Abnormalities in tumor microvasculature structure and function contribute to the pathophysiologic microenvironment of tumors, which is characterized by inadequate oxygen delivery for the metabolic demands of the tissue.1, 2, 3, 4, 5, 6 It is well established that hypoxia can influence tumor biology and physiology, gene expression, metastatic potential, treatment efficacy, and patient survival. In addition to the detrimental effect on radiosensitivity,7 hypoxia can have a direct and indirect negative impact on chemotherapy.8 Hypoxia not only affects cancer therapy, it also affects tumor development, and strong evidence suggests that hypoxia can drive malignant progression through gene expression.9, 10 Given that most human solid tumors have been shown to have hypoxic regions, there is a strong motivation to better understand the causes and consequences of tumor hypoxia.
Classically, tumor hypoxia with microvascular origins has been described as being “chronic” or “acute.” Chronic hypoxia is attributed to sparsely vascularized regions with long oxygen diffusion distances between vessels, and acute hypoxia is attributed to transient cessation of blood flow in microvessels.7 Recent research has added depth and complexity to the notions of chronic and acute hypoxia with the identification of other contributing factors. Two such factors are temporal fluctuations in tissue and microvascular longitudinal gradients in oxygen transport. Prior studies have shown the existence of temporal and spatial heterogeneities in oxygenation and hypoxia in tumors using oxygen microelectrodes11 and phosphorescence lifetime imaging.12 Other research has shown the existence of low frequency ( [cpm]) fluctuations in tumor that can lead to intermittent hypoxia without cessation of blood flow.13 Recent research suggests that intermittent hypoxia may have more clinical relevance in terms of its impact on treatment and tumor progression than classically described chronic and acute hypoxia14, 15, 16 and thus warrants further study.
Another notable characteristic of tumor microvasculature is the existence of arteriovenous (AV) anastomoses.17 AV anastomoses are also found in some normal tissues with highly variable blood flow, such as skin.18 In tumors, however, a large portion of the blood flow, 30% in malignant tumors by some estimates,19 can be via AV shunts.20 Some tumors tend to develop AV anastomoses with other organs, such as hepatocellular carcinomas, which commonly develop shunts to the lungs.21 An important consequence of this development is that chemotherapeutic agents can bypass the tumor,22 rendering them ineffective.
Imaging measurements of microvessel oxygen transport and function can potentially provide insight into the connections between microregional hypoxia and gene expression and may also elucidate oxygen transport effects of certain classes of drugs, such as vascular targeting agents. Previously, we described a microscope-based spectral imaging system to measure hemoglobin saturation (HbSat) in the microvasculature of tumors grown in mouse dorsal skin-fold window chambers.23 In this paper, we demonstrate the ability of the system to measure fluctuations in tumor microvascular oxygen transport, identify connections between microvessels of very different HbSats, and document an effect on oxygen transport presumably due to tumor AV anastomoses at the microvascular level in a mouse mammary adenocarcinoma.
Materials and Methods
Zeiss Axioskop II (Duke University) and AxioImager (University of Florida) microscopes (Carl Zeiss, Inc., Thornwood, New York) served as the imaging platform. A tungsten halogen lamp was used for transillumination of the window chamber. Images were acquired at and dynamic range with a DVC 1412 charge-coupled device (CCD) camera (DVC Company, Austin, Texas) that was thermoelectrically cooled to . The objectives used were all air immersion with long working distances (WD) (Carl Zeiss, Inc.): [numerical aperture , ] and ( , ) Fluars, and a ( , ) Plan-NeoFluar. Bandlimited optical filtering for hyperspectral imaging was accomplished with a C-mounted liquid crystal tunable filter (CRI, Inc., Woburn, Massachusetts) with a transmission range and nominal bandwidth placed in front of the camera. Images were saved as tagged image files. The field-of-view captured by the CCD camera was different for the two microscope systems due to slight demagnification ( , Duke microscope) or magnification ( , University of Florida microscope) in relay lenses used to create an infinity space for the liquid crystal tunable filter. Thus, the fields-of-view imaged by the CCD camera were the following: (Duke) or (Florida), (Duke) or (Florida), (Duke) or (Florida). Scale bars in the figures give an indication of the field-of-view and object dimensions in the images.
