Biomedicine implant material with controllable degrading rate and its application

A technology for biomedical and implantable materials, applied in the field of biomedical metal implant materials, can solve the problems of degradation time and strength, disproportionate rigidity, low hardness and rigidity, poor processing stability, etc. Low, high specific stiffness effect

Inactive Publication Date: 2006-11-08
INST OF METAL RESEARCH - CHINESE ACAD OF SCI
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  • Summary
  • Abstract
  • Description
  • Claims
  • Application Information

AI Technical Summary

Problems solved by technology

[0002] At present, most of the degradable materials used in medicine are polymer materials. The degradable polymer materials have the following problems: 1. Low strength, low hardness and rigidity; 2. Poor degradation controllability, degradation time is not proportional to strength and rigidity, degradation In the process, it is easy to lose strength prematurely and cause the device to fail early; 3. The processing stability is poor, and the processing of degradable polymer materials requir

Method used

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Examples

Experimental program
Comparison scheme
Effect test

Embodiment 1

[0019] Use pure magnesium to make a coronary stent sample (after polishing, the wire diameter is 70-80 μm), ultrasonically clean it in acetone and alcohol for 5 minutes, dry it in a vacuum oven, and then put it into a polylactic acid (PLA) solution ( Soak in 0.1g / mL) for 10 minutes, use a stepping motor to pull the pure magnesium sample out of the solution at a uniform speed, centrifuge at 1000 rpm for 1 minute, and then put the bracket in a vacuum drying oven to dry, according to the thickness requirements The number of times of dipping is repeated, the thickness of the coating in this embodiment is 11 μm, after treatment, it will be completely corroded and degraded after being soaked in the simulated plasma solution prepared in Table 1 for about 9 months.

[0020] Since the corrosion rate of pure magnesium materials can be adjusted by factors such as impurity content, grain size and heat treatment, the degradation rate of polylactic acid can also be controlled according to th...

Embodiment 2

[0023]After the AZ31B magnesium alloy was polished, it was ultrasonically cleaned in acetone and alcohol for 5 minutes, dried in a vacuum oven, and then immersed in polyglycolic acid (PGA) solutions (0.2g / mL) of different molecular weights for 20 minutes. Pull the AZ31B magnesium alloy sample out of the solution at a uniform speed with a stepping motor, centrifuge it at 1000 rpm for 1 minute, then put the bracket into a vacuum drying oven to dry, and repeat the number of times of dipping according to the thickness requirements. In this example The coating thickness was 23 μm.

[0024] Since the corrosion rate of the AZ31B magnesium alloy material can be adjusted by factors such as impurity content, grain size and heat treatment, the degradation rate of polyglycolic acid can also be controlled according to the molecular weight and the thickness of the coating, so the medical can be prepared according to the above process. Controlled Degradation The degradation rate of magnesium...

Embodiment 3

[0026] After high-purity magnesium (99.98%) is polished, it is ultrasonically cleaned in acetone and alcohol for 5 minutes, dried in a vacuum oven, and then put into a copolymer of polylactic acid and polyglycolic acid (PLGA) solution (0.05g / mL) Soak in medium for 40 minutes, use a stepping motor to pull the pure magnesium sample out of the solution at a uniform speed, centrifuge at 1000 rpm for 30 seconds, then put the bracket in a vacuum drying oven to dry, and repeat the dipping times according to the thickness requirements , the thickness of the coating in this embodiment is 8 μm. .

[0027] Since the corrosion rate of pure magnesium materials can be adjusted by factors such as impurity content, grain size and heat treatment, the degradation rate of the copolymer of polylactic acid and polyglycolic acid can also be controlled according to the ratio of the two and the thickness of the coating, so The degradation rate of the medical controllable degradable magnesium alloy m...

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Abstract

The present invention relates to biomedicine metal implant material, and is especially biomedicine implant material with controllable degrading rate and its application. The biomedicine implant material with controllable degrading rate has a magnesium or magnesium alloy matrix and a coated degradable polymer layer with thickness controlled within 0.01-5 mm. The biodegradation is completed step by step so as to ensure the mechanical performance of the material during degradation and match the degradation rate with the service period of the implanted device. The biomedicine metal implant material of magnesium or magnesium alloy may be used in preparing temporary or short term implanted device, such as degradable blood rack and peripheral rack, bone fracture plate and bone nail for inner fixing, tissue engineering rack, etc.

Description

technical field [0001] The invention relates to a biomedical metal implant material, in particular to a biomedical implant material with a controllable degradation rate and its application. Background technique [0002] At present, most of the degradable materials used in medicine are polymer materials. The degradable polymer materials have the following problems: 1. Low strength, low hardness and rigidity; 2. Poor degradation controllability, degradation time is not proportional to strength and rigidity, degradation In the process, it is easy to lose strength prematurely and cause the device to fail early; 3. The processing stability is poor, and the processing of degradable polymer materials requires special processing environments and equipment; Both patient needs and the development of biomaterials are important. [0003] The corrosion resistance of magnesium and magnesium alloys is poor, and the standard potential of pure magnesium is -2.37V, especially when it contain...

Claims

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Application Information

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IPC IPC(8): A61L27/40A61L27/04A61L27/14A61L31/02A61L31/04A61L31/12A61L31/14
Inventor 任伊宾黄晶晶杨柯张炳春谭丽丽
Owner INST OF METAL RESEARCH - CHINESE ACAD OF SCI
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