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Tumor oxygenation has long been recognized as a significant factor influencing cancer therapy. We recently established a novel magnetic resonance in vivo approach to measuring regional tumor oxygen tension, FREDOM (Fluorocarbon Relaxometry Using Echo Planar Imaging for Dynamic Oxygen Mapping), using hexafluorobenzene (HFB) as the reporter molecule. We have now investigated oxygen dynamics in the two Dunning prostate R3327 rat tumor sublines, AT1 and H. FREDOM revealed considerable intratumoral heterogeneity in the distribution of pO2 values in both sublines. The anaplastic fastergrowing AT1 tumors were more hypoxic compared with the size-matched, well-differentiated, and slower-growing H tumors. Respiratory challenge with oxygen produced significant increases in mean and median pO2 in all the H tumors (P<.001), but no response in half of the larger AT1 tumors (>3 cm3). Immunohistochemical studies using the hypoxia marker, pimonidazole, and the vascular endothelial cell marker, CD31, confirmed that the H tumors had more extensive vasculature and less hypoxia than the AT1 tumors. These results further validate the utilization of FREDOM to monitor tumor oxygenation and concur with the hypothesis that the level of hypoxia is related to tumor growth rate and poor vascularity.
It is well recognized that hypoxia in solid tumors affects response to radiotherapy [1–3] and some chemotherapeutic drugs . Recent evidence, in experimental and clinical studies, indicates that tumor hypoxia might also be a mechanism for malignant progression and metastasis in solid tumors [5,6]. Given the importance of oxygen, many techniques for monitoring pO2 have been developed . Although each method has specific attributes, many are highly invasive and impractical for longitudinal studies of specific regions of interest.
We recently demonstrated the feasibility of measuring tumor oxygenation based on 19F nuclear magnetic resonance (NMR) echo planar imaging (EPI) following direct intratumoral injection of the reporter molecule, hexafluorobenzene (HFB)—FREDOM (Fluorocarbon Relaxometry Using Echo Planar Imaging for Dynamic Oxygen Mapping) . This technique allows us to not only simultaneously examine multiple specific locations within a tumor, but also observe dynamic changes at individual locations with respect to intervention. Our previous studies of Dunning R3327 prostate rat tumor sublines have demonstrated that the faster-growing metastatic MAT-Lu tumors were more hypoxic than the relatively well-differentiated and slower-growing HI tumors . In order to further investigate the potential correlation between hypoxia and tumor malignant progression, we have now studied and compared tumor oxygen tension dynamics in two other Dunning prostate rat tumor sublines: the welldifferentiated and slower-growing H and the anaplastic fastgrowing AT1, which derives originally from the course of passage of the H .
There is a close relationship between hypoxia and vascular extent in solid tumors, and it is widely accepted that tumor hypoxia results in part from poor vascularity . Immunohistochemistry based on bioreductive chemical markers and vascular endothelial cell markers can reveal spatial patterns of tumor hypoxia and vasculature, as well as their relationship at the cellular level [12–14]. We have now compared direct pO2 measurements using FREDOM with histological investigations of hypoxia and vasculature using pimonidazole and anti-CD31 antibody, and show that the macroscopic dynamic imaging is consistent with the histological microstructure.
Experiments were approved by the Institutional Animal Care and Research Advisory Committee.
