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J Biomech. Author manuscript; available in PMC 2010 May 29.

Published in final edited form as:

Published online 2009 April 8. doi: 10.1016/j.jbiomech.2009.02.021

PMCID: PMC2683914

NIHMSID: NIHMS102474

Elastohydrodynamic lubrication (EHL) protects soft tissues from damage and wear in many biological systems (e.g. synovial joints, cornea of the eye, and pleural surfaces of the lung and chest wall). Among studies of lubrication of deformable solids, few have examined the effects of external loads, geometry, and material properties on EHL of soft tissues. To examine these effects, we studied the tribology of soft tissues in a two dimensional finite element simulation of a thin layer of fluid separating a sliding rigid surface from a soft asperity or bump with an initial sinusoidal shape. We computed the frictional force, deformation of the solid, and change in fluid thickness as functions of independent variables: sliding velocity, normal load, material properties, and bump amplitude and length. Double logarithmic regression was used to determine the exponents of the scaling relationships of friction coefficient and minimum fluid thickness to the independent variables. The analysis showed that frictional shear force is strongly dependent on velocity, viscosity, and load, moderately dependent on bump length and elasticity, and only weakly dependent on the bump amplitude. The minimum fluid thickness is strongly dependent on velocity and viscosity, and changes moderately with load, elasticity, amplitude, and length. The shape of the bump has little effect. The results confirm that the shear-induced deformation of an initially symmetrical shape, including generalizations to other symmetrical geometries such as quadratic or piecewise linear bumps, leads to load-supporting behavior.

The study of elastohydrodynamic lubrication (EHL) in biological systems has received considerable attention in the last two decades. Dowson and colleague investigated the role of tribology in natural synovial joint regions and metal joint replacements (Dowson and Zhong-Jin, 1986) and showed that a microelastohydrodynamic regime smoothes out the unevenness of cartilage surfaces under loading conditions in synovial joints and that EHL is a major regime associated with the tribology of synovial joints. Later, using an iterative numerical procedure, Dowson and Jin, 1992) studied the influence of geometrical variables of a single sinusoidal asperity on the minimum fluid thickness. They observed that fluid thickness increases with longer wavelengths as the sinusoidal bump becomes flattened. Later, they studied microelastohydrodynamic lubrication of a single asperity analytically (Jin and Dowson, 1997). They found that when the amplitude of roughness increases or the wavelength decreases the overall film thickness decreases, confirming their earlier numerical study. Skotheim and Mahadevan (2005) considered a combination of different geometries and material properties, and showed that in lubrication of soft materials, elastic deformation couples tangential and normal forces leading to load-supporting behavior.

For several years, we have been exploring mechanisms that may affect lubrication in serosal cavities (e.g. the pleural and pericardial spaces), in which soft tissues slide against each other without discernable wear. The nature of lubrication in these regions, whether mixed (implying points of contact) or elastohydrodynamic, is still in debate. Using computational methods, Lai et al. (2002) modeled the pleural space in two dimensions as a deformable flat membrane sliding against a rigid bump. Their study showed that motion between pleural surfaces reduces unevenness of the surfaces and prevents asperities from touching. Subsequently, Gouldstone et al. (2003) used finite element methods to model the pleural space in two dimensions. The results confirmed that the deformation due to sliding leads to smoothening of the surface and promotes uniformity of fluid thickness. They found that longer bumps undergo larger deformations resulting in more uniform fluid thickness. We later modeled the interaction of soft solid and fluid in 3D using a simple cylindrical geometry with an uneven solid-fluid interface in rotation (Moghani et al., 2007). Our result indicated that deformation of soft solids in EHL generates a positive net pressure profile which is load supporting. Frictional shear torque was less than proportional to normal load, as expected in soft material lubrication (Hamrock, 1994).

When an uneven soft surface is deformed by sliding to generate lift and reduce friction, how do material properties and morphologic features of the sliding surface affect frictional force? In this paper we modeled the interaction of an initially symmetrical deformable asperity with a lubricated sliding surface, using ADINA-FSI, a finite element software package for analysis of solid interactions with fluid. We examined the effects of material properties, geometry, velocity, and load on friction coefficient, minimum fluid thickness, and deformation of the asperity. We captured the essence of these relationships using scaling arguments, and determined the scaling exponents with double logarithmic regression.

