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The steady motion of a semi-infinite bubble through a flexible-walled channel

Published online by Cambridge University Press:  26 April 2006

Donald P. Gaver
Affiliation:
Department of Biomedical Engineering, Tulane University, New Orleans. LA 70118, USA
David Halpern
Affiliation:
Department of Mathematics, University of Alabama, Tuscaloosa, AL 35487, USA
Oliver E. Jensen
Affiliation:
Department of Mathematics and Statistics, University of Newcastle upon Tyné, Newcastle upon Tyne, NE1 7RU, UK
James B. Grotberg
Affiliation:
Departments of Biomedical Engineering and Anesthesia, Northwestern University, Evanston, IL 60208, USA

Abstract

We performed a theoretical investigation of the progression of a finger of air through a liquid-filled flexible-walled channel - an initial model of pulmonary airway reopening. Positive pressure, Pb* drives the bubble forward, and separates flexible walls that are modelled as membranes under tension, T, supported by linearly elastic springs with elasticity K. The gap width between the walls under stress-free conditions is 2H, and the liquid has constant surface tension, γ, and viscosity, μ. Three parameters define the state of the system: Ca = μU/γ is a dimensionless velocity that represents the ratio of viscous to capillary stresses; η = T/γ is the wall tension to surface tension ratio, and γ = KH2/γ is the wall elastance parameter. We examined steady-state solutions as a function of these parameters using lubrication analysis and the boundary element method.

These studies showed multiple-branch behaviour in the Pb-Ca relationship, where Pb = Pb*/(γ/H) is the dimensionless bubble pressure. Low Ca flows (Ca [Lt ] min (1, (Γ3/η)1/2)) are dominated by the coupling of surface tension and elastic stresses. In this regime, Pb decreases as Ca increases owing to a reduction in the downstream resistance to flow, caused by the shortening of the section connecting the open end of the channel to the fully collapsed region. High Ca behaviour (max (1, (γ3/η)1/2) [Lt ] Ca [Lt ] η) is dominated by the balance between fluid viscous and longitudinal wall tension forces, resulting in a monotonically increasing PbCa relationship. Increasing η or decreasing Γ reduces the Ca associated with the transition from one branch to the other. Low Ca streamlines show closed vortices at the bubble tip, which disappear with increasing Ca.

Start-up yield pressures are predicted to range from 1 [les ] Pyield*/(γ/L*) [les ] 2, which is less than the minimum pressure for steady-state reopening, Pmin/(γ/L*), where L* is the upstream channel width. Since Pyield* < Pmin*, the theory implies that low Ca reopening may be unsteady, a behaviour that has been observed experimentally. Our results are consistent with experimental observations showing that Pb* in highly compliant channels scales with γ/L*. In contrast, we find that wall shear stress scales with γ/H. These results imply that wall shear and normal stresses during reopening are potentially very large and may be physiologically significant.

