Abstract
The prediction of soft-tissue failure may yield a better understanding of the pathogenesis of arterial dissection and help to advance diagnostic and therapeutic strategies for the treatment of this and other diseases and injuries involving the tearing of soft tissue, such as aortic dissection. In this paper, we present computational models of tear propagation in fibre-reinforced soft tissue undergoing finite deformation, modelled by a hyperelastic anisotropic constitutive law. We adopt the appropriate energy argument for anisotropic finite strain materials to determine whether a tear can propagate when subject to internal pressure loading. The energy release rate is evaluated with an efficient numerical scheme that makes use of adaptive tear lengths. As an illustration, we present the calculation of the energy release rate for a two-dimensional strip of tissue with a pre-existing tear of length \(a\) under internal pressure \(p\) and show the effect of fibre orientation. This calculation allows us to locate the potential bifurcation to tear propagation in the \((a,p)\) plane. The numerical predictions are verified by analytical solutions for simpler cases. We have identified a scenario of tear arrest, which is observed clinically, when the surrounding connective tissues are accounted for. Finally, the limitations of the models and further directions for applications are discussed.
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References
Khan IA, Nair CK (2002) Clinical, diagnostic, and management perspectives of aortic dissection. Chest J 122(1):311–328
Foundation MHI (2013) Mortality for acute aortic dissection near one percent per hour during initial onset. ScienceDaily, 10 March 2013. www.sciencedaily.com/releases/2013/03/130310164230.htm. Accessed 6 January 2015
Rajagopal K, Bridges C, Rajagopal K (2007) Towards an understanding of the mechanics underlying aortic dissection. Biomech Model Mechanobiol 6:345–359
de Figueiredo Borges L, Jaldin RG, Dias RR, Stolf NAG, Michel JB, Gutierrez PS (2008) Collagen is reduced and disrupted in human aneurysms and dissections of ascending aorta. Hum Pathol 39(3):437–443
Tada H, Paris PC, Irwin GR, Tada H (2000) The stress analysis of cracks handbook. ASME Press, New York
Krishnan VR, Hui CY, Long R (2008) Finite strain crack tip fields in soft incompressible elastic solids. Langmuir 24(24):14245–14253
Stephenson RA (1982) The equilibrium field near the tip of a crack for finite plane strain of incompressible elastic materials. J Elast 12(1):65–99
Ionescu I, Guilkey JE, Berzins M, Kirby RM, Weiss JA (2006) Simulation of soft tissue failure using the material point method. J Biomech Eng 128(6):917
Volokh KY (2004) Comparison between cohesive zone models. Commun Numer Methods Eng 20(11):845–856
Gasser TC, Holzapfel GA (2006) Modeling the propagation of arterial dissection. Eur J Mechs A 25(4):617–633
Elices M, Guinea G, Gomez J, Planas J (2002) The cohesive zone model: advantages, limitations and challenges. Eng Fract Mech 69(2):137–163
Bhattacharjee T, Barlingay M, Tasneem H, Roan E, Vemaganti K (2013) Cohesive zone modeling of mode I tearing in thin soft materials. J Mech Behav Biomed Mater 28:37–46
Ferrara A, Pandolfi A (2008) Numerical modelling of fracture in human arteries. Comput Methods Biomech Biomed Eng 11(5):553–567
Ferrara A, Pandolfi A (2010) A numerical study of arterial media dissection processes. Int J Fract 166(1–2):21–33
Ortiz M, Pandolfi A (1999) Finite-deformation irreversible cohesive elements for three-dimensional crack-propagation analysis. Int J Numer Methods Eng 44(9):1267–1282
Griffith AA (1921) The phenomena of rupture and flow in solids. Philos Transa R Soc Lond Ser A 221:163–198
Irwin G, Wells A (1965) A continuum-mechanics view of crack propagation. Metallurg Rev 10(1):223–270
Willis J (1967) A comparison of the fracture criteria of Griffith and Barenblatt. J Mech Phys Solids 15(3):151–162
Zehnder AT (2012) Fracture mechanics. Lecture notes in applied and computational mechanics, vol 62. Springer
Knees D, Mielke A (2008) Energy release rate for cracks in finite-strain elasticity. Math Methods Appl Sci 31(5):501–528
Taylor RL (2011) FEAP— a finite element analysis program: Version 8.3 User manual. University of California at Berkeley
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):1–48
Flory P (1961) Thermodynamic relations for high elastic materials. Trans Faraday Soc 57:829–838
Taylor RL (2011) FEAP—a finite element analysis program: Version 8.3 Programmer manual. University of California at Berkeley
Holzapfel GA (2000) Nonlinear solid mechanics: a continuum approach for engineering. Wiley, New York
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LW is supported by a China Scholarship Council Studentship and the Fee Waiver Programme at the University of Glasgow.
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Appendices
Appendix 1: Derivative of Cauchy stress and tangential moduli for a quasi-incompressible material (6)
1.1 Cauchy stress
Follow the standard formulas of the theory of finite elasticity, e.g. see [25]. We firstly calculate the second Piola–Kirchhoff stress,
where
Substitute these into (10) to obtain the explicit expression for the second Piola–Kirchhoff stress. Pushing it forward using
immediately gives the Cauchy stress
where \(\bar{{\mathsf {b}}} = J^{-2/3}{\mathsf {FF}}^\mathrm{T}\) and \({\mathsf {m}}_n={\mathsf {FM}}_n{\mathsf {F}}^\mathrm{T}\). In particular,
where \(\mathbf {a}_i={\mathsf {F}}\mathbf {A}_i~(i=1,2)\) represents the deformed vector of the unit vector \(\mathbf {A}_i\) characterising the orientation of the \(i\hbox {th}\) family of fibres in the reference configuration.
