| HOME | HELP | FEEDBACK | SUBSCRIPTIONS | ARCHIVE | SEARCH | TABLE OF CONTENTS |
|
|
|
|||||||
|
|||||||||
Department of Bioengineering, University of California, San Diego, La Jolla, California 92093-0412
 |
ABSTRACT |
|---|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
Effect of increasing blood viscosity during extreme hemodilution on capillary perfusion and tissue oxygenation was investigated in the awake hamster skinfold model. Two isovolemic hemodilution steps were performed with 6% Dextran 70 [molecular weight (MW) = 70,000] until systemic hematocrit (Hct) was reduced by 65%. A third step reduced Hct by 75% and was performed with the same solution [low viscosity (LV)] or a high-molecular-weight 6% Dextran 500 solution [MW = 500,000, high viscosity (HV)]. Final plasma viscosities were 1.4 and 2.2 cP (baseline of 1.2 cP). Hct was reduced to 11.2 ± 1.1% from 46.2 ± 1.5% for LV and to 11.9 ± 0.7% from 47.3 ± 2.1% for HV. HV produced a greater mean arterial blood pressure than LV. Functional capillary density (FCD) was substantially higher after HV (85 ± 12%) vs. LV (38 ± 30%) vs. baseline (100%). PO2 levels measured with Pd-porphyrin phosphorescence microscopy were not statistically changed from baseline until after the third hemodilution step. Wall shear rate (WSR) decreased in arterioles and venules after LV and only in arterioles after HV. Wall shear stress (WSR × plasma viscosity) was substantially higher after HV vs. LV. Increased mean arterial pressure and shear stress-dependent release of endothelium-derived relaxing factor are possible mechanisms that improved arteriolar and venular blood flow and FCD after HV vs. LV exchange protocols.
functional capillary density; shear rate; shear stress; dextran; tissue oxygenation
| |
INTRODUCTION |
|---|
|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
HEMODILUTION CHANGES the physical properties of blood by reducing the number of circulating red blood cells (RBCs) thus decreasing the oxygen-carrying capacity of blood and blood viscosity. During moderate levels of hemodilution, reduction of the systemic hematocrit (Hct) up to 50% is compensated for with a decrease in blood viscosity leading to an increased blood flow velocity and decreased diffusional oxygen exit from arterioles, resulting in augmented or maintained oxygen delivery to tissue (28, 30). In addition, reduction of systemic Hct during intentional hemodilution is not mirrored at the microcirculatory level, since capillary Hct is sustained near control levels (26, 29, 37, 38) thus maintaining tissue oxygenation.
When systemic Hct is reduced by 60% or more (Hct that is 40% of normal or less) there is a significant decrease in blood viscosity and a lowering of blood hemoglobin concentration to levels where oxygen-carrying capacity is marginal and tissue oxygenation may be impaired. Under these conditions, oxygen delivery to tissue hinges on increasing oxygen extraction and maintaining the surface area for exchange, which is determined by the functional capillary density (FCD).
Blood viscosity is mainly determined by the concentration of RBCs, whereas the shear rate at the wall is a function of the plasma viscosity (15). The viscous properties of the plasma and the plasma layer in setting vessel wall shear stress are particularly significant in the microcirculation due to the migration of RBCs to the centerline of the vessel (1). Viscosity and flow velocity of blood define shear stress at the blood vessel wall, which stimulates vascular endothelium to produce vasoactive substances such as prostacylin (12) and nitric oxide [NO (4)]. In moderate hemodilution, the reduction in viscosity is compensated by the increased flow; thus the shear stress sensed by the endothelium does not change significantly.
We hypothesize that, during extreme hemodilution, the cardiac output can no longer be sustained, and consequently blood flow will not develop the sufficient shear stress required for shear stress-dependent release of mediators, resulting in a reduced capillary perfusion. This is not the situation found in moderate hemodilution where the reduction in Hct and thus blood viscosity is compensated for by an increased blood velocity. The shear stress sensed by the endothelium in this situation is actually increased due to the increased flow and an essentially unchanged plasma viscosity. To determine if viscosity is a factor involved in regulating FCD and microvascular flow during extreme hemodilution, we designed a study in which we lower oxygen-carrying capacity but augment plasma viscosity by exchanging blood with a high-viscosity (HV) ultrahigh- molecular-weight dextran solution. Increased plasma viscosity at extreme hemodilution levels was analyzed in terms of microvascular tone, blood flow, FCD, and oxygen distribution to determine the functional state of the microvasculature under these conditions.
| |
MATERIALS AND METHODS |
|---|
|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
Animal Preparation
Investigations were performed on 55- to 65-g golden Syrian hamsters (Simonsen, Gilroy, CA). Animal handling and care were provided following the procedures outlined in the Guide for the Care and Use of Laboratory Animals (National Re- search Council, 1996). The study was approved by the local Animal Subjects Committee. The hamster chamber window model is widely used for microvascular studies in the unanesthetized state, and the complete surgical technique is described in detail elsewhere (8, 11). Briefly, the animal was prepared for chamber implantation with a 5 mg/kg ip injection of pentobarbital sodium anesthesia. After hair removal, sutures were used to lift the dorsal skin away from the animal, and one frame of the chamber was positioned on the animal's back. A chamber consisted of two identical titanium frames with a 15-mm circular window. With the aid of backlighting and a stereomicroscope, one side of the skinfold was removed following the outline of the window until only a thin monolayer of retractor muscle and the intact subcutaneous skin of the opposing side remained. Saline and then a cover glass were placed on the exposed skin held in place by the other frame of the chamber. The intact skin of the other side was exposed to the ambient environment. The animal was allowed at least 2 days for recovery; then its chamber was assessed under the microscope (×650) for any signs of edema, bleeding, or unusual neovascularization. Barring these complications, the animal was anesthetized again with pentobarbital sodium. Arterial and venous catheters were implanted in the carotid artery (PE-50) and jugular vein (PE-10), respectively. The catheters were filled with a heparinized saline solution (30 IU/ml) to ensure their patency at the time of experiment. Catheters were tunneled under the skin and exteriorized at the dorsal side of the neck where they were attached to the chamber frame with tape. The experiment was performed after at least 24 h but within 48 h after catheter implantation.Inclusion criteria. Animals were suitable for the experiments if 1) systemic parameters were within normal range, namely, heart rate (HR) >320 beats/min, mean arterial blood pressure (MAP) >80 mmHg, systemic Hct >45%, and arterial PO2 >50 mmHg; and 2) microscopic examination of the tissue observed under ×650 magnification did not reveal signs of edema or bleeding.
Systemic Parameters
MAP was measured continuously over the entire experimental period, except during the actual blood exchange, by attaching the arterial catheter to a pressure transducer (Beckman Recorder; Spectramed Pressure Transducer). HR was determined from the pressure trace. Hct was measured from centrifuged arterial blood samples taken in heparinized capillary tubes (Readacrit Centrifuge; Clay Adams, Division of Becton-Dickinson, Parsippany, NJ).Blood Chemistry and Rheology
Arterial blood sampled in two heparinized capillary tubes from the carotid artery catheter was immediately analyzed for arterial PO2, PCO2, and pH at 37°C using a pH/blood gas analyzer (model 248; Chiron Diagnostics, Norwood, MA). Hemoglobin content of blood was determined from a drop of blood using a handheld photometric device (B-Hemoglobin Photometer Hemocue). Blood samples for viscosity and colloid osmotic pressure measurements were quickly withdrawn from the animal with a heparinized 3-ml syringe at the end of the experiment for immediate analysis or refrigerated for next-day analysis. The small animal size allowed for only ~2 ml of blood to be withdrawn from the animal after an experiment, which was not sufficient volume to measure colloid osmotic pressure, blood viscosity, and plasma viscosity. Because of the small sample volume, only one or two of these parameters could be measured in each animal. Measurements were then combined and taken to be representative of the entire group. Blood samples were centrifuged, and colloid osmotic pressure in the plasma was measured using a colloid osmometer (model 420; Wescor, Logan, UT). Calibration of the osmometer was made with a 5% albumin solution using a 30,000 molecular weight cut off membrane (Amicon, Danvers, MA) (44). The viscosity of plasma and whole blood was determined at a shear rate of 160 s
1 at 37°C in a
500-µm-diameter capillary viscometer (33).