Two sublines of the Dunning prostate R3327 adenocarcinoma were selected: H, a well-differentiated and slowgrowing tumor with volume doubling time (VDT) of 16 days , and AT1, an anaplastic and faster-growing subline with VDT of 5 days . Tumors were originally obtained from Dr. J. T. Isaacs (Johns Hopkins, Baltimore, MD) and provided to us by Dr. P. Peschke (DKFZ, Heidelberg, Germany). Tumors were implanted in a skin pedicle surgically created on the foreback of adult male Copenhagen-2331 rats (~250 g; Harlan, Indianapolis, IN), as described in detail previously . Tumors were allowed to grow and were investigated by magnetic resonance imaging (MRI) when about 1 cm3 or when >3 cm3 (~10 mm or >20 mm in diameter). Twelve H tumors, including six small (size range 0.6–1.5cm3) and six large tumors (range 3.0–4.6 cm3), and 13 AT1 tumors, including seven small (range 0.7–1.8 cm3) and six large tumors(range 3.0–5.2 cm3),wereinvestigated. In preparation for MRI, each rat was given ketamine hydrochloride (200 µl, 100 mg/ml, i.p.; Aveco, Fort Dodge, IA) as a relaxant and maintained under general gaseous anesthesia (1 dm3/min air and 1.3% isoflurane; Baxter International, Deerfield, IL). HFB (50 µl; Lancaster, Gainesville, FL) was deoxygenated by bubbling nitrogen for 5 minutes before use, and injected directly into the tumors using a Hamilton syringe (Hamilton, Reno, NV) with a custom-made fine sharp needle (32 gauge), as described in detail previously . Generally, HFB was administered along three tracks in the form of a fan in a single central plane of the tumor coronal to the rat's body. The needle was inserted manually to penetrate across the whole tumor and withdrawn ~1 mm to reduce pressure, and 3 µl of HFB was deposited. The needle was repeatedly withdrawn a further 2 to 3 mm and additional HFB was deposited. Typically, HFB was deliberately deposited at about 16 individual locations pertumor, in both the central and peripheral regions of the tumors, to ensure that the interrogated regions would be representative of the whole tumor. Each animal was placed on its side in a cradle with a thermal blanket to maintain body temperature.
Magnetic resonance experiments were performed using an Omega CSI 4.7 horizontal bore magnet system with actively shielded gradients (Bruker Instrument, Fremont, CA). A tunable (1H/19F) MR coil, 2 or 3 cm in diameter matched to the tumor size (constructed from a cylindrical copper tube about 2 cm deep and acting as a single-turn solenoid), was placed around the tumor-bearing pedicle. Proton images were obtained for anatomical reference using a three-dimensional (3D) spin-echo sequence. The coil was then retuned in place to 188.27 MHz, and corresponding [19F]MR images were obtained. Overlaying the [19F]MR images on the corresponding proton images revealed the distribution of HFB.
Following conventional MR imaging, tumor oxygenation was estimated on the basis of 19F pulse burst saturation recovery (PBSR) EPI relaxometry of the HFB, as described previously . The ARDVARC (Alternated R1 Delays with Variable Acquisitions to Reduce Clearance effects) data acquisition protocol was applied to optimize data quality. This approach provided pO2 maps with 1.25 mm in-plane voxel resolution in 8 minutes with typically ~50 to 150 individual pO2 measurements (voxels per tumor). The spin-lattice relaxation rate [R1 (sec-1)=1/T1] was estimated on a voxel-by-voxel basis using a three-parameter monoexponential function, and pO2 was estimated using the relationship pO2 (Torr)=(R1-0.0835)/0.001876 . Three consecutive baseline pO2 measurements were made over 24 minutes while the rats breathed air. The inhaled gas was then altered to oxygen (100% O2) and pO2 maps were immediately acquired with no equilibration period. Five consecutive maps were acquired over 40 minutes. The gas was then returned to air, and five further maps were acquired over 40 minutes.
Histological studies were performed on large AT1 and H tumors.
For H&E staining, tumor tissues were fixed in 10% formalin, embedded in paraffin, and sectioned (4 µm). Tumor necrotic regions were identified on the H&E stained slides examined under low magnification (x2 objective). All fields (~30) in each section were captured by a digital camera and processed using Metaview software (Universal Imaging, West Chester, PA). Fields were calibrated according to magnification, and areas occupied by necrotic cells were outlined, calculated, and expressed in square millimeters. The area of the entire cross section was determined manually. The proportion of necrotic areas (% necrosis) was calculated as follows: sum of all necrotic areas in a single cross section divided by total area of cross section and multiplied by 100. Five slides representing each tumor type were analyzed and the percentage of necrosis was calculated and averaged for each tumor.
