BioMedical Engineering OnLine 2006, 5:42http://www.biomedical-engineering-online.com/content/5/1/42and <strong>the</strong> <strong>to</strong>tal displacement thickness δ** = δ* + θδ ∗∗ R ⎛ ⎞= ∫ 2d ν 1−x⎟dr,220 ⎜ 2⎝ V ⎠leads <strong>to</strong>∗∗1 ∂δ V ∂θ 2θ + δ ∂V+ +2V ∂ t ∂ x V ∂ xwith u(0, t) = V(0, t), θ(0, t) = δ*(0, t) = 0, (24)where c f is a non-dimensional friction fac<strong>to</strong>r defined asτcf x, t .1ρ0V22The only difference <strong>to</strong> plane flow is <strong>the</strong> term involving∂R d /∂ x . If R d → ∞ or ∂R d /∂x → 0, equation (23) reduces <strong>to</strong><strong>the</strong> von Kármán <strong>integral</strong> momentum equation for planeflow. Compared <strong>to</strong> <strong>the</strong> frictional term c f /2 <strong>the</strong> influence of<strong>the</strong> term involving ∂R d /∂x on <strong>the</strong> <strong>boundary</strong> <strong>layer</strong> propertiesis indeed small (below 0.3%), thus disregarding <strong>the</strong>term for simplicity is appropriate. The <strong>boundary</strong> conditionsin (24) assume a uniform inflow profile.Falkner-Skan equationSuitable solutions <strong>to</strong> <strong>the</strong> <strong>boundary</strong> <strong>layer</strong> equations inei<strong>the</strong>r plane or axial symmetry are found by <strong>the</strong> introductionof <strong>the</strong> stream function. A suitable coordinate transformationturns <strong>the</strong> equation for <strong>the</strong> stream function in<strong>to</strong><strong>the</strong> Görtler equation (derivation see [59]). The followingapproach mainly consists in assuming that <strong>the</strong> flow islocally self-similar and that it depends weekly on <strong>the</strong> coordinatex, so that <strong>the</strong> velocity profiles can be mapped on<strong>to</strong>each o<strong>the</strong>r by suitable scaling fac<strong>to</strong>rs in y. Falkner andSkan have found a family of similarity solutions, where<strong>the</strong> free-stream velocity is of <strong>the</strong> power-law formV(x) = Cx n , (26)⎟( )( ) = ( 25)θ ∂ R cd νw f+ − − = 0,( 23)Rd∂ x V 2with a constant C and <strong>the</strong> power-law parameter n. Thesimilarity variable η ~ y/δ(x) is set as( ) ( )1 + n V xu( x, y) = V( x) f′( η) where η = y,2vx( 27 )where f(η) is <strong>the</strong> dimensionless stream function and <strong>the</strong>prime refers <strong>to</strong> derivative with respect <strong>to</strong> η. The coordinatenormal <strong>to</strong> <strong>the</strong> plate is denoted by y. However <strong>the</strong>re areo<strong>the</strong>r general similarity solutions including <strong>the</strong> temporaldependence of <strong>the</strong> profile evolution [61]. The above similarityvariables turn <strong>the</strong> <strong>boundary</strong> <strong>layer</strong> equations in<strong>to</strong> anon-linear ordinary differential equation of order three,which is known as <strong>the</strong> Falkner-Skan-Equation2n( ) = β = ( 28 )+f′′′ + ff′′ + − f′2β 1 0 where( ) = ′( ) = ′( ) = ( )with f 0 f 0 0 and lim f η 1.29η→∞The parameter β is a measure of <strong>the</strong> pressure gradient ∂p/∂x. If β is positive, <strong>the</strong> pressure gradient is negative orfavourable, β = 0 indicates no pressure gradient (i.e. <strong>the</strong>Blasius solution <strong>to</strong> flat plate flow) and negative β denotesa positive or unfavourable pressure gradient. We note thatby assumption, β should vary slowly with coordinate x.The solutions are found numerically by a shooting<strong>method</strong> with f''(0) as free parameter by Hartree [62]. Toavoid extensive calculations we follow a curve fit representationof three quantities extracted from solutions of <strong>the</strong>Falkner-Skan equation used in [19]:f1H∗2δ ∂Vν ∂ x( ) = = − −δ ∗2 2The relation <strong>to</strong> flat plate flow is generally given by <strong>the</strong>shape fac<strong>to</strong>r, which is defined as H = δ * /0, whereas H 0 is<strong>the</strong> equivalent value for plane flow over a flat plate. Thecurve fits provide a good approximation for values of Hbetween 1 and 20. At <strong>the</strong> separation point <strong>the</strong> wall shearstress vanishes, i.e. ∂V X /∂r = 0, which is equivalent <strong>to</strong> ashape fac<strong>to</strong>r H = 4. Relation (32) is not required for <strong>the</strong>calculations, however it is useful <strong>to</strong> predict <strong>the</strong> actual<strong>boundary</strong> <strong>layer</strong> thickness δ 99 , where <strong>the</strong> fluid velocity differsby 1% from <strong>the</strong> free stream value. The relation for <strong>the</strong>shear stress given in [19] isconsequently <strong>the</strong> friction fac<strong>to</strong>r isA schematic illustration of <strong>the</strong> actual flow profile along<strong>the</strong> tube axis is shown in Figure 5. We have chosen a uniforminflow profile with velocity V(0, t). The <strong>boundary</strong><strong>layer</strong> (dashed line) grows from <strong>the</strong> leading edge, decreasesin <strong>the</strong> converging part, while it grows in <strong>the</strong> divergent part1043 . H0−H2. 