The potential for bone and poly(methyl methacrylate) (PMMA) debris to initiate wear on ASTM-F75 and ASTM-F799 CoCrMo alloys articulating against ultrahigh molecular weight polyethylene (UHMWPE) was investigated. Third-body wear particles of bone and PMMA bone cement (with and without the radiopacifier, barium sulfate) were introduced between CoCrMo and UHMWPE in a reciprocating sliding wear test. A scanning electron microscope and a white light interference surface profilometer were used to study the surface damage and quantify the surface roughnesses of the worn alloys. The CoCrMo alloys, which are widely used as the femoral components in total artificial knees and hips, showed surface damage as the result of wear in the presence of bone or PMMA debris. Severe scratches were generated within 2700 cycles (94.5-m sliding distance) on the alloy's surface. Ploughing was the major wear mechanism. Carbides in the F75 alloy surface appeared to be unaffected by the debris. A quantitative study was performed on the surface roughness (average roughness, R(a), and root mean square roughness, RMS) of the alloy after wear testing. A nonparametric Wilcoxon rank sum test of wear severity (R(a) and RMS) was performed based on the surface roughness data. The surfaces of the specimens tested with the PMMA and bone particles were significantly rougher than those of the controls (p < 0.01). Small scratches also occurred on some of the control specimen surfaces and may have been second-body wear caused by defects and impurities in the UHMWPE.

In this study, we analyzed the surface roughness of retrieved cobalt-chromium-molybdenum (CoCrMo) femoral components of porous coated anatomic (PCA) artificial total knee joints, using a white light interference surface profilometer (WLISP). Thirty-eight PCA retrieved specimens obtained from the Anderson Clinic (Arlington, VA) were used. The artificial knees were originally implanted between 1982-1993, and the specimens were retrieved during revision surgeries between 1988-1996. We examined specimens damaged by three wear modes: femoral component against the ultra high molecular weight polyethylene (UHMWPE) articular surface (mode I), femoral component against the metal tibial tray (because of UHMWPE tibial component wear-through) (mode II), and femoral component against metal-debris-embedded-UHMWPE (with metal debris from the porous coating) (mode III). The mean surface roughness of each femoral component was the average of 80 surface roughness measurements. The in vivo alloy femoral component surfaces were rougher by an order of magnitude over controls, and the alloy surfaces were predominantly worn by the formation of parallel scratches in the direction of articulation. There was no correlation between the surface roughness of the femoral components and patient age, sex, weight, and total time of implantation. Significant surface roughness increases accompanied mode II and mode III wear. Different carbide morphologies were found on different femoral component surfaces, indicating that a variety of sintering processes, with different times and temperatures, may have been applied to the alloy femoral components during manufacture. Metal component roughness may be important to the wear of UHMWPE components and the success of total artificial knee joint.

The articulating surfaces of CoCrMo alloy wear specimens and retrieved femoral components of artificial total knee joints are subject to uneven wear. A repeatable and reliable measurement method is necessary to evaluate the surface damage. In this study, the surface roughness of CoCrMo alloy specimens subjected to in vitro third-body wear, and retrieved femoral components of knee joints were analyzed using a white light interference surface profilometer. Each third-body wear specimen was divided into a 19x19 grid of 1-mm(2) squares (361 squares) and each femoral condyle of retrieved specimens was divided into two 10x10 grids of 1-mm(2) squares (100 squares). The surface roughness average (Ra) and root mean square roughness (RMS) were measured for each of the squares. The average of all points measured was defined as the true surface roughness mean (TSRM). Measurements were then performed on 40-60 (in vitro specimens) or 30 (retrieved specimens) randomly selected points on each surface and a cumulative average was calculated. The cumulative average surface roughness value from only a few (5-15) measurement points generated large deviations (>40%) from the TSRM, but converged to the TSRM as the number of measurements increased. The number of randomly selected points necessary for the cumulative average roughness to be within 10% of the TSRM was defined as the representative measurement number (RMN). The RMN for the third-body wear specimens (surface area of 573 mm(2)) was 40 points, and the RMN for the retrieved femoral components (surface area of 100 mm(2)) was 20 points. To obtain the cumulative surface roughness average within a desired percentage of the TSRM, it is important to define or experimentally determine the critical minimum number of measurements, RMN. Several types of measurements may be necessary to understand wear and damage on metal components of artificial knee joints. The TSRM represents a consistent and reproducible measure of surface damage, and a starting point to develop appropriate measurement protocols to quantify damage on a specific surface.

No abstract

No abstract