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At least 19 recordsLinked to original sources
PubMed1979

Dialysis of middle molecules at pulsatile flow.

Pulsatile flow was used in a continuous flow flat-plate dialyzer in order to achieve the more efficient removal of middle molecules. The solutes ranged in the molecular weights from 342 (sucrose) to 1355 (vitamin B-12). The permeability of Cuprophane membrane to sucrose, raffinose and vitamin B-12 were calculated both for pulseless and pulsatile flows. It was found that pulsatile flow is more favorable than steady flow with regard to increase of membrane permeability. However, as the solute molecular weight increases, fluid-phase resistances become relatively less important and the transport rate becomes dominated by the membrane properties.

Dialysis↗
PubMed1995

Flow pulsatility does not increase mean microvascular pressure or filtration in zone 3 rabbit lungs.

We previously reported that mean pulmonary arterial pressure (Ppa) during pulsatile flow exceeded that for steady flow when flow was greater than the normal resting value and speculated that this was due to irregularities of the flow profiles in precapillary vessels, mainly the larger arteries. From this we hypothesized that neither mean microvascular pressure nor the rate of fluid filtration would be affected by flow pulsatility. We therefore compared the effects of steady vs. pulsatile flow on the double-occlusion pressure (Pdo) and on edema formation (rate of weight gain) in zone 3 rabbit lungs. Excised left lungs (n = 19) were perfused with Tyrode solution and ventilated with an end-expiratory pressure of 2.5 cmH2O. A diaphragm pump generated pulsatile flow with a stroke volume of 1.0 ml (approximately 0.8 the normal resting value for rabbit left lung). Nonpulsatile flow was generated by raising an arterial reservoir. Flow rate was set at 100 or 400 ml/min (approximately 0.4 or 1.6 x the normal resting cardiac output, respectively). Vascular pressures (referenced to the bottom of the lung) were measured after ventilation, at end expiration, was interrupted. Pdo values were obtained in random order at 15 time points that were evenly distributed within the pulse cycle, averaged across pulses to obtain the mean capillary pressure profile, and then averaged over time. At the lower flow of 100 ml/min, mean Ppa and Pdo were slightly lower (3-4%) during pulsatile compared with nonpulsatile conditions. At the higher flow of 400 ml/min, mean Ppa was higher under pulsatile conditions (13%), whereas downstream the mean Pdo values were equal.(ABSTRACT TRUNCATED AT 250 WORDS)

Animals↗
PubMed1985

Interaction of peristaltic flow with pulsatile flow in a circular cylindrical tube.

The effect of pulsatile flow on peristaltic transport in a circular cylindrical tube is analysed. The flow of a Newtonian viscous incompressible fluid in a flexible circular cylindrical tube on which an axisymmetric travelling sinusoidal wave is imposed, is considered. The initial flow in the tube is induced by an arbitrary periodic pressure gradient. A perturbation solution with amplitude ratio (wave amplitude/tube radius) as a parameter is obtained when the frequency of the travelling wave and that of the imposed pressure gradient are equal. The interaction effects of periodic wall induced flow and periodic pressure imposed flow are visualized through the presence of substantially different components of steady and higher harmonic oscillating flow in the first order flow solution. Numerical results show a strong variation of steady state velocity profiles with boundary wave number and Reynolds number and a strong phase shift behaviour of the flow in the radial direction.

Humans↗
PubMed1983

Temperature gradients and rewarming time during hypothermic cardiopulmonary bypass with and without pulsatile flow.

Pulsatile perfusion during cardiopulmonary bypass (CPB) has been reported to have a number of beneficial effects, including attenuation of hormonal stress responses and improved organ blood flow and function. To determine the effect of pulsatile perfusion on temperature gradients and the time required for cooling and rewarming during CPB, we studied 21 patients scheduled for elective coronary artery operations. The patients were divided into two comparable groups: Group 1 (N = 11) had standard nonpulsatile perfusion, while in Group 2 (N = 10), a pulsatile pump was used. Rectal and esophageal temperatures were monitored, as were deltoid muscle temperatures and upper arm and finger skin temperatures in the same extremity. Ambient temperature, bypass flow and pressure, and bypass time were similar in both groups. Time required to cool to the lowest esophageal temperature was virtually identical for both groups (Group 1, 17 +/- 3 min; Group 2, 17.6 +/- 5 min), as was rewarming time (Group 1, 26.8 +/- 11 min; Group 2, 27.2 +/- 6 min). There were no significant differences in temperature measurements between groups except briefly during rewarming when finger skin temperature rose more rapidly in Group 1 (p less than 0.05). Temperature changes following CPB were the same for both groups, with rectal and esophageal temperatures showing an inverse relationships. These data demonstrate that pulsatile flow does not substantially alter rewarming time or temperature gradients during hypothermic CPB.

