Abstract
There is no doubt that one of the most significant health problems facing people around the world is vascular disease that compromises perfusion of vital organs (e.g., heart, brain, etc.). Abnormal mechanical stresses and deformation of blood vessels have been identified as key culprits in the initiation and progression of vascular disease. To understand the blood circulation through blood vessels, one must consider the blood, the blood vessel wall, the tissue surrounding the vessel wall, the geometry of the vascular system, and the driving forces from pumping of the heart. Blood vessels are remarkable organs that nurture organisms, transport many enzymes and hormones, contain blood cells that flow or clot when needed, and transport oxygen and carbon dioxide between the lungs and the cells of the tissues. Physiologists study these important functions of the vasculature as they relate to the functioning of the body. Bioengineers apply engineering principles to understand biological systems. For the bioengineer, the understanding of the biomechanics of circulation is a central focus to explain vascular health and disease.
Access this chapter
Tax calculation will be finalised at checkout
Purchases are for personal use only
References
Bao, X., Lu, C., & Frangos, J. A. (2001). Mechanism of temporal gradients in shear-induced ERK1/2 activation and proliferation in endothelial cells. American Journal of Physiology-Heart and Circulatory Physiology, 281, H22–H29. https://doi.org/10.1152/ajpheart.2001.281.1.H22
Bathe, K. J. (1995). Finite element procedures. Englewood Cliffs: Prentice-Hall.
Bergel, D. H. (1972). In Y. C. Fung, N. Perrone, & M. Anliker (Eds.), Biomechanics: Its foundations and objectives (pp. 105–138). Englewood Cliffs, NJ: Prentice- Hall.
Berger, S. A., & Jou, L. D. (2002). Flows in stenotic vessels. Annual Review of Fluid Mechanics, 32, 347–382. https://doi.org/10.1146/annurev.fluid.32.1.347
Buchanan, J. R., Jr., Kleinstreuer, C., Truskey, G. A., & Lei, M. (1999). Relation between non-uniform hemodynamics and sites of altered permeability and lesion growth at the rabbit aorto-celiac junction. Atherosclerosis, 143, 27–40. https://doi.org/10.1016/S0021-9150(98)00264-0
Chen, H., & Kassab, G. S. (2016). Microstructure-based biomechanics of coronary arteries in health and disease. Journal of Biomechanics, 49(12), 2548–2559. https://doi.org/10.1016/j.jbiomech.2016.03.023
Chen, H., Liu, Y., Zhao, X., Lanir, Y., & Kassab, G. S. (2011). A micromechanics finite-strain constitutive model of fibrous tissue. Journal of the Mechanics and Physics of Solids, 59, 1823–1837. https://doi.org/10.1016/j.jmps.2011.05.012
Chen, H., Luo, T., Zhao, X., Lu, X., Huo, Y., & Kassab, G. S. (2013). Microstructural constitutive model of active coronary artery media. Biomaterials, 34(31), 7575–7583. https://doi.org/10.1016/j.biomaterials.2013.06.035
Chen, H., Zhao, X., Lu, X., & Kassab, G. S. (2013). Nonlinear micromechanics of soft tissue. International Joural of Non-linear Mechanics, 56, 79–85. https://doi.org/10.1016/j.ijnonlinmec.2013.03.002
Chorin, A. J. (1968). Numerical solution of the Navier-Stokes equations. Mathematics of Computation, 22, 745–762. https://doi.org/10.1090/S0025-5718-1968-0242392-2
Chorin, A. J. (1969). On the convergence of discrete approximations to the Navier-Stokes equations. Mathematics of Computations, 23, 341–353. https://doi.org/10.2307/2004428
DeBakey, M. E., Lawrie, G. M., & Glaeser, D. H. (1985). Patterns of atherosclerosis and their surgical significance. Annals of Surgery, 201(2), 115–131. https://doi.org/10.1097/00000658-198502000-00001
Dobrin, P. B. (1978). Mechanical properties of arteries. Physiological Reviews, 58, 397–460. https://doi.org/10.1152/physrev.1978.58.2.397
Donea, J., Giuliani, S., & Halleux, J. P. (1982). An arbitrary Lagrangian Eulerian finite element method for transient dynamic fluid structure interactions. Computer Methods in Applied Mechanics and Engineering, 33, 689–723. https://doi.org/10.1016/0045-7825(82)90128-1
Douglas, J. E., & Greenfield, J. C. (1970). Epicardial coronary artery compliance in the dog. Circulation Research, 27, 921–929. https://doi.org/10.1161/01.RES.27.6.921
Farmakis, T. M., Soulis, J. V., Giannoglou, G. D., Zioupos, G. J., & Louridas, G. E. (2004). Wall shear stress gradient topography in the normal left coronary arterial tree: Possible implications for atherogenesis. Current Medical Research and Opinion, 20(5), 587–596. https://doi.org/10.1185/030079904125003340
Fefferman, C. L. (2000). Existence and smoothness of the Navier–Stokes equation. Princeton, NJ: Princeton University.