We consider a deformable 2D sine-shaped geometry separated by fluid from a sliding flat surface. We adopt Cartesian coordinates(*x*, *z*), where *x* and *z* are longitudinal and transverse axes relative to the fluid channel respectively, as shown in Fig 1. The top boundary of the solid is constrained to vertical displacements and is initially located at *z* = *h*_{0} + *A* + *h _{s,}* where

The initial undeformed geometry of the bottom surface of the solid is given by,

$$h={h}_{0}+A(1-sin\pi x/L)$$

(1)

where *h* is the fluid thickness as a function of *x* in the interval [0,*L*].

The solid is pressed downward by a uniform pressure *P* at the top boundary. The bottom plane of the fluid moves with uniform velocity *V* in the *x* direction. Zero fluid pressure is imposed at the fluid inlet and outlet (*x* = 0, *L*). The solid-fluid interface has a no-slip boundary condition.

We modeled the solid as linearly elastic, isotropic, and nearly incompressible with Poisson’ s ratio υ=0.49. Hydrodynamic pressures remind sufficiently small to enable the lubricant to be treated as Newtonian and incompressible. We neglect gravitational, inertial, and thermal effects.

Special mixed-interpolated elements are used to improve the continuity of pressure within the soft solid. We used plane strain 9-node solid elements, the most accurate 2D elements available in ADINA for soft materials, and 9-node fluid elements suitable for Stokes flows. We used a direct method in which solid and fluid models are solved together in one matrix system, improving the stability and robustness. Because all pressures in biological spaces are atmospheric to within a few percent, no attempt was made to simulate cavitation.

We studied the effects of the independent variables: amplitude *A*, length *L,* velocity *V,* normal load (applied pressure) *P,* viscosity *μ*, and elastic Young’s modulus *E* on the friction coefficient *F _{c}* (defined as the ratio of axial shear force on the bottom solid boundary to the normal force load), and minimum fluid thickness

With six independent variables and three fundamental dimensions (mass, length, time), there are three dimensionless groups according to Buckingham’s theorem (Shames, 1982). For convenience (and specifically to isolate the pressure to only one dimensionless variable), we choose *A*/*L, P*/*E,* and *μV/LE* as the sufficient set of three. The friction coefficient is already nondimensional; the minimum fluid thickness is nondimensionalized by channel length. We write the scaling equations as

$${F}_{c}={k}_{1}{(A/L)}^{{\alpha}_{1}}{(P/E)}^{{\beta}_{1}}{(\mu V/LE)}^{{\gamma}_{1}}$$

(2)

$${h}_{min}/L={k}_{2}{(A/L)}^{{\alpha}_{2}}{(P/E)}^{{\beta}_{2}}{(\mu V/LE)}^{{\gamma}_{2}}$$

(3)

The logarithms of Eq. 2 and 3 are linear functions of the exponents; these were determined by regression over variations in the dimensionless groups. This allowed us to characterize the dependence of friction coefficient *F _{c}* and minimum fluid thickness

The steady state behavior of the model was examined for a combination of geometrical variables(*A*,*L*), material properties(*E*, *μ*), loading condition (*P*), and velocity (*V*), by performing a transient analysis and allowing sufficient time for the results to reach steady state. Fig. 2 shows the pressure distribution of the deformed solid and fluid models simulated at reference values (Table 1). Positive and negative hydrodynamic pressures upstream and downstream of the bump deformed it, elongating the converging channel and shortening the diverging channel to create an asymmetric wedge that supports the normal load.

The dependence of the friction coefficient *F _{c}* on the dimensionless groups

Normal and longitudinal deformation under 2 normal pressures. Normal and longitudinal displacements are of similar magnitude.

Fig. 3b shows that *F _{c}* decreases with

Fig. 3c shows that *F _{c}* increases with

Fig. 4 shows normal (*z)* and longitudinal (*x*) deformations of the bump surface under reference conditions with loads *P* = 20 and 40 Pa. Normal and longitudinal deformations are of similar magnitude and increase slightly with increasing *P*.

Fig. 5a shows changes in *h*_{min} with *A*/*L* for fixed *P/E* and *μV*/*LE.* As *A*/*L* increases *h*_{min} decreases, i.e. for a constant length *L*, rougher bumps lead to thinner *h*_{min.} It is of interest that roughness has little effect on *F _{c,}* whereas it has a considerable influence on

Fluid thickness as a function of position under bumps of amplitudes *A* = 0.0005 and *A* = 0.001 cm at *V* = 0.6 cm/s and *F*_{N} = 40*μ*N.

Fig. 5b shows that under higher *P/E*, *h*_{min} gets thinner while the rate of thinning decreases as *P*/*E* increases.

Fig. 5c shows that *h*_{min} increases as *μV*/*LE* increases for constant *A*/*L* and *P*/*E* (i.e. the fluid layer gets thicker for higher values of *V* or *μ*).

For the friction coefficient, we used the data from 120 simulations using various geometrical, loading and material conditions. The independent variables were changed in the range provided in Table 2 for all the simulations. Regression analysis resulted in the following relationships:

$${F}_{c}=2.58{(A/L)}^{-0.018}{(P/E)}^{-0.66}{(\mu V/LE)}^{0.52}$$

(4)

$${h}_{min}/L=0.84{(A/L)}^{-0.21}{(P/E)}^{-0.30}{(\mu V/LE)}^{0.59}$$

(5)

Figs. 7 and and88 show the fit of *F _{c}* and

In the previous section we characterized lubrication properties for a sine-shaped geometry. Here we examine the role of shape in EHL. Consider a simple case of a piecewise linear wedge. We computed friction coefficients of linear and sine-shaped asperities under identical conditions. Fig. 9 shows a comparison of friction coefficient for the two geometries. It is of interest that the friction coefficients for the two geometries are almost identical while minimum fluid thickness is less for the linear wedge according to Fig. 10. This is consistent with the following argument: the effective fluid thickness (occurring under the flattened segment) happens over a longer length of the asperity in the sine-shaped geometry, increasing *F _{c,}* whereas the minimum thickness is thicker for this geometry and contributes to a decrease in

Comparison of friction coefficients between two geometries: sine-shaped wedge and piecewise linear wedge.

Our simulations included only a single bump, whereas biological tissues and other soft deformable surfaces have multiple bumps on their surface. The load support generated by a single bump in our 2-D model could also be simulated in a 3-D model with multiple bumps, each bump supplying load support to maintain separation of tissues. However, in a simple 2-D model configured with multiple bumps, there would be no mechanism whereby the fluid in the space between bumps could be replenished independent of the flow past neighboring bumps. This would cause pressure in the spaces between bumps to be determined by the imbalance of flow past the adjacent bumps, and each bump would thus strongly influence its neighbors. In a 3-D model, this artifactual interdependence would be less important because the fluid between bumps forms an interconnected reservoir of approximately constant pressure, allowing multiple bumps to provide relatively independent load support. Although we were limited by computational considerations to a 2D model with one bump, we believe our qualitative findings are valid for 3D situations with multiple bumps.

We studied the tribology of soft tissues in a two dimensional finite element simulation of a thin layer of fluid separating a sliding rigid surface from a soft asperity initially sine-shaped. We computed the frictional force and minimum fluid thickness as functions of sliding velocity, normal load, material properties, and bump amplitude and length.

Double logarithmic regression was used to determine the exponents of the scaling relationships of friction coefficient and minimum fluid thickness to the independent variables. Results showed that frictional shear force is strongly dependent on velocity, viscosity, and load, moderately dependent on bump length and elasticity, and only weakly dependent on the bump amplitude. The minimum fluid thickness is strongly dependent on velocity and viscosity, and changes moderately with load, elasticity, bump amplitude, and length.

We conclude that softer material and longer bump wavelength lead to a decrease in the friction coefficient and an increase in the minimum fluid thickness, improving lubrication performance. However, variations in velocity, viscosity, or load lead to changes in friction coefficient and minimum fluid thickness of the same sign. For example, increasing load *P* decreases *F _{c}* by improving the load-bearing qualities of the shape but simultaneously decreases

Note that in *vivo* not all these parameters enjoy a large range. For example, velocity and load are usually dictated by environment. However, in artificial joints one can improve the unevenness on the sliding surfaces or the elasticity of material to protect the surfaces from wear (e.g. modifying to longer bump wavelength or using softer materials).

We studied the influence of shape on lubrication behavior of soft asperities by comparing piecewise linear to sine-shaped wedge. The results showed little dependence of friction coefficient on shape in EHL, while fluid thickness was different depending on the geometrical shape. Importantly, the morphology of the asperity has little effect on friction. The results confirm that shear induced deformation of an initially symmetrical shape leads to load-supporting behavior, and suggest that an uneven soft surface sliding in lubricant will be deformed so as to generate lift and maintain separation between the surfaces.

This work was supported by a grant HL-63737 from the National Institutes of Health.

**Conflict of interest statement**

The authors have no financial or other interest that could affect the objectivity with which they approach the subject matter of this investigation.

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