- 學位論文
陽極處理製程參數對商業用純鈦表面耐受性質之影響
Study on the Tolerance of Ceramic Coatings on Commercial Pure Titanium Surfaces Obtained Through Anodic Treatments
摘要
本研究將生醫級純鈦(GR.4)金屬試片經陽極發色、陽極Type II處理及微弧氧化處理後，對試片進行其表面形貌、成份分析、結晶相分析、粗糙度、潤濕性分析、表面硬度測試、表面耐磨耗測試、表面耐腐蝕測試，以進行其表面性質評估。 研究結果顯示生醫級純鈦(GR.4)經陽極發色、陽極Type II處理及微弧氧化處理後表面形成TiO2氧化膜層且表面富含氧及磷元素；於陽極Type II處理隨著電壓與氧化時間影響氧化膜層厚度，且表面有氣泡及推擠產生的痕跡，具TiO2(Anatase)結晶相，使其表面粗糙度由50.3nm和51.3nm提升至73.0nm，硬度因氧化膜層增厚使其硬度由263.7 HV和282 HV上升至最高346.86HV，硬度與粗糙度的提升，影響試片表面之耐磨耗性，刮痕深度由5.2μm和4.5μm下降至最低0.5μm，表面富含氧及磷元素使其接觸角值由60.53°和58.99°下降至最低40.39°，因氧化膜層影響生醫級純鈦(GR.4)經陽極處理後，表面腐蝕電位(Ecorr)由-0.2 Ewe/V和 -0.23Ewe/V增加至0.1 Ewe/V，表面氧化膜層較為耐腐蝕；於微弧氧化處理隨著電壓與氧化時間影響氧化膜層厚度隨之增加，且表面具微孔洞及TiO2(Anatase)結晶相，使其表面粗糙度由50.3nm和51.3nm提升至111.2nm，硬度因氧化膜層增厚使其硬度由263.7 HV和282 HV上升至最高372.64HV，硬度與粗糙度的提升，影響試片表面之耐磨耗性，刮痕深度由4μm和3μm下降至最低0.2μm，表面富含氧及磷元素使其接觸角值由60.53°和58.99°下降至最低35.89°，因氧化膜層影響生醫級純鈦(GR.4)經陽極處理後，表面腐蝕電位(Ecorr)由-0.2 Ewe/V和-0.23Ewe/V增高-0.06 Ewe/V，表面氧化膜層較為耐腐蝕；綜合上述得知，兩製程處理後在表面分析結果皆優於未經處理之生醫級純鈦(GR.4)及陽極發色處理，可預期此兩製程具有良好機械性質。
並列摘要
In this study, after the biomedical pure-grade titanium (GR.4) metal test specimen was subjected to anodizing, Type II anodizing and micro-arc oxidation, the surface morphology, material analysis, crystalline phase analysis, roughness, wettability analysis, surface hardness test, surface wearability test, surface corrosion test are conducted to the test specimen in order to evaluate its surface properties. The results show that, after biomedical pure-grade titanium (GR.4) was subjected to anodizing, Type II anodizing and micro-arc oxidation, TiO2 oxide film forms on the surface which is rich in oxygen and phosphorus. It was addressed with Type II anodizing, and the thickness of oxide film was influenced by voltage and oxidation time; also, bubbles traces of pushing are likely formed on the surface. It possesses TiO2 (Anatase) with crystalline phase, and thus the surface roughness was increased from 50.3nm and 51.3nm to 73.0nm; the hardness was also increased from 263.7 HV and 282 HV to a maximum of 346.86 HV due to thicker oxide film. The increase of hardness and roughness can affect the wearability of the test specimen’s surface. The scratch depth decreases from 5.2μm and 4.5μm to a minimum of 0.5μm. The surface is rich in oxygen and phosphorus, which results in the decrease of contact angle value from 60.53° and 58.99° to a minimum of 40.39°. The surface electric corrosion potential (Ecorr) increased from -0.2 Ewe/V and -0.23Ewe/V to 0.1 Ewe/V due to oxide film after anodizing of biomedical pure-grade titanium (GR.4); thus, it is more resistant to corrosion. The thickness of the oxide film increases due to voltage and oxidation time after the micro-arc oxidation, and the surface has micro-pores and TiO2 (Anatase) crystalline phase, which increases the surface roughness from 50.3nm and 51.3nm to 111.2 nm, and the hardness increases from 263.7 HV and 282 HV to a maximum of 372.64 HV due to thicker oxide film. The increase of hardness and roughness can affect the wearability of the test specimen’s surface. The scratch depth decreases from 4 μm and 3 μm to a minimum of 0.2μm. The surface is rich in oxygen and phosphorus, which results in the decrease of contact angle value from 60.53° and 58.99° to a minimum of 35.89°. The electric corrosion potential (Ecorr) is increased by -0.2 Ewe/V and -0.23Ewe/V to -0.06 Ewe/V due to oxide film after anodizing of biomedical pure-grade titanium (GR.4); thus, it is more resistant to corrosion. In sum, the surface analysis results show that the performance after both addressing is better than non-addressed biomedical pure-grade titanium (GR.4) and anodizing. It is expected that the two addressing have good mechanical properties.