Active Publication Date: 2014-11-26
HARBIN ENG UNIV
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  • Summary
  • Abstract
  • Description
  • Claims
  • Application Information

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Problems solved by technology

However, the performance of conventional rare earth magnesium alloys cannot meet the actual needs of biomedicine
The main reasons are as follows: the stable phase and metastable phase particles in the high rare earth magnesium alloy significantly improve the mechanical properties, but they form galvanic corrosion with the magnesium matrix, resulting in a faster corrosion rate and easy to cause a large number of severe pitting corrosion; low rare earth magnesium alloys The alloy has slightly better corrosion resistance, but lower strength

Method used

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  • Preparation method of medical magnesium alloy capable of being evenly degraded
  • Preparation method of medical magnesium alloy capable of being evenly degraded
  • Preparation method of medical magnesium alloy capable of being evenly degraded

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Experimental program
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Effect test

Embodiment 1

[0033] Using high-purity magnesium ingot (99.98wt%), pure zinc ingot (99.95wt%), Mg-20wt% Gd master alloy and Mg-20wt% Er master alloy as raw materials, according to Mg 98.8 Gd 0.6 Er 0.3 Zn 0.3 The proportion of the alloy. Under the protection of argon, first melt the pure magnesium ingot in a resistance furnace, when the temperature rises to 750°C, add Mg-Gd and Mg-Er intermediate alloys, and stir for 10 minutes after it melts; then add pure zinc ingot , After melting, argon was introduced to stir and refine for 5 minutes, and then stand at 740°C for 15 minutes. Finally, the temperature was lowered to 700°C, the scum on the surface of the alloy liquid was removed, and poured into the crystallizer under the protection of argon. The diameter of the crystallizer is 100mm, the flow rate of cooling water is 220L / min, and the casting speed is 100mm / min. Subsequently, the obtained alloy cast rod was subjected to heat preservation and heat treatment at 510° C. for 12 hours, and...

Embodiment 2

[0036] Using high-purity magnesium ingot (99.98wt%), pure zinc ingot (99.95wt%), Mg-20wt% Gd master alloy and Mg-20wt% Er master alloy as raw materials, according to Mg 98.8 Gd 0.3 Er 0.6 Zn 0.3 The proportion of the alloy. Under the protection of argon, first melt the pure magnesium ingot in a resistance furnace, when the temperature rises to 750°C, add Mg-Gd and Mg-Er intermediate alloys, and stir for 8 minutes after it melts; then add pure zinc ingot , After melting, argon was introduced to stir and refine for 10 minutes, and then stand still at 740°C for 20 minutes. Finally, the temperature was lowered to 710°C, the scum on the surface of the alloy liquid was removed, and poured into the crystallizer under the protection of argon. The diameter of the crystallizer is 100mm, the flow rate of cooling water is 220L / min, and the casting speed is 80mm / min. Subsequently, the obtained alloy cast rod was subjected to heat preservation heat treatment at 520° C. for 8 hours, and...

Embodiment 3

[0038] Using high-purity magnesium ingot (99.98wt%), pure zinc ingot (99.95wt%) and Mg-20wt% Er master alloy as raw materials, according to Mg 98.8 Er 0.9 Zn 0.3 The proportion of the alloy. Under the protection of argon, first melt the pure magnesium ingot in a resistance furnace, when the temperature rises to 750 ° C, add the Mg-Er intermediate alloy, wait for it to melt, stir for 10 minutes; then add pure zinc ingot, wait for melting , Stirring and refining by argon gas for 10 minutes, and then static at 740°C for 25 minutes. Finally, the temperature was lowered to 700°C, the scum on the surface of the alloy liquid was removed, and poured into the crystallizer under the protection of argon. The diameter of the crystallizer is 100mm, the flow rate of cooling water is 220L / min, and the casting speed is 110mm / min. Subsequently, the obtained alloy cast rod was subjected to heat preservation heat treatment at 520° C. for 8 hours, and the cooling method was air cooling. Then...

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Abstract

The invention provides a preparation method of a medical magnesium alloy capable of being evenly degraded. The preparation method comprises the following steps: designing a Mg1-a-bREaZnb alloy according to an atomic ratio; smelting raw materials at 720 DEG C to 750 DEG C to form a smelting liquid, feeding argon to stir and refine for 5 to 10 minutes, then standing at 740 DEG C for 15 to 25 minutes, cooling to 700 DEG C to 710 DEG C and pouring so as to obtain an alloy casting rod; carrying out heat preservation on the alloy casting rod at 500 DEG C to 530 DEG C for 8 to 12 hours, and cooling in an air-cooling manner; carrying out hot extrusion on the alloy casting rod subjected to the heat treatment at 380 DEG C to 430 DEG C under the conditions that the extrusion rate of an extrusion rod is 0.5 to 1mm / s and the extrusion ratio is greater than 20; carrying out aging treatment on the alloy subjected to the hot extrusion at 180 to 220 DEG C for 10 to 100 hours. The prepared magnesium-rare earth alloy which can be degraded and absorbed is excellent in mechanical property, high in corrosion resistance and even in degradation behavior. Thus, the prepared magnesium-rare earth alloy can serve as a degradable human body hard tissue implant material.

Description

technical field [0001] The invention relates to a preparation method of a biomedical degradable material. Background technique [0002] Artificial implants for human hard tissue repair or replacement are widely used clinically and are closely related to human life and health. Biomedical stainless steel series and titanium series alloy materials have excellent mechanical properties, biocompatibility and corrosion resistance, but these materials are inert materials and cannot be degraded. Secondary surgery after recovery cannot be avoided, which increases patient risks and medical expenses . At the same time, their mechanical properties do not match those of bone tissue, especially the elastic modulus, which will cause stress shielding effect, and then make the bone tissue around the implant loose or atrophy; although polymer materials can be absorbed by the human body, they are not strong enough to provide The function of structural support, and the degradation products are...

Claims

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Application Information

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IPC IPC(8): C22C23/06C22F1/06B22D11/00
Inventor 张景怀徐驰张丽张密林巫瑞智徐龙江焦玉凤
Owner HARBIN ENG UNIV
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