Formaggia, L., & Nobile, F. (1999). A stability analysis for the arbitrary Lagrangian Eulerian formulation with finite elements. East-West Journal of Numerical Mathematics, 7, 105–131.
Fung, Y. C. (1983). What principle governs the stress distribution in living organs? In Y. C. Fung, E. Fukada, & J. Wang (Eds.), Biomechanics in China, Japan and USA (pp. 1–13). Beijing, China: Science.
Fung, Y. C. (1990). Biomechanics: Motion, flow, stress and growth. New York: Springer.
Fung, Y. C. (1993). Biomechanics: Mechanical properties of living tissues (2nd ed.). New York: Springer.
Fung, Y. C. (1994). A first course in continuum mechanics (3rd ed.). Englewood Cliffs, NJ: Prentice Hall.
Fung, Y. C. (1997). Biomechanics: Circulation. New York: Springer.
Giezeman, M. J., VanBavel, E., Grimbergen, C. A., & Spaan, J. A. (1994). Compliance of isolated porcine coronary small arteries and coronary pressure-flow relations. American Journal of Physiology-Heart and Circulatory Physiology, 36, H1190–H1198. https://doi.org/10.1152/ajpheart.1994.267.3.H1190
Glowinski, R., Pan, T. W., Hesla, T. I., Joseph, D. D., & Periaux, J. (2001). A fictitious domain approach to the direct numerical simulation of incompressible viscous flow past moving rigid bodies: Application to particulate flow. Journal of Computational Physics, 169(2), 363–426. https://doi.org/10.1006/jcph.2000.6542
Glowinski, R., Pan, T. W., & Periaux, J. (1994). A fictitious domain method for Dirichlet problem and applications. Computer Methods in Applied Mechanics and Engineering, 111(3–4), 283–303. https://doi.org/10.1016/0045-7825(94)90135-X
Green, A. E., & Adkins, J. E. (1960). Large deformations and nonlinear continuum mechanics. Oxford: Oxford University Press.
Gregersen, H., & Kassab, G. S. (1996). Biomechanics of the gastrointestinal tract. Neurogastroenterology & Motility, 8, 277–297. https://doi.org/10.1111/j.1365-2982.1996.tb00267.x
Gregg, D. E., Green, H. D., & Wiggers, C. J. (1935). Phasic variations in peripheral coronary resistance and their determinants. American Journal of Physiology, 112, 362–373. https://doi.org/10.1152/ajplegacy.1935.112.2.362
Guccione, J. M., Kassab, G., & Ratcliffe, M. (Eds.). (2010). Computational cardiovascular mechanics: Modeling and applications in heart failure. New York: Springer.
He, X., & Ku, D. N. (1996). Pulsatile flow in the human left coronary artery bifurcation: Average conditions. Journal of Biomechanical Engineering, 118, 74–82. https://doi.org/10.1115/1.2795948
Hughes, T. J. R., Liu, W. K., & Zimmermann, T. K. (1981). Lagrangian Eulerian finite element formulation in incompressible viscous flows. Computer Methods in Applied Mechanics and Engineering, 29, 329–349. https://doi.org/10.1016/0045-7825(81)90049-9
Kassab, G. S. (2001). Analysis of coronary circulation: A bioengineering approach. In Y. C. Fung (Ed.), Introduction to bioengineering (pp. 93–105). Singapore: World Scientific.
