Problems with Common Medical Implants

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Introduction

Common types of medical implants are ar-throplastical prostheses, or joint replacements, which serve to take over joint functions for patients suffering from musculoskeletal dysfunction or severe pains in e.g. the knee, hip (see Figure 1), or shoulder. Joint replacements generally consist of multiple parts made of different materials. The common hip joint re-placement prosthesis shown in Figure 2 consists of a metal ball, socket and stem and a plastic spacer. The metals used are mostly CoCr, austenitic stainless steels, Co–Cr–Mo alloys and Ti or Ti alloys, for their hardness, corrosion resistance, fracture toughness, low modulus and good machinability [1, 2]. The plastic spacer is typically made of polyethylene. The prosthesis is secured to the host body through either press-fitting or cementing .

Biocompatibility of a material refers to “(i) an appropriate response of the host tissue and living system to the material, and (ii) the response of the material due to contact with living matter” [1]. A lack of biocompatibility can have an undesirable effect on the functionality of prostheses due to e.g. metal toxicity or sensitivity and osteolysis.

Figure 1. X-ray image of a pelvis with total hip joint replacement [3].

Osteolysis is the loss of bone due to polyethylene wear debris. Small parts of polyethylene from the prosthesis lead to inflammation , which in turn may cause loosening of the implant–tissue interface [4]. Loosening may also occur due to wear debris or fatigue of the cement or metal, leading to painful implant movement inside the bone.

Figure 2. Typical metal-and-plastic ball-and-socket hip joint replacement prosthesis

[www.ntmc.go.jp.e.eo.hp.transer.com/p_other/contents/66.htm].

Corrosion o...

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...lectric field over the electrolyte leads to the deposition of the oxide film onto the base material;

2 Locally increasing the voltage over the electrolyte until a critical value is reached results in local breakdown of the oxide film and locally changes the TiO2 layer structure (within 1 ms);

3 Subsequent repetition of (2) over the entire film surface leads to the modification of the entire TiO2 film.

The resulting modified film can be divided into two layers — the inner layer (of thickness ~15 µm) is hard and highly abrasive and protects the base material, while the outer layer (of thickness 10–20 μm) is porous and worn out relatively easily but promotes tissue generation. Moreover, application of Ca2+- and PO43−-containing electrolytes leads to the incorporation of Ca and P ions into the film, in turn providing in nutrition for new tissue generation [12].

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