Microhemodynamic Parameters
Detailed mappings were made of the chamber vasculature so that the same vessels studied in control could be followed throughout the experiment. Functional capillaries, defined as those capillary segments that have RBC transit of at least a single RBC in a 30-s period, were assessed in 10 successive microscopic fields, totaling a region of ~0.46 mm2. Observation of the fields was done systematically by displacing the microscopic field of view by a field width in 10 successive steps in the lateral direction (relative to the observer). Each step was viewed on the video monitor and was 240 µm long when referred to the tissue. The first field was chosen by a distinctive anatomic landmark (i.e., large vascular bifurcation) to easily and quickly reestablish the same fields and vessels at each observation time point. Each field had between two and five capillary segments with RBC flow. FCD (cm1), i.e., total length
of RBC perfused capillaries divided by the area of the microscopic
field of view, was evaluated by measuring and adding the length of
capillaries that had RBC transit in the field of view. The relative
change in FCD from baseline levels after each intervention is
indicative of the extent of capillary perfusion.
Arteriolar and venular blood flow velocity were measured on-line using
the photodiode/cross-correlator system of Intaglietta et al. (19; Fiber
Optic Photo Diode Pickup and Velocity Tracker model 102B; Vista
Electronics, San Diego, CA). The measured centerline velocity was
corrected according to vessel size to obtain the mean RBC velocity
(V; see Ref. 27). The video image
shearing technique was used to measure vessel diameter
(D) on-line (Digital Video Image
Shearing Monitor model 908; Vista Electronics). Blood flow rate
(
) is equal to the mean RBC velocity times the
cross-sectional area of the vessel and was calculated according to the
expression = V · 
(D/2)2.
Wall shear stress (WSS) is defined by the formula
|
(1) |
is the plasma viscosity.
Intravascular and Extravascular PO2 Measurements
Oxygen tension measurements were made using palladium-porphyrin phosphorescence quenching microscopy (39, 45), which is based on the relationship between the decay rate of excited palladium-mesotetra-(4-carboxyphenyl)porphyrin (Porphyrin Products, Logan, UT) bound to albumin and the partial pressure of oxygen according to the Stern-Volmer equation (45). Animals received a slow intravenous injection of 15 mg/kg body wt at a concentration of 10.1 mg/ml of the phosphorescence dye ~10 min before PO2 measurements. Albumin exchange between plasma and tissue allows sufficient concentrations of albumin-bound dye within the interstitium to achieve an adequate signal-to-noise ratio for interstitial PO2 measurements (41). Simultaneous tissue PO2 measurements using this system and the classic microelectrode technique have found nearly identical values (3).In our system described in detail elsewhere (39), intravascular
measurements are made by placing an optical rectangular window within
the vessel of interest, and the longest side of the rectangle is
positioned parallel to the vessel wall. Intravascular PO2 measurements were made in large
feeding arterioles, smaller arcading arterioles, large venules, and
smaller collecting venules. Tissue
PO2 measurements were made in
interstitial regions devoid of large vessels with a 10 µm by 10 µm
optical window to obtain an estimate of the lowest oxygen level within the chamber (21). The decay curves are analyzed off-line, using a
standard single exponential least squares numerical fitting technique.
Resultant time constants are applied to the Stern-Volmer equation to
calculate PO2, where the quenching
constant and the phosphorescence lifetime in the absence of oxygen
measured are 325 mmHg1 · s1
and 600 µs, respectively, in this system. The phosphorescence decay
due to quenching at a specific PO2
yields a single decay constant (42), and in vitro calibration has been
demonstrated to be valid for in vivo measurements.
Acute Isovolemic Hemodilution
Progressive hemodilution to a final systemic Hct level of 25% of baseline was accomplished with three isovolemic exchange steps. The volume of each exchange was a percentage of the animal's total blood volume, estimated at 7% of the body weight. The level 1 exchange of 40% of the blood volume was followed by level 2 and 3 exchanges, where 35% of the blood volume was exchanged at each step. Level 1 exchange results in a moderate hemodilution. Level 2 and 3 exchanges result in an extreme hemodilution where systemic Hct falls below 40% of normal. Using an infusion pump, we first passed the exchange solution through an in-line 0.22-µm syringe filter and then into the animal via the jugular vein catheter at a rate of 100 µl/min. Blood was simultaneously withdrawn by hand from the carotid artery at the same rate, a method found to be more accurate than using the automated syringe pump where the detection of catheter obstruction usually due to blood clotting is delayed. Because of the size of the animals, a slow rate of exchange was chosen to ensure a stable blood pressure during the exchange period. The animal was given a 5-min recovery period before data acquisition.Experimental Design
The unanesthetized animal was placed in a restraining tube where it had access to wet feed during the entire experimental period. The animal was given 30 min to adjust to the tube environment before the control systemic parameters (MAP, HR, blood gases, and Hct) were measured. The conscious animal in the tube was then affixed to the microscopic stage of a transillumination intravital microscope (Leitz Ortholux II). The tissue image was projected onto a charge-coupled device camera (COHU 4815-2000) connected to a videocassette recorder (AG-7355; Panasonic) and viewed on a monitor (PVM-1271Q; Sony). The baseline FCD was assessed using a ×25 (numerical aperture = 0.7, Leitz) salt water objective. For easier detection of RBC passage, the contrast between RBCs and tissue was enhanced with a BG12 (420 nm) bandpass filter. The animal, still situated in the restraining tube, was then repositioned on an inverted microscope (IMT-2 Olympus, New Hyde Park, NY) equipped with a ×20 dry objective (numerical aperture = 0.46; Olympus), where arterioles and venules chosen for study (4-7 of each type) were characterized by their blood flow velocity and caliber. Microscopic images were televised on another identical video system. The animal was repositioned on each microscope after each exchange to follow the changes of the microvascular parameters. Fields of observations and vessels were chosen for study at locations in the tissue where the vessels were in sharp focus. The same fields and vessels were investigated throughout the experiment so that comparisons are related directly to baseline levels.Animals were randomly divided into the following five experimental groups: 1) control (no hemodilution); 2) level 1 [hemodilution with Dextran 70 (6% wt/vol mean molecular weight of 70,000; Pharmacia) to Hct of 60% of baseline]; 3) level 2 (hemodilution with Dextran 70 to Hct of 40% of baseline); 4) level 3 low viscosity (LV; hemodilution with Dextran 70 to Hct of 25% of baseline); 5) level 3 HV [hemodilution with Dextran 70 to Hct of 35% of baseline followed by hemodilution with 6% wt/vol Dextran 500 (mean molecular weight: 500,000; Pharmacia) in 0.9% normal saline to Hct of 25% of baseline].
