Bioactive film on titanium metal surface and its sand blasting-micro arc oxidizing compounding process

Abstract

The present invention relates to film on the surface of medical titanium-base metal material and its sand blasting-micro arc oxidizing compounding process. Through the first surface sand blasting treatment of titanium or titanium alloy material and the subsequent micro arc oxidizing in electrolyte solution containing phosphate radical ion and calcium ion and with the titanium or titanium alloy material as anode, stainless steel or titanium as cathode and DC power source or DC pulse power source, one bioactive film is in-situ formed on the surface of the titanium or titanium alloy material. The bioactive film of rough porous hydroxyapatite has surface roughness Ra of 2-4.5 micron, no interface with the substrate, elastic modulus reaching that of bone and excellent bioactivity, and may be used as the substitute for femur, hip joint, tooth root, etc. The bioactive film has optimized combination strength, stability and bioactivity.

Description

technical field

[0001] The invention relates to a method for preparing a bioactive film layer on the surface of a medical metal material, in particular to a bioactive film layer on the surface of a titanium metal used as a femur, a hip joint and a tooth root and a sandblasting-micro-arc oxidation composite process thereof. Background technique

[0002] In recent years, the development and application of various biomedical materials have developed rapidly, among which metal materials were the first to be used. Metal biomaterials generally have high strength and toughness, and are suitable for hard tissue repair and fixation. Commonly used metal biomaterials include cobalt-based alloys, tantalum, titanium, and titanium alloys. Among them, titanium and its alloys are widely used for their superior corrosion resistance, high specific strength, good biocompatibility, and suitable for implantation. attention. However, due to the low surface hardness and poor wear resistance of t...

Examples

Embodiment 1

[0025] Using 25μm Al 2 o 3Sandblasted titanium. Use distilled water to prepare a solution containing 0.01 mol / L of sodium phosphate, 0.01 mol / L of sodium β-glycerophosphate, and 0.5 mol / L of calcium acetate. With sandblasting pretreated titanium as the anode and stainless steel or titanium as the cathode, DC power is used for micro-arc oxidation. The voltage is 300-500V; keep the electrolyte temperature not higher than 50°C. The micro-arc oxidation was 5 minutes, and a porous layer with a thickness of about 20 μm was formed on the titanium surface; X-ray diffraction analysis showed that the film layer was mainly composed of hydroxyapatite; the surface roughness of the film layer was measured by the surface profiler Ra=2.1 μm; the film layer The binding strength is 43MPa, and it has good biological activity.

Embodiment 2

[0027] The titanium alloy is sandblasted with 75 μm SiC. Use distilled water to prepare a solution containing 0.15 mol / L of sodium β-glycerophosphate and 0.3 mol / L of calcium chloride. With sandblasting pretreated titanium alloy as the anode and stainless steel or titanium as the cathode, DC power is used for micro-arc oxidation. The voltage is 200-400V; keep the electrolyte temperature not higher than 50°C. The micro-arc oxidation is 30min, and the thickness of the titanium surface is about 33

[0028] The porous layer is μm; X-ray diffraction analysis shows that the film layer is mainly composed of hydroxyapatite; the surface profiler measures the film layer roughness Ra=2.9μm; the film bonding strength is 37MPa, which has good biological activity.

Embodiment 3

[0030] Using 125μm TiO 2 Grit blasting of titanium alloy. Use distilled water to prepare a solution containing 0.02 mol / L of sodium dihydrogen phosphate and 0.2 mol / L of calcium nitrate. With sandblasting pretreated titanium alloy as anode and stainless steel or titanium as cathode, DC pulse power supply is used for micro-arc oxidation. The voltage is 250-450V, the frequency is 300Hz, and the duty cycle is 60%; the electrolyte temperature is kept at 30-50°C. The oxidation deposition time is 60 minutes; a porous layer with a thickness of about 28 μm is formed on the titanium surface; X-ray diffraction analysis shows that the film layer is mainly composed of hydroxyapatite; the surface roughness of the film layer is Ra=3.6 μm measured by the surface profiler; the film layer The binding strength is 33MPa, and it has good biological activity.

technical field

[0001] The invention relates to a method for preparing a bioactive film layer on the surface of a medical metal material, in particular to a bioactive film layer on the surface of a titanium metal used as a femur, a hip joint and a tooth root and a sandblasting-micro-arc oxidation composite process thereof. Background technique

[0002] In recent years, the development and application of various biomedical materials have developed rapidly, among which metal materials were the first to be used. Metal biomaterials generally have high strength and toughness, and are suitable for hard tissue repair and fixation. Commonly used metal biomaterials include cobalt-based alloys, tantalum, titanium, and titanium alloys. Among them, titanium and its alloys are widely used for their superior corrosion resistance, high specific strength, good biocompatibility, and suitable for implantation. attention. However, due to the low surface hardness and poor wear resistance of t...

Examples

Embodiment 1

[0025] Using 25μm Al 2 o 3Sandblasted titanium. Use distilled water to prepare a solution containing 0.01 mol / L of sodium phosphate, 0.01 mol / L of sodium β-glycerophosphate, and 0.5 mol / L of calcium acetate. With sandblasting pretreated titanium as the anode and stainless steel or titanium as the cathode, DC power is used for micro-arc oxidation. The voltage is 300-500V; keep the electrolyte temperature not higher than 50°C. The micro-arc oxidation was 5 minutes, and a porous layer with a thickness of about 20 μm was formed on the titanium surface; X-ray diffraction analysis showed that the film layer was mainly composed of hydroxyapatite; the surface roughness of the film layer was measured by the surface profiler Ra=2.1 μm; the film layer The binding strength is 43MPa, and it has good biological activity.

Embodiment 2

[0027] The titanium alloy is sandblasted with 75 μm SiC. Use distilled water to prepare a solution containing 0.15 mol / L of sodium β-glycerophosphate and 0.3 mol / L of calcium chloride. With sandblasting pretreated titanium alloy as the anode and stainless steel or titanium as the cathode, DC power is used for micro-arc oxidation. The voltage is 200-400V; keep the electrolyte temperature not higher than 50°C. The micro-arc oxidation is 30min, and the thickness of the titanium surface is about 33

[0028] The porous layer is μm; X-ray diffraction analysis shows that the film layer is mainly composed of hydroxyapatite; the surface profiler measures the film layer roughness Ra=2.9μm; the film bonding strength is 37MPa, which has good biological activity.

Embodiment 3

[0030] Using 125μm TiO 2 Grit blasting of titanium alloy. Use distilled water to prepare a solution containing 0.02 mol / L of sodium dihydrogen phosphate and 0.2 mol / L of calcium nitrate. With sandblasting pretreated titanium alloy as anode and stainless steel or titanium as cathode, DC pulse power supply is used for micro-arc oxidation. The voltage is 250-450V, the frequency is 300Hz, and the duty cycle is 60%; the electrolyte temperature is kept at 30-50°C. The oxidation deposition time is 60 minutes; a porous layer with a thickness of about 28 μm is formed on the titanium surface; X-ray diffraction analysis shows that the film layer is mainly composed of hydroxyapatite; the surface roughness of the film layer is Ra=3.6 μm measured by the surface profiler; the film layer The binding strength is 33MPa, and it has good biological activity.