Custom designed software created with LABVIEW (National Instruments Corp., Austin, Texas) was used to control the tuning of the filter and operation of the camera. The software allows automated image acquisition with user-specified camera exposure time and gain for each filter wavelength. For each HbSat time point, 16 images were acquired from in intervals. The transmission of the liquid crystal tunable filter is lower at shorter wavelengths and higher at longer wavelengths; therefore, the image acquisition time was adjusted a priori for each wavelength such that the full dynamic range of the camera was used. The minimum exposure time used was to average out fluctuations in the signal due to random red blood cell motion.23 A typical data set was acquired in about , which included image acquisition, filter tuning, image transfer, and saving of the images to the computer hard drive.
In vivo Surgery and Imaging
All in vivo experiments were conducted under protocols approved by the Duke University Institutional Animal Care and Use Committee and the University of Florida Institutional Animal Care and Use Committee. A titanium window chamber was surgically implanted under anesthesia [ketamine intraperitoneal (IP) and xylazine IP] on the back of athymic (nu/nu) nude mice. The tumors used in these experiments were the 4T1 metastatic mouse mammary adenocarcinoma and the 4TO7 nonmetastatic subclone of the 4T1 tumor. A window chamber tumor was established during chamber implantation by injecting of a single cell suspension of cells into the dorsal skin flap prior to placing a diameter #2 round glass coverslip (Erie Scientific, Portsmouth, New Hampshire) over the exposed skin. In this window chamber model, one piece of skin was removed completely and replaced with a coverslip, but the other piece of skin in the window chamber remained intact and without any coverslip. The tumor had unrestricted growth on the side of the chamber without a coverslip and thus bulged out during growth. This limited transillumination imaging to a maximal tumor size of about because the light that penetrated the tumor was insufficient for the hyperspectral imaging technique due to poor signal to noise ratio and experiments were terminated at this point. Animals were housed in an environmental chamber with free access to food and water and standard light and dark cycles. Animals were placed on a heating pad attached to the microscope stage during the imaging session. A custom-built window chamber holder secured the window chamber under the microscope objective. The holder was fastened to a stage mount that allowed the window chamber to be positioned under the microscope objective using the standard manual controls on the microscope stage. Anesthesia for immobilization during imaging was provided by isoflurane (1 to 1.5%) in medical air. Image data sets were acquired as follows. (1) For investigations of time-averaged values of HbSat in microvessels, image data sets were acquired at intervals of 1 or for approximately . (2) For HbSat fluctuation analysis, image data sets were acquired at intervals for . Data set acquisition at intervals represents the maximum achievable time resolution with the current imaging system parameters, with image exposure time being the limiting factor. In one set of experiments, animals were imaged while the breathing gases were changed from room air to 100% oxygen. In this case, anesthesia for immobilization during imaging was provided by ketamine IP and xylazine IP.
Image and Data Processing
Image processing was performed using MATLAB software (The Mathworks, Inc., Natick, Massachusetts). All images were converted into double-precision arrays for mathematical processing. The raw pixel values were converted to absorbance values by manually selecting avascular regions in the images to use as an estimate of unattenuated light. Pure reference spectra of oxy- and deoxyhemoglobin obtained with the imaging system were used in a linear mixing model to solve for HbSat by a linear least-squares regression of the data according to the method of Shonat25 as described previously.23, 24 Regions-of-interest (ROIs) on individual microvessels were manually selected for data points of HbSat. The calculated values of HbSat for each pixel were accepted or rejected based on the value for the fit of the model to the data based on the calculated unknowns. was calculated according to the standard definition for the coefficient of determination:26 , where sum of squares (variance considering regressors), and variance (no regressors considered). Pixels with values were rejected and not considered in calculations or included in saturation maps. The HbSat value of the ROI is reported as the mean HbSat value of the pixels within the ROI. The 95% confidence intervals of the mean HbSat for the ROIs at a single time point were calculated as , where mean, for 95% confidence level, standard deviation, and of pixels in the ROI. For statistical analysis, analysis of variance (ANOVA) was performed followed by Newman-Keuls comparison when statistical differences were indicated. A value of was used as the threshold for statistical significance.
For HbSat fluctuation analysis, median ROI HbSat values from time series were analyzed by examining the power spectra of each time series. Each series of data contained 123 data points sampled at intervals. In some cases, excessive animal movement or other artifact corrupted the data such that a time point was lost. In this case, linear interpolation was used to fill in the missing data point. No more than two data points in any data set were lost and had to be treated in this manner. To obtain the power spectrum, the data were mean-subtracted to remove the dc component and padded with zeros at the end of the time series to 128 data points (a power of 2) so the fast Fourier transform algorithm could be used for the Fourier transform. Fourier transform of the time series and power spectra were calculated with MATLAB software.
