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CORROSION DISSOLUTION OF AN IMPLANT MADE OF NZ30K ALLOY ALLOYED WITH Ag AND COATED WITH A LAYER OF SILVER IN A MODEL SOLUTION OF THE OSTEOSYNTHESIS PROCESS
Abstract
In this paper, the magnesium alloy NZ30K alloyed with 0.1 wt. % Ag and clad with a 900 nm thick silver layer. It has been found that in the Ringer-Locke solution, the cylindrical sample underwent contact corrosion over the entire surface and crevice corrosion at the transition from the cylindrical to the flat part, which caused the coating delamination from the alloy under the mechanical action of hydrogen "bubbles" formed at the cathodic areas and corrosion products in the crevice, which have a higher specific volume than the Ringer-Locke solution. It has been found that the sample has subjected to the greatest localized corrosion damage during the first 1020 seconds of testing in this solution, since its corrosion potential Ecor during this period was rapidly shifting to the negative side at a rate of 0.04 mV/s. This is due to an intensive increase in the contact area of the alloy with the Ringer-Locke solution, since the standard potential of the alloy is about 3V more negative than that of the silver coating. It was recorded that the rate of shift of the corrosion potential Ecor of the sample to the negative side slowed down to 0.0063 mV/s until its stationary value Ecor = -1.471 V has been established after 2300 seconds of testing. This is due to the "inhibition" of anodic corrosion processes from crevice corrosion in the above-mentioned areas of the sample and the development of contact corrosion at a constant rate. The NZ30K + 0.1 wt.% Ag alloy clad with a 900 nm thick silver layer is recommended for the manufacture of biodegradable implants for the treatment of bone fractures and its research in clinical conditions, given the negative impact of stress concentrators in its manufacture.
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