Aged↗
PubMed1997

Influence of imaging parameters, flow velocity, and pulsatile flow on three-dimensional time-of-flight MR angiography: experimental studies.

OBJECTIVE: The purpose of this study is to evaluate the influence of imaging parameters (TR and flip angle), velocity and pulsatility of flow on three-dimensional time-of-flight magnetic resonance (3D TOF MR) angiography by using a flow phantom. METHODS: The 3D TOF MR angiography of a flow phantom was performed at 1.5-T with various TRs, flip angles and flow velocity. The influence of pulsatile flow was also evaluated. RESULTS: The imaging parameters and flow velocity affected the saturation effects of inflowing spins. Signal loss due to saturation of inflowing spins was more pronounced with a shorter TR, larger flip angle, or lower flow velocity. However signal intensity of stationary tissue were more suppressed with a shorter TR resulting in a larger signal difference to noise ratio of the flowing fluid. Velocity of the flow also affected the signal loss due to intravoxel phase dispersion, which was apparently observed with a stenotic tube. Pulsatility of flow resulted in decreased intensity of flowing fluid and in ghost artifacts along the phase-encoding and slice-select directions. The spacing between these ghosts and intensity of them were dependent on TR, flip angle and pulse rates. CONCLUSIONS: Understanding the influence of imaging parameters and flow characteristics is essential for evaluating the MR angiograms or for improving their quality.

Blood Flow Velocity↗
PubMed1990

Detection of moving flow separation in pulsatile flow and the degree of stenosis by power of Doppler shift signals.

Power ratios were derived from the principle of ultrasonic Doppler velocimetry to determine a ratio of the volume of vortices to the total vessel volume under the ultrasonic beam. This ratio also equals the ratio of the cross-sectional area of vortices to the vessel lumen. In vitro pulsatile flow experiments were performed in a Reynolds number range of 1,230-4,320 with axisymmetric constrictions with area reductions of 55%, 65%, 70%, and 85% to model carotid stenosis. Flow separation downstream from the model stenoses was detected, and the power ratio fluctuated when vortices with the forward- and reverse-flow velocity components passed by the measurement position. The power ratio estimated the degree of stenosis within 10% of error. Ensemble average of the power ratio was computed to obtain the statistically averaged separated flow region. The moving flow reattachment point was revealed downstream from the 85% stenosis at a Reynolds number of 900.

Blood Circulation↗
PubMed1986

Volume flow measurement of pulsatile flow by digitised cine angiography.

The validation, by phantom experiments, of a method of measuring volumetric, pulsatile blood flow in vessels of about 4 mm calibre is described. 'Instantaneous' as well as integrated flow is obtained from cine angiograms by digitisation of the images and densitometric analysis in an advanced computer vision analysis system. From 48 frames per second cine, pulsatile flow at any moment between 0 and about 400 ml/min was calculated within about 10 per cent of the electromagnetic flow meter reading. Further improvement is expected. It is proposed to advance to 3D and have the methodology available for clinical use in due course.

Angiography, Digital Subtraction↗
PubMedDate not supplied

Flow visualization analysis of pulsatile flow in elastic straight tubes.

Effects of wall compliance on the flow characteristics were studied by visualizing pulsatile flow in two straight elastic tubes having different compliance and in a rigid tube. The elastic tubes were made of segmented polyether polyurethane and their compliance was adjusted by varying the wall thickness. Their diameter changes were +/- 3.3 and +/- 4.9% for the pressure pulsation between 20 and 250 mm Hg. An acrylic pipe was used for the rigid model. An air-driven artificial heart was used to generate the pulsatile flow having the mean Reynolds number and frequency parameter of 740 and 11.4, respectively. The flow was visualized by the hydrogen bubble method at every 5% of the pulsatile flow cycle. Velocity distributions along the tube diameter were determined from still images of time lines taken with a CCD camera. The ratio of the wall shear rate in the elastic tubes to that in the rigid tube at each phase correlated well with the radial velocity of tube wall, while it had no significant correlation with the instantaneous tube diameter. These results suggest that the wall compliance either increases or decreases the wall shear rate depending on the phasic relation between the flow and pressure waves. When studying the hemodynamic effects on vascular diseases by model experiments, it may be important to take wall elasticity into account.

