Abstract
The mechanical behavior of most biological soft tissue is nonlinear viscoelastic rather than elastic. Many of the models previously proposed for soft tissue involve ad hoc systems of springs and dashpots or require measurement of time-dependent constitutive coefficient functions. The model proposed here is a system of evolution differential equations, which are determined by the long-term behavior of the material as represented by an energy function of the type used for elasticity. The necessary empirical data is time independent and therefore easier to obtain. These evolution equations, which represent non-equilibrium, transient responses such as creep, stress relaxation, or variable loading, are derived from a maximum energy dissipation principle, which supplements the second law of thermodynamics. The evolution model can represent both creep and stress relaxation, depending on the choice of control variables, because of the assumption that a unique long-term manifold exists for both processes. It succeeds, with one set of material constants, in reproducing the loading–unloading hysteresis for soft tissue. The models are thermodynamically consistent so that, given data, they may be extended to the temperature-dependent behavior of biological tissue, such as the change in temperature during uniaxial loading. The Holzapfel et al. three-dimensional two-layer elastic model for healthy artery tissue is shown to generate evolution equations by this construction for biaxial loading of a flat specimen. A simplified version of the Shah–Humphrey model for the elastodynamical behavior of a saccular aneurysm is extended to viscoelastic behavior.
Similar content being viewed by others
References
Anthony RL, Caston RH, Guth E (1942) Equations of state for natural and synthetic rubber-like materials. I. J Phys Chem 46:826–840
Apter JT (1964) Mathematical development of a physical model of some visco-elastic properties of the aorta. Bull Math Biophys 26:267–288
Apter JT, Marquez E (1968) Correlation of visco-elastic properties of large arteries with microscopic structure. IV. Circ Res 22:393–404
Apter JT, Rabinowitz M, Cummings DH (1966) Correlation of visco-elastic properties of large arteries with microscopic structure. I, II, III. Circ Res 19:104–121
Bennett MB, Ker RF, Dimery NJ, Alexander RMcN (1986) Mechanical properties of various mammalian tendons. J Zool Lond A 209:537–548
Bonet J (2001) Large strain viscoelastic constitutive models. Int J Solids Struct 38:2953–2968
Coleman BD (1964) Thermodynamics of materials with memory. Arch Ration Mech Anal 17:1
Decraemer WF, Maes MA, Vanhuyse VJ, Vanpeperstraete P (1980) A non-linear viscoelastic constitutive equation for soft biological tissues, based upon a structural model. J Biomech 13:559–564
Fung YC (1972) Stress–strain history relations of soft tissues in simple elongation. In: Fung YC, Perrone N, Anliker M (eds) Biomechanics: its foundations and objectives. Prentice-Hall, Englewood Cliffs, pp 181–208
Fung YC (1973) Biorheology of soft tissues. Biorheology 10:139–155
Fung YC (1993) Biomechanics. Mechanical properties of living tissues, 2nd edn. Springer, Berlin Heidelberg New York
Gow BS, Taylor MG (1968) Measurement of viscoelastic properties of arteries in the living dog. Circ Res 23:111–122
Guth E, Wack PE, Antony RL (1946) Significance of the equation of state for rubber. J Appl Phys 17:347–351
Haslach HW Jr (1997) Geometrical structure of the non-equilibrium thermodynamics of homogeneous systems. Rep Math Phys 39(2):147–162
Haslach HW Jr (2002) A non-equilibrium thermodynamic geometric structure for thermoviscoplasticity with maximum dissipation. Int J Plast 18(2):127–153
Haslach HW Jr, Zeng N-N (1999) Maximum dissipation evolution equations for nonlinear thermoviscoelasticity. Int J Non-linear Mech 34:361–385
Holzapfel GA (2000) Nonlinear solid mechanics. Wiley, Chichester
Holzapfel GA, Gasser TC, Ogden RW (2000) A new constitutive framework for arterial wall mechanics and a comparative study of material models. J Elast 61:1–48
Holzapfel GA, Gasser TC, Stadler M (2002) A structural model for the viscoelastic behavior of arterial walls: continuum formulation and finite element analysis. Eur J Mech A/Solids 21:441–463
Humphrey JD, Vawter DL, Vito RP (1987) Pseudoelasticity of excised visceral pleura. J Biomech 109:115–120
