Polyethylene in total hip arthroplasty: half a century in the limelight
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- García-Rey, E. & García-Cimbrelo, E. J Orthopaed Traumatol (2010) 11: 67. doi:10.1007/s10195-010-0091-1
It is well known that polyethylene (PE) wear is the major limiting factor in longevity of primary total hip arthroplasty (THA) . Many studies report that cup loosening due to wear is the most frequent reason for revision in the long term for both cemented and uncemented THA, especially in young and active patients [2, 3, 4, 5, 6, 7]. To date, this phenomenon is known to produce osteolysis secondary to particle debris on both the acetabular and femoral sides [3, 8, 9, 10, 11]. Ultrahigh molecular weight PE was introduced by Sir John Charnley in the early 1960s. He developed the low-friction arthroplasty (LFA) consisting of cemented fixation with a bearing surface of a 22.25-mm metallic femoral head and an all-PE cup . That type of PE has been used for >40 years and is still the most frequent bearing surface used in total joint replacements.
Conventional PE is sterilized by gamma irradiation in air. This process offers the benefits of molecular cross-linking but can also produce free radicals that, in the presence of air, oxidize . Oxidation decreases resistance of the biomaterial, resulting in degradation and brittle PE, and thus may increase wear . PE wear is multifactorial: among the different factors associated with wear are a patient’s higher activity level, a big femoral-head diameter or thin PE liners, vertical orientation of the acetabular cup, or the use of modular uncemented cups [15, 16]. When PE wear is evaluated on radiographs, penetration of the femoral head into the PE liner is examined. The different radiographic methods of evaluating PE wear include manual [17, 18, 19, 20] and digitized methods using two- and three-dimensional techniques [15, 21, 22, 23]. All these techniques suffer from different degrees of error and are of limited value, as they have only been validated in a laboratory model but not in vivo studies . Sychterz et al. assessed the time pattern of PE wear on X-rays and reported different findings; they observed that femoral-head penetration into the PE liner is due to two different phenomena: the so-called bedding-in process, which is the result of creep and settling of the liner into the cup; and true wear, which is due to the removal of particles [22, 25]. Bedding-in occurs in the first two postoperative years and true wear over time. These results have recently been confirmed by different authors [26, 27].
In another study, we evaluated two different generations of a cementless cup to assess clinical and radiological results over a minimum follow-up of 10 years . We compared 83 Harris-Galante I and 93 Harris-Galante II hemispherical uncemented cups (Zimmer, Warsaw, IN, USA) with a conventional PE liner sterilized by gamma irradiation in air using 32- and 28-mm femoral-head diameters, respectively. Nine Harris-Galante I cups and two Harris-Galante II cups were revised due to aseptic loosening or PE problems. When we analyzed the lineal PE wear using the above-described method, we observed that the initial PE wear at 6 months after surgery was greater for the first-generation cup, although the mean wear was similar in both cups. Mean femoral-head penetration at 6 week after surgery was 0.15 ± 0.05 mm for the Harris-Galante I cup and 0.12 ± 0.03 for the Harris-Galante II cup (P < 0.001); but mean wear was 0.13 ± 0.23 mm/year for the Harris-Galante I cup and 0.11 ± 0.10 for the Harris-Galante II cup (P = 0.740). The appearance of radiolucent lines and osteolysis was related to a greater initial wear, greater mean wear, and greater wear at the end of follow-up. Most metallic shells in both groups showed stable fixation. The so-called second-generation cups had a lower initial PE wear that resulted in less PE wear at the latest the follow-up, but the overall wear rate was similar in both groups despite the different femoral-head sizes and the improved locking mechanism. In both studies, we confirmed that the most important factor to affect the long-term result of a THA, especially in the uncemented cups, is PE wear rather than bone fixation, which usually is not a problem. We also observed the bedding-in or creep process that occurs when we sequentially analyzed penetration of the femoral head into the PE liner, described by Sychterz and others. Factors that influence PE wear, such as a vertical cup position or thin liner (like the ACS system) are also described, as well as other factors related to the design, such as a locking mechanism of the cup to the PE liner or the femoral-head size not influencing the mean wear but only the initial bedding-in process. This last observation could be examined by the probability that liner thickness and cup settling into the liner as well as PE creep that occur during the first postoperative 2 years are more important for final wear than other factors.
Since the late 1980s, new PEs have been developed to lessen the effects of wear. Different methods of sterilization have also been used to avoid the appearance of free radicals and their oxidation. These methods include gamma radiation in nitrogen, low-oxygen package, ethylene oxide, or plasma gas . Clinical results of these PEs did not improve over conventional PE, and some were even worse [32, 33, 34].
New highly cross-linked polyethylenes
Different clinical studies comparing conventional and highly cross-linked polyethylene
Results of wear (mm/year)
Digas et al. 
Digas et al. 
Manning et al. 
Dorr et al. 
Engh et al. 
Geerdink et al. 
Uncemented ABG II
Triclot et al. 
Garcia-Rey et al. 
The so-called second-generation HXLPE is being developed. To decrease free radical oxidation and increase the mechanical properties of the polymers, different strategies are being used. The sequential annealing process maintains the mechanical properties of the PE at the same time as it theoretically reduces the production of free radicals. In vitro preliminary results report better performance by this newer HXLPE than with conventional or even first-generation HXLPE [52, 53]. The other strategy is to introduce vitamin E, the antioxidant alpha-tocopherol, into ultra-high-molecular weight PE (UHMWPE) prior to consolidation to help prevent the oxidative degradative reaction. This would avoid the deleterious effect of the melting process that decreases the mechanical properties of PE . Preliminary in vitro results report good wear and improved mechanical and fatigue properties .
The orthopedic surgeon must keep in mind that the most important factor limiting primary THA longevity is PE wear. In most cases, with primary osteoarthritis and avascular necrosis without acetabular bone loss, bone fixation is achieved independently regardless of the choice of cemented or uncemented implant. Thus, the bearing surface would seem to be one of the critical aspects. Mid-term results of new highly cross-linked PEs seem to indicate that HXLPE is one of the materials of choice, especially in young and/or active patients with a long life expectancy and who are being considered for a THA.
Conflict of interest
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