SEARCH · PubMed Health

Results for “Flow”

Explore indexed PubMed citations for clinical trials, systematic reviews and public health research. Read source abstracts and follow each citation to its original PubMed record.

Quote a phrase for an exact phrase match. Source license links do not imply unrestricted reuse.

At least 19 recordsLinked to original sources

PubMed1992

A flexible blood flow phantom capable of independently producing constant and pulsatile flow with a predictable spatial flow profile for ultrasound flow measurement validations.

The validation of the ultrasound time-domain correlation method of measuring blood flow has required the development of a flexible blood flow phantom capable of generating predictable flow profiles under a wide variety of conditions. The purpose of the phantom is to generate flow with well-known flow properties and not to mimic actual in vivo vessels. This paper describes a flow phantom which can independently generate both constant and pulsatile flow over a wide range of flow rates with a spatially fully developed laminar flow profile. It incorporates a computer-controlled pulsatile pump, which can produce different temporal pulsatile waveforms. The flow phantom also supports multiple vessels, different vessel sizes, as well as different attenuating media. The fluid most commonly used in the phantom is Sephadex mixed with water, and the probability density function of ultrasound reflected from Sephadex is experimentally determined and compared with that of blood. Examples of different constant and pulsatile flow experiments using the phantom are presented.

Adult↗

PubMed1987

Left ventricular internal resistance and unloaded ejection flow assessed from pressure-flow relations: a flow-clamp study on isolated rabbit hearts.

Left ventricular pressure-flow relations were studied, using excised working rabbit hearts and imposing constant flow ejections (flow-clamps) to separate the effects of flow on pressure from those of time, flow duration, starting volume, ejected volume, and volume at specified time. Pressure-flow data at given volume and time were independent of flow duration, starting volume, and ejected volume for flow-clamp durations exceeding 30 msec. Flow history independent of pressure-flow relations was linear for flow values larger than +/- 5 ml/sec. The time-varying elastance model, E(t), of the ventricle was extended with a resistive component. Transient effects of flow can be explained by including a second elastance. The resulting verified 3-component model is consistent with recent reported experimental findings. The properties of internal resistance correspond to a constant unloaded ejection flow Qmax, which was tested by extrapolating the linear pressure-flow relations to zero pressure. Qmax reached a plateau value of approximately 25 ml/sec within 50 msec after the start of contraction. In relaxation, Qmax is only slightly smaller. Qmax did not depend on volume; therefore, the following equation was adequate for the relation between pressure, p(t); volume, V(t); and flow Q(t), during the flow-clamped ejections from 30 minutes after the start of the flow: (t) = E(t).(V(t)-Vd).(1-Q(t)/Qmax)

Animals↗

PubMed1991

A new method for noninvasive estimation of ventricular septal defect shunt flow by Doppler color flow mapping: imaging of the laminar flow convergence region on the left septal surface.

An accurate but simple and noninvasive method for quantifying flow across a ventricular septal defect has yet to be implemented for routine clinical use. A region of flow convergence is commonly imaged by Doppler color flow mapping on the left septal surface of the ventricular septal defect, appearing as a narrowed region of laminar flow with aliased flow velocities entering the orifice. If the first aliasing region represents a hemispheric isovelocity boundary of a surface of flow convergence and all flow at this surface crosses the ventricular septal defect, the flow through the defect can be estimated by using the radius (R), measured from the first alias to the orifice, and the Nyquist limit (NL) velocity (the flow velocity at the first alias). Doppler color flow imaging was performed in 18 children with a single membranous ventricular septal defect undergoing cardiac catheterization at a mean age of 29.8 months (Group I). Indexes of maximal flow rate across the defect were developed from either the radius or the area, obtained by planimetry, of the first alias, based on Doppler color flow images. All indexes were corrected for body surface area and compared with shunt flow (Qp-Qs) and pulmonary to systemic flow ratio (Qp/Qs) determined at cardiac catheterization. Doppler color flow indexes derived from images of flow convergence in both the long-axis (n = 15) and oblique four-chamber (n = 10) views correlated closely with Qp/Qs (r = 0.71 to 0.92) and Qp - Qs (r = 0.69 to 0.97).(ABSTRACT TRUNCATED AT 250 WORDS)

Blood Flow Velocity↗

PubMed1991

A new method for quantification of regurgitant flow rate using color Doppler flow imaging of the flow convergence region proximal to a discrete orifice. An in vitro study.