1.2 Tangent moduli
Similarly, the material tangent moduli associated with the increment of the second Piola–Kirchoff stress \({\mathsf {S}}\) and the Green strain tensor \({\mathsf {E}} = \frac{1}{2}({\mathsf {C-I}})\) is derived first:
where \({\mathsf {S}}^x=2 {\partial \varPsi _x}/{\partial {\mathsf {C}}}, x =\{v,m,f\}\). In index notation,
We note some useful differentials:
Substituting (14) into (13) gives the explicit expression for the material tangent moduli. Pushing it forward gives the spatial tangent moduli required by a user-provided material model in FEAP. Its components are as follows:
Finally, transforming (12) and (15) into the corresponding matrix form gives all formulas for the user subroutine for the HGO material model.
Appendix 2: Verification of material model for simple cases
We verify our model on the basis of comparisons with analytical results for a plane strain problem for a unit-square sample of fibre-reinforced material. For simplicity, both families of fibres have the same orientation, along the \(x\)-axis.
Firstly, we stretch the block along the \(x\)-axis with a stretch ratio \(\lambda _x\). Plane strain and incompressibility ensure that the deformation gradient can be written as
Substituting (16) into (4) gives the corresponding strain energy (Fig. 14). For an incompressible material (4) we derive the Cauchy stress
where \(\mathfrak {L}\) is the Lagrange multiplier. Without loss of generality, we consider a material with both families of fibres along the horizontal direction, \(\mathbf {A}_1=\mathbf {A}_2=[1,0,0]^T\). Substituting (16) into (17) gives the Cauchy stress
Since the surfaces with normal directions parallel to the \(y\)-axis are traction free, we have
and thus \(\mathfrak {L}=1/\lambda _x^2\). Substituting into (18) we have
This analytical response is shown in Fig. 15.
We now compare the analytical with the numerical results. In the computations, the penalty parameter \(K\) in (6) is chosen to be \(10^5\), at which value or greater the numerical results agree with analytical predictions for both the energy (Fig. 14) and stress (Fig. 15).
Appendix 3: A simple beam model for ERR
Inequality (2) is known as the Griffith criterion when applied to linear elastic problems. Consider a beam of constant Young’s modulus \(E\) and second moment of area \(J\). The beam is bonded to a surface except for a region \(0\le x\le a\), where \(x\) measures the length along the beam from one end. The deflection of the beam is \(w(x)\), and the boundary conditions are
The equation satisfied by \(w(x)\) depends on the loading experienced by the beam. We take a general function \(F(x,w)\) so that
Different choices of \(F(x,w)\) give different external boundary conditions, e.g. in what follows we simulate the effect of the constraint of the surrounding connective tissue. In particular, we are interested in the calculation of the mechanical energy
where \(F(x,w)=-\partial f/\partial w\) and \(G=-\hbox {d} \varPi / \hbox {d}a\). For a given value of \(G_c\), (23) enables us to use (2) to determine whether a tear of length \(a\) can propagate.
We now use this simple beam model to explore the type of phenomena we obtained from the numerical experiments. To simulate the boundary condition, we set \(F(x,w)=p\), a constant. Solving the ordinary differential beam equation (22) gives
and therefore, substituting into (23), we find that
The energy release rate is
\(G\) is a monotonically increasing function of \(a\) and \(p\), and therefore an increase in either the length of the unbonded region (the tear) or the pressure results in the propagation of the tear being energetically favourable.
To consider the effect of surrounding connective tissues, we set \(F(x,w)=p-kw\), where the constant \(k\) is the stiffness per unit length of the springs, as shown in Fig. 16. Consequently, \(f=-pw+kw^2/2\), and the solution for \(w(x)\) is
where \(W(x)\) satisfies
This is solved to give
with \(A, B, C\) and \(D\) chosen to satisfy the boundary conditions. Non-dimensionalising the deflection with \(p/k\) and \(x\), with \(\left( 4EJ/k\right) ^{1/4}\), leads to the canonical problem
with boundary conditions \(y''(0)=y'''(0)=0\) and \(y(\alpha )=y'(\alpha )=0\), where \(\alpha =a/l\). The solution to this problem is
The mechanical energy is
This expression simplifies to
and then we obtain the ERR
We display the curve of \(G(a)\) for a set of typical parameters in Fig. 17. When subject to a constant pressure, \(G(a)\) is not a monotonically increasing function of \(a\), and propagation arrest occurs. This is qualitatively similar to what is seen in Fig. 12 in the numerical simulations for a strip of fibre-reinforced tissues subject to finite strain.
Tear arrest is also demonstrated by the beam model when connective tissue is present. The ERR \(G\) is no longer a monotonic function of \(a\), and for a given critical value \(G_c\), a tear of length \(a\), where \(a_1 < a < a_2\) or \(a > a_3\), will propagate. However, the tear arrests when \(a_2 < a < a_3\)
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Wang, L., Roper, S.M., Luo, X.Y. et al. Modelling of tear propagation and arrest in fibre-reinforced soft tissue subject to internal pressure. J Eng Math 95, 249–265 (2015). https://doi.org/10.1007/s10665-014-9757-7
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DOI: https://doi.org/10.1007/s10665-014-9757-7