4 1 e ( ) with H02.59 30n( ) = ( )cfV ⎛ 4 1 ⎞f ( H) = = ⎜ − ⎟ ( 31)2vH ⎝ H H ⎠( )( − )δ99H + 2 4 H 4 H 25f3( H) = =H − 1+ − ..∗3δHτωμ fV 2xt , ,θ( ) = ( 33)2μfcf x, t2.ρ Vθ( ) = ( 34 )0( 32 )Page 8 of 25(page number not for citation purposes)
BioMedical Engineering OnLine 2006, 5:42http://www.biomedical-engineering-online.com/content/5/1/42 Boundary Figure 5 <strong>layer</strong> evolution in <strong>the</strong> myocardial bridgeBoundary <strong>layer</strong> evolution in <strong>the</strong> myocardial bridge. Illustration of <strong>boundary</strong> <strong>layer</strong> separation in a series of two myocardialbridges at a deformation of ζ 0 = 0.2; geometry and <strong>boundary</strong> <strong>layer</strong> thickness are displayed in realistic proportions, <strong>the</strong>velocity profiles are schematically drawn. The inflow profile is uniform with velocity V. We note that <strong>the</strong> extension of <strong>the</strong> separationzones differ, because <strong>the</strong> second myocardial bridge experiences different flow conditions.of <strong>the</strong> tube. The upward triangles (▲) denote <strong>the</strong> point ofseparation, while downward triangles (▼) indicate <strong>the</strong>reattachment of <strong>the</strong> <strong>boundary</strong> <strong>layer</strong>. After separation <strong>the</strong>flow field can be seen as a <strong>to</strong>p hat profile in <strong>the</strong> centre anda recirculation zone close <strong>to</strong> <strong>the</strong> walls. Due <strong>to</strong> <strong>the</strong> adjacentconverging part <strong>the</strong> reattachment is forced early, becausefluid is accelerated. In contrast <strong>the</strong> reattachment after <strong>the</strong>second diverging part takes place fur<strong>the</strong>r downstream.Averaged flow equationsThe simultaneous viscid-inviscid <strong>boundary</strong> <strong>layer</strong>approach assumes an inviscid core flow, which followsequation (19) and a viscous <strong>boundary</strong> <strong>layer</strong>, which maybe found by <strong>the</strong> solution of equation (23). The onedimensionalequations commonly used <strong>to</strong> simulateunsteady, incompressible blood flow in elastic tubes withfrictional losses [53,63] are given in averaged flow variablesas∂ A∂ t∂ q, 35∂ x=− ( )∂ q ⎡ ∂ ⎛=−⎢∂ t ∂x⎜⎣⎢⎝2χ qA⎞ A ∂ p⎟ +⎤⎥⎠ρ0∂ x⎦F v⎥ + ,( 36 )where F ν is <strong>the</strong> viscous friction term and χ is <strong>the</strong> momentumcorrection coefficient. The viscous friction term isdefined as⎡ ∂υx⎤Fν( x, t) = 2π Rν⎢ ,⎣ ∂ r⎥⎦and <strong>the</strong> momentum correction coefficient isRχ1 2xt , ∫ νx Auda .2 A( ) = ( 38 )We rearrange <strong>the</strong> equations written in area and flow ratein terms of area and area-averaged axial flow velocity sothat∂ A′ ⎡ ∂ Au ∂ A=− +∂ t⎢⎣ ∂ x ∂ t( )d⎤, 39⎦⎥ ( )∂ u ⎡ u χ −1 ∂ Au ∂χu1 ∂ p ⎤ F=−⎢+ u +ν .∂ t ⎣ A ∂ x ∂xρ0∂ x ⎦ A⎥ + ( 40 )The derivative of A d with respect <strong>to</strong> time in equation (39)is a prescribed function depending on R d (x, t). It is responsiblefor <strong>the</strong> volume displacement caused by <strong>the</strong> forceddeformation of <strong>the</strong> tube.Hagen-Poiseuille viscous friction and momentum correctionThe determination of viscous friction fac<strong>to</strong>r and momentumcorrection coefficient requires knowledge about <strong>the</strong>velocity profile. For pulsatile laminar flow in small axiallysymmetric vessels a flow profile of <strong>the</strong> form( ) = ( )ν x xr , u x+ ⎡ r− ⎛ γγ 2⎝ ⎜⎞ ⎤⎢ 1 ⎟ ⎥ 41γ R⎣⎢⎠⎦⎥( )is used [50]. Here û is <strong>the</strong> free stream value of <strong>the</strong> axialvelocity and R is <strong>the</strong> actual radius of tube, while γ is <strong>the</strong>profile exponent, which for a Hagen-Poiseuille flow profileis equal <strong>to</strong> two. Consequently <strong>the</strong> friction term is givenbyF ν = -2 π ν(γ + 2) u = K ν u, (42)Page 9 of 25(page number not for citation purposes)
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