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. 2010 Jun 18;43(9):1787-93.
doi: 10.1016/j.jbiomech.2010.02.014. Epub 2010 Mar 1.

Macroscopic assessment of cartilage shear: effects of counter-surface roughness, synovial fluid lubricant, and compression offset

Quynhhoa T Nguyen  1 , Benjamin L Wong, June Chun, Yeoung C Yoon, Frank E Talke, Robert L Sah
Affiliations

Macroscopic assessment of cartilage shear: effects of counter-surface roughness, synovial fluid lubricant, and compression offset (V体育官网入口)

Quynhhoa T Nguyen et al. J Biomech. .

"V体育ios版" Abstract

During joint articulation, cartilage is subjected to compression, shear, and sliding, mechanical factors that regulate and affect cartilage metabolism. The objective of this study was to use an in vitro material-on-cartilage shear test to elucidate the effects of counter-surface roughness (Polished, Mildly rough, and Rough), lubricants (phosphate buffered saline (PBS) and bovine synovial fluid (bSF)), and compression offset on the shearing and sliding of normal human talar cartilage under dynamic lateral displacement. Peak shear stress (sigma(xz,m)) and strain (E(xz,m)) increased with increasing platen roughness and compression offset, and were 30% higher with PBS than with bSF. Compared to PBS, bSF was more effective as a lubricant for P than for M and R platens as indicated by the higher reduction in kinetic friction coefficient (-60% vs. -20% and -19%, respectively), sigma(xz,m) (-50% vs. -14% and -17%) and E(xz,m) (-54% vs. -19% and -17%). Cartilage shear and sliding were evident for all counter-surfaces either at low compression offset (10%) or with high lateral displacement (70%), regardless of lubricant. An increase in tissue shear occurred with either increased compression offset or increased surface roughness VSports手机版. This material and biomechanical test system allow control of cartilage sigma(xz,m) and E(xz,m), and hence, sliding magnitude, for an imposed lateral displacement. It therefore can facilitate study of cartilage mechanobiological responses to distinct regimes of cartilage loading and articulation, such as shear with variable amounts of sliding. .

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Conflict of interest statement

CONFLICT OF INTEREST

The authors have no conflicts of interest to disclose.

Figures

Figure 1
Figure 1
Mechanical loading sequence. (A) Samples were compressed to 3 levels, δ1, δ2, and δ3 and allowed to stress-relax for 30 minutes. δ1, δ2, and δ3 are either 10, 20, 30% strain relative to initial thickness or compression levels to achieve 0.05, 0.1, and 0.2 MPa equilibrium compressive stress. (B) After relaxation, 3 cycles of lateral displacement of Upx (30% or 70% of the compressed thickness) were applied. (C) The time axis was expanded to show details of the applied lateral displacements.
Figure 2
Figure 2
Schematics of applied dynamic lateral displacement (A, C, and E), expected patterns of lateral force response (B, D, and F) and predicted relationships between loading platen and cartilage tissue (illustrations) in three regimes: full adhesion, moderate friction with relatively high shear, and low friction with relatively low shear, respectively. Loading platen has compressed cartilage by displacement d, and then translates laterally between upx = 0 and upx = Upx during the period T. Other variables and parameters, ux(t), Fx(t), upx, Ux, and Fx,m are described in the text. (A, B) When the lateral displacement is relatively small (< Ux), the tissue deforms without sliding. (C, D). When the lateral displacement is intermediate (between Ux and 2Ux) with moderate friction, cartilage underwent relatively high shear. (E, F) When the displacement is relatively large (> 2Ux) with low friction, cartilage underwent relatively low shear in all cycles.
Figure 3
Figure 3
The effects of the compression offset (10, 20, and 30%), counter-surface roughness ((A, B, C) polished, (D, E, F) mildly rough, and (G, H, I) rough platen), and lubricant type (PBS and bSF) on the average lateral force and corresponding shear stress over 3 cycles of dynamic lateral displacement e. Lateral displacement was applied at equilibrium after compression by (A, D, G) 10%, (B, E, H) 20%, and (C, F, I) 30%. Samples were tested in lubricant baths of PBS and then bovine synovial fluid. Data shown are average values with SEM shown for selected data points near peak values, n=6.
Figure 4
Figure 4
Biomechanics of shearing-sliding for samples compressed by 10, 20, and 30% in lubricant baths of PBS and then bovine synovial fluid. Samples were tested with platens that had polished (P, Ra=0.12μm), mildly rough (M, Ra=1.3μm), and rough (R, Ra=8.0μm) counter-surface. (A) Equilibrium compressive stress. (B,C,D) Maximum shear stress. (E,F,G) Maximum shear strain [% compressed thickness]. Data shown are mean ± SEM, n=6.
Figure 5
Figure 5
Coefficient of kinetic friction for samples compressed by 0.05, 0.1, and 0.2 MPa stress levels. Samples were tested in lubricant bath of PBS and then bovine synovial fluid and with platens that had polished (P), mildly rough (M), and rough (R) surface. Data shown are mean ± SEM, n=4.
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