Biorheology

The piezoelectricity of semicrystalline biopolymers was first discovered for wood and bone in the 1950’s. Piezoelectric properties have since been investigated for a number of biological substances, including polysaccharides, proteins and deoxyribonucleates. The shear piezoelectric constants -d₁₄ = d₂₅ were determined for their oriented structures with a uniaxial symmetry D ∞ . From studies of synthetic polypeptides and optically active polymers, it was concluded that the origin of piezoelectricity lies in the internal rotation of dipoles such as CONH. Values of d₁₄ = -10 pC/N were determined for highly elongated films of poly-L-lactic acid, optically active and biodegradable. The implantation of this polymer induced the growth of bone, possibly because ionic current caused by piezoelectric polarization stimulated the activity of bone cells. Submicron-thick polyurea films were prepared by evaporating diisocyanate and diamine monomers in vacuum. After poling, the films exhibited pyro- and piezoelectric effects. The tensile piezoelectric constant d₃₁ = 10 pC/N persisting up to 200°C was also observed for aliphatic polyurea films.

In practical measurement of stress-relaxation, a certain length of time is required to apply the initial stress to a specimen. We refer to this process as pre-extension. In the stress-relaxation analysis of the plant cell wall which we developed, a wall specimen is stretched at a constant rate in pre-extension. The condition of pre-extension, such as the length of the pre-extension period, affects the subsequent stress-relaxation process. Thus, the stress-relaxation time spectrum calculated directly from the stress-relaxation process is an approximation. In this study, the condition during pre-extension was formulated in a stress-relaxation function and the stress-relaxation time spectrum, H ( τ ) , was calculated as H ( τ ) = b · { exp ( − T 0 / τ ) − exp ( − T m / τ ) } / { r · τ · ( l − exp ( − T p / τ ) ) } where T 0 and T m are the minimum and maximum relaxation times, τ is the relaxation time, b is the relaxation rate, r is the extension rate in pre-extension and T p is the pre-extension time. The effect of the pre-extension condition on the spectrum is discussed.

To study the possible role of nonlinear viscoelastic effects in the thrombelastograph (TEG), clotting of bovine plasma was studied by both thrombelastography and with a controlled strain rheometer. Clot rheology is dominated by elastic effects at frequencies of interest. There is a well-defined regime of linear elasticity for strains less than around 2%, while at larger strains the clots show significant strain hardening. Oscillatory shear applied during clotting has little effect on the resulting clot provided that the strain is less than 2%, but leads to substantial weakening of clots formed at larger strains. The TEG operates within the regime of nonlinear elasticity, significantly obscuring the interpretation of TEG amplitude in terms of an elastic modulus. Comparing the results of standard TEG experiments with those conducted with a modified TEG, having no oscillation during clotting, shows that deformation during standard thrombelastography leads to weaker clots than are produced under quiescent conditions.

Because arteriovenous fistulae are associated with a palpable thrill and an audible murmur, the vibrational activity of the blood vessel walls about experimental arteriovenous fistulae in rabbits was investigated using, for the first time, a high-resolution laser vibrometer. Frequencies of mural vibrations up to 2200 Hz were recorded at different sites about the fistulae. The relationship of this vibratory activity of blood vessel walls to physiological and pathological conditions warrants further investigation.

The effect of temperature on the flow of diluted blood [Hct = 0.21], through 5 µm Nuclepore filters, is described by the Arrhenius equation with an energy of activation of 27.7 kJ/mol. Plasma, diluted with PBS, is almost three times less sensitive to temperature, with an energy of activation of 9.8 kJ/mol, while red cells are of intermediate sensitivity, with an energy of activation of 14.7 kJ/mol. The most sensitive elements to changes in temperature are leukocytes, with energies of activation of 31 kJ/mol and 35 kJ/mol for fast-flowing leukocytes (granulocytes and lymphocytes) and slow-flowing leukocytes (monocytes) respectively. Hence, the major determinants of the decline in filterability of blood through micropore filters are the leukocytes. This effect is compounded when blood is kept for 10 minutes or more at 10Âř C due to activation of granulocytes, which leads to permanent pore blocking when the affected blood is filtered at room temperature. The combination of increased passage time of leukocytes through peripheral areas at abnormally low temperatures and subsequent activation might influence the flow of blood in non-affected tissues. The effect of temperature on the filterability of red blood cells through 3 µm filters is not described by the Arrhenius equation and the deviations are seen as a gradual change of slope rather than a sharp break between two straight lines. The data are consistent with a gradual shift in rate limiting step away from the entry event into pores, which dominates at low temperature but becomes progressively less important at elevated temperatures. The changing parameter is probably the volume of the red cell, which is less important when flow is measured through 5 µm pores.

This study describes the in vivo measurement of pressure drop and flow during the cardiac cycle in the femoral artery of a dog, and the computer simulation of the experiment based on the use of the measured flow, vessel dimensions and blood viscosity. In view of the experimental uncertainty in obtaining the accurate velocity profile at the wall region, the velocity pulse at the center was measured and numerical calculations were performed for the center line instantaneous velocity and within the two limits of spatial distribution of inlet flow conditions: uniform and parabolic. Temporal and spatial variations of flow parameters, i.e., velocity profile, shear rate, non-Newtonian viscosity, wall shear stress, and pressure drop were calculated. There existed both positive and negative shear rates during a pulse cycle, i.e., the arterial wall experiences zero shear three times during a cardiac cycle. For the parabolic inlet condition, the taper of the artery not only increased the magnitude of the positive and negative shear rates, but caused a steep gradient in shear rate, a phenomenon which in turn affects wall shear stress and pressure. In contrast, for the uniform inlet condition, the flow through the tapered artery was predominantly the developing type, which resulted in reduction in magnitude of wall shear rate along the axial direction.