Figure 1 shows examples of HbSat calculations based on linear least-squares fits of the spectral imaging data for individual image pixels. The pixels came from ROIs 1 and 2 in Fig. 10 for the 100% air-breathing condition in the tumor image. Only pixels with were accepted in the creation of the HbSat image maps and calculation of HbSat values in image ROIs; the rest were colored as background in the image maps and omitted from ROI calculations in the figures as detailed previously.23
Oxygen Transport Longitudinal Gradients
Figure 2 shows a region of 4T1 tumor microvasculature nine days after tumor cell implantation with various ROIs indicated. The ROIs were chosen such that they followed the course of several microvessels to observe the presence of gradients in HbSat along the vessels. Figure 3 is a graph of the fluctuations recorded at intervals in HbSat over time for one group of ROIs associated with a particular vessel path. Table 1 is a list of the time-averaged HbSat for each of the ROIs in Fig. 3, with the ROIs grouped by association with a particular vessel path (see Fig. 2). ANOVA and Newman-Keuls comparisons of the time-averaged HbSat were performed on the separate groups of ROIs (i.e., ROIs 1 to 6, 7 to 10, and 11 to 15). It is evident from Fig. 3 and Table 1 that, for the selected vessels, there is little indication of time-averaged gradients in HbSat. Although for one group of ROIs the difference in the average HbSat of ROI 1 from ROIs 2 to 6 rises to the level of statistical significance , biologically this difference is probably not meaningful (maximum average of 85% for ROIs 2 to 6). In ROIs 11 to 15, ROIs 13 and 11, respectively, are statistically the highest and lowest time-averaged values with the other ROIs somewhere in between and not statistically different from each other. The largest measured fluctuation range in the ROIs for this tumor occurred with ROI 11 (minimum , maximum , ). The average fluctuation range of all the ROIs is .
Time-averaged values of mean HbSat±standard deviation for the ROIs in Fig. 2. The ROIs were grouped for statistical analysis (see Sec. 2.4 for details) according to apparent common microvascular flow pathways with groups indicated by horizontal borders in table. Statistically significant differences (ANOVA and Newman-Keuls, p<0.05 ) are indicated in the table (Y).
|ROIs||Time-Averaged HbSat (%) Mean±St.Dev.||Statistical Difference P<0.05|
Figure 4 shows a region of 4T1 tumor microvasculature seven days after tumor cell implantation in a tumor different from the one in Fig. 2 with various ROIs chosen similarly as before. A graph of the fluctuations in HbSat over time recorded at intervals for a group of ROIs is shown in Fig. 5 , and Table 2 is a list of the time-averaged HbSat for each of the ROIs in Fig. 4. Statistical comparisons were performed as before. The graph of HbSat temporal fluctuations in Fig. 5 for the selected group of ROIs clearly clearly shows the presence of gradients in HbSat that persist over time. The time-averaged HbSat values in Table 2 indicate the existence of time-averaged gradients in HbSat in the various groups of ROIs, particularly for ROIs 5 to 9. In this tumor, the fluctuations in HbSat tended to be larger than those for the previously described tumor. The largest measured fluctuation range in the ROIs for the tumor in Fig. 4 occurred with ROI 11 (minimum , maximum , ). The average fluctuation range of all the ROIs is . An interesting observation is that within each group of ROIs in this tumor, the ROIs with the highest time-averaged HbSat (ROIs 4, 8, 9, and 13) are all located in close proximity (see Fig. 4), and the average HbSat tends to decrease along each of the respective microvessel branches toward the junction where they meet (ROI 1), at which point the average HbSat increases. This may imply a common underlying mechanism that affects the general region of the tumor where the observed vessels are located.
Time-averaged values of mean HbSat±standard deviation for the ROIs in Fig. 4. The ROIs were grouped for statistical analysis (see Sec. 2.4 for details) according to apparent common microvascular flow pathways with groups indicated by horizontal borders in table. Statistically significant differences (ANOVA and Newman-Keuls, p<0.05 ) are indicated in the table (Y). ROIs 8 and 9 were not statistically different from each other (indicated by “*”) but were different from the other ROIs in the analysis group.
|ROIs||Time-Averaged HbSat (%) Mean±St.Dev.||Statistical Difference P<0.05|
In contrast to the tumor microvascular networks, gradients in HbSat such as those found in the tumor were not evident in normal microvessels. Figure 6 shows vessels in a nontumor bearing window chamber two days postsurgery. Next to each ROI in the figure is the time-averaged HbSat with data points taken at intervals. With the exception of the ROIs marked with a “ ,” there was no statistical difference in the average HbSat in this network of vessels (ANOVA and Newman-Keuls, ) when ROIs were compared to those grouped in the same branch and vessel segment.