Type
Research Article
Copyright
© 1996 Cambridge University Press

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References

Brebbia, C. A. & Dominguez, J. 1989 Boundary Elements - An Introductory Course. Computational Mechanics, Southampton, UK.
Bretherton, F. P. 1961 The motion of long bubbles in tubes. J. Fluid Mech. 10, 166188.Google Scholar
Coyle, D. J., Macosko, C. W. & Scriven, L. E. 1986 Film-splitting flows in forward roll coating. J. Fluid Mech. 171, 183207.Google Scholar
Gaver, D. P., Samsel, R. W. & Solway, J. 1990 The effects of surface tension and viscosity on airway opening. J. Appl. Physiol. 69(1), 7485.Google Scholar
Greaves, I. A., Hildebrandt, J. & Hoppin, F. G. 1986 Micromechanics of the lung. In: Handbook of Physiology: The Respiratory System, Mechanics of Breathing, sect. 3, vol. 3, pt. 1, chap. 14, pp. 195216, Am. Physiol. Soc., Bethesda, MD, USA.
Grotberg, J. B. 1994 Pulmonary and transport phenomena. Ann. Rev. Fluid Mech. 26, 529571.Google Scholar
Halpern, D. & Gaver, D. P. 1994 Boundary element analysis of the time-dependent motion of a semi-infinite bubble in a channel. J. Comput. Phys. 115(2), 366375.Google Scholar
Halpern, D. & Grotberg, J. B. 1992 Fluid-elastic instabilities of liquid-lined flexible tubes. J. Fluid Mech. 244, 615632.Google Scholar
Halpern, D. & Grotberg, J. B. 1993 Surfactant effects on fluid-elastic instabilities of liquid-lined flexible tubes - a model of airway closure. J. Biomech. Engng 115(3), 271277.Google Scholar
Halpern, D. & Secomb, T. W. 1989 The squeezing of red blood cells through capillaries with near-minimal diameters. J. Fluid Mech. 203, 381400.Google Scholar
Halpern, D. & Secomb, T. W. 1991 Viscous motion of disk-shaped particles through parallel-sided channels with near-minimal widths. J. Fluid Mech. 231, 545560.Google Scholar
Hsu, S., Strohl, K. P. & Jamieson, A. 1994 Role of viscoelasticity in the tube model of airway reopening. I. Nonnewtonian sols. J. Appl. Physiol. 76, 24812489.Google Scholar
Johnson, M., Kamm, R. D., Ho, L. W., Shapiro, A. & Pedley, T. J. 1991 The nonlinear growth of surface-tension-driven instabilities of a thin annular film. J. Fluid Mech. 233, 141156.Google Scholar
Kamm, R. D. & Schroter, R. C. 1989 Is airway closure caused by liquid film instability? Respir. Physiol. 75, 141156.Google Scholar
Ladyzhenskaya, O. A. 1963 The Mathematical Theory of Viscous Incompressible Flow. Gordon and Breach.
Landau, L. & Levich, B. 1942 Dragging of a liquid by a moving plate. Acta Phys-chim. URSS 17, (1–2), 4254.Google Scholar
McEwan, A. D. & Taylor, G. I. 1966 The peeling of a flexible strip attached by a viscous adhesive. J. Fluid Mech. 26, 115.Google Scholar
Macklem, P. T. 1971 Airway obstruction and collateral ventilation. Physiol. Rev. 51, 368436.Google Scholar
Macklem, P. T., Proctor, D. F. & Hogg, J. C. 1970 The stability of peripheral airways. Respir. Physiol. 8, 191210.Google Scholar
Naureckas, E. T., Dawson, C. A., Gerber, B. S., Gaver, D. P., Gerber, H. L., Linehan, J. H., Solway, J. & Samsel, R. 1994 Airway reopening pressure in isolated rat lungs. J. Appl. Physiol. 76(3), 13721377.Google Scholar
Otis, D. R., Johnson, M., Pedley, T. J. & Kamm, R. D. 1993 The role of pulmonary surfactant in airway closure - a computational study. J. Appl. Physiol. 75(3), 13231333.Google Scholar
Park, C. W. & Homsy, G. M. 1984 Two-phase displacement in Hele-Shaw cell: theory. J. Fluid Mech. 139, 291308.Google Scholar
Perun, M. L. & Gaver, D. P. 1995a An experimental model investigation of the opening of a collapsed untethered pulmonary airway. J. Biomech. Engng 117, 245253.Google Scholar
Perun, M. L. & Gaver, D. P. 1995b The interaction between airway lining fluid forces and parenchymal tethering during pulmonary airway reopening. J. Applied Physiol. 75, 17171728.Google Scholar
Ratulowski, J. & Chang, H. C. 1990 Marangoni effects of trace impurities on the motion of long gas bubbles in capillaries. J. Fluid Mech. 210, 303328.Google Scholar
Reinelt, D. A. & Saffman, P. G. 1985 The penetration of a finger into a viscous fluid in a channel and tube. SIAM J. Sci. Stat. Comput. 6, 542561.Google Scholar
Saffman, P. G. & Taylor, G. I. 1958 The penetration of a fluid into a porous medium or Hele-Shaw cell containing a more viscous liquid. Proc. R. Soc. Lond. A 245, 312329.Google Scholar
Wiswell, T. E. & Mendiola, J. 1993 Respiratory distress syndrome in the newborn: innovative therapies. Am. Fam. Phys. 47, 407414.Google Scholar
Yap, D. Y. K., Liebkemann, W. D., Solway, J. & Gaver, D. P. 1994 The influence of parenchymal tethering on the reopening of closed pulmonary airways. J. Appl. Physiol. 76(5), 20952105.Google Scholar