While color Doppler flow mapping has yielded a quick and relatively sensitive method for visualizing the turbulent jets generated in valvular insufficiency, quantification of the degree of valvular insufficiency has been limited by the dependence of visualization of turbulent jets on hemodynamic as well as instrument-related factors. Color Doppler flow imaging, however, does have the capability of reliably showing the spatial relations of laminar flows. An area where flow accelerates proximal to a regurgitant orifice is commonly visualized on the left ventricular side of a mitral regurgitant orifice, especially when imaging is performed with high gain and a low pulse repetition frequency. This area of flow convergence, where the flow stream narrows symmetrically, can be quantified because velocity and the flow cross-sectional area change in inverse proportion along streamlines centered at the orifice. In this study, a gravity-driven constant-flow system with five sharp-edged diaphragm orifices (ranging from 2.9 to 12 mm in diameter) was imaged both parallel and perpendicular to the direction of flow through the orifice. Color Doppler flow images were produced by zero shifting so that the abrupt change in display color occurred at different velocities. This "aliasing boundary" with a known velocity and a measurable radial distance from the center of the orifice was used to determine an isovelocity hemisphere such that flow rate through the orifice was calculated as 2 pi r2 x Vr, where r is the radial distance from the center of the orifice to the color change and Vr is the velocity at which the color change was noted. Using Vr values from 54 to 14 cm/sec obtained with a 3.75-MHz transducer and from 75 to 18 cm/sec obtained with a 2.5-MHz transducer, we calculated flow rates and found them to correlate with measured flow rates (r = 0.94-0.99). The slope of the regression line was closest to unity when the lowest Vr and the correspondingly largest r were used in the calculation. The flow rates estimated from color Doppler flow imaging could also be used in conjunction with continuous-wave Doppler measurements of the maximal velocity of flow through the orifice to calculate orifice areas (r = 0.75-0.96 correlation with measured areas).(ABSTRACT TRUNCATED AT 250 WORDS)

Adult↗

PubMed1992

Inspiratory muscle work of breathing during flow-by, demand-flow, and continuous-flow systems in patients with chronic obstructive pulmonary disease.

The effect of flow-by continuous positive airway pressure (CPAP) in comparison with continuous-flow (CF) CPAP on inspiratory muscle work of breathing (WI) in intubated patients is not known. We hypothesized that WI during flow-by CPAP would be comparable with that during CF CPAP. In nine intubated male patients recovering from acute respiratory failure related to chronic obstructive pulmonary disease, we compared the effects of flow-by, demand-flow, and CF CPAP on WI. We also evaluated the extent to which the addition of 5 cm H2O of pressure support to demand-flow CPAP (DF-PS5) decreases WI. At CPAP levels of zero and 8 cm H2O, flow-by, demand-flow, DF-PS5 were applied in random order followed by CF CPAP for 15 min each. WI (expressed as Joules per liter and Joules per minute), maximal airway pressure drop during inspiration (delta Paw), total lung resistance (RL), lung compliance (CL), and ventilatory variables were measured. At CPAP of zero cm H2O, WI with flow-by was comparable with CF CPAP, and significantly less than with demand-flow CPAP. At both CPAP of zero and 8 cm H2O, the addition of 5 cm H2O PS to demand-flow CPAP reduced WI significantly to a level comparable with that of flow-by CPAP. At both CPAP levels, delta Paw was the largest, with demand-flow CPAP. RL and CL were not significantly different between the different CPAP systems. We conclude that WI with flow-by CPAP is comparable with that with CF CPAP, and significantly less than with demand-flow CPAP.(ABSTRACT TRUNCATED AT 250 WORDS)

Aged↗

PubMed1985

Variable effects of changes in flow rate through the aortic, pulmonary and mitral valves on valve area and flow velocity: impact on quantitative Doppler flow calculations.