Oxygen Transport Fluctuations
Figure 7 is an example analysis of time series data of HbSat fluctuations. The data in the figure is for a 4TO7 tumor at seven days after tumor cell implantation. In Fig. 7a, the transmitted light image shows a region at the periphery of a tumor, with normal tissue on the left of the image and tumor tissue on the right of the image. ROI 1 is from an arteriole in an area of normal tissue, ROI 2 is from a venule in normal tissue, and ROI 3 is a representative vessel from the tumor microvessel bed seen in the image. Figure 7b is a plot of the HbSat fluctuations over time for the three ROIs in Fig. 7a. Even though the arteriole HbSat exhibits relatively high frequency HbSat fluctuations, low frequency fluctuations dominate the venule data. The tumor microvessel tends to have an intermediate average HbSat value between the arteriole and venule with low frequency HbSat fluctuations that follow the pattern of the nearby venule. The tumor microvessel fluctuations are larger in magnitude than the venule fluctuations. In Fig. 7c, it can be seen that a number of higher frequency components are present in the arteriole power spectrum, but lower frequency components dominate the power spectra of the venule and tumor microvessel. This trend was consistent in the 4T1 and 4TO7 tumors that were imaged and for normal arterioles and venules in nontumor bearing window chambers. Similar to the spectra in Fig. 7c, the largest peaks in the power spectra for venules and tumor microvessels occurred for frequencies below , and other frequency components generally had less than half the magnitude of the largest peak.
Anastomosis of Vessels with Different Oxygenations
Figure 8 depicts a direct connection between 4T1 tumor vessels with considerable differences in HbSat. Several smaller vessels with respective saturations of about 66% and 37% converged into one larger diameter vessel. There appeared to be laminar flow in the large diameter vessel, as the different flows propagated without mixing for a distance of at least . The HbSat and direction of blood flow are indicated in the figure. Figure 9 is another example of this type of connection in a 4T1 tumor. Similar to Fig. 8, several vessels with different HbSats are seen merging together. The saturations of the merging vessels in this example, 61% and 39%, are similar to the values in the previous example in Fig. 8.
Figure 10 is an example of the effect, presumably due to AV anastomoses or similar structures, on oxygen transport in a 4T1 tumor nine days after implantation of tumor cells. One set of images shows the tumor, and the other set of images illustrates adjacent normal tissue (some tumor feeding vessels from the tumor images are also visible in the lower right of the normal tissue images). Table 3 contains HbSat values for the ROIs indicated in Fig. 10. Under normal air-breathing conditions, the HbSat in some of the venules immediately adjacent to the tumors (ROIs 4 and 5 in the Fig. 10 tumor) was slightly elevated compared to other nearby venule branches (ROIs 2 and 3 in the Fig. 10 tumor). In the switch to 100% oxygen breathing, there was an appreciable increase in HbSat of almost 30% in the venules that had elevated air-breathing values, which may indicate that some highly oxygenated red blood cells largely bypassed the tumor and were diverted into adjacent venules. Farther away from the tumor in normal tissue, there was no conspicuous indication of this effect in the microvasculature and only a minimal increase in venule HbSat with oxygen breathing. The arterioles in both the tumor (ROI 1) and normal tissue (ROI 2) images in Fig. 10 increased to about the same HbSat with oxygen breathing.
HbSat values for the ROIs indicated in Fig. 10. The ROIs are indicated in the middle group of images (“Air”). The HbSat values are given as the Mean±standard deviation (rounded to the nearest percent) and 95% confidence intervals for the means HbSat of the ROI.