Immediately after baseline systemic measurements, animals in the control group received a bolus injection of palladium-porphyrin dye, and measurements of oxygen distribution and microvascular hemodynamics were performed. In the experimental exchange groups, successive hemodilution was performed after baseline systemic, microvascular, and hemodynamic characterization. After each exchange and the ensuing stabilization period, measurements were performed following the schedule shown in Fig. 1, where exchanges begin every hour, i.e., the second exchange commences exactly 1 h after the first exchange. Repeated PO2 measurements over time were not made to reduce possible complications from light and dye overexposure, which may affect the microhemodynamic response of the tissue. Blood samples were withdrawn from level 3 exchange animals at the end of the experiment for subsequent analysis of viscosity and colloid osmotic pressure. The duration of the experiments was between 1 and 5 h depending on the degree of hemodilution.
|
The concentration of the high-molecular-weight Dextran 500 solution and the exchange protocol were determined from pilot studies where the animals were hemodiluted to the exchange level 3 with a 25% wt/vol solution, and their venular microvasculature was observed for signs of RBC aggregation, since rheological disturbances appear in vessels with low shear (15). Pilot studies found that animals could withstand an entire third exchange with 6% Dextran 500 solution without visible in vivo RBC aggregation. To avoid this critical concentration of Dextran 500, the level 3 exchange protocol began with 10% of the total blood volume exchange using 6% Dextran 70 solution followed by 25% of the total blood volume exchange with the 6% Dextran 500. This procedure ensured an increased blood viscosity compared with a level 3 exchange made solely with Dextran 70 and an absence of rheological complications. Pertinent physical properties of the exchange solutions used in this study are listed in Table 1.
|
Data Analysis
Results are presented as means ± SD unless otherwise noted. Data are presented relative to levels at baseline. All measurements were compared with their levels at baseline before the blood exchange except for the PO2 measurements in which oxygen levels were compared between groups of animals. For repeated measurements, time-related changes were assessed by analysis of variance. Comparison between different groups of animals was performed with the Student's t-test and the Mann-Whitney rank sum test. Multiple comparisons were made with the Student-Newman-Keuls test (SigmaStat Windows 95/v2.0; Jandel Scientific). Changes were considered statistically significant at P < 0.05.| |
RESULTS |
|---|
|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
Thirty-nine animals were entered into this study and assigned randomly to the following protocol exchange groups: control (n = 9); level 1 (n = 7); level 2 (n = 6); level 3 LV (n = 9); level 3 HV (n = 8). All animals tolerated the entire hemodilution protocol without visible signs of discomfort except two out of nine animals in the level 3 LV exchange group who experienced a decline of MAP below 50 mmHg and a complete shutdown in flow to the subcutaneous vascular bed under study.
Systemic and Blood Gas Parameters
Changes in the systemic and blood gas parameters for each experimental group are presented in Table 2. There were no statistically significant differences between experimental groups before the exchange protocol. Systemic Hct after level 1 and 2 exchange was 0.56 ± 0.04 and 0.40 ± 0.04 of baseline (P < 0.05 relative to baseline), respectively. Level 3 LV and HV exchange reduced the systemic Hct to 0.24 ± 0.02 and 0.25 ± 0.02 of baseline, respectively, which were statistically reduced from baseline (P < 0.05) but not statistically different from each other.
|
MAP was not changed from baseline in the level 1 exchange group, but upon further hemodilution with Dextran 70 MAP fell to 0.92 ± 0.05 and 0.62 ± 0.10 of baseline in level 2 and level 3 LV groups, respectively (P < 0.05). In the level 3 HV group, MAP fell to 0.90 ± 0.09 of baseline (P < 0.05), a statistically higher level than the MAP after level 3 LV exchange. HR was not affected by any of the hemodilution protocols.
Systemic arterial blood gas analysis showed a statistically significant rise in PO2 from baseline and a fall in PCO2 with increasing degree of hemodilution in all groups. There were no statistical differences in arterial blood gases between the level 3 exchange groups. Blood pH was not statistically changed from baseline among all the experimental groups.
Physical Properties of Blood
Comparison of rheological properties and colloid osmotic pressure of the blood after level 3 LV and HV exchange is presented in Table 3. Changes in blood and plasma viscosity were statistically different from baseline and between HV and LV groups (P < 0.05). Blood viscosity was reduced to 0.47 and 0.63 of baseline, and plasma viscosity was increased to 1.15 and 1.83 of baseline levels for level 3 exchange LV and HV groups, respectively. Colloid osmotic pressure was statistically unchanged during the progressive hemodilution.
|
Microhemodynamics
Vascular tone. The changes in the diameter of large feeding and small arcading arterioles (range, 23-95 µm) and small collecting venules and large venular vessels (range, 24-203 µm) were measured after each hemodilution step. Figure 2A shows that arteriolar diameter was unchanged after level 1 exchange. Upon further blood exchange to level 2, arterioles dilated to 1.15 ± 0.28 (n = 46, P < 0.001) of baseline. This trend reversed after level 3 LV exchange, resulting in a slight arteriolar vasoconstriction to 0.94 ± 0.15 (n = 49, P < 0.05) of baseline. After the level 3 HV exchange, arteriolar diameter remained dilated at 1.22 ± 0.28 (n = 47, P < 0.001) of baseline.
|
Venular changes due to the hemodilution protocol are shown in Fig. 2B as a function of the Hct. Venules responded to level 1 exchange by constricting to 0.95 ± 0.13 of baseline (n = 42, P < 0.05) and then returning to baseline levels after level 2 exchange (n = 36). When the exchange protocol was continued to the level 3 LV protocol, the venules constricted to 0.85 ± 0.20 (n = 37, P < 0.001) of baseline. Level 3 HV protocol did not change venular diameters from baseline levels (n = 38).
RBC velocity and blood flow. Figure 3 shows the change in RBC velocity in arterioles (A) and venules (B) as a function of the Hct. An increase in both arteriolar and venular RBC velocity was detected after level 1 exchange to 1.67 ± 1.03 (P < 0.05) and 1.55 ± 1.23 (P < 0.05) of baseline, respectively. After level 2 exchange, arteriolar RBC velocity remained increased from baseline (1.39 ± 0.93, P < 0.05), whereas venular RBC velocity returned to baseline levels. Level 3 LV exchange reduced both arteriolar and venular RBC velocity to 0.67 ± 0.58 and 0.70 ± 0.76 of baseline, respectively (P < 0.05). Level 3 HV exchange did not alter RBC velocity from baseline levels in either vessel type.
|
The relationships between arteriolar and venular blood flow after the hemodilution protocols and Hct are presented in Fig. 4. The results are given as means ± SE to show the trend of this parameter calculated from vessel diameter and RBC velocity. Both arteriolar and venular blood flow were statistically increased from baseline after level 1 and level 2 exchange. Upon further hemodilution with Dextran 70 these increased levels could not be sustained, and blood flow was statistically reduced from baseline levels in both arterioles and venules. However, level 3 HV exchange caused a return of the arteriolar and venular blood flow to baseline levels.
|
Wall Shear Rate
Wall shear rate (s1) is
calculated using the diameter and mean velocity of each vessel studied
after level 3 LV and HV exchanges. The
calculated values of wall shear rate are presented as means ± SE to
show the trend rather than the distribution of the parameter. Before
the exchange protocol, there were no statistically significant differences in wall shear rate
(s1) among the arterioles
(LV: 614.5 ± 35.0; HV: 574.5 ± 34.4) and venules (LV: 107.6 ± 18.0; HV: 146.7 ± 17.9) in each group. After the
level 3 LV exchange, arteriolar and
venular wall shear rate (s1) were reduced to 0.68 ± 0.09 (P < 0.001) and 0.65 ± 0.15 (P < 0.001) of baseline.
Level 3 HV exchange decreased
arteriolar wall shear rate to 0.82 ± 0.10 (P < 0.01) of baseline. In the
venules, wall shear rate was 1.36 ± 0.21 of baseline and not
statistically different from baseline. Statistical comparison between
the LV and HV groups after the exchange protocol found no statistical difference in arteriolar wall shear rate. However,
level 3 HV exchange did significantly
increase wall shear rate relative to the LV exchange protocol in
venules (P < 0.001).