Doppler echocardiographic methods for measuring volumetric flow through the aortic, pulmonary and mitral valves provide the cardiologist with several potentially interchangeable noninvasive methods for determining cardiac output. In addition, comparison of flow differences through individual valves offers the potential to quantitate shunt flow and regurgitant volumes. To date, however, no study has compared the relative accuracies of each of these flow measurements in a controlled experimental setting. Therefore, in this study, Doppler echocardiography was used to measure aortic, pulmonary and mitral valve flows in seven open chest dogs on right atrial bypass where forward cardiac output was precisely controlled with a roller pump. Correlations with roller pump output were better for Doppler measurements of aortic (r = 0.98, SD = 0.3) and mitral (r = 0.97, SD = 0.3) than for pulmonary (r = 0.93, SD = 0.5) valve flow. Interobserver reproducibility was also better for aortic (r = 0.94) and mitral (r = 0.97) than for pulmonary (r = 0.88) valve flow measurements. All valves showed flow-related increases in cross-sectional area, but the slope of this response was variable: 0.05, 0.16 and 0.21 for the aortic, the pulmonary and the mitral valve, respectively. Increased forward flow through the aortic valve, therefore, was manifested primarily by an increase in velocity, whereas increasing flow through the pulmonary and mitral valves produced more significant area changes with correspondingly smaller increases in the velocity component. Recalculation of Doppler-determined outputs, assuming a fixed valve area for the entire range of flows, resulted in a decreased correlation with roller pump output. Both velocity and valve area should be measured at each flow rate for greatest accuracy in volumetric flow calculations.

Animals↗

PubMed1990

Quantitative color flow imaging to measure the two-dimensional distribution of blood flow velocity and the flow rate.

A quantitative Doppler color flow imaging was employed to measure the two-dimensional distribution of blood flow velocity and flow rate in a large vessel. Regional blood flow velocity was determined by converting the color intensity at the respective pixel into corresponding flow velocity and correcting the flow velocity for spatial ultrasound beam incident angle. Instantaneous flow rate was determined precisely from the image of velocity distribution on the cross-section of the flow tract in a steady flow model circuit. In clinical application, the differences in phasic changes in two-dimensional velocity distribution in the ascending aorta, between normal subjects and the patient with aortic regurgitation, were clearly depicted. The quantitative color flow imaging may have great potential to determine noninvasively and real-timely the two-dimensional distribution of flow velocity as well as flow rate in a large vessel.

Aortic Valve Insufficiency↗

PubMed1988

Intracranial arterial blood flow velocity and brain blood flow during hypocarbia and hypercarbia in newborn lambs: a validation of range-gated Doppler ultrasound flow velocimetry.

A transfontanellar range-gated ultrasound Doppler technique for recording blood flow velocity in an artery on the base of the skull was validated in eight anesthetized newborn lambs during hypo-, normo-, and hypercarbia. Blood flow velocity was linearly related to PaCO2 from 20 to 80 mm Hg; mean blood flow velocity (Vmean) (r = 0.86, p less than 0.001), peak systolic blood flow velocity (r = 0.83, p less than 0.001), and end-diastolic blood flow velocity (r = 0.87, p less than 0.001). Vmean changed 2.0% per mm Hg of PaCO2. A linear relationship was demonstrated between brain blood flow (BBF), as determined by the microsphere method, and PaCO2 (r = 0.91, p less than 0.001), with BBF changing 3.6%/mm Hg of PaCO2. Blood flow velocity was linearly related to BBF in the PaCO2 range studied; Vmean (r = 0.89, p less than 0.001), peak systolic blood flow velocity (r = 0.87, p less than 0.001), and end-diastolic blood flow velocity (r = 0.87, p less than 0.001). However, Vmean predicted only approximately 55% of the change in BBF, which suggests a concomitant change in the cross-sectional area of the artery being studied. Despite this limitation, these data suggest that blood flow velocity, recorded by a transfontanellar range-gated Doppler technique from one of the two main arteries perfusing the brain, provides qualitative information on changes in BBF.

Animals↗

PubMed1991

Autoregulation of cochlear blood flow. A comparison of cerebral blood flow with muscular blood flow.