Kleinstreuer, C., Hyun, S., Buchanan, J. J. R., Longest, P. W., Archie, J. P., Jr., & Truskey, G. A. (2001). Hemodynamic parameters and early intimal thickening in branching blood vessels. Critical Reviews in Biomedical Engineering, 29, 1–64. https://doi.org/10.1615/CritRevBiomedEng.v29.i1.10
Kovacs, S. J., McQueen, D. M., & Peskin, C. S. (2001). Modelling cardiac fluid dynamics and diastolic function. Philosophical Transactions of the Royal Society of London Series A-Mathematical Physical and Engineering Sciences, 359(1783), 1299–1314. https://doi.org/10.1098/rsta.2001.0832
Ku, D. N. (1997). Blood flow in arteries. Annual Review of Fluid Mechanics, 29, 399–434. https://doi.org/10.1146/annurev.fluid.29.1.399
Kuo, L., Chilian, W. M., & Davis, M. J. (1991). Interaction of pressue- and flow-induced responses in porcine coronary resistance vessels. American Journal of Physiology, 261, H1706–H1715. https://doi.org/10.1152/ajpheart.1991.261.6.H1706
Kuo, L., Davis, M. J., & Chilian, W. M. (1988). Myogenic activity in isolated subepicardial and subendocardial coronary arterioles. American Journal of Physiology, 255, H1558–H1562. https://doi.org/10.1152/ajpheart.1988.255.6.H1558
Lei, M., Kleinstreuer, C., & Truskey, G. A. (1996). A focal stress gradient-dependent mass transfer mechanism for atherogenesis in branching arteries. Medical Engineering & Physics, 18(4), 326–332. https://doi.org/10.1016/1350-4533(95)00045-3
Manor, D., Beyar, R., Shofti, R., & Sideman, S. (1994). In-vivo study of the mechanical properties of epicardial coronary arteries. Journal of Biomechanical Engineering, 116, 131–132. https://doi.org/10.1115/1.2895697
McQueen, D. M., & Peskin, C. S. (1983). Computer-assisted design of pivoting-disc prosthetic mitral valves. The Journal of Thoracic and Cardiovascular Surgery, 86, 126–135.
McQueen, D. M., & Peskin, C. S. (1985). Computer-assisted design of butterfly bileaflet valves for the mitral position. Scandinavian Journal of Thoracic and Cardiovascular Surgery, 19, 139–148. https://doi.org/10.3109/14017438509102709
McQueen, D. M., & Peskin, C. S. (2000). A three-dimensional computer model of the human heart for studying cardiac fluid dynamics. Computer & Graphics, 34(1), 56–60. https://doi.org/10.1145/563788.604453
McQueen, D. M., Peskin, C. S., & Yellin, E. L. (1982). Fluid dynamics of the mitral valve: Physiological aspects of a mathematical model. American Journal of Physiology, 242, H1095–H1110. https://doi.org/10.1152/ajpheart.1982.242.6.H1095
Nakayama, K., Osol, G., & Halpern, W. (1988). Reactivity of isolated porcine coronary resistance arteries to cholinergic and adrenergic drugs and transmural pressure changes. Circulation Research, 62, 741–748.
Patankar, S. V. (1980). Numerical heat transfer and fluid flow. New York: Hemisphere Publishing Corporation.
Patel, D. J., & Janicki, J. S. (1970). Static elastic properties of the left coronary circumflex artery and the common carotid artery in dogs. Circulation Research, 2, 149–158. https://doi.org/10.1161/01.RES.27.2.149
Perktold, K., Resch, M., & Florian, H. (1991). Pulsatile non-Newtonian flow characteristics in a three-dimensional human carotid bifurcation model. Journal of Biomechanical Engineering, 113, 464–475. https://doi.org/10.1115/1.2895428
Perktold, K., Resch, M., & Peter, R. O. (1991). Three dimensional numerical analysis of pulsatile flow and wall shear stress in the carotid artery bifurcation. Journal of Biomechanics, 24, 409–420. https://doi.org/10.1016/0021-9290(91)90029-M
Peskin, C. S. (1972). Flow patterns around heart valves: A digital computer method for solving the equations of motion. (Ph.D.), Albert Einstein College of Medicine, Univ. Microfilms.
Peskin, C. S. (1977). Flow patterns around heart valves: A numerical method. Journal of Computational Physics, 25, 220–252. https://doi.org/10.1016/0021-9991(77)90100-0
Peskin, C. S. (2002). The immersed boundary method. Acta Numerica, 11, 479–517. https://doi.org/10.1017/S0962492902000077
Peskin, C. S., & McQueen, D. M. (1993). Computational biofluid dynamics. In A. Y. Cheer & C. P. van Dam (Eds.), Fluid dynamics in biology (Vol. 141, pp. 161–186). Oxford: Oxford University Press.