Functional Capillary Density
Figure 5 shows the effect of hemodilution on the length of RBC perfused capillaries per unit area. FCD after level 1 exchange was 0.93 ± 0.05 of baseline and not statistically different from baseline. Level 2 exchange reduced FCD to 0.84 ± 0.04 of baseline (P < 0.05). FCD was further reduced after level 3 LV and HV to 0.38 ± 0.38 and 0.85 ± 0.12 of baseline, respectively (P < 0.05). A greater increase in capillary perfusion was obtained after level 3 exchange with the HV than with the LV protocol (P < 0.05). This preparation under normal conditions and during the course of the experimental procedures shows a decrease of FCD of 13% over a period of 6 h. Therefore, the loss in FCD found after level 2 and level 3 HV is near the expected change of this parameter.
|
Microvascular Oxygen Distribution
Oxygen distribution was measured in the animals that had blood flow to the tissue under study. The effect of the hemodilution with Dextran 70 (level 1, 2, and 3 LV) and with augmented plasma viscosity using high-molecular-weight Dextran 500 (level 3 HV) for arterioles, venules, and tissue is presented in the histograms of Fig. 6. The median and quartiles of each distribution are listed in Table 4. Level 1 and 2 exchange groups did not show statistical changes in arteriolar, venular, and tissue PO2 histograms from the control group. However, the shape of the three distributions narrowed relative to the control group after level 1 exchange, and the greater separation between the mean arteriolar and venular PO2 suggests an increased oxygen extraction. After level 2 exchange, there is a shift in the arteriolar PO2 toward higher values; however, the changes were not statistically different from the control group. Level 3 exchange with both LV and HV fluids caused a widening of the arteriolar PO2 histogram as evidenced by the 25 and 75% quartiles, resulting in a decreased median PO2. Both venular and tissue histograms for level 3 exchange were shifted completely to the left. The PO2 histograms obtained after level 3 LV and HV exchange were significantly different from control but were statistically unchanged from each other.
|
|
| |
DISCUSSION |
|---|
|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
Our principal finding is that normal levels of tissue perfusion in terms of arteriolar and venular blood flow and the FCD could be obtained during extreme hemodilution when plasma viscosity is increased by the addition of a high-molecular-weight Dextran 500 solution in the blood volume replacement fluid, a scenario that could not be achieved with a lower-viscosity solution. These results suggest that an increase in plasma viscosity, thus returning whole blood viscosity toward baseline conditions, elicits a regulatory mechanism that becomes inactivated during extreme hemodilution with a lower-viscosity fluid.
Oxygen delivery or systemic oxygen transport capacity during moderate intentional hemodilution is maintained because the decrease in the number of circulating RBCs reduces blood viscosity thereby enhancing cardiac output. Given the premise that higher blood viscosity should decrease blood flow and reduce tissue perfusion, an increase in blood viscosity, particularly with dextrans, which has been shown to cause aggregation by macromolecular bridging (6), could be potentially detrimental (14, 23). In our study, we found that increasing plasma viscosity was beneficial to tissue perfusion. This concept is supported by previous investigators who showed that organ blood flow and oxygen delivery were not impaired by plasma hyperviscosity. Comparison of tissue oxygenation achieved during moderate hemodilution with 3 and 6% Dextran 60, a 33% difference in plasma viscosity, showed similar elevations in PO2 levels on the surface of liver and skeletal muscle (2). Investigators found that a higher-viscosity replacement fluid was able to achieve increased organ blood flow not observed with a lower-viscosity fluid. Krieter et al. (22) progressively hemodiluted by small infusions of a similar high-molecular-weight dextran used in the present study and found that an increase in plasma viscosity to 3 mPa · s did not compromise perfusion or oxygenation of vital organs. They proposed that the concomitant decrease in Hct from the hemodilution was completely offset by the elevated plasma viscosity, resulting in normal tissue oxygenation and organ perfusion. Use of high-molecular-weight Dextran 500 solutions (molecular weight = 500,000) has also been shown to better lower mortality and limit the severity of pancreatitis (34) over the levels achieved with lower-weight dextran solutions. In further support of our finding, Waschke et al. (43) found that cerebral perfusion was not compromised when they altered the viscosity of plasma while keeping the oxygen content of blood constant. They achieved this by performing a complete blood exchange with a fluid consisting of cell-free hemoglobin and 2% polyvinylpyrrolidone (molecular weight = 400,000). Chen et al. (5) exchanged whole blood with a 20% wt/vol solution of Dextran 500 in blood, elevating plasma viscosity fourfold (4 mPa · s), and observed compensatory vasodilation reflected by a reduction of vascular hindrance in several vital organs, which served to maintain blood flow and nutrient transport despite the induced hyperviscosity. These investigations on the effects of induced hyperviscosity in different animals and tissues support the concept that induced plasma hyperviscosity is not detrimental to tissue perfusion and in some instances improves perfusion over lower-viscosity fluids, as shown in our study.
Our findings show that the reduction in FCD observed after level 3 LV exchange can be prevented by hemodilution using high-molecular-weight Dextran 500 to augment plasma viscosity. A mechanism directly related to an increase in plasma viscosity is the enhancement of shear stress via an increase in the viscous drag on the vessel wall. Release of vasodilators from the vascular endothelium such as NO (4) and prostacyclin (12) by endothelial cells has been shown to be shear stress induced. Increase in vessel wall shear stress by elevation of plasma viscosity using Dextran 500 has been shown to induce sustained NO-mediated dilation in the hamster cremaster muscle in vivo (9); increasing the plasma viscosity by 64.3% led to a 24.3% dilation in large feeding arterioles. In our study, increasing the plasma viscosity by 58.7% during the last exchange with Dextran 500 led to a 28.8% arteriolar vasodilation over the levels achieved with Dextran 70 as the sole hemodilutant. Systemic vasodilation, implying a reduction in total peripheral resistance during moderate hemodilution, has also been shown to be a result of endogenous NO release (10). Theoretical analysis applied to artificial blood replacement fluids suggests that lowered blood viscosity during blood substitution without proportionate increases in blood flow to maintain a constant vessel wall shear stress would lead to diminished mechanotransduction of the viscous drag by blood flow to the endothelium, resulting in vasoconstriction (18). Wall shear stress is also directly a function of fluid flow, and increases in blood flow have also been found to induce vasodilation (35). In the present investigation, the increase in arteriolar and venular blood flow achieved with the HV protocol beyond that of the LV protocol suggests that the difference in wall shear stress, increase in viscosity and blood flow, led to the observed higher levels of tissue perfusion during extreme hemodilution.
The relative viscosity of the two RBC suspensions obtained after HV and
LV protocols being different even though the concentration of RBCs is
similar suggests the presence of interactions among the blood
components. Dextrans are known to interact with RBCs as a function of
molecular size (15), and the dissimilarity between the relative
viscosities of the two RBC suspensions may be indicative of either
differences in the extent of RBC aggregation/adhesion and/or
RBC deformability in the two suspensions. RBC aggregation could cause
RBC sedimentation in horizontal venules, leading to venular occlusion,
which was not observed. Moreover, because FCD was not affected by the
HV protocol, it is likely that RBC aggregation is not the predominant
mechanism, as this would lead to capillary occlusion by RBC aggregates
and result in a decrease in FCD. Changes in RBC deformability could
affect RBC distribution at vessel bifurcations; however, in the present
study, capillaries without RBC flux are usually characterized by the
presence of stationary RBCs. Therefore, RBC deformability does not
appear to be a major factor affecting our FCD measurements. The average
shear rate of 160 s1 used
in these viscosity measurements is one at which whole blood is somewhat
non-Newtonian. To test blood in a Newtonian regime, it would be more
desirable to use a shear rate >500
s1; however, this would
require a larger blood sample than is available from these small
animals. The average shear rate selected is a compromise between the
need to characterize blood viscosity at a shear rate that is high
enough so that complex rheology is not a principal factor and the small
blood samples that can be obtained from these animals. Wall shear
stress was estimated following Eq. 1
and was found to be significantly higher after the HV than with the LV
protocol. The significantly higher wall shear stress in arterioles
stemmed from the increased blood plasma viscosity after the HV protocol
since there were not differences in wall shear rate. The already
increased venular wall shear rate after the HV protocol compounded with
the increased blood viscosity to substantially increase wall shear
stress in the venules relative to that in the LV protocol.
