A biphasic finite element study on the role of the articular cartilage superficial zone in confined compression

Abstract

The aim of this study was to investigate the role of the superficial zone on the mechanical behavior of articular cartilage. Confined compression of articular cartilage was modeled using a biphasic finite element analysis to calculate the one-dimensional deformation of the extracellular matrix (ECM) and movement of the interstitial fluid through the ECM and articular surface. The articular cartilage was modeled as an inhomogeneous, nonlinear hyperelastic biphasic material with depth and strain-dependent material properties. Two loading conditions were simulated, one where the superficial zone was loaded with a porous platen (normal test) and the other where the deep zone was loaded with the porous platen (upside down test). Compressing the intact articular cartilage with 0.2 MPa stress reduced the surface permeability by 88%. Removing the superficial zone increased the rate of change for all mechanical parameters and decreased the fluid support ratio of the tissue, resulting in increased tissue deformation. Apparent permeability linearly increased after superficial removal in the normal test, yet it did not change in the upside down test. Orientation of the specimen affected the time-dependent biomechanical behavior of the articular cartilage, but not equilibrium behavior. The two tests with different specimen orientations resulted in very different apparent permeabilities, suggesting that in an experimental study which quantifies material properties of an inhomogeneous material, the specimen orientation should be stated along with the permeability result. The current study provides new insights into the role of the superficial zone on mechanical behavior of the articular cartilage.

Keywords: Articular cartilage; Biphasic; Confined compression; Finite element analysis; Superficial zone.

Fig. 1

Schematic diagram of the confined compression tests modeled where the cartilage is orientated normal (left) and upside down (right).

Fig. 2

Depth-dependent aggregate modulus (Chen et al., 2001; Schinagl et al., 1997; Wang et al., 2001) and initial permeability (Maroudas, 1968) of the articular cartilage used in the models.

Fig. 3

Overall strain (a) and peak strain (b) as functions of time in different cases.

Fig. 4

Apparent aggregate modulus (a) and permeability (b) for different cases.

Fig. 5

Permeabilities at the cartilage surface close to the porous plate in different cases. The permeabilities were constant after 100s, and only the results for 0 to 200s are shown. For the upside–down orientation, the permeability was similar for all cases (intact and SZ removed), and thus only one case was plotted. Initial permeabilities are represented by open circles.

Fig. 6

Permeability (a), compressive strain (b), compressive stress (c), and maximum principal shear stress (d) at z=1.2 mm of the articular cartilage in different cases.

Fig. 7

Fluid support ratios as functions of time in different cases.