Ramaswamy, S. D., Vigmostad, S. C., Wahle, A., Lia, Y. G., Olszewski, M. E., Braddy, K. C., … Chandran, K. B. (2004). Fluid dynamics in a human left anterior descending coronary artery with arterial motion. Annals of Biomedical Engineering, 32, 1628–1641. https://doi.org/10.1007/s10439-004-7816-3
Reneman, R. S., & Arts, T. (1985). Dynamic capacitance of epicardial coronary arteries in vivo. Journal of Biomechanical Engineering, 107, 29–33. https://doi.org/10.1115/1.3138515
Sankaranarayanan, M., Ghista, D. N., Poh, C. L., Seng, T. Y., & Kassab, G. S. (2006). Analysis of blood flow in an out-of-plane CABG model. American Journal of Physiology-Heart and Circulatory Physiology, 291, H283–H295. https://doi.org/10.1152/ajpheart.01347.2005
Santamarina, A., Weydahl, E., Sigel, J. M., & Moore, J. S. (1998). Computational analysis of flow in a curved tube model of the coronary arteries: Effects of time-varying curvature. Annals of Biomedical Engineering, 26, 944–954. https://doi.org/10.1114/1.113
Singer, C. (1959). A short history of scientific ideas to 1900. New York: Oxford University Press.
Spaan, J. A. E. (1985). Coronary diastolic pressure-flow relation and zero-flow pressure explained on the basis of intramyocardial compliance. Circulation Research, 56(3), 293–309. https://doi.org/10.1161/01.RES.56.3.293
Stroud, J. S., Berger, S. A., & Saloner, D. (2002). Numerical analysis of flow through a severely stenotic carotid artery bifurcation. Journal of Biomechanical Engineering, 124, 9–20. https://doi.org/10.1115/1.1427042
Taylor, C. A., Hughes, T. J. R., & Zarins, C. K. (1998). Finite element modeling of three-dimensional pulsatile flow in the abdominal aorta: Relevance to atherosclerosis. Annals of Biomedical Engineering, 26, 975–987. https://doi.org/10.1114/1.140
Tomoike, H., Ootsubo, H., Sakai, K., Kikuchi, Y., & Nakamura, M. (1981). Continuous measurement of coronary artery diameter in situ. American Journal of Physiology-Heart and Circulatory Physiology, 240, H73–H79. https://doi.org/10.1152/ajpheart.1981.240.1.H73
Vigmond, E. J., Clements, C., McQueen, D. M., & Peskin, C. S. (2008). Effect of bundle branch block on cardiac output: A whole heart simulation study. Progress in biophysics & molecular biology, 97(2–3), 520–542. https://doi.org/10.1016/j.pbiomolbio.2008.02.022
Weydahl, E. S., & Moore, J. E. (2001). Dynamic curvature strongly affects wall shear rates in a coronary artery bifurcation model. Journal of Biomechanics, 34, 1189–1196. https://doi.org/10.1016/S0021-9290(01)00051-3
Zeng, D., Ding, Z., Friedman, M. H., & Ethier, C. R. (2003). Effect of cardiac motion on right coronary artery hemodynamics. Annals of Biomedical Engineering, 31, 420–429. https://doi.org/10.1114/1.1560631
Zhang, W., Chen, H. Y., & Kassab, G. S. (2007). A novel rate insensitive linear viscoelastic model for soft tissues. Biomaterials, 28(24), 3579–3586. https://doi.org/10.1016/j.biomaterials.2007.04.040
Author information
Authors and Affiliations
Appendices
Appendix 1: Derivation of Circumferential Stress (Laplace’s Law) and Longitudinal Stress in a Vessel
If a body is in equilibrium, every part of it is in equilibrium. To determine the internal reaction stresses, one can cut free certain parts of the body and examine their conditions of an equilibrium. Consider a cylindrical vessel subjected to an internal pressure Pi, as shown in Fig. 1.5a below, where cuts are made in different planes. The blood pressure induces stress in the vessel wall. Under equilibrium conditions, the force in the vessel wall in the circumferential direction 2τθ(ro − ri)L, is balanced by the force in the vessel lumen contributed by the pressure 2LriPi, as shown in Fig. 1.5b. Hence, the equilibrium equation in the circumferential direction is given by:
where τθ is circumferential stress, ri is internal radius, and ro is outer radius of vessel.