The cochlear blood flow of healthy adult guinea pigs was measured with a laser Doppler flowmeter and flow dynamics were analyzed on the basis of autoregulation. Angiotensin II infusion was used to raise blood pressure, while phlebotomy was done to lower blood pressure. The characteristics of autoregulation of cerebral blood flow and muscular blood flow were also investigated. Cochlear blood flow was considered to have some autoregulation but was less than brain blood flow, which showed significant regulation. Muscular blood flow seemed to have no similar regulatory mechanism.

Angiotensin II↗

PubMed1989

[Study on intracardiac blood flow with color flow mapping in human fetus--the reverse flow at tricuspid valve in human fetus during labor].

This study was performed to determine the relation among the reverse flow signal of tricuspid valve, fetal heart rate pattern and uterine contraction. The blood flow signal through the tricuspid valve was continuously recorded with color flow mapping and direct fetal electrocardiogram as well as uterine contraction in 17 human fetuses during labor. Gestational ages ranged from 36 to 41 weeks. No fetus had a congenital heart anomaly. The detection rate of the reverse flow signal at the tricuspid valve was 100% in variable deceleration, 33% in late deceleration, 5% in normocardia and none in early deceleration. In investigation of the time relation between the reverse flow signal and variable deceleration, the reverse flow signal started after the onset of the recovery phase of deceleration. The tricuspid reverse flow, which was observed in variable deceleration, was caused by an increase in the venous return when cord compression disappeared at the onset of the recovery phase of variable deceleration.

Echocardiography, Doppler↗

PubMed1978

[Coronary flow measurements with cine densitometry. II. Quantitative determinations of flow velocities and flow volumes through severe coronary stenoses during rest (author's transl)].

The normal flow values through healthy or moderately narrowed coronary arteries, which had been determined by a new method of cine radiography, together with a computer, were published in this Journal in 1976. In the present paper we report the results of further studies of flow velocity and flow volume through high-grade coronary artery stenosis of severity III and III--IV. Compared with the results obtained on normal and mildly stenosed arteries, measurements at rest through severely stenosed coronaries showed an almost constant flow. The first results on aorto-coronary vein graft measurement are described.

Absorptiometry, Photon↗

PubMed1989

[Aortic flow patterns in normal neonates with patent ductus arteriosus: evaluation by Doppler color flow imaging].

Serial Doppler echocardiography was performed in 12 normal neonates (0.5-4.0 hrs after birth) to evaluate flow patterns through the ductus arteriosus, and in the aorta and brachiocephalic artery. At the initial examination, flow through the ductus arteriosus was bidirectional in eight of the 12 neonates and continuously left-to-right in the remaining four. The bidirectional ductal shunts became continuous left-to-right flows within 11-21 hrs after birth in seven of the eight neonates and resolved by 29-47 hrs after birth. In the remaining four neonates, the continuous left-to-right shunts disappeared 14-36 hrs after birth. Systolic ejection flow patterns in the aorta and brachiocephalic artery had a triangular shape with the peak velocity in early systole, followed by a minimal flow reversal in all sites examined. Diastolic flow patterns in each arterial site were as follows: 1. In the ascending aorta, there was slow and sustained diastolic forward flow, which did not change with increasing age. 2. In the brachiocephalic artery, there was a pan-diastolic flow reversal in the neonates with bidirectional ductal flow (7/8). This pattern changed to slow pan-diastolic forward flow when the ductal changed to continuous left-to-right flow or when the ductal closure was confirmed. Most (3/4) of the remaining four neonates with continuous left-to-right ductal flow exhibited pan-diastolic forward flow. Another showed a pan-diastolic flow reversal 2 hrs after birth, which changed to pan-diastolic forward flow in the second examination 6 hrs after birth. 3. In the distal aortic arch, there was a pan-diastolic forward flow in all the neonates, and the velocity decreased when a closure of the ductus was confirmed. 4. In the descending aorta, there was a pan-diastolic flow reversal in neonates with bidirectional ductal flow (7/8). This reversal changed to pan-diastolic forward flow, when the ductal flow changed to continuous left-to-right flow or when the ductal closure was confirmed. In the remaining four neonates with continuous left-to-right ductal flow, two showed a pan-diastolic flow reversal at the initial examinations 2 to 3 hrs after birth. This became a pan-diastolic forward flow at the second examinations 6 and 12 hrs after birth. In the other two, there was a pan-diastolic forward flow which did not change. This pan-diastolic flow reversal observed in the brachiocephalic artery and descending aorta was closely related to the bidirectional ductal flow.(ABSTRACT TRUNCATED AT 400 WORDS)

Aorta↗

PubMed1986

Pulsatile flow of Casson's fluid through stenosed arteries with applications to blood flow.

