Womersley number

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The Womersley number (α) is a dimensionless number in biofluid mechanics. It is a dimensionless expression of the pulsatile flow frequency in relation to viscous effects. It is named after John R. Womersley (1907–1958) for his work with bloodflow in arteries.[1] The Womersley number is important in keeping dynamic similarity when scaling an experiment. An example of this is scaling up the vascular system for experimental study. The Womersley number is also important in determining the thickness of the boundary layer to see if entrance effects can be ignored.

Derivation[edit]

The Womersley number, usually denoted \alpha, is defined by the relation

\alpha^2 = \frac{\text{transient inertial force}}{\text{viscous force}} = \frac{ \rho \omega U}{\mu U R^{-2} } = \frac{ \omega R^{2} }{\mu \rho^{-1} } =  \frac{ \omega R^{2} }{\nu} \, ,

where R is an appropriate length scale (for example the radius of a pipe), ω is the angular frequency of the oscillations, and ν, ρ, μ are the kinematic viscosity, density, and dynamic viscosity of the fluid, respectively.[2] The Womersley number is normally written in the powerless form

\alpha = R \left( \frac{\omega}{\nu} \right)^\frac{1}{2} \ = R \left( \frac{\omega \rho}{\mu} \right)^\frac{1}{2} \, .

It can also be written in terms of the dimensionless Reynolds number (Re) and Strouhal number (Sr):

\alpha = \left( 2\pi\, \mathrm{Re} \, \mathrm{Sr} \right)^{1/2}\, .

The Womersley number arises in the solution of the linearized Navier Stokes equations for oscillatory flow (presumed to be laminar and incompressible) in a tube. It expresses the ratio of the transient or oscillatory inertia force to the shear force. When \alpha is small (1 or less), it means the frequency of pulsations is sufficiently low that a parabolic velocity profile has time to develop during each cycle, and the flow will be very nearly in phase with the pressure gradient, and will be given to a good approximation by Poiseuille's law, using the instantaneous pressure gradient. When \alpha is large (10 or more), it means the frequency of pulsations is sufficiently large that the velocity profile is relatively flat or plug-like, and the mean flow lags the pressure gradient by about 90 degrees. Along with the Reynolds number, the Womersley number governs dynamic similarity.[3]

The boundary layer thickness \delta that is associated with the transient acceleration is related to the Womersley number. It is equal to inverse of the Womersley number. The Womersley number is also equal to the square root of the Stokes number.[4]

\delta = \left( L/\alpha \right)= \left( \frac{L}{\sqrt{\mathrm{Stk}}}\right),

where L is a characteristic length.

Biofluid mechanics[edit]

In a flow distribution network that progresses from a large tube to many small tubes (e.g. a blood vessel network), the frequency, density, and dynamic viscosity are (usually) the same throughout the network, but the tube radii change. Therefore the Womersley number is large in large vessels and small in small vessels. As the vessel diameter decreases with each division the Womersley number soon becomes quite small. The Womersley numbers tend to 1 at the level of the terminal arteries. In the arterioles, capillaries, and venules the Womersley numbers are less than one. In these regions the inertia force becomes less important and the flow is determined by the balance of viscous stresses and the pressure gradient. This is called microcirculation.[4]

Some typical values for the Womersley number in the cardiovascular system for a canine at a heart rate of 2 Hz are:[4]

  • Ascending Aorta — 13.2
  • Descending Aorta — 11.5
  • Abdominal Aorta — 8
  • Femoral Artery — 3.5
  • Carotid Artery — 4.4
  • Arterioles —0.04
  • Capillaries — 0.005
  • Venules — 0.035
  • Inferior Vena Cava — 8.8
  • Main Pulmonary Artery — 15

It has been argued that universal biological scaling laws (power-law relationships that describe variation of quantities such as metabolic rate, lifespan, length, etc., with body mass) are a consequence of the need for energy minimization, the fractal nature of vascular networks, and the crossover from high to low Womersley number flow as one progresses from large to small vessels.[5]

References[edit]

  1. ^ Womersley, J.R. (March 1955). "Method for the calculation of velocity, rate of flow and viscous drag in arteries when the pressure gradient is known". J Physiol. 127 (3): 553–563. PMC 1365740. PMID 14368548. 
  2. ^ Fung, Y. C. (1990). Biomechanics - Motion, flow, stress and growth. New York (USA): Springer-Verlag. p. 569. 
  3. ^ Nichols, W.W., O'Rourke, M.F. (2005). McDonald's Blood Flow in Arteries (5th ed.). London (England): Hodder-Arnold. ISBN 0-340-80941-8. 
  4. ^ a b c Fung, Y.C. (1996). Biomechanics Circulation. Springer Verlag. p. 571. 
  5. ^ West GB, Brown JH, Enquist BJ (4 April 1997). "A general model for the origin of allometric scaling laws in biology". Science 276 (5309): 122–6. doi:10.1126/science.276.5309.122. PMID 9082983.