The longitudinal stress in a vessel wall can be determined based on the equilibrium of forces in the longitudinal direction. The product of the longitudinal stress and the cross-sectional area of the vessel wall is the force that balances the total longitudinal force acting on the vessel as shown in Fig. 1.5c. The longitudinal force in the vessel wall \( {\tau}_z\pi \left({r}_{\mathrm{o}}^2-{r}_{\mathrm{i}}^2\right) \) is balanced only by the pressure component \( {P}_{\mathrm{i}}\pi {r}_{\mathrm{i}}^2 \) as the external pressure is assumed to be zero. Thus, the desired equation follows:
where τz is the longitudinal stress. If the wall thickness-radius ratio is small, so that ro = ri = r and ro − ri = h, then these equations are simplified to
Appendix 2: Constitutive Equation of a Homogeneous, Isotropic, and Linear Elastic Solid (Hooke’s Law)
The constitutive equations of a solid that consists of a homogeneous, isotropic, linearly elastic material contain only two material constants given by Hooke’s law:
where i and j are indices ranging from integers 1 to 3. The ith index denotes the component in the ith direction whereas the jth index denotes the surface perpendicular to the jth direction. The repetition of an index in a term denotes a summation with respect to that index over its range.
Several special cases will be considered:
Special Case 1
A uniaxial state of stress with the non-zero stress-component τ11 corresponding to the x1-direction. From Eq. (1.4), the following holds:
The coefficient between stress and strain can be expressed as:
which is called the elastic modulus or Young’s modulus. This module can be readily measured in a uniaxial tension test. The ratio −ε22/ε11 = − ε33/ε11 is given by:
which is known as Poisson’s ratio. Poisson’s ratio is a measure of the lateral contraction (extension) produced by an axial tension (compression).
Special Case 2
Consider a state of plane stress in pure shear in which the only non-zero component of the stress tensor is τ12 = τ21 ≠ 0. The corresponding non-zero strain component is given by
The ratio of shearing stress τ12 and the corresponding change 2ε12 of an initially right material angle is known as the shear modulus. In the engineering literature, the symbol G is widely used to describe the shear modulus.
Special Case 3
Finally, consider a hydrostatic state of stress, given by:
If this result is combined with Eq. (1.4), the following holds:
Setting i = j, and summing on j, one finds:
where εii = ε11 + ε22 + ε33 and proportionality constant given by:
known as the bulk modulus. The bulk modulus is a measure of the compressibility of the solid. For an incompressible material, K and hence λ are unbounded (→∞). If a hydrostatic pressure is to be accompanied by a volume decrease, then the bulk modulus K must be positive. Since shearing should occur in the direction of the shearing stress, the following constrains holds for the parameters:
The corresponding bounds on E and v are given by:
Hence, a simple tension is always accompanied by an extension. On the other hand, in a direction normal to the direction of this tension, a contraction may take place.
Appendix 3: Equations for Fluids and Solids
The governing equations for the fluid domain are the Navier–Stokes (NS) and continuity equations (Fefferman, 2000):
where V is fluid velocity, P is fluid pressure, ρ is fluid mass density, η is fluid dynamic viscosity, \( \overrightarrow{\nabla} \) is the gradient operator, and D is the fluid rate of deformation tensor.
The governing equations for the solid are the momentum and equilibrium equations (Fung, 1997):
where sΩ(t) is the structural domain at time t, t1 is surface traction vector, σij is stress of the solid, and ai is the acceleration of the material point along the ith direction.
Rights and permissions
Copyright information
© 2019 Springer Science+Business Media, LLC, part of Springer Nature
About this chapter
Cite this chapter
Kassab, G.S. (2019). Biomechanics. In: Coronary Circulation. Springer, Cham. https://doi.org/10.1007/978-3-030-14819-5_1
Download citation
DOI: https://doi.org/10.1007/978-3-030-14819-5_1
Published:
Publisher Name: Springer, Cham
Print ISBN: 978-3-030-14817-1
Online ISBN: 978-3-030-14819-5
eBook Packages: Biomedical and Life SciencesBiomedical and Life Sciences (R0)