The effects of non-Newtonian nature of blood and pulsatility on flow through a stenosed tube have been investigated. A perturbation method is used to analyse the flow. It is of interest to note that the thickness of the viscous flow region is non-uniform (changing with axial distance). An analytic relation between viscous flow region thickness and red cell concentration has been obtained. It is important to mention that some researchers have obtained an approximate solution for the flow rate-pressure gradient equation (assuming the ratio between the yield stress and the wall shear to be very small in comparison to unity); in the present analysis, we have obtained an exact solution for this non-linear equation without making that assumption. The approximate and exact solutions compare well with one of the exact solutions. Another important result is that the mean and steady flow rates decrease as the yield stress theta increases. For the low values of the yield stress, the mean flow rate is higher than the steady flow rate, but for high values of the yield stress, the mean flow rate behaviour is of opposite nature. The critical value of the yield stress at which the flow rate behaviour changes from one type to another has been determined. Further, it seems that there exists a value of the yield stress at which flow stops for both the flows (steady and pulsatile). It is observed that the flow stop yield value for pulsatile flow is lower than the steady flow. The most notable result of pulsatility is the phase lag between the pressure gradient and flow rate, which is further influenced by the yield stress and stenosis. Another important result of pulsatility is the mean resistance to flow is greater than its steady flow value, whereas the mean value of the wall shear for pulsatile flow is equal to steady wall shear. Many standard results regarding Casson and Newtonian fluids flow, uniform tube flow and steady flow can be obtained as the special cases of the present analysis. Finally, some applications of this theoretical analysis have been cited.

Arterial Occlusive Diseases↗

PubMedDate not supplied

Instantaneous cross-sectional flow velocity profiles: a comparative study of two ultrasound Doppler methods applied to an in vitro pulsatile flow model.

Two methods based on different techniques for construction of cross-sectional flow velocity profiles from Doppler ultrasound signals were compared: an intraluminal method using pulsed-wave Doppler echocardiography and an extraluminal method using two-dimensional (color) Doppler ultrasound. The methods were applied to an in vitro pulsatile flow model. With the intraluminal method, pulsed Doppler recordings obtained throughout several flow pulses at different positions across a tube were digitized, and cross-sectional flow velocity profiles were obtained by matching the onset of flow velocity at the various positions. With the extraluminal method, cross-sectional flow velocity profiles were obtained by time interpolation between the digital flow velocity data obtained from several flow velocity maps. The first flow velocity map was recorded at onset of flow and the following maps were incrementally delayed with 20 msec from one flow pulse to the next. The time lag caused by the time needed to update each of the flow velocity maps was compensated for by time interpolation between the sequentially recorded flow velocity maps. The cross-sectional flow velocity profiles obtained with the two methods were compared at identical positions within the tube model at equal flow settings and throughout the pulsatile flow periods. At three different flow settings with peak flow velocity of 0.3, 0.5, and 0.7 m/sec, the difference (mean +/- SD) between the obtained velocities were 0.01 +/- 0.04, -0.01 +/- 0.05, and -0.03 +/- 0.07 m/sec, respectively. The findings suggest that cross-sectional flow velocity profiles from pulsatile flow velocity recordings can be obtained equally well with both methods.

Blood Flow Velocity↗

PubMedDate not supplied

Doppler color flow mapping of the proximal isovelocity surface area: a new method for measuring volume flow rate across a narrowed orifice.