Humphrey JD, Strumpf RK, Yin FCP (1992) A constitutive theory for biomembranes: application to epicardal mechanics. J Biomech Eng 114:461–466
Kyriacou SK, Humphrey JD (1996) Influence of size, shape and properties on the mechanics of axisymmetric saccular aneurysms. J Biomech 29(8):1015–1022
Lanir Y (1983) Constitutive equations for fibrous connective tissues. J Biomech 16:1–12
Ogden RW (1972) Large deformation isotropic elasticity—on the correlation of theory and experiment for incompressible rubberlike solids. Proc R Soc Lond A 326:565–584
Patel DJ, Tucker WK, Janicki JS (1970) Dynamic elastic properties of the aorta in the radial direction. J Appl Physiol 28:578–562
Perkins RW (1983) Models for predicting the elastic, viscoelastic, and inelastic mechanical behavior of paper and board. In: Mark RE (ed) Chapter 2 in Handbook of physical and mechanical testing of paper and paperboard, vol 1, Marcel Dekker, NY
Rigby BJ (1964) The effect of mechanical extension upon the thermal stability of collagen. Biochim et Biophys Acta 79:634–636
Rosa E Jr, Altenberger AR, Dahler JS (1992) Model calculations based on a new theory of rubber elasticity. Acta Phys Pol B 23:337–356
Roy CS (1880) The elastic properties of the arterial wall. J Physiol 3:125–159
Scott S, Ferguson GG, Roach MR (1972) Comparison of the elastic properties of human intracranial arteries and aneurysms. Can J Physiol Pharmacol 50:328–332
Shah AD, Humphrey JD (1999) Finite strain elastodynamics of intracranial saccular aneurysms. J Biomech 32:593–599
Skalak R, Rachev A, Tozeren A (1975) Stress–strain relations for membranes under finite deformations. Bulg Acad Sci: Biomech 2:24–29
Steiger HJ, Aaslid R, Keller S, Reulen H-J (1989) Strength, elasticity and viscoelastic properties of cerebral aneurysms. Heart Vessels 5:41–46
Tanaka TT, Fung YC (1974) Elastic and inelastic properties of the canine aorta and their variations along the aortic tree. J Biomechan 7:357–370
Tanaka E, Yamada H (1990) An inelastic constitutive model of blood vessels. Acta Mech 82:21–30
Tong P, Fung YC (1978) The stress–strain relationship for the skin. J Biomechanics 9:649–657
Truesdell C (1984) Rational thermodynamics. Springer, Berlin Heidelberg New York
Viidik A (1968) A rheological model for uncalcified parallel-fibered collogeneous tissue. J Biomech 1:3–11
Woo SL-Y, Simon BR, Kuel SC, Akeson WH (1980) Quasi-linear viscoelastic properties of normal articular cartilage. J Biomech Eng 102:85–90
Author information
Authors and Affiliations
Corresponding author
Appendix
Appendix
1.1 Evolution equation when the strain energy is a function of a tensor
Let E be a second order tensor of state variables, and let H be the second order tensor of conjugate control variables. Assume that the energy function has the form
The affinities are the second order tensor, X=∂ψ/∂E. The affinities are a function of E, so that X=h(E). Assume that h is invertible so that ψ(E; H) can be written in terms of the affinities for fixed control variables, \(\bar \psi ({\mathbf{X}};{\mathbf{H}}).\)
The gradient dissipation condition (Eq. 5) is that the evolution of the affinities obeys \({\mathbf{\dot X}} = - k\partial \bar \psi /\partial {\mathbf{X}}\) for fixed controls, where \({\mathbf{\dot X}}\) is a second order tensor. By the chain rule,
Here ∂X/∂E is a fourth order tensor. Again by the chain rule,
Substitution of Eqs. 43 and 44 into \({\mathbf{\dot X}} = - k\partial \bar \psi /\partial {\mathbf{X}}\) yields the evolution equation in terms of the state variables,
This form reduces to that of Eq. 6 in the case that E has only diagonal non-zero entries. Then H also has only diagonal non-zero entries. The affinity is a second order tensor defined by
If ψ only depends on E11, E22, and E33, then the only non-zero terms of X are the three terms X ii .
The fourth order tensor ∂X/∂E is defined by
The only non-zero terms of this tensor, if only the diagonal entries of E are non-zero, have the form
The evolution equation therefore has the form of Eq. 6.
Rights and permissions
About this article
Cite this article
Haslach, H.W. Nonlinear viscoelastic, thermodynamically consistent, models for biological soft tissue. Biomech Model Mechanobiol 3, 172–189 (2005). https://doi.org/10.1007/s10237-004-0055-6
Received:
Accepted:
Published:
Issue Date:
DOI: https://doi.org/10.1007/s10237-004-0055-6