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Peter R. Hoskins Patricia V. Lawford - Cardiovascular Biomechanics

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Peter R. Hoskins Patricia V. Lawford Cardiovascular Biomechanics

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Springer International Publishing Switzerland 2017
Peter R. Hoskins , Patricia V. Lawford and Barry J. Doyle (eds.) Cardiovascular Biomechanics 10.1007/978-3-319-46407-7_1
1. Introduction to Solid and Fluid Mechanics
Peter R. Hoskins 1
(1)
Edinburgh University, Edinburgh, UK
Peter R. Hoskins
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Learning outcomes
  1. Explain the difference between a solid and a fluid.
  2. Describe features of stressstrain behaviour of a solid measured using a tensile testing system.
  3. Explain stressstrain behaviour of biological and non-biological materials in terms of their composition.
  4. Define Youngs modulus.
  5. Describe the measurement of Youngs modulus using a tensile testing system.
  6. Discuss values of Youngs modulus for non-biological and biological materials.
  7. Define Poisson ratio and discuss values for different materials.
  8. Describe viscoelasticity, its effect on stressstrain behaviour, and models of viscoelasticity.
  9. Discuss linear elastic theory and its applicability to biological tissues.
  10. Define hydrostatic pressure and values in the human.
  11. Define viscosity in terms of shear stress and shear rate.
  12. Describe different viscous behaviours.
  13. Describe measurement of viscosity.
  14. Describe typical measures of viscosity for different fluids.
  15. Discuss Poiseuille flow: pressure-flow relationships for flow of Newtonian fluid through a cylinder.
  16. Discuss Reynolds number and flow states.
  17. Discuss pressure-flow relationships in unsteady flow in cylindrical tubes.
  18. Discuss energy considerations in flow including the Bernoulli equation.
An understanding of the functioning of the cardiovascular system draws heavily on principles of fluid flow and of the elastic behaviour of tissues. Indeed, much of the cardiovascular system consists of a fluid (blood), flowing in elastic tubes (arteries and veins). This chapter will introduce basic principles of fluid flow and of solid mechanics. This area has developed over many centuries and Appendix provides details of key scientists and their contribution.
The concept of a fluid and a solid is familiar from everyday experience. However, from a physics point of view, the question arises as to what distinguishes a fluid from a solid? For a cubic volume element there are two types of forces which the volume element experiences (Fig. ); a force perpendicular to a face and a force in the plane of a face. The forces perpendicular to the face cause compression of the material and this is the case whether the material is liquid or solid. The force parallel to the face is called a shear force. In a solid, the shear force is transmitted through the solid and the solid is deformed or sheared. The shear force is resisted by internal stresses within the solid and, provided the force is not too great, the solid reaches an equilibrium position. At the nano level the atoms and molecules in the solid retain contact with their neighbours. In the case of a fluid, a shear force results in continuous movement of the material. At the nano level the atoms and molecules in the fluid are not permanently connected to their neighbours and they are free to move. The key distinction between a fluid and a solid is that a solid can sustain a shear force whereas a fluid at rest does not.
Fig 11 A cube of material is subject to force parallel to a face which cause - photo 1
Fig. 1.1
A cube of material is subject to force parallel to a face which cause shearing and forces normal to each face which cause compression
1.1 Solid Mechanics
Solid mechanics is concerned with the relationship between the forces applied to a solid and the deformation of the solid. These relationships go by the name of the constitutive equations and are important in areas such as patient-specific modelling discussed in Chap.. In general, these relationships are complex. For small deformations many materials deform linearly with applied force, which is fortunate as both experimental measurement and theory are relatively straightforward. This section on solid mechanics will start with 1D deformation of a material, develop linear elastic theory, then describe more complex features including those of biological materials.
1.1.1 1D Deformation
The elastic behaviour of a material is commonly investigated using a tensile testing system. A sample of the material is clamped into the system and then stretched apart. Both applied force and deformation are measured and can be plotted. Figure further increase in force eventually leads to fracturing of the material at the point U, called the ultimate tensile strength (UTS).
Fig 12 Force-extension curve for steel L linear behaviour Y yield point P - photo 2
Fig. 1.2
Force-extension curve for steel. L linear behaviour; Y yield point; P plastic deformation; U (uniaxial) ultimate strength. Redrawn from Wikipedia under a GNU free documentation licence; the author of the original image is Bbanerje. https://commons.wikimedia.org/wiki/File:Hyperelastic.svg
The force-deformation behaviour can be understood at the atomic level. The chemical bonds between atoms and molecules are deformable and small deformations from the equilibrium position can be tolerated without change in structure. The equations governing the force-extension behaviour at the atomic level demonstrate linear behaviour and the macroscopic behaviour of a material is the composite of a multitude of interactions at the atomic and molecular level. In the plastic region there are changes in structure at the atomic and molecular level. In many materials this arises through slip processes involving the movement of dislocations or through the creation and propagation of cracks.
Biological materials are generally composite in nature. From a mechanical point of view the most important components are collagen fibres, elastin, reticulin and an amorphous, hydrophilic, material called ground substance which contains as much as 90 % water. The elastic behaviour of the biological tissue is determined by the proportion of each component and by their physical arrangement. For example, collagen fibres in the wall of arteries are arranged in a helical pattern. Collagen is especially important in determining mechanical properties of soft biological tissues. Collagen is laid down in an un-stretched state. These unstressed fibres have a wavy, buckled shape, referred to as crimp. On application of a force, the fibres begin to straighten and the crimp disappears and, as a result, the tissue deforms relatively easily. With increasing extension the fibres straighten fully and resist the stretch. This leads to collagen having a non-linear force-extension behaviour, which explains the non-linear force-extension behaviour of most biological soft tissues.
A simple 1D tensile testing system can also be used to demonstrate viscoelasticity. It was stated above that in elastic behaviour the loading and unloading curves are the same. For a viscoelastic material they are different. In elastic behaviour the application of a force results more or less immediately in deformation of the material. Viscoelastic behaviour is associated with a time- lag between the applied force and the resulting deformation. The term viscoelastic implies that the material has a mix of elastic and viscous properties. If the tensile testing system stretches the material in a cyclic manner, then as the tissue is loaded and unloaded, the resulting force-deformation curve will be in the shape of an ellipse (Fig. ). During loading the force increases but the extension increases more slowly. During unloading the force decreases but the extension decreases more slowly. If the viscous component is low compared to the elastic component then the loading and unloading curves will be close together. For materials with a higher viscous component the curves are more separated and the width of the ellipse is larger.
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