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Quantification of Self-Polishing from Ex Vivo 36mm Metal-on-Metal Total Hip Prostheses +
1Joyce, T J;
1Grigg, H;
12Langton, D J;
2Nargol, A V N
+1Newcastle University, Newcastle upon Tyne, UK,
2University Hospital of North Tees, Stockton on Tees, UK
INTRODUCTION:
Most total hip replacement operations are very successful procedures.
Typically a hip prosthesis consists of a cobalt chrome femoral head
which articulates within a polymeric acetabular cup. The majority of hip
prostheses fail due to aseptic loosening, which is considered to be the
body’s reaction to polyethylene wear debris. Therefore one way to
remove this problem is to replace the polyethylene with a harder
material such as cobalt chrome, to give a metal-on-metal (MoM)
articulation. Clinical results for such MoM hip prostheses are generally
positive and similar encouraging results are also reported from in vitro
studies [1]. In these laboratory tests ‘self polishing’ of the articulating
surfaces of test prostheses has been reported [2]. Self polishing
describes a beneficial process in which surfaces become smoother
through the process of articulating against each other. Therefore self-
polishing can also be tied in with a ‘bedding in’ period. Self-polishing
has been claimed from explanted hip prostheses but these assertions are
based on qualitative rather than quantitative data [3-5].
METHODS:
Two MoM total hip prostheses, consisting of femoral head and
acetabular cup, of 36mm nominal articulating diameter, were obtained at
revision surgery (figure 1). The explants were examined using a ZYGO
NewView 5000 non-contacting profilometer. This device allowed
measurements of surface roughness to be obtained and these were taken
at a range of positions on the explanted heads and cups. A minimum of
165 readings were taken per component. Roughness was measured in
terms of Ra (roughness average) and Rsk (skewness). In addition the
spherical diameters of each head and cup were measured using a
Mitutoyo 544 co-ordinate measuring machine. From these
measurements, together with knowing the material properties of cobalt
chrome and typical operating conditions for a total hip replacement the
minimum effective film thickness and thus the lambda ratio was
calculated for the total hip replacement when new, based on the
‘unworn’ area, and for the ‘worn’ area using the following equations [6]: 21.0
2*
65.0
*
min 80.2
−
=
xxxRE
w
RE
u
R
h η
( ) ( )[ ] 2/12
2
2
1
min
aaRR
h
+=λ
In the above equations, hmin is the minimum effective film thickness (m),
Rx is the effective radius (m), η is the lubricant viscosity (Pa s), u is the
entraining velocity (m/s), E* is the equivalent elastic modulus (Pa), w is
the load (N), λ is the lambda ratio, and Ra1 and Ra2 are the roughness
values of the femoral head and acetabular cup.
Fig. 1: The femoral head (left) and acetabular cup (right) from one of the
explanted total hip replacements.
RESULTS: The roughness data indicted that, in the ‘worn’ (figure 2) areas, Ra
values were reduced compared with ‘unworn’ (figure 3) parts of the
articulating surfaces of the explants. Typical values were 0.006µm Ra
and 0.020µm Ra respectively. In addition the Rsk values were negative
in the ‘worn’ areas compared with positive in the ‘unworn’ areas. Using
the measured data allowed lambda ratios of 0.9 (boundary lubrication)
for the ‘unworn’ area, and 3.0 (mild mixed lubrication) in the ‘worn’
area to be calculated.
Fig. 2: Typical topography of ‘worn’ region of explant. Note lack of
localized peaks, multi-directional scratches and Ra value of 0.003µm.
Fig. 3: Typical topography of ‘unworn’ region of explant. Note
localized peaks, lack of scratches and Ra value of 0.015µm.
DISCUSSION:
To the authors’ best knowledge this is the first time that quantitative
data related to the surface topography of explanted MoM total hip
replacements has been offered which supports the concept of self-
polishing in vivo. While other papers have offered this opinion, Milosev
et al [4] only offered Ra data for femoral components, and both Milosev
et al [4] and Reinisch et al [5] reported on components that had high
(0.1-0.15µm and 0.07µm respectively) Ra values in both ‘worn’ and
‘unworn’ areas. In addition the skewness values reported here show that
the surface has changed from one with a majority of peaks (positive
Rsk) to one with a majority of ‘valleys’ (negative Rsk). The lambda
ratios also indicate that these prostheses, when ‘worn’ would have
operated in the benign mild mixed lubrication regime, a useful
improvement on the lower initial lambda ratios.
REFERENCES:
[1] Rieker, C.B., Schon, R. and Kottig, P., “Development and
validation of a second-generation metal-on-metal bearing:
Laboratory studies and analysis of retrievals”, J Arthroplasty, 19
(8, Supp 1), 2004, 5-11.
[2] Firkins, P.J., Tipper, J.L., Ingham, E., Stone, M.H., Farrar, R. and
Fisher, J., “Influence of simulator kinematics on the wear of
metal-on-metal hip prostheses”, J Engng in Med, 215, 2001, 119-
121.
[3] Sieber, H., Rieker, C. and Kottig, P., “Analysis of 118 second-
generation metal-on-metal retrieved hip implants”, J Bone Jt Surg,
81-B, 1999, 46-50.
[4] Milosev, I., Trebse, R., Kovac, S., Cor, A. and Pisot, V.,
“Survivorship and Retrieval Analysis of Sikomet metal-on-metal
total hip replacements at a mean of seven years”, J Bone Jt Surg,
88(6), 2006, 1173-1182.
[5] Reinisch, G., Judmann, K.P., Lhotka, C., Lintner, F. and
Zweymuller, K.A., “Retrieval study of uncemented metal-metal
hip prostheses revised for early loosening”, Biomaterials, 24,
2003, 1081-1091.
[6] Jin, Z.M., Stone, M., Ingham, E. and Fisher, J., “Biotribology”,
Current Orthopaedics, 20(1), 2006, 32-40.
Poster No. 2276 • 56th Annual Meeting of the Orthopaedic Research Society