In the retrieval analysis of explanted hip joints, the estimation of wear volume and visualization of wear pattern are commonly used to evaluate in-vivo performance. While many studies report wear volumes from explanted hips, it is important to understand the limitations of these estimates including the sources and magnitude of uncertainty of the reported results. This study builds on a previous uncertainty analysis by Carmignato et al. to quantify the magnitude of uncertainty caused by the assumption that the as-manufactured shape of an explanted hip component is a perfect sphere. Synthetic data sets representing idealized measurements of spheroidal explants (prolate, oblate and pinched) with a nominal diameter of 50 mm were generated. These data sets represent the shape and magnitude of form deviations observed for explanted hip components (Figure 1). Data were simulated for either unworn components or those with a known volume and magnitude of wear simulated to represent 5 µm penetration of a 49.90 mm femoral head into an acetabular cup (Table 1). The volume of wear and wear pattern were estimated using a custom Matlab script developed for analysis of metrology data from explanted hip joints. This script fits a least squares sphere to data points in unworn, as manufactured regions of the surface to estimate the as-manufactured shape of the component. The diameter of the best fit sphere, and wear volume were compared to the known wear depths and volumes from the synthetic datasets. The results showed that the Matlab script estimated a wear volume of up to 1.4 mm3 for an unworn cup with a radial deviation of 10 µm. The maximum error of 13.3 mm3 was for a pinched cup with wear at the pole. The complete results are shown in Table 2. In some cases with aspherical form deviations, the least squares sphere fitted to the synthetic data was displaced in the Z direction with respect to the origin of the spheroid and the radius of the least squares sphere was outside the range of the principal radii of the spheroid. For instance, in case 5, the center was shifted 22 µm vertically from the mathematical center. The results from this study show that the magnitude of uncertainty due to form deviations on wear volume varies depending on the shape and magnitude of the form deviations and in some cases was greater than 10 mm3. A further important finding is that in some instances, the diameter and center of the least squares sphere fitted to the unworn regions may not be consistent with the mathematical radius and center of the synthetic data. This may have important implications for the “reverse engineering” of the as-manufactured dimensions from worn explanted hip joints.
Figure 1 Graphical depiction of a) synthetic data set, b) deviation map of a hemispherical acetabular cup with simulated wear, c) deviation map of a prolate spheroid with simulated wear at rim with color bar set to ±5 microns, d) deviation map of pinched ellipsoid with simulated wear at 45 degrees from pole.
There is considerable interest in the orthopaedic community in understanding the multifactorial process of taper fretting corrosion in total hip arthroplasty (THA). Previous studies have identified some patient and device factors associated with taper damage, including length of implantation, stem flexural rigidity, and head offset. Due to the complexity of this phenomenon, we approached the topic by developing a series of matched cohort studies, each attempting to isolate a single implant design variable, while controlling for confounding factors to the extent possible. We also developed a validated method for measuring material loss in retrieved orthopaedic tapers, which contributed to the creation of a new international standard (ASTM F3129-16). Based on our implant retrieval collection of over 3,000 THAs, we developed independent matched cohort studies to examine (1) the effect of femoral head material (metal vs. ceramic, n=50 per cohort) and (2) stem taper surface finish (smooth vs. microgrooved, n=60 per cohort). Within each individual study, we adjusted for confounding factors by balancing implantation time, stem taper flexural rigidity, offset, and, when possible, head size. We evaluated fretting and corrosion using a four-point semiquantitative score. We also used an out-of-roundness machine (Talyrond 585) to quantify the material loss from the tapers. This method was validated in a series of experiments of controlled material removal on never-implanted components.Introduction
Methods
Previous studies of retrieved CoCr alloy femoral heads have identified imprinting of the stem taper surface features onto the interior head bore, leading researchers to hypothesize that stem taper microgrooves may influence taper corrosion. However, little is known about the role of stem taper surface morphology on the magnitude of in vivo corrosion damage. We designed a matched cohort retrieval study to examine this issue. From a multi-institutional retrieval collection of over 3,000 THAs, 120 femoral head-stem pairs were analyzed for evidence of fretting and corrosion using a visual scoring technique based on the severity and extent of fretting and corrosion damage observed at the taper. A matched cohort design was used in which 60 CoCr head-stem pairs with a smooth stem taper were matched with 60 CoCr head-stem pairs having a micro-grooved surface, based on implantation time, flexural rigidity, apparent length of taper engagement, and head size. This study was adequately powered to detect a difference of 0.5 in corrosion scores between the two cohorts, with a power of 82% and 95% confidence. Both cohorts included CoCr and Ti-6-4 alloy femoral stems. A high precision roundness machine (Talyrond 585, Taylor Hobson, UK) was used to measure surface morphology and categorize the stem tapers into smooth vs. micro-grooved categories. Fretting and corrosion damage at the head/neck junction was characterized using a modified semi-quantitative adapted from the Goldberg method by three independent observers. This method separated corrosion damage into four visually determined categories: minimal, mild, moderate and severe damage.Introduction
Methods
First-generation annealed HXLPE has been clinically successful at reducing both clinical wear rates and the incidence of osteolysis in total hip arthroplasty. However, studies have observed oxidative and mechanical degradation occurring in annealed HXLPE. Thus, it is unclear whether the favorable clinical performance of 1st generation HXLPE is due to the preservation of bearing surface tribological properties or, at least partially, to the reduction in patient activity. The purpose of this study was to evaluate the in vitro wear performance (assessed using multidirectional pin-on-disk (POD) testing) of 1st-generation annealed HXLPE with respect to in vivo duration, clinical wear rates, oxidation, and mechanical properties. 103 1st-generation annealed HXLPE liners were collected at revision surgery. 39 annealed HXLPE liners were selected based on their implantation time and assigned to three equally sized cohorts (n=13 per group); short-term (1.4–2.7y), intermediate term (5.2–8.0y) and long-term (8.3–12.5y). From each retrieved liner, two 9-mm cores were obtained (one from the superior region and one from the inferior region). Sixteen cores were fabricated from unimplanted HXLPE liners that were removed from their packaging and six pins from unirradiated GUR 1050 resin served as positive controls. Multidirectional POD wear testing was conducted against wrought CoCr disks in a physiologically relevant lubricant (20 g/L protein concentration) using a 100-station SuperPOD (Phoenix Tribology, UK). Each pin had its own chamber with 15mL lubricant maintained at 37±1°C. An elliptical wear pattern with a static contact stress of 2.0 MPa was employed. Testing was carried out to 1.75 million cycles at 1.0 Hz and wear was assessed gravimetrically. POD wear rates were calculated using a linear regression of volumetric losses. In vivo penetration was measured directly using a calibrated micrometer. Oxidation was assessed on thin films obtained from superior and inferior regions of the liners (ASTM 2102). Mechanical properties were assessed using the small punch test (ASTM 2183).Introduction
Materials and Methods
Previous studies regarding modular head-neck taper corrosion were largely based on cobalt chrome (CoCr) alloy femoral heads. Less is known about head-neck taper corrosion with ceramic femoral heads. We asked (1) whether ceramic heads resulted in less taper corrosion than CoCr heads; (2) what device and patient factors influence taper fretting corrosion; and (3) whether the mechanism of taper fretting corrosion in ceramic heads differs from that in CoCr heads.Background:
Questions/purposes:
