Metallic biomaterials are used in medical devices in humans more than any other family of materials. The corrosion resistance of an implant material affects its functionality and durability and is a prime factor governing biocompatibility. The fundamental paradigm of metallic biomaterials, except biodegradable metals, has been “the more corrosion resistant, the more biocompatible.” The body environment is harsh and raises several challenges with respect to corrosion control. In this invited review paper, the body environment is analysed in detail and the possible effects of the corrosion of different biomaterials on biocompatibility are discussed. Then, the kinetics of corrosion, passivity, its breakdown and regeneration in vivo are conferred. Next, the mostly used metallic biomaterials and their corrosion performance are reviewed. These biomaterials include stainless steels, cobalt-chromium alloys, titanium and its alloys, Nitinol shape memory alloy, dental amalgams, gold, metallic glasses and biodegradable metals. Then, the principles of implant failure, retrieval and failure analysis are highlighted, followed by description of the most common corrosion processes in vivo. Finally, approaches to control the corrosion of metallic biomaterials are highlighted.

Corrosion of Metallic Biomaterials: A Review

Triboelectrochemical techniques and interpretation methods in tribocorrosion: A comparative evaluation

In modern history, metals have been used as implants since more than 100 years ago when Lane first introduced metal plate for bone fracture fixation in 1895 (Lane, 1895). In the early development, metal implants faced corrosion and insufficient strength problems (Lambotte, 1909, Sherman, 1912). Shortly after the introduction of the 18-8 stainless steel in 1920s, which has had far-superior corrosion resistance to anything in that time, it immediately attracted the interest of the clinicians.

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Metals for Biomedical Applications

Titanium alloys are widely used in total-joint replacements due to a combination of outstanding mechanical properties, biocompatibility, passivity, and corrosion resistance. Nevertheless, retrieval studies have pointed out that these materials can be subjected to localized or general corrosion in modular interfaces when mechanical abrasion of the oxide film (fretting) occurs. Modularity adds large crevice environments, which are subject to micromotion between contacting interfaces and differential aeration of the surface. Titanium alloys are also known to be susceptible to hydrogen absorption, which can induce precipitation of hydrides and subsequent brittle failure. In this work, the surface of three designs of retrieved hip-implants with Ti-6Al-4V/Ti-6Al-4V modular taper interfaces in the stem were investigated for evidence of severe corrosion and precipitation of brittle hydrides during fretting-crevice corrosion in the modular connections. The devices were retrieved from patients and studied by means of scanning electron microscopy (SEM), X-ray diffraction (XRD), and chemical analysis. The surface qualitative investigation revealed severe corrosion attack in the mating interfaces with evidence of etching, pitting, delamination, and surface cracking. In vivo hydrogen embrittlement was shown to be a mechanism of degradation in modular connections resulting from electrochemical reactions induced in the crevice environment of the tapers during fretting-crevice corrosion.

In vivo severe corrosion and hydrogen embrittlement of retrieved modular body titanium alloy hip‐implants

Recently, “tribocorrosion,” a research area combining the science of tribology and corrosion, has drawn attention from scientists and engineers belonging to a wide spectrum of research domains. This is due to its practical impact on daily life and also the accompanying economical burdens. It encompasses numerous applications including the offshore, space, and biomedical industry, for instance, in the case of artificial joints (Total Hip Replacement, THR) in orthopedic surgery, where implant metals are constantly exposed to tribological events (joint articulations) in the presence of corrosive solutions, that is, body fluids. Keeping the importance of this upcoming area of research in biomedical applications in mind, it was thought to consolidate the work in this area with some fundamental aspects so that a comprehensive picture of the current state of knowledge can be depicted. Complexity of tribocorrosion processes has been highlighted, as it is influenced by several parameters (mechanical and corrosion) and also due to the lack of an integrated/efficient test system. Finally a review of the recent work in the area of biotribocorrosion is provided, by focusing on orthopedic surgery and dentistry.

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Significance of Tribocorrosion in Biomedical Applications: Overview and Current Status

https://oatao.univ-toulouse.fr/651/1/Viguier_651.pdf

Influence of oxide films on primary water stress corrosion cracking initiation of alloy 600

Fretting-corrosion of materials used as orthopaedic implants

Wear analysis of materials used as orthopaedic implants

Several grades of 18% chromium-8% nickel stainless steel (SS) with varying sulfur contents and immersed in 3% sodium chloride (NaCl) demonstrated essentially passive behaviors, with local ...

Effect of Complex Inclusions on Pit Initiation in 18% Chromium-8% Nickel Stainless Steel Types 303, 304, and 321

Wear of Poly (methyl methacrylate), PMMA, against a metallic surface, AISI 316L stainless steel (SS) has been investigated in dry conditions. These materials have been used to simulate the degradation of the contact, femoral stem-bone cement in the field of hip prosthesis. First of all, no significant wear was observed on the 316L SS. PMMA wear has been quantified: the energy wear coefficient, slope of the line, and wear volume according to the cumulated dissipated energy, don't depend on the normal load, FN. This energy analysis allows predicting the PMMA wear depth. According to the comparison between the measured dissipated energy and the energy breaking polymer chains, mechanical dissipated energy is used essentially to transform third body structure and to expel it from the contact between the two materials. Moreover, the experimental results have highlighted the stick-slip phenomenon. Lastly, Attenuated Total Reflectance-Fourier Transform InfraRed and Reflection Absorption-Fourier Transform InfraRed have shown that PMMA debris configuration and conformation have changed after wear against 316L SS. The driving force of these changes seems to be the acid–base interactions between PMMA and hydroxyl groups of the SS surface. POLYM. ENG. SCI., 47:633–648, 2007. © 2007 Society of Plastics Engineers.

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Pierre Combrade

Papers

Influence of oxide films on primary water stress corrosion cracking initiation of alloy 600

Fretting-corrosion of materials used as orthopaedic implants

Wear analysis of materials used as orthopaedic implants

Effect of Complex Inclusions on Pit Initiation in 18% Chromium-8% Nickel Stainless Steel Types 303, 304, and 321

Wear of poly (methyl methacrylate) against a metallic surface in dry conditions