Pimonidazole hydrochloride (Hypoxyprobe-1; NPI, Belmont, MA) was injected into the tail vein at a dose of 60 mg/kg. Ninety minutes later, rats were anesthesized and then perfused for 20 minutes with physiological saline containing 5 mM CaCl2. For immunohistochemistry, the tissues were immediately immersed in liquid nitrogen and stored at -80°C. After cryostat sectioning (6 µm thick), tumor sections were fixed in acetone for 5 minutes and then rehydrated in phosphate-buffered saline containing 0.1% Tween-20 (PBST) for 10 minutes. Monoclonal antibody Mab1 (NPI) that detects pimonidazole-protein adducts was diluted 1:100 and added to frozen sections followed by incubation for 2 hours at 37°C. Slides were then incubated for 1 hour at 37°C with horseradish peroxidase (HRP)-conjugated goat antimouse secondary antibody (1: 100 dilution; Serotec, Raleigh, NC). After a PBST wash, sections were immersed in AEC substrate (3-amino-9-ethylcarbazole; Vector Laboratories, Burlingame, CA) for 15 minutes at room temperature. Finally, sections were counterstained with hematoxylin and observed under light microscopy. Hypoxic fraction was determined as area positively stained for pimonidazole relative to the total tissue area using Metaview software.
Mouse antirat CD31 monoclonal antibody (1:20; Serotec) and HRP-conjugated goat antimouse secondary antibody (1:100) were used to detect tumor blood vessels on 6-Am sections immediately adjacent to those used for detection of hypoxia. Vascular density was evaluated using the “hot spot” technique described by Weidner . The five most vascularized areas in each tumor were selected under low magnification (x4). Vascular density was determined by counting the total number of structures positive for CD31 using x10 objective (area 0.318 mm2) and calculating the mean number of vessels per square millimeter.
The statistical significance of changes in oxygenation was assessed using analysis of variance (ANOVA) on the basis of Fisher's Protected Least Significant Difference (PLSD) (Statview; SAS Institute, Cary, NC). Where appropriate, the Student's t-test was applied. Hypoxic fractions (HF2.5,5,10 <2.5, 5, 10 Torr) measured by FREDOM in all the tumors were calculated from the fraction of hypoxic voxels in each pO2 map. All data are quoted ±SE.
Overlay of 19F on 1H images (not shown) confirmed that HFB was widely distributed, predominantly in a central slice, and occupied voxels representing 5% to 10% of the whole tumor. In the series of EPI relaxation data sets, typically ~50 to 300 voxels provided an R1 fit and potential pO2 value. Because even noise may give an apparent relaxation curve (R1) fit, data were selected within a region of interest, having T1 error <2.5 seconds and ratio T1 error/T1 <50%. With respect to respiratory interventions, only those voxels that provided consistently reliable data during the time course were included for further analysis. The number of such acceptable voxels ranged from 11 to 74 per tumor. Figure 1 shows typical pO2 maps of the selected regions obtained from representative small H and AT1 tumors under baseline air breathing and during oxygen challenge. During air breathing, both tumors exhibited extensive heterogeneity in pO2 distribution, but the H tumor was better oxygenated than the AT1 tumor (P<.001). Upon switching to oxygen breathing, both tumors responded with significantly increased mean pO2 (P<.001).
Data for small and large tumors in the H and AT1 sublines are pooled as histograms in Figures 2 and and3,3, respectively. For the H tumors (Figure 2), a total of 219 voxels from the six small H tumors were pooled and gave a mean baseline pO2=31±2 Torr (median=27 Torr), which was significantly greater (P<.001) than for the six larger H tumors (159 voxels), which had a value of 14±1 Torr (median=12 Torr). For the AT1 subline (Figure 3), the seven small tumors (280 voxels) had a mean pO2 of 14±1 Torr (median=11 Torr), which was significantly greater (P<.001) compared to the six large AT1 tumors (149 voxels; mean=4±1 Torr, median=3 Torr). Comparison of the pooled mean baseline pO2 between the two sublines showed that both the small and large groups of AT1 tumors had significantly lower mean pO2 than the size-matched H groups (P<.001). Oxygen breathing produced significant increase in mean pO2 in all the tumor groups (P<.001). However, hypoxic fractions (pO2<2.5 Torr; 2.5<pO2<5 Torr; 5<pO2<10 Torr) behaved differently between the H and AT1 tumors. Specifically, for the larger tumors, the hypoxic fractions of all the ranges in the H tumors (18%, 8%, and 18%) decreased dramatically to less than 5%, whereas no distinct changes were observed in the large AT1 tumors (Figures 2 and and33).