This manuscript describes a new method, validated in in vitro models, for quantitating volume flow rate across an orifice with Doppler color flow mapping. Flow through a narrowed orifice is characterized by the convergence of radial streamlines proximal to the orifice. In this color Doppler method, one or more isovelocity surface areas (PISA), delineated by blue and red aliasing velocity interfaces, can be identified proximal to the narrowed orifice. Volume flow rate (in milliliters per second) can then be calculated as PISA (in square centimeters) multiplied by the isovelocity of the PISA (in centimeters per second). Doppler color flow mapping was performed in in vitro models of constant and pulsatile flow through an orifice in a wall. The first proximal isovelocity surface area, with an isovelocity corresponding to the aliasing velocity, that is, one half the Nyquist sampling limit, could be identified as a blue and red color interface proximal to the orifice. Over a range of circular orifice diameters from 3 mm to 16 mm and flow rates from 0.5 to 18.7 L/min, the proximal isovelocity surface area could be imaged in two planes. This PISA was best described by a hemielliptic mathematical model with two different radii measured from long-axis and short-axis views. In the constant flow model, volume flow rate calculated from the Doppler PISA correlated well with actual volume flow rate measured simultaneously with a cylinder and stopwatch (r = 0.98, p less than 0.001, standard error of the estimate [SEE] = 0.36 L/min). In the pulsatile flow model, with jet velocities ranging from 2.6 to 7.7 m/sec and flow volume ranging from 1.0 to 10.3 L/min, calculated volume flow rate also demonstrated an excellent correlation with actual volume flow rate (r = 0.99, p less than 0.001, SEE = 0.53 L/min). Findings from these in vitro models suggest that quantification of the proximal isovelocity surface area by Doppler color flow mapping appears to be a promising technique for estimating volume flow rate across a narrowed orifice. This new color Doppler flow method may have advantages over previous Doppler methods in estimating volume flow rate in various clinical situations, for example, valvular regurgitation and shunt lesions.

Blood Flow Velocity↗

PubMed1976

[Quantitative measurement of the basilar arterial flow in the dog-electromagnetic flow-meter study of the extra-and intracranial arterial occlusion (author's transl)].

Recent advances in microneurosurgery have markedly improved the result of surgical treatment of aneurysm and arteriovenous malformation in the posterior cranial fossa. However, more precise study on hemodynamics of the vertebro-basilar system may be necessary for further progress in treatment of the vascular lesions. From this point of view, the authors studied the basilar arterial flow of the dog by means of an electromagnetic flow-meter and the flow probe which was specially devised by the authors. (1) The ratio of absolute value of the mean basilar flow to the total brain weight was calculated, and the flow rate was expressed in ml/100 g brain/min. Mean value was 7.1 ml/100 g brain/min under normocapnea. (2) The effect of occlusion of the common carotid, of the external carotid, of the intracranial internal carotid, and of the extracranial internal carotid on the basilar flow was less remarkable in this order. (3) Under normocapnea, occlusion of the unilateral common carotid artery produced 115% increase in the basilar arterial flow. Bilateral common carotid occlusion resulted in 312% increase of the flow, demonstrating a remarkable ability of compensation of the basilar artery through the circle of Willis and leptomeningeal anastomoses. Under hypercapnea, unilateral common carotid occlusion was followed by 81% increase in the basillar flow. Occlusion of both common carotids caused 230% increase in the basilar flow. Percent increase in the basilar flow after unilateral or bilateral common carotid occlusion under normocapnea was significantly larger than under hypercapnea (p less than 0.05 and p less than 0.01 respectively). It may be supposed that under normacapnea the increased basilar flow following bilateral common carotid occlusion may compensate the decrease in total cerebral blood flow due to carotid occlusion. However, the compensatory rise in the basilar flow under hypercapnea may be not enough to supply the dilated vascular bed in the carotid and basilar territories. There might be even a risk of deficiency of blood supply in the territory of the basilar artery, if the vascular resistance in the carotid area could become less than that in the basilar. The significance of CO2 inhalation therapy for ischemic cerebral lesion was discussed. (4) After the both common carotid arteries were occluded, the basilar aretry was clamped temporarily. Following release of basilar occlusion, reactive hyperemia was observed in the basilar flow. Magnitude and duration of the reactive hyperemia increased progressively depending on duration of the basilar occlusion to some extent. The phenomenon may be best explained by a progressive accumulation of vasodilating metabolities in the ischemic area. (5) Unilateral vertebral occlusion caused 37% decrease in the basilar flow. Bilateral vertebral occlusion resulted in reverse of the basilar flow, averaging 61% of the original value in flow rate. (6) Occlusion of the unilateral subclavian artery produced "subclavian steal phenomenon"...