Changes in FCD reflect mechanisms that modulate the entrance of RBCs into the capillaries and occur both in normal and diseased states. Perfusion pressure has been shown to directly affect FCD (25). Arteriolar vasoconstriction is a mechanism that could lead to capillary shutdown (40). The combined effects of arteriolar vasodilation and the relatively high level of perfusion pressure observed after the HV protocol are mechanisms leading to sustained capillary perfusion during extreme hemodilution.
Our systemic and microvascular observations after level 1 exchange are supported by previous studies of moderate or limited hemodilution. Animals in this study compensated for the progressive reduction in oxygen-carrying capacity with hyperventilation. Increasing arterial PO2 and pH along with the concomitant decrease in arterial PCO2 as a function of progressive hemodilution agrees with previous findings in hamsters (24) and other species (28). In our study, both HR and MAP were unchanged, a finding that concurs with previous investigations in this animal model (29). The decline in MAP after level 3 LV and HV may in part be due to the critically low oxygen carrying capacity of the blood at this exchange level. In the same model and tissue, Mirhashemi et al. (29) found that a 50% exchange with Dextran 70 did not affect arteriolar diameter, which is similar to our finding after level 1 exchange. In various anesthetized animal models and different tissue beds, large feeding arterioles similar to those in our investigation resulted in arteriolar vasoconstriction after moderate hemodilution (17, 24, 26, 38). This discrepancy may be partially due to their use of anesthetics, which has been shown to affect vascular tone in our tissue (7) and other regulatory mechanisms in different tissues. In our study, the increase in arteriolar and venular blood velocity observed after level 1 and 2 exchange is primarily a consequence of reduced blood viscosity due to blood replacement with a less viscous fluid. This is similar to the previously reported observations by investigators from this laboratory (29) and in various tissues by others (17, 24, 26, 38). Our findings show that arteriolar blood flow was still increased from baseline after level 2 exchange as these vessels remained vasodilated and exhibited increased RBC velocity above baseline levels. This increase in volumetric flow was not apparent in all venular flow measurements, and on the average blood flow was only slightly increased from baseline. This discrepancy is most likely a consequence of redistribution of blood in this subcutaneous vascular network system, which characteristically has more venules than arterioles.
A significant finding in the present study is that local tissue oxygenation levels are maintained even after reduction of the systemic Hct by 60% corresponding to an absolute Hct of 19.5%. The shift of the intravascular PO2 frequency distributions to higher and lower PO2 in arterioles and venules, respectively, is indicative of an increased oxygen extraction. The slight rise in arteriolar PO2 is a result of the elevated systemic arterial PO2 brought on by hyperventilation and the increase in blood flow, decreasing circulatory transit time resulting in the delivery of blood with higher oxygen content. Oxygen tension measurements made by others using surface multiwire platinum electrodes in the same tissue and model also did not detect any difference in oxygen levels from baseline after isovolemic hemodilution with Dextran 60 to a Hct of 30% (13, 32). However, the multiwire electrode technique provides only a lumped indicator of surface oxygen levels and does not enable one to resolve between the actual oxygen distribution in the vasculature and the interstitium. Oxygen tension histograms in the multiwire electrode study showed a more homogenous tissue PO2 level after hemodilution with low-molecular-weight dextran to a systemic Hct of 30% (13, 32). Our results after level 1 exchange show a right shift and narrowing of the extravascular and arteriolar PO2 histograms, which when combined with the left shift in the venous PO2 distribution would not result in the more homogeneous microvascular PO2 distribution observed by others (13). Multiwire electrode measurements can only be performed after lifting the cover glass of the skinfold window and thereby exposing the tissue to atmospheric oxygen. Moreover, superfusion of the exposed tissue with saline could be another source of oxygen for the tissue and could mask the oxygen delivered by blood perfusion. Repositioning of the surface electrode would also exacerbate the oxygen diffusional fields between the tissue, superfusate, and electrode surface. These factors would lead to higher PO2 measurements; paradoxically, only 4% of the measurements reported after moderate exchange with Dextran 70 were >30 mmHg after hemodilution (32). Our findings do concur on the concept that moderate hemodilution does not cause regions of hypoxia (PO2 levels <5 mmHg).
Our analysis of oxygen tension did not include the two animals that had no tissue perfusion after the level 3 LV protocol, since the phosphorescence probe needed for PO2 measurements could not reach the tissue under study. It is likely that the intravascular and perivascular PO2 levels in a nonperfused tissue are close to 0 mmHg. Correction of the PO2 histograms for level 3 LV to include these two animals that had no blood flow in the skinfold chamber would result in a slight left shift toward lower oxygen tensions. However, this minor readjustment would not alter our finding that local PO2 levels fall after 75% hemodilution regardless of the viscosity of the dilutant and the state of tissue perfusion and is a consequence of a reduction in oxygen-carrying capacity beyond the limit of compensatory mechanisms. Because of the large volume of blood exchanged in each hemodilution step, we are not able to determine if tissue oxygenation above baseline levels can be achieved in this tissue during moderate hemodilution as has been suggested by theoretical studies (16, 31). However, others have suggested that the oxygen sensitivity of the vasculature may evoke autoregulatory mechanisms (20), thereby restricting oxygen levels to within a narrow range and thus making higher-than-baseline tissue oxygen levels unattainable.
FCD is an indicator of tissue perfusion and the homogeneity of tissue oxygenation (40). In the current study, we found that a higher FCD could be achieved with the HV than with the LV protocol. Our method for evaluating FCD tends to underestimate the number of capillaries perfused during extreme hemodilution, since, as the hemodilution progresses, the number of RBCs transiting decreases and may lead to a low-Hct vessel being labeled as a nonfunctional capillary. However, because the same method is used in both groups and the systemic Hct levels are the same, the finding that the HV fluid can better maintain the FCD during extreme hemodilution than the LV fluid should not be affected by this limitation in the methodology.
In a study on severe hemorrhagic shock by Kerger et al. (21), maintenance of FCD was the sole critical microvascular parameter that separated surviving from nonsurviving animals. Systemic Hct was reduced to 22.5% due to autotransfusion. Thus our results suggest that reperfusion with HV plasma expanders may be beneficial in volume restitution, since the higher plasma viscosity may aid in restoring or maintaining FCD.
The present study demonstrates that replacing blood with a HV fluid at extreme hemodilution (systemic Hct of 12%) and thus returning blood viscosity toward normal results in levels of tissue perfusion that would not be achieved with lower-viscosity fluid. It is proposed that increasing plasma viscosity led to an increase in wall shear stress and along with the maintained blood flow triggered vasodilation in the microvascular bed. Direct PO2 measurements using palladium-porphyrin phosphorescence quenching microscopy document for the first time that local tissue oxygenation in subcutaneous tissue is maintained after a 60% isovolemic hemodilution.
| |
ACKNOWLEDGEMENTS |
|---|
This research was supported by National Heart, Lung, and Blood Institute Grant HL-48018. H. Sakai is fellow of the Japan Society for the Promotion of Science.
| |
FOOTNOTES |
|---|
Present addresses: B. Friesenecker, Dept. of Anesthesia and Intensive Care Medicine, Leopold-Franzens-Univ. of Innsbruck, Anichstrasse 35, A-6020 Innsbruck, Austria; H. Sakai, Dept. of Polymer Chemistry, Waseda Univ., 3-4 Ohkubo, Skinjuku-ku, Tokyo 169, Japan.
The costs of publication of this article were defrayed in part by the payment of page charges. The article must therefore be hereby marked "advertisement" in accordance with 18 U.S.C. §1734 solely to indicate this fact.
Address for reprint requests: A. G. Tsai, Dept. of Bioengineering, 0412, Univ. of California, San Diego, 9500 Gilman Dr., La Jolla, CA 92093-0412.
Received 5 January 1998; accepted in final form 5 August 1998.
| |
REFERENCES |
|---|
|
Top
Abstract
Introduction
Materials & Methods
Results
Discussion
References
|
|---|
1.
Barbee, J. H.,
and
G. R. Cokelet.
The Fahraeus effect.
Microvasc. Res.
3:
6-16,
1971[Medline].
2.
Bruckner, U. B.,
F. Kefalianakis,
H. Krieter,
and
K. Messmer.
Organ blood supply and tissue oxygenation after limited normovolemic hemodilution with 3% versus 6% Dextran 60.
Infusionsther. Transfusionsmed.
20:
130-139,
1993[Medline].
3.
Buerk, D. G.,
A. G. Tsai,
M. Intaglietta,
and
P. C. Johnson.
In vivo tissue PO2 measurements in hamster skinfold by recessed PO2 microelectrodes and phosphorescence quenching are in agreement.
Microcirculation
5:
219-225,
1998[Medline].
4.
Buga, G. M.,
M. E. Gold,
J. M. Fukuto,
and
L. J. Ignarro.
Shear stress-induced release of nitric oxide from endothelial cells grown on beads.
Hypertension
17:
187-193,
1991
5.
Chen, R. Y. Z.,
R. D. Carlin,
S. Simchon,
K.-M. Jan,
and
S. Chien.
Effects of dextran-induced hyperviscosity on regional blood flow and hemodynamics in dogs.
Am. J. Physiol.
256 (Heart Circ. Physiol. 25):
H898-H905,
1989
6.
Chien, S.,
and
K.-M. Jan.
Red cell aggregation by macromolecules: roles of surface adsorption and electrostatic repulsion.
J. Supramol. Struct.
12:
385-409,
1973.
7.
Colantuoni, A.,
S. Bertuglia,
and
M. Intaglietta.
Effects of anesthesia on the spontaneous activity of the microvasculature.
Int. J. Microcirc. Clin. Exp.
3:
13-28,
1984[Medline].
8.
Colantuoni, A.,
S. Bertuglia,
and
M. Intaglietta.
Quantitation of rhythmic diameter changes in arterial microcirculation.
Am. J. Physiol.
246 (Heart Circ. Physiol. 15):
H508-H517,
1984
9.
De Wit, C.,
C. Schaefer,
P. von Bismarck,
S.-S. Bolz,
and
U. Pohl.
Elevation of plasma viscosity induces sustained NO-mediated dilation in the hamster cremaster microcirculation in vivo.
Pflügers Arch.
434:
354-361,
1997[Medline].
10.
Doss, D. N.,
F. G. Estafanous,
C. M. Ferrario,
J. M. Brum,
and
P. A. Murray.
Mechanism of systemic vasodilation during normovolemic hemodilution.
Anesth. Analg.
81:
30-34,
1995[Abstract].
11.
Endrich, B.,
K. Asaishi,
A. Gotz,
and
K. Messmer.
Technical report
a new chamber technique for microvascular studies in unanesthetized hamsters.
Res. Exp. Med. (Berl.)
177:
135-143,
1980[Medline].
12.
Frangos, J. A.,
S. G. Eskin,
L. V. McIntire,
and
C. L. Ives.
Flow effects on prostacyclin production by cultured human endothelial cells.
Science
227:
1477-1479,
1985
13.
Funk, W.,
and
V. Baldinger.
Microcirculatory perfusion during volume therapy. A comparative study using crystalloid or colloid in awake animals.
Anesthesiology
82:
975-982,
1995[Medline].
14.
Gelin, L. E.
Studies in anemia of injury.
Acta Chir. Scand. Suppl.
210:
1-130,
1956.
15.
Gustafsson, L.,
L. Appelgren,
and
H. E. Myrvold.
Effects of increased plasma viscosity and red blood cell aggregation on blood viscosity in vivo.
Am. J. Physiol.
241 (Heart Circ. Physiol. 10):
H513-H518,
1981.
16.
Hint, H.
The pharmacology of dextran and physiological background of the clinical use of Rheomacrodex.
Acta Anaesthesiol. Belg.
19:
119-138,
1968[Medline].
17.
Hudak, M. L.,
J. M. Douglas Jones,
A. S. Popel,
R. C. Koehler,
R. J. Traystman,
and
S. L. Zeger.
Hemodilution causes size-dependent constriction of pial arterioles in the cat.
Am. J. Physiol.
257 (Heart Circ. Physiol. 26):
H912-H917,
1989
18.
Intaglietta, M.
Whitaker Lecture 1996: Microcirculation, biomedical engineering, and artificial blood.
Ann. Biomed. Eng.
25:
593-603,
1997[Medline].
19.
Intaglietta, M.,
N. R. Silverman,
and
W. R. Tompkins.
Capillary flow velocity measurements in vivo and in situ by television methods.
Microvasc. Res.
10:
165-179,
1975[Medline].
20.
Jackson, W. F.,
and
B. R. Duling.
The oxygen sensitivity of hamster cheek pouch arterioles: in vitro and in situ studies.
Circ. Res.
53:
515-525,
1983
21.
Kerger, H.,
D. J. Saltzman,
M. D. Menger,
K. Messmer,
and
M. Intaglietta.
Systemic and subcutaneous microvascular PO2 dissociation during 4-h hemorrhagic shock in conscious hamsters.
Am. J. Physiol.
270 (Heart Circ. Physiol. 39):
H827-H836,
1996
22.
Krieter, H.,
U. B. Bruckner,
F. Kefalianakis,
and
K. Messmer.
Does colloid-induced plasma hyperviscosity in haemodilution jeopardize perfusion and oxygenation of vital organs?
Acta Anaesthesiol. Scand.
39:
236-244,
1995[Medline].
23.
Kroemer, H.,
A. Haass,
K. Muller,
H. Jager,
E. M. Wagner,
P. Heimburg,
and
U. Klotz.
Haemodilution therapy in ischaemic stroke: plasma concentrations and plasma viscosity during long-term infusion of dextran 40 or hydroxyethyl starch 200/0.5.
Eur. J. Clin. Pharmacol.
31:
705-710,
1987[Medline].
24.
Kuo, L.,
and
R. N. Pittman.
Effect of hemodilution on oxygen transport in arteriolar networks of hamster striated muscle.
Am. J. Physiol.
254 (Heart Circ. Physiol. 23):
H331-H339,
1988
25.
Lindbom, L.,
and
K.-E. Arfors.
Mechanism and site of control for variation in the number of perfused capillaries in skeletal muscle.
Int. J. Microcirc. Clin. Exp.
4:
121-127,
1985[Medline].
26.
Lipowsky, H. H.,
and
J. C. Firrell.
Microvascular hemodynamics during systemic hemodilution and hemoconcentration.
Am. J. Physiol.
250 (Heart Circ. Physiol. 19):
H908-H922,
1986.
27.
Lipowsky, H. H.,
and
B. W. Zweifach.
Application of the "two-slit" photometric technique to the measurement of microvascular volumetric flow rates.
Microvasc. Res.
15:
93-101,
1978[Medline].
28.
Messmer, K.,
L. Sunder-Plassmann,
W. P. Klovekorn,
and
K. Holper.
Circulatory significance of hemodilution: rheological changes and limitations.
Adv. Microcirc.
4:
1-77,
1972.
29.
Mirhashemi, S.,
G. A. Breit,
R. H. C. Chavez,
and
M. Intaglietta.
Effects of hemodilution on skin microcirculation.
Am. J. Physiol.
254 (Heart Circ. Physiol. 23):
H411-H416,
1988
30.
Mirhashemi, S.,
K. Messmer,
K.-E. Arfors,
and
M. Intaglietta.
Microcirculatory effects of normovolemic hemodilution in skeletal muscle.
Int. J. Microcirc. Clin. Exp.
6:
359-369,
1987[Medline].
31.
Mirhashemi, S.,
K. Messmer,
and
M. Intaglietta.
Tissue perfusion during normovolemic hemodilution investigated by a hydraulic model of the cardiovascular system.
Int. J. Microcirc. Clin. Exp.
6:
123-136,
1987[Medline].
32.
Nolte, D.,
P. Steinhauser,
S. Pickelmann,
S. Berger,
R. Hartl,
and
K. Messmer.
Effects of diaspirin-cross-linked hemoglobin (DCLHb) on local tissue oxygen tensions in striated skin muscle: an efficacy study in the hamster.
J. Lab. Clin. Med.
130:
328-338,
1997[Medline].
33.
Reinhart, W. H.,
S. J. Danoff,
S. Usami,
and
S. Chien.
Rheologic measurements on small samples with a new capillary viscometer.
Eur. J. Clin. Pharmacol.
104:
921-931,
1984.
34.
Schmidt, J.,
C. Fernandez Castillo,
D. W. Rattner,
K. B. Lewandrowski,
K. Messmer,
and
A. L. Warshaw.
Hyperoncotic ultrahigh molecular weight dextran solutions reduce trypsinogen activation, prevent acinar necrosis, and lower mortality in rodent pancreatitis.
Am. J. Surg.
165:
40-45,
1993[Medline].
35.
Smiesko, V.,
and
P. C. Johnson.
The arterial lumen is controlled by flow-related shear stress.
News Physiol. Sci.
8:
34-38,
1993.
36.
Sunder-Plassmann, L.,
M. Kessler,
F. Jesch,
R. Dieterle,
and
K. Messmer.
Acute normovolemic hemodilution: changes in tissue oxygen supply and hemoglobin-oxygen affinity.
In: Intentional Haemodilution, edited by K. Messmer,
and H. Schmid-Schoenbein. Basel: Karger, 1975, p. 44-53.
37.
Tigno, X. T.,
and
H. Henrich.
Flow characteristics of the microcirculation following intentional hemodilution.
Acta Med. Port.
22:
5-12,
1986.
38.
Tigno, X. T.,
and
H. Henrich.
Flow characteristics of the microcirculation following intentional hemodilution. II. Hemodynamic response of the pre-capillary arterioles.
Acta Med. Port.
22:
53-58,
1986.
39.
Torres Filho, I. P.,
and
M. Intaglietta.
Microvessel PO2 measurements by phosphorescence decay method.
Am. J. Physiol.
265 (Heart Circ. Physiol. 34):
H1434-H1438,
1993
40.
Tsai, A. G.,
B. Friesenecker,
and
M. Intaglietta.
Capillary flow impairment and functional capillary density.
Int. J. Microcirc. Clin. Exp.
15:
238-243,
1995[Medline].
41.
Tsai, A. G.,
B. Friesenecker,
M. C. Mazzoni,
H. Kerger,
D. G. Buerk,
P. C. Johnson,
and
M. Intaglietta.
Microvascular and tissue oxygen gradients in the rat mesentery.
Proc. Natl. Acad. Sci. USA
95:
6590-6596,
1998
42.
Vanderkooi, J. M.,
G. Maniara,
T. J. Green,
and
D. F. Wilson.
An optical method for measurement of dioxygen concentration based upon quenching of phosphorescence.
J. Biol. Chem.
252:
5476-5482,
1987.
43.
Waschke, K. F.,
H. Krieter,
G. Hagen,
D. M. Albrecht,
K. Van Ackern,
and
W. Kuschinsky.
Lack of dependence of cerebral blood flow on blood viscosity after blood exchange with a Newtonian oxygen carrier.
J. Cereb. Blood Flow Metab.
14:
871-876,
1994[Medline].
44.
Webb, A. R.,
S. A. Barclay,
and
E. D. Bennett.
In vitro colloid osmotic pressure of commonly used plasma expanders and substitutes: a study of the diffusibility of colloid molecules.
Intensive Care Med.
15:
116-120,
1989[Medline].
45.
Wilson, D. F.
Measuring oxygen using dependent quenching of phosphorescence: a status report.
Adv. Exp. Med. Biol.
333:
225-232,
1993[Medline].
This article has been cited by other articles:
|
|
 |
|
  P. Cabrales, G. Sun, Y. Zhou, D. R. Harris, A. G. Tsai, M. Intaglietta, and A. F. Palmer Effects of the molecular mass of tense-state polymerized bovine hemoglobin on blood pressure and vasoconstriction J Appl Physiol, November 1, 2009; 107(5): 1548 - 1558. [Abstract] [Full Text] [PDF]
|
|
|
|
 |
|
 P. Cabrales, A. G. Tsai, and M. Intaglietta Isovolemic exchange transfusion with increasing concentrations of low oxygen affinity hemoglobin solution limits oxygen delivery due to vasoconstriction Am J Physiol Heart Circ Physiol, November 1, 2008; 295(5): H2212 - H2218. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales Effects of erythrocyte flexibility on microvascular perfusion and oxygenation during acute anemia Am J Physiol Heart Circ Physiol, August 1, 2007; 293(2): H1206 - H1215. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, B. Y. S. Vazquez, A. G. Tsai, and M. Intaglietta Microvascular and capillary perfusion following glycocalyx degradation J Appl Physiol, June 1, 2007; 102(6): 2251 - 2259. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales and A. G. Tsai Plasma viscosity regulates systemic and microvascular perfusion during acute extreme anemic conditions Am J Physiol Heart Circ Physiol, November 1, 2006; 291(5): H2445 - H2452. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, J. Martini, M. Intaglietta, and A. G. Tsai Blood viscosity maintains microvascular conditions during normovolemic anemia independent of blood oxygen-carrying capacity Am J Physiol Heart Circ Physiol, August 1, 2006; 291(2): H581 - H590. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
J. Martini, A. G. Tsai, P. Cabrales, P. C. Johnson, and M. Intaglietta Increased cardiac output and microvascular blood flow during mild hemoconcentration in hamster window model Am J Physiol Heart Circ Physiol, July 1, 2006; 291(1): H310 - H317. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, P. C. Johnson, and M. Intaglietta Oxygen release from arterioles with normal flow and no-flow conditions J Appl Physiol, May 1, 2006; 100(5): 1569 - 1576. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
O. Yalcin, F. Aydin, P. Ulker, M. Uyuklu, F. Gungor, J. K. Armstrong, H. J. Meiselman, and O. K. Baskurt Effects of red blood cell aggregation on myocardial hematocrit gradient using two approaches to increase aggregation Am J Physiol Heart Circ Physiol, February 1, 2006; 290(2): H765 - H771. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, R. M. Winslow, and M. Intaglietta Extreme hemodilution with PEG-hemoglobin vs. PEG-albumin Am J Physiol Heart Circ Physiol, December 1, 2005; 289(6): H2392 - H2400. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
J. A. Plock, C. Contaldo, H. Sakai, E. Tsuchida, M. Leunig, A. Banic, M. D. Menger, and D. Erni Is hemoglobin in hemoglobin vesicles infused for isovolemic hemodilution necessary to improve oxygenation in critically ischemic hamster skin? Am J Physiol Heart Circ Physiol, December 1, 2005; 289(6): H2624 - H2631. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