|1||(55.2 to 56.8)||(91.9 to 94.1)|
|2||(15.7 to 16.3)||(35.6 to 36.6)|
|3||(22.6 to 25.0)||(26.8 to 29.9)|
|4||(31.2 to 33.2)||(59.7 to 61.7)|
|5||(34.2 to 35.3)||(66.1 to 67.6)|
|1||(20.8 to 22.2)||(27.5 to 29.0)|
|2||(75.9 to 78.5)||(93.5 to 96.2)|
We previously described a hyperspectral imaging system for in vivo microscopy measurements of tumor microvessel HbSat.23 An understanding of tumor oxygen transport at the microvascular level is necessary to more fully comprehend the various factors that influence tumor biology, physiology, and therapeutic outcome. For example, longitudinal oxygen gradients of sufficient magnitude to result in chronic intravascular hypoxia have been documented in tumors,12 demonstrating that patent functional tumor microvessels can still be ineffective at delivering oxygen to some tumor regions. Although individual tumor microvessels are rarely hypoxic, the tissue between the vessels is exquisitely sensitive to the microvessel oxygen concentration. Lanzen recently demonstrated fluctuations in oxygenation of tumor tissue, including fluctuations in the radiobiologic hypoxic range , that were well correlated to fluctuations in red cell flux of surrounding tumor microvessels.27 The authors also demonstrated how one vessel with a relatively large red cell flux can strongly influence the oxygenation of a region of tumor compared to other nearby vessels. Intermittent hypoxia has emerged as a potentially more important factor than chronic hypoxia in terms of promoting tumor metastasis.16 Fluctuating tumor oxygenation resulting in intermittent hypoxia-reoxygenation episodes was shown to confer survival and proliferation advantages to both tumor and endothelial cells at a molecular level via hypoxia-inducible factor- (HIF- ) mediated pathways.15 Slow fluctuations in documented in spontaneous canine tumors increase the likelihood that such effects also occur in human tumors.28 Taken together, this knowledge indicates that HIF- is an important target to be considered for drug development to ameliorate the negative effects of fluctuating oxygenation on tumor progression and treatment.14 In another example, a recent review of the tumor oxygenation effects of a variety of angiogenesis-inhibiting agents (AIAs) revealed mixed results—increases, decreases, and no changes were documented—thus the mechanisms involved in alterations of tumor oxygenation by AIAs are at present not fully understood.29 Knowledge of the oxygenation effects of AIAs is important so that they can be rationally combined with other conventional therapies for maximum effect, particularly for radiation therapy.29
In this paper, we demonstrate spectral imaging measurements of HbSat fluctuations and spatial gradients in 4T1 and 4TO7 mouse mammary adenocarcinomas. The data in Figs. 2, 3, 4, 5 illustrate differences in oxygen transport in tumor microvascular networks that can occur between individual tumors. In the tumor in Fig. 2, there were relatively few longitudinal gradients that persisted over time. The average fluctuations in HbSat that occurred were generally consistent between the ROIs (standard deviation of 5%). In contrast, the tumor in Fig. 4 had more examples of chronic longitudinal gradients; the fluctuations in HbSat on average were larger than in the tumor in Fig. 2; and there was greater variation in the range of fluctuations between the ROIs (standard deviation of 12%). The HbSat longitudinal gradients observed in the tumor microvessel branches were not observed in normal vessel branches as in Fig. 6. Duling documented longitudinal gradients in a hamster cheek pouch normal microvascular network along network vessels with HbSat values (calculated from microelectrode measurements) of 70% at an artery to about 33% at a precapillary arteriole.30 Assuming a linear gradient in HbSat, then a rough estimation of the gradient in the networks measured by Duling (represented in Fig. 3 from Ref. 30) was minimally and maximally . In contrast, for the tumor in Fig. 4 in this study for ROIs 5 to 9, the gradient in HbSat is roughly , or 2.75 to 17 times greater than that measured by Duling. This contrast may reflect differences in tissue type, such as normal versus tumor microvessels, or animal model, such as mouse skin versus hamster cheek pouch. It should also be noted that in the network measured by Duling, the longitudinal gradients occurred along several different branching orders of vessels, but in the tumor data presented here, the observed gradients occurred along what appeared to be a single vessel segment, albeit a tortuous, highly branched, and abnormal one. Imaging on consecutive days is required to see if these characteristics are relatively stable for a particular tumor or if they change over time as the tumor develops.