Animals↗
PubMed1987

Characteristics of secondary flow in steady and pulsatile flows through a symmetrical bifurcation.

Steady and pulsatile flow in a glass model simulating an arterial bifurcation was investigated by flow visualization techniques. Secondary flow generated at the bifurcation has a similar pattern to a vortex, called the horseshoe vortex, produced around a wall-based protuberance in a circular tube. The same flow disturbance was clearly observed during the decelerating phase of pulsatile flow. The vortex produces a stagnation point on the top and bottom wall just upstream from the bifurcation apex. When aluminium dust was suspended in the test fluid perfusing the blood vessel model, particles deposited over an area spreading from the stagnation point to the lateral corners of the bifurcation. Comparison between the present results and topographical patterns of atherosclerosis reported in the literature suggests that it is in such low shear regions that lipid deposition tends to occur most.

Arteries↗
PubMedDate not supplied

An LDA and flow visualization study of pulsatile flow in an aortic bifurcation model.

The structure of pulsatile flow in a rigid aortic bifurcation model was studied by means of a flow visualization technique and three-dimensional laser-Doppler anemometry. The model was made of glass, having the same shape as that of the average human aortic bifurcation. It was installed into a mock circulatory loop that generated physiological pulsatile flow. Flow separation was observed during accelerated and decelerated flow periods. Double helical flow existed inside the flow separation in the early accelerated flow period. In the decelerated flow period, disturbed flow appeared behind the separation zone. Flow was strongly disturbed during the back flow period, and then was gradually stabilized in the forward flow period. The flow separation and the disturbances released from the flow separation zone greatly influenced near-wall velocities along the lateral wall. The wave form of the near-wall velocity in the flow separation zone was much different from that observed in the aortic portion and behind the separation zone; for example, the magnitude of the negative peak velocity in the direction of the tube axis was larger than that of the positive one, and mean velocity in a cycle was very low. This abnormal phasic change of the near-wall velocity may be associated with atherogenesis. The three-dimensional velocity measurement is very useful for the detailed analysis of near-wall velocity patterns.

Aorta↗
PubMed2001

Blood flow in abdominal aortic aneurysms: pulsatile flow hemodynamics.

Numerical predictions of blood flow patterns and hemodynamic stresses in Abdominal Aortic Aneurysms (AAAs) are performed in a two-aneurysm, axisymmetric, rigid wall model using the spectral element method. Physiologically realistic aortic blood flow is simulated under pulsatile conditions for the range of time-averaged Reynolds numbers 50< or =Re(m)< or =300, corresponding to a range of peak Reynolds numbers 262.5< or =Re(peak) < or = 1575. The vortex dynamics induced by pulsatile flow in AAAs is characterized by a sequence of five different flow phases in one period of the flow cycle. Hemodynamic disturbance is evaluated for a modified set of indicator functions, which include wall pressure (p(w)), wall shear stress (tau(w)), and Wall Shear Stress Gradient (WSSG). At peak flow, the highest shear stress and WSSG levels are obtained downstream of both aneurysms, in a pattern similar to that of steady flow. Maximum values of wall shear stresses and wall shear stress gradients obtained at peak flow are evaluated as a function of the time-average Reynolds number resulting in a fourth order polynomial correlation. A comparison between predictions for steady and pulsatile flow is presented, illustrating the importance of considering time-dependent flow for the evaluation of hemodynamic indicators.

Aortic Aneurysm, Abdominal↗
PubMed2002

Pulmonary capillaries are recruited during pulsatile flow.

