Cartilage Biomechanics

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Biphasic Nature

Synovial joints have high loads applied to them statically, cyclically, and repetitively over a lifetime. The solid matrix, the collagens, proteoglycans, and other molecules is arranged in such a way to to sustain these loads. It must be strong, fatigue-resistant, and tough.

What we find regarding the material properties of cartilage is that it is porous, permeable, and very soft. Water makes up a large percentage of the total weight, and can flow through the porous-permeable solid matrix by pressure gradients or compaction of the matrix. The term biphasic means that cartilage can be viewed as having both a solid phase and a fluid phase.

Permeability

Water can flow through the cartilage with applied pressure gradients across the tissue. It has a very large frictional drag coefficient and so any interstitial fluid flow causes large drag forces to be generated. Therefore very high pressure gradients are needed to move water through cartilage.

Also, with compression water can flow through the porous-permeable solid matrix. The compressive stress leads to the solid matrix being compacted, which raises the pressure in the interstitium, and forces the fluid out of the tissue.

There is a direct relationship between permeability and water content, and an inverse relationship between permeability and proteoglycan content.

Viscoelasticity

Articular cartilage is viscoelastic, meaning it exhibits a time dependent behaviour when subjected to constant load or deformation.

It displays creep, in that with constant compression stress, deformation increases will time, until an equilibrium is reached. Similarly, with a constant strain, the stress rises to a peak, and then slowly relaxes until an equilibrium is reached.

There are two mechanisms that provide articular cartilage with viscoelastic properties: flow-independent, and flow-dependent mechanisms.

Flow-independent: derives from intermolecular friction
Flow-dependent: derives from interstitial fluid flow and pressurisation. The drag that comes about from interstitial fluid flow is the main contributor to the compressive viscoelastic behaviour.

Flow Dependent Properties with Compression

Under constant load, with creep continuing, the load supported is slowly transferred from the fluid phase to the solid phase as the fluid pressure reduces. In normal cartilage it takes 2.5 to 6 hours to reach this equilibrium, at which point the load is supported entirely by the compressed collagen-proteoglycan solid matrix.

In vivo, this equilibrium doesn't ever occur because the joints tend to always move even with sleep. Therefore there is almost always fluid pressurisation within the tissue. In normal states, fluid pressurisation is the dominant physiologic load-supporting mechanism. The solid matrix is very soft, and has a low permeability, and so allows for this. The ratio of load supported by fluid pressure to that supported by solid matrix is greater than 20 to 1 in normal tissue.

In early osteoarthritic change, there is increased water content and decreased proteoglycan content. This leads to increased tissue permeability, which in turn reduces the fluid pressurisation mechanism of load support in cartilage. In this setting, the solid matrix is called upon to bear more of the load, which is detrimental to the long term viability of cartilage.

Flow Independent Properties with Shear

Collagen is organised randomly with entrapped proteoglycan molecules in the middle zones of cartilage . This contributes to its shear stress-strain curve.

There is a nonlinear response with increasing compression leading to increased resistance to shear stresses.

With pure shear forces, there is no interstitial fluid flow because there is no pressure gradient or volume change.

The stiffness and energy dissipation of cartilage in shear is provided by the proteoglycan-collagen structure, not by the proteoglycan-proteoglycan network. The proteoglycans function to maintain the inflated spatial form of the collagen network, rather than providing any significant resistance to shear.

Tensile Properties

With stretching or compression of a material there is always a change in volume, and so both flow-dependent and flow-independent viscoelastic processes occur with tension stresses.

The tensile modulus is the proportionality constant in the linear phase of the stress-strain curve, and it varies from 5 to 50 MPa. The tensile modulus depends on the many variable such as location, depth, and composition. Superficial zone cartilage is stiffer than middle and deep zone cartilage due to higher concentration and higher degree of collagen fibrils. There is a reduction in tensile stiffness with osteoarthritic changes.

Cartilage Swelling

Swelling is the increase in size or weight with a material being soaked in solution. Articular cartilage swells because of physicochemical forces. Physicochemical refers to the force deriving from the charged nature of the proteoglycans. Proteoglycans have 1 or 2 negative charges on each dimeric hexosamine. In osteoarthritis, the fixed charge density dramatically reduces due to loss of proteoglycans.

The negative charges need opposing positive charges for electroneutrality, and the total ion concentration in the tissue needs to be greater than that in the bath. The ion imbalance leads to an internal swelling pressure greater than the pressure in the bath. This swelling pressure is restrained by the stress from the solid matrix that resists expansion. It is thought that collagen provides most of the resistance to swelling pressure.

How much the swelling pressure contributes to load support depends on the load that is applied. In light loads, the swelling pressure has significant contribution. For highly loaded structures in physiological range and in dynamically loaded structures, it is uncertain how much the swelling pressure contributes.

In early osteoarthritis, the loss of swelling pressure is less severe than the compromise of mechanical properties of the solid matrix.