Animals↗

PubMed1975

Venous flow velocity, venous volume and arterial blood flow.

The relationship of arterial blood flow and venous volume to venous flow velocity was studied in normal subjects. The effects of current modes of treatment in venous thrombosis and of a vasodilator drug on venous flow velocity were also investigated. Total calf flow and venous volume were measured by venous occlusion plethysmography while venous flow axial velocity was determined by the transit time of 131-I albumin from calf to inguinal region. Local intravenous epinephrine administration induced venoconstriction and increased venous flow velocity. Intra-arterial isoproterenol and angiotensin increased and decreased arterial flow, respectively, with no change in venous flow velocity of volume, but local heat increased arterial flow and venous flow velocity with no change in venous volume. Local cold, despite venoconstriction, decreased venous flow velocity accompanied by a decreased arterial flow. Intravenous heparin did not affect venous flow velocity. Intravenous but not oral nylidrin increased venous flow velocity. Therefore venous flow velocity can be significantly increased by venocontriction, by large increases in arterial flow (local heat), and by a parenteral vasodilator drug. These experiements indicate that there is a basis for applying heat but not cold in the prevention and treatment of venous thrombosis.

Adult↗

PubMed1978

alpha- and beta-receptor blockade of isoproterenol- and norepinephrine-induced effects on regional blood flow and blood flow acceleration.

The effects of the beta-receptor blocking agent propranolol (100 microgram/kg i.v.) and of the alpha-receptor blocking agent dihydroergotamine (50 microgram/kg i.v.) on hemodynamic responses to isoproterenol and norepinephrine (both 1--1024 ng/kg) were investigated in anesthetized dogs. The effects studied were: (1) flow in the ascending aorta and the coronary, common hepatic, gastroduodenal, splenic, cranial mesenteric, renal and femoral arteries: (2) maximal flow acceleration in the splenic, cranial mesenteric and femoral arteries; (3) maximal rate of change of left ventricular pressure (LV dP/dt max). Propranolol shifted the dose-response curves for the isoproterenol-induced flow increases in the common hepatic, gastro-duodenal, and cranial mesenteric arteries to the right. It did not influence the flow responses to isoproterenol in the ascending aorta or the coronary, splenic, renal and femoral arteries. Propranolol prevented the decrease of arterial pressure evoked by isoproterenol. Propranolol shifted the isoproterenol-induced increase of LV dP/dt max and maximal blood flow to the same extent. Propranolol blocked the flow to the liver and gastrointestinal tract to a greater extent than the LV dP/dt max and maximal flow acceleration. Propranolol had no effect on the norepinephrine-induced increases in flow in the splenic, femoral and coronary arteries, but blocked the norepinephrine-evoked increases of flow accelerations and LV dP/dt max to the same extent. Dihydroergotamine inhibited the norepinephrine-induced increase in flow in the femoral artery and the decreases in flow in the hepatic, splenic, cranial mesenteric and renal arteries, and reversed the reduction of flow in the gastroduodenal artery. It is argued that dihydroergotamine may inhibit the increase in femoral flow through two mechanisms: (1) blocking the flow reduction to norepinephrine in the abdomen, and thereby passively shunting blood from the abdomen in preference to the femoral bed; (2) attenuating the norepinephrine-evoked reflexogenic femoral vasodilatation. It is concluded that: (1) propranolol is a beta-receptor blocking agent with a preference for blockade of isoproterenol-induced vascular effects; (2) norepinephrine-induced flow increases are not direct actions on vascular beta-receptors; (3) the increase of maximal blood flow accelerations after isoproterenol and norepinephrine is mediated by stimulation of cardiac beta-receptors; (4) dihydroergotamine is an alpha-receptor blocking agent particularly in the splanchnic vascular region.

Adrenergic alpha-Antagonists↗