Capillaries recruit when pulmonary arterial pressure rises. The duration of increased pressure imposed in such experiments is usually on the order of minutes, although recent work shows that the recruitment response can occur in <4 s. In the present study, we investigate whether the brief pressure rise during cardiac systole can also cause recruitment and whether the recruitment is maintained during diastole. To study these basic aspects of pulmonary capillary hemodynamics, isolated dog lungs were pump perfused alternately by steady flow and pulsatile flow with the mean arterial and left atrial pressures held constant. Several direct measurements of capillary recruitment were made with videomicroscopy. The total number and total length of perfused capillaries increased significantly during pulsatile flow by 94 and 105%, respectively. Of the newly recruited capillaries, 92% were perfused by red blood cells throughout the pulsatile cycle. These data provide the first direct account of how the pulmonary capillaries respond to pulsatile flow by showing that capillaries are recruited during the systolic pulse and that, once open, the capillaries remain open throughout the pulsatile cycle.

Animals↗
PubMed1992

Pulmonary pressures at high flows in the intact pulsatile flow perfused lung.

Pulmonary pressure-flow curves can be easily generated in the intact animal by using a combination of systemic arteriovenous (a-v) fistulas and inferior vena cava (IVC) occlusion. By combining this technique with pulmonary artery occlusion, pulmonary pressure-flow curves may be studied over a broader range of pressures than has been previously been done in the intact, resting animal using pulsatile flow. Pressure-flow curves were generated by varying flow through opening and closing of the a-v fistulas in conjunction with inflating and deflating a balloon in the inferior vena cava. The pressure-flow curves were done under two conditions; (1) with both lungs perfused; (2) with the right lung excluded from the circulation (PA occlusion). PA occlusion resulted in no change in alveolar arterial oxygen tension gradient. The pressure-flow relationships for one lung and two lungs were well described by linear equations (r2 = 0.83 +/- 0.03 and 0.82 +/- 0.04 respectively). The slope of the equations increased with PA occlusion (3.6 +/- 0.4 mmHg.L-1 to 5.9 +/- 0.9 mmHg.L-1). There was no change in the pressure axis intercept with PA occlusion (8.34 +/- 0.8 mmHg pre-occlusion and 8.9 +/- 1.3 mmHg post-occlusion). It is concluded that the pulmonary pressure-flow relationship is well described by a linear function above a mean pulmonary artery pressure (PAP) of 10-12 mmHg.

Animals↗
PubMedDate not supplied

How to produce a pulsatile flow with low haemolysis?

It is evident that a pulsatile flow is important for blood circulation because the flow pulsatility can reduce the resistance of peripheral vessels. It is difficult, however, to produce a pulsatile flow with an impeller pump, since blood damage will occur when a pulsatile flow is produced. Further investigation has revealed that the main factor for blood damage is turbulence shear, which tears the membranes of red blood cells, resulting in free release of haemoglobin into the plasma, and consequently leads to haemolysis. Therefore, the question for developing a pulsatile impeller blood pump is: how to produce a pulsatile flow with low haemolysis? The authors have successively developed a pulsatile axial pump and a pulsatile centrifugal pump. In the pulsatile axial pump, the impeller reciprocates axially and rotates simultaneously. The reciprocation is driven by a pneumatic device and the rotation by a dc motor. For a pressure of 40 mm Hg pulsatility, about 50 mm axial reciprocating amplitude of the impeller is desirable. In order to reduce the axial amplitude, the pump inlet and the impeller both have cone-shaped heads, and the gap between the impeller and the inlet pipe changes by only 2 mm, that is the impeller reciprocates up to 2 mm and a pressure pulsatility of 40 mm Hg can be produced. As the impeller rotates with a constant speed, low turbulence in the pump may be expected. In the centrifugal pulsatile pump, the impeller changes its rotating speed periodically; the turbulence is reduced by designing an impeller with twisted vanes which enable the blood flow to change its direction rather than its magnitude during the periodic change of the rotating speed. In this way, a pulsatile flow is produced and the turbulence is minimized. Compared to the axial pulsatile pump, the centrifugal pulsatile pump needs only one driver and thus has more application possibilities. The centrifugal pulsatile pump has been used in animal experiments. The pump assisted the circulation of calves for several months without harm to the blood elements and the organ functions of the experimental animal. The experiments demonstrated that the pulsatile impeller pump is the most efficient pump for assisting heart recovery, because it can produce a pulsatile flow like a diaphragm pump and has no back flow as occurs in a non-pulsatile rotary pump; the former reduces the circulatory resistance and the latter increases the diastole pressure in aorta and thus increases the perfusion of coronary arteries of the natural heart.

Animals↗
PubMed1990

Post-stenotic core flow behavior in pulsatile flow and its effects on wall shear stress.

Arteries of several species, including man, tend to adjust their diameters such that the mean wall shear stress is in the range of 10-20 dynes cm-2. Additionally, intimal thickening in the human carotid bifurcation correlates well with the reciprocal of wall shear stress as determined in model studies. The correlation indicates that wherever the local mean wall shear stress exceeds approximately 10 dynes cm-2, the artery tends to be spared from intimal thickening. However, it is not known whether mean shear stress, i.e. the time-averaged value, or the instantaneous shear stress is the appropriate correlative variable. Each of these variables suggests different mechanisms for the reaction of the artery wall to its hemodynamic environment. It is therefore important to devise means by which the effects of mean shear and pulsatile shear can be separated in the study of atherogenesis. The present investigation examines the post-stenotic flow field in Plexiglas models under pulsatile conditions approximating those in the aortas of the cynomolgus monkey, an animal often employed in atherogenesis research. Behavior of the core flow and its effects on wall shear stress are studied for stenoses of 75 and 90% area reductions using laser velocimetry. The results show that the post-stenotic field contains regions in which the mean wall shear stress is low, but the pulsatile excursions are large.(ABSTRACT TRUNCATED AT 250 WORDS)

Animals↗
PubMed1983

Comparison of steady and pulsatile flow in a double branching arterial model.

Data are presented to compare fluid flow parameters for steady flow with those for time-varying flow in a simplified two branch model which simulates the region of the abdominal aorta near the celiac and superior mesenteric branches of the dog. Measurements in the model included laser doppler anemometry velocity profiles during steady flow, sinusoidal flow with a superimposed mean flow (referred to as simple oscillatory flow) and arterial pulsatile flow. Shear rate measurements were made by an electrochemical technique during steady flow. Flow visualization studies were done during steady and pulsatile flow. Fluid flow effects in the simplified model during steady flow showed many similarities to the results from previous steady flow studies in a canine aortic cast. Shear rates in the region of the proximal (first, or celiac) branch were independent of flow rates in the distal (second, or mesenteric) branch, but the shear pattern within the proximal branch changed significantly as flow in the proximal branch increased. Shear rates on the proximal flow divider (leading edge into the distal branch) depended primarily on the flow rate to the proximal branch, but not on flow to the distal branch. At certain daughter branch flow ratios (approximately 2:1, proximal to distal), flow separation was promoted at the outer wall of the second branch, but flow separation did not occur in the first branch. In contrast to the canine aortic case results, flow separation was never detected on the distal (mesenteric) flow divider of the simplified model. This observation reflects the subtle effects of geometry on flow since the mesenteric flow divider in the canine cast protrudes into the main flow whereas the distal flow divider in the simplified model does not. There were distinct differences in the flow phenomena between steady, simple oscillatory and arterial pulsatile flow. Peak shear rates during pulsatile flow were as much as 10--100 times greater than steady flow shear rates at comparable mean flow rates. Particularly noteworthy for the pulsatile flow with a Womersley parameter of sixteen were very blunt velocity profiles throughout systole, and the absence of flow separation or reversal in those regions of the model that exhibited flow separation during steady flow. The shape of the waveform influences the nature of the flow during time-varying flows. Future studies of fluid dynamics in model systems must consider the pulsatile nature of the flow if a true interpretation of arterial flow phenomena is to be made.

Aorta, Abdominal↗
PubMed1990

Pulmonary lobar vascular resistances during constant and pulsatile flows.

We measured arterial and venous occlusion pressure profiles in left lower lobes of dog lungs perfused in constant flow and pulsatile flow. Initially, pulmonary arterial pressure, flow rate, and venous pressure were recorded during a series of inflow and outflow occlusions effected during constant flow perfusion. The perfusion was then made pulsatile and while keeping the same flow rate, a second series of vascular occlusions was performed. The arterial occlusion pressures measured with the two modes of perfusion were similar. During pulsatile perfusion, the variation in arterial pressure following an arterial occlusion varied with the timing of occlusion in the pressure cycle. The arterial pressure drop could be recovered by selecting the time-averaged pulmonary arterial pressure as the upstream pressure. During both types of perfusion, the venous occlusion curves were similar. The arterial and venous pressure drops were approximately 4.8 mm Hg and 4.2 mm Hg, respectively. We concluded that the longitudinal distribution of pulmonary vascular pressures can be inferred from occlusion measurements obtained in pulsatile flow.

Animals↗