J. Martini, B. Carpentier, A. C. Negrete, J. A. Frangos, and M. Intaglietta Paradoxical hypotension following increased hematocrit and blood viscosity Am J Physiol Heart Circ Physiol, November 1, 2005; 289(5): H2136 - H2143. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
F. J. Pearce, C. Waasdorp, H. Hufnagel, D. Burris, J. DeFeo, P. Soballe, and W. R. Drucker Subcutaneous PO2 as an index of the physiological limits for hemodilution in the rat J Appl Physiol, September 1, 2005; 99(3): 814 - 821. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, R. M. Winslow, and M. Intaglietta Effects of extreme hemodilution with hemoglobin-based O2 carriers on microvascular pressure Am J Physiol Heart Circ Physiol, May 1, 2005; 288(5): H2146 - H2153. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. C. Johnson, K. Vandegriff, A. G. Tsai, and M. Intaglietta Effect of acute hypoxia on microcirculatory and tissue oxygen levels in rat cremaster muscle J Appl Physiol, April 1, 2005; 98(4): 1177 - 1184. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, and M. Intaglietta Alginate plasma expander maintains perfusion and plasma viscosity during extreme hemodilution Am J Physiol Heart Circ Physiol, April 1, 2005; 288(4): H1708 - H1716. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
A. G. Tsai, C. Acero, P. R. Nance, P. Cabrales, J. A. Frangos, D. G. Buerk, and M. Intaglietta Elevated plasma viscosity in extreme hemodilution increases perivascular nitric oxide concentration and microvascular perfusion Am J Physiol Heart Circ Physiol, April 1, 2005; 288(4): H1730 - H1739. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, H. Sakai, A. G. Tsai, S. Takeoka, E. Tsuchida, and M. Intaglietta Oxygen transport by low and normal oxygen affinity hemoglobin vesicles in extreme hemodilution Am J Physiol Heart Circ Physiol, April 1, 2005; 288(4): H1885 - H1892. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, and M. Intaglietta Increased tissue PO2 and decreased O2 delivery and consumption after 80% exchange transfusion with polymerized hemoglobin Am J Physiol Heart Circ Physiol, December 1, 2004; 287(6): H2825 - H2833. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, N. D. Kanika, B. N. Manjula, A. G. Tsai, S. A. Acharya, and M. Intaglietta Microvascular PO2 during extreme hemodilution with hemoglobin site specifically PEGylated at Cys-93({beta}) in hamster window chamber Am J Physiol Heart Circ Physiol, October 1, 2004; 287(4): H1609 - H1617. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, J. A. Frangos, J. C. Briceno, and M. Intaglietta Oxygen delivery and consumption in the microcirculation after extreme hemodilution with perfluorocarbons Am J Physiol Heart Circ Physiol, July 1, 2004; 287(1): H320 - H330. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
P. Cabrales, A. G. Tsai, and M. Intaglietta Microvascular pressure and functional capillary density in extreme hemodilution with low- and high-viscosity dextran and a low-viscosity Hb-based O2 carrier Am J Physiol Heart Circ Physiol, July 1, 2004; 287(1): H363 - H373. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
K. Tsukada, E. Sekizuka, C. Oshio, K. Tsujioka, and H. Minamitani Red blood cell velocity and oxygen tension measurement in cerebral microvessels by double-wavelength photoexcitation J Appl Physiol, April 1, 2004; 96(4): 1561 - 1568. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
E. Saldivar, P. Cabrales, A. G. Tsai, and M. Intaglietta Microcirculatory changes during chronic adaptation to hypoxia Am J Physiol Heart Circ Physiol, November 1, 2003; 285(5): H2064 - H2071. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
A. G. Tsai, P. Cabrales, R. M. Winslow, and M. Intaglietta Microvascular oxygen distribution in awake hamster window chamber model during hyperoxia Am J Physiol Heart Circ Physiol, October 1, 2003; 285(4): H1537 - H1545. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
C. Contaldo, S. Schramm, R. Wettstein, H. Sakai, S. Takeoka, E. Tsuchida, M. Leunig, A. Banic, and D. Erni Improved oxygenation in ischemic hamster flap tissue is correlated with increasing hemodilution with Hb vesicles and their O2 affinity Am J Physiol Heart Circ Physiol, August 7, 2003; 285(3): H1140 - H1147. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
D. Erni, R. Wettstein, S. Schramm, C. Contaldo, H. Sakai, S. Takeoka, E. Tsuchida, M. Leunig, and A. Banic Normovolemic hemodilution with Hb vesicle solution attenuates hypoxia in ischemic hamster flap tissue Am J Physiol Heart Circ Physiol, May 1, 2003; 284(5): H1702 - H1709. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
B. Matheson, H. E. Kwansa, E. Bucci, A. Rebel, and R. C. Koehler Vascular response to infusions of a nonextravasating hemoglobin polymer J Appl Physiol, October 1, 2002; 93(4): 1479 - 1486. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
H. Sakai, S. Takeoka, R. Wettstein, A. G. Tsai, M. Intaglietta, and E. Tsuchida Systemic and microvascular responses to hemorrhagic shock and resuscitation with Hb vesicles Am J Physiol Heart Circ Physiol, September 1, 2002; 283(3): H1191 - H1199. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
M. A. Haidekker, A. G. Tsai, T. Brady, H. Y. Stevens, J. A. Frangos, E. Theodorakis, and M. Intaglietta A novel approach to blood plasma viscosity measurement using fluorescent molecular rotors Am J Physiol Heart Circ Physiol, May 1, 2002; 282(5): H1609 - H1614. [Abstract] [Full Text] [PDF]
|
|
|
|
 |
|
 R. Y. Inoue, J. A. R. Gontijo, and K. G. Franchini Hemodilution mediates hemodynamic changes during acute expansion in unanesthetized rats Am J Physiol Regulatory Integrative Comp Physiol, December 1, 2000; 279(6): R2243 - R2251. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
A. Caron, P. Menu, B. Faivre-Fiorina, P. Labrude, A. Alayash, and C. Vigneron Systemic and renal hemodynamics after moderate hemodilution with HbOCs in anesthetized rabbits Am J Physiol Heart Circ Physiol, June 1, 2000; 278(6): H1974 - H1983. [Abstract] [Full Text] [PDF]
|
|
|
|
|
|
A. Rebel, J. A. Ulatowski, K. Joung, E. Bucci, R. J. Traystman, and R. C. Koehler Regional cerebral blood flow in cats with cross-linked hemoglobin transfusion during focal cerebral ischemia Am J Physiol Heart Circ Physiol, March 1, 2002; 282(3): H832 - H841. [Abstract] [Full Text] [PDF]
|
|
| ||||||||||||||||||||||||||||||||||||||||||||||||||||||||||||||||
| HOME | HELP | FEEDBACK | SUBSCRIPTIONS | ARCHIVE | SEARCH | TABLE OF CONTENTS |
| Visit Other APS Journals Online |
, Dextran 70 exchange; 
, Dextran 500 exchange. Broken
line represents baseline level.
* P < 0.05. Baseline diameters
(µm) in each animal group were as follows: level
1 [arterioles (A): 62.4 ± 18.2, n = 44, venules (V): 68.8 ± 37.5, n = 42]; level
2 (A: 57.9 ± 17.8, n = 46, V: 70.9 ± 39.2, n = 36); level
3 LV (A: 58.6 ± 12.3, n = 49, V: 78.5 ± 23.9, n = 37); level
3 HV (A: 57.4 ± 15.3, n = 47, V: 68.9 ± 32.7 n = 38).
n, No. of vessels studied.