Uniquely, FREDOM allows the oxygen dynamics at multiple individual locations to be followed noninvasively and simultaneously, specifically revealing the fate of initially hypoxic regions. Voxels with initial pO2<10 Torr through all the three baseline measurements were followed with respect to respiratory challenge for both H (92 voxels) and AT1 (248 voxels) sublines (Figure 4, a and b). Figure 4a shows that oxygen breathing produced a significant increase in mean pO2 for these initially hypoxic regions in both the H (mean baseline pO2=3.9±0.4 Torr; maximum pO2 observed with oxygen=54.7±4.6 Torr) and the AT1 (mean baseline pO2=1.2±0.1 Torr; maximum pO2=17.9±2.3 Torr) tumors (P<.01). However, comparison of the median pO2 for these voxels showed a dramatic increase in the H tumors (baseline pO2=4.1 Torr to maximum pO2=46.2 Torr) versus only a small increase in the corresponding regions of the AT1 tumors (baseline pO2=1.5 Torr to maximum pO2=5.3 Torr). We also examined these hypoxic voxels grouped as having baseline pO2<5 Torr, or in the range 5 to 10 Torr. For the AT1 tumors, both subsets behaved equivalently and in line with the trace shown in Figure 4a. For the H tumors, each subset showed a significant increase, but the pO2 achieved was significantly higher for those voxels, which started in the 5- to 10-Torr group. Moreover, Figure 4b shows that about 90% initially hypoxic regions became well oxygenated with oxygen breathing in the H tumors, whereas>60% of the hypoxic regions in the AT1 tumors remained. Hypoxic regions in the groups of small and large AT1 tumors did not behave significantly differently (P>.3).
pO2 data were also compared on the basis of differences between individual tumors, as shown in Table 1. As with the pooled data, for both the H and AT1 tumors, the large tumors were significantly more hypoxic than the smaller tumors, and the AT1 tumors were significantly less well oxygenated than the size-matched H tumors (P<.05; Tables 1 and and2).2). With respect to oxygen challenge, all the tumors in the H subline and the small AT1 showed significant increases in global mean pO2 (P<.001), whereas three of six larger AT1 tumors did not respond to oxygen. The mean and median pO2 increased, and the HF5 or 10 decreased significantly in the H and the small AT1 tumors with oxygen inhalation (P<.05; Table 1). Mean pO2 of the group of six large tumors did increase, but only reached a P<.1 level of significance.
AT1 tumors were significantly more hypoxic than the H tumors of comparable size (Figure 5 and Table 2). The positive staining for pimonidazole in the AT1 tumors was primarily detected in tumor cells located in perinecrotic regions and more than 100 µm away from blood vessels, which were recognized by the anti-CD31 antibody (Figure 5, C and D). The total number of vessels per square millimeter was 139±30 (range 88–227) in the better-oxygenated H tumors, which was significantly higher than for the more hypoxic AT1 tumors (45±13/mm2, range 28–71, P<.05; Figure 5 and Table 2). This difference in vascularity also coincided with the greater necrotic fraction: about 7% area in the AT1 tumors compared with only 2% in the H tumors (Table 2).
The anaplastic and faster-growing AT1 tumors were significantly more hypoxic than the well-differentiated and slower-growing H tumors from which they were originally derived. These results are consistent with previous reports comparing oxygenation and radiation sensitivity of the AT and H sublines. Based on electrode polarographic pO2 measurements, the H subline was found to be considerably less hypoxic . This coincided with [31P]NMR showing greater phosphocreatine and less inorganic phosphate (Pi) in H tumors . Moreover, radiation sensitivity of AT, but not H, tumors could be enhanced by misonidazole , suggesting a lack of hypoxia in the H tumors. We have ourselves examined AT1 tumors previously during the development of the [19F]MRI oximetry technique [8,21]. The mean and median pO2 values reported now and previously are remarkably similar, together with distribution histograms and hypoxic fractions. In all cases, we have found that larger tumors are significantly less well oxygenated than small tumors and, indeed, this was also observed in other Dunning prostate R3327 tumors sublines (MAT-Lu and HI) [9,22] and rat breast tumors . Yeh et al.  found no such correlