Abstract
The quasi-static mechanical behaviour of the aortic valve (AV) is highly non-linear and anisotropic in nature and reflects the complex collagen fibre kinematics in response to applied loading. However, little is known about the viscoelastic behaviour of the AV. The aim of this study was to investigate porcine AV tissue under uniaxial tensile deformation, in order to establish the directional dependence of its viscoelastic behaviour. Rate dependency associated with different mechanical properties was investigated, and a new viscoelastic model incorporating rate effects developed, based on the Kelvin-Voigt model. Even at low applied loads, experimental results showed rate dependency in the stress–strain response, and also hysteresis and dissipation effects. Furthermore, corresponding values of each parameter depended on the loading direction. The model successfully predicted the experimental data and indicated a ‘shear-thinning’ behaviour. By extrapolating the experimental data to that at physiological strain rates, the model predicts viscous damping coefficients of 8.3 MPa s and 3.9 MPa s, in circumferential and radial directions, respectively. This implies that the native AV offers minimal resistance to internal shear forces induced by blood flow, a potentially critical design feature for substitute implants. These data suggest that the mechanical behaviour of the AV cannot be thoroughly characterised by elastic deformation and fibre recruitment assumptions alone.
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Acknowledgments
AAB is funded by a studentship from the UK Engineering & Physical Sciences Research Council (EPSRC). Research was also supported by a Discipline Bridging Initiative (DBI) grant from the EPSRC and Medical Research Council (MRC).
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Appendix 1
Appendix 1
Let the variables (a 1, a 2, a 3) identify a particle in the original configuration of the continuum, and (x 1, x 2, x 3) be the coordinates of that particle when the body is deformed. The deformation of the body is known if (x 1, x 2, x 3) is a known function of (a 1, a 2, a 3) [29]:
This could mathematically be considered as a transformation from a 1, a 2, a 3 to x 1, x 2, x 3. The transformation is one-to-one, such that is the functions in (11) are single-valued, continuous and have a unique inverse:
for every point in continuum [29].
Consider an infinitesimal line element connecting the point P(a 1, a 2, a 3) to a neighbouring point P′(a 1 + da 1, a 2 + da 2, a 3 + da 3). The length of the line PP′ in the original configuration of the continuum will be:
When P and P′ are deformed to the points Q(x 1, x 2, x 3) and Q′(x 1 + dx 1, x 2 + dx 2, x 3 + dx 3), respectively, the length ds of the new deformed QQ′ line is:
From Eqs. 11 and 12 one can get:
Considering Eq. 15, Eqs. 13 and 14 can now be written as:
where δ ij is the Kronecker delta. Now the following can be written:
The Green strain tensor is defined by the term in parenthesis in the above equation as [29]:
Defining the extension ratios in the principle planar directions of 1 and 2 by λ 1 and λ 2, as the ratio of the final length of the element to its original length, we will have:
Now the components of the Green strain tensor in Eq. 19 for deformation in directions 1 and 2 can be written by the extension ratios in Eq. 20 as:
Taking the time derivative of Eq. 18 gives the rate of deformation tensor in terms of the time rate of Green strain tensor:
where v i is the ith component of the in-plane velocity field, x i , and the rate of deformation tensor would be:
For an arbitrary choice of coordination component, and considering Eq. 22, the above equation becomes:
From Eqs. 21 and 24, the components of the rate of deformation tensor in directions 1 and 2 can be obtained as:
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Anssari-Benam, A., Bader, D.L. & Screen, H.R.C. A combined experimental and modelling approach to aortic valve viscoelasticity in tensile deformation. J Mater Sci: Mater Med 22, 253–262 (2011). https://doi.org/10.1007/s10856-010-4210-6
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DOI: https://doi.org/10.1007/s10856-010-4210-6