中国组织工程研究
中國組織工程研究
중국조직공정연구
Journal of Clinical Rehabilitative Tissue Engineering Research
2014年
47期
7561-7565
,共5页
生物材料%口腔生物材料%稳态电位%电偶序%电偶腐蚀%纯钛%金合金%钴铬合金%钛合金%镍铬合金
生物材料%口腔生物材料%穩態電位%電偶序%電偶腐蝕%純鈦%金閤金%鈷鉻閤金%鈦閤金%鎳鉻閤金
생물재료%구강생물재료%은태전위%전우서%전우부식%순태%금합금%고락합금%태합금%얼락합금
titanium%gold aloys%chromium aloys
背景：国内有学者运用动电位极化技术测定常用牙科金属自腐蚀电位值来评价低贵金属的腐蚀性能，发现合金的贵金属含量是影响其耐腐蚀性能的主要原因。目的：评价TA2型商业纯钛、金合金、钴铬合金、钛合金及镍铬合金的体外耐腐蚀性能。方法：将TA2型商业纯钛、金合金、钴铬合金、钛合金及镍铬合金分别浸入人工唾液中，运用动电位极化技术测量5种材料在人工唾液中的自腐蚀电位和自腐蚀电流密度。结果与结论：5种合金的自腐蚀电位值由大到小排列顺序为金合金、商业纯钛、钛合金、钴铬合金、镍铬合金；金合金与纯钛电位较正，不易发生腐蚀；钛合金和钴铬合金居中，由于可以形成稳定氧化膜，具有较强的抗孔蚀和缝隙腐蚀能力；镍铬合金电位较负，则较容易发生溶解。5种合金的自腐蚀电流密度值排列顺序为金合金<商业纯钛<钛合金<钴铬合金<镍铬合金；金合金与纯钛电流密度值较小，达10-8，这表明金合金和纯钛的腐蚀速度较小，镍铬合金的腐蚀速度最大。结果说明金合金、纯钛是耐腐蚀性较好的材料，镍铬合金的腐蚀速度最大，应尽量避免用镍铬合金作为种植体上部结构。
揹景：國內有學者運用動電位極化技術測定常用牙科金屬自腐蝕電位值來評價低貴金屬的腐蝕性能，髮現閤金的貴金屬含量是影響其耐腐蝕性能的主要原因。目的：評價TA2型商業純鈦、金閤金、鈷鉻閤金、鈦閤金及鎳鉻閤金的體外耐腐蝕性能。方法：將TA2型商業純鈦、金閤金、鈷鉻閤金、鈦閤金及鎳鉻閤金分彆浸入人工唾液中，運用動電位極化技術測量5種材料在人工唾液中的自腐蝕電位和自腐蝕電流密度。結果與結論：5種閤金的自腐蝕電位值由大到小排列順序為金閤金、商業純鈦、鈦閤金、鈷鉻閤金、鎳鉻閤金；金閤金與純鈦電位較正，不易髮生腐蝕；鈦閤金和鈷鉻閤金居中，由于可以形成穩定氧化膜，具有較彊的抗孔蝕和縫隙腐蝕能力；鎳鉻閤金電位較負，則較容易髮生溶解。5種閤金的自腐蝕電流密度值排列順序為金閤金<商業純鈦<鈦閤金<鈷鉻閤金<鎳鉻閤金；金閤金與純鈦電流密度值較小，達10-8，這錶明金閤金和純鈦的腐蝕速度較小，鎳鉻閤金的腐蝕速度最大。結果說明金閤金、純鈦是耐腐蝕性較好的材料，鎳鉻閤金的腐蝕速度最大，應儘量避免用鎳鉻閤金作為種植體上部結構。
배경：국내유학자운용동전위겁화기술측정상용아과금속자부식전위치래평개저귀금속적부식성능，발현합금적귀금속함량시영향기내부식성능적주요원인。목적：평개TA2형상업순태、금합금、고락합금、태합금급얼락합금적체외내부식성능。방법：장TA2형상업순태、금합금、고락합금、태합금급얼락합금분별침입인공타액중，운용동전위겁화기술측량5충재료재인공타액중적자부식전위화자부식전류밀도。결과여결론：5충합금적자부식전위치유대도소배렬순서위금합금、상업순태、태합금、고락합금、얼락합금；금합금여순태전위교정，불역발생부식；태합금화고락합금거중，유우가이형성은정양화막，구유교강적항공식화봉극부식능력；얼락합금전위교부，칙교용역발생용해。5충합금적자부식전류밀도치배렬순서위금합금<상업순태<태합금<고락합금<얼락합금；금합금여순태전류밀도치교소，체10-8，저표명금합금화순태적부식속도교소，얼락합금적부식속도최대。결과설명금합금、순태시내부식성교호적재료，얼락합금적부식속도최대，응진량피면용얼락합금작위충식체상부결구。
BACKGROUND:Domestic scholars use the potentiodynamic polarization technique to determine the corrosion potential of the dental aloys, which is used to evaluate the corrosion performance of the lownoble metal. They have discovered that the main reason affecting corrosion resistance is the content of noble metal. OBJECTIVE:To evaluate the corrosion resistance of Ti, Au aloy, Co-Cr aloy, Ti aloy, and Ni-Cr aloy. METHODS: Five aloys were immersed in synthetic saliva solution. The corrosion potential and corrosion current density of the aloys were determined with potentiadynamic polarization technique. RESULTS AND CONCLUSION:The galvanic series of five kinds of aloys were ranged as folows: Au aloy > pure Ti > Ti aloy > Co-Cr aloy > Ni-Cr aloy. Au aloy and pure Ti had more positive potential that were not easy to produce corrosion; Ti aloy and Co-Cr aloy could form stable oxidation film with a strong ability of anti-pitting and crevice corrosion; Ni-Cr aloy potential was more negative and easy to be dissolved. The corrosion current density of five kinds of aloys was ranged as folows: Au aloy < pure Ti < Ti aloy < Co-Cr aloy < Ni-Cr aloy. Au aloy and pure Ti had lowest current density which was 10-8, indicating that the corrosion rate of Au aloy and pure Ti was lower; in contrast, Ni-Cr aloy possessed the maximum corrosion rate. These findings indicate that Au aloy and pure Ti exhibit a very high corrosion resistance. The corrosion rate of Ni-Cr aloy is the highest; therefore, Ni-Cr aloy is the least acceptable material for implant suprastucture.