Data acquisition at higher temporal resolution revealed slow fluctuations in HbSat in tumor microvessels. As seen in Fig. 7, these fluctuations were similar to those in normal venules, but the arteriole data showed high magnitude fluctuations with relatively high frequency. The magnitude of the fluctuations in the tumor microvessels was sometimes larger than in normal venules. Braun postulate that a number of different mechanisms, including arteriolar vasomotion, blood flow changes induced by hemodynamic phenomena, and intussusceptive microvessel growth, may be responsible for observed fluctuations in tumor measured with oxygen microelectrodes.13 The measured slow temporal fluctuations in tumor microvessel HbSat were consistent with microelectrode measurements of fluctuations in rat mammary adenocarcinoma, fibrosarcoma, and glioma tumors ,13, 31 and spontaneous canine tumors ( or ).28 Our preliminary data suggest that at least in some tumor microvessels, mechanisms that are responsible for fluctuations in normal venule HbSat may contribute to fluctuations in tumor microvessel HbSat and hence to tumor fluctuations.
There was significant vasomotion in the arterioles observed during imaging. Arteriole vasomotion in the frequency range of has been documented previously.32, 33 It is possible that the arteriole data contains artifacts due to vasomotion and the fact that accurate sampling of frequencies higher than are beyond the frequency resolution of the imaging system ( sampling rate results in a Nyquist frequency of ), thus there may be aliasing of higher frequency components represented as artifacts in frequencies below in our data. It should be noted that due to the geometry of the window chamber, tumors had unrestricted growth on the side of the chamber without a coverslip and thus would bulge out at some point during growth. Thus, the vessels that were imaged at later time points were generally on the tumor periphery. These vessels are general relatively well oxygenated compared to vessels located deeper in the tumor. However, vessels that emerge from deeper in the tissue to the surface (periphery) are also sometimes seen, and these vessels generally have lower saturation on the order of 30% or less. This may explain why the venules from normal tissue in Fig. 6 have lower saturations than the tumor vessels in Figs. 3 and 5.
In Figs. 8 and 9, we visualized the convergence and direct connection of tumor microvessels with diameters and HbSats that differed by more than 20%. As both of the merging vessels are venules, the difference in oxygenation may be explained in part by the different paths taken by the vessels through the tumor tissue. In Fig. 8, for example, the less oxygenated vessel emerges from deeper tumor tissue but the more oxygenated vessel traverses a more superficial path. The merging of vessels like this will undoubtedly affect the flow dynamics within the local network due to differences in the mechanical properties of the red blood cells (less oxygenated red blood cells are less deformable than well oxygenated ones34).
During the process of angiogenesis and neovascularization, sprouts arising from venules can anastomose with neighboring arterioles. In some instances, tumor vascular networks can be both supplied and drained by venules due to AV anastomoses.19 AV anastomoses in tumors may adversely impact various therapeutic modalities, including chemo-, radio-, and immunotherapies, by providing an alternate route for blood flow that bypasses tumor tissue.35 Angiography studies, such as those by Lagergren in human fibrosarcomas, demonstrated shunting of contrast medium from the arterial to venous side of a tumor microvascular network, highlighting the presence of AV anastomoses.36 Warren details work that showed an increase in the oxygen content of venous blood existing tumors, presumably due to AV shunts.37 Mariani demonstrated intratumoral shunting of arterially injected radio-labeled particles from malignant gliomas to the lungs.38 In Fig. 10, venules immediately adjacent to a tumor showed what appeared to be a diversion of highly oxygenated red blood cells around the tumor upon a switch from air to 100% oxygen breathing, presumably due to AV anastomoses or equivalent structures within the tumor. This phenomenon was not observed in venules further removed from the tumor. Several methods have been studied preclinically and clinically to ameliorate tumor hypoxia by increasing microvascular oxygen content; however, those based on hyperoxic gas breathing at ambient and hyperbaric pressures have had very limited success.39, 40 A number of factors have been implicated for the failure of hyperoxic gas breathing to significantly improve radiotherapeutic outcome, including longitudinal gradients, abnormal tumor microvascular geometry, inadequate oxygen delivery relative to tumor demands, and unstable blood flow due to vasoactive effects.41 The diversion of oxygenated blood to tumor draining venules, as demonstrated in this study, may be another mechanism that limited the success of previous hyperoxic gas breathing trials.
Recent publications have demonstrated the utility of spectral imaging for measurements of HbSat in networks of microvessels.23, 42 In this paper, we have demonstrated that spectral imaging of tumor microvasculature can be used for measurements of oxygen transport parameters with relevance to current questions about tumor biology and treatment outcome. In future studies, we plan to employ this technique to study tumor oxygen transport effects of vascular-targeting drugs.
Funding for this project was provided in part by National Institutes of Health Grants Nos. R01 CA 40355 (NCI), P50 CA 068438 (NCI), and T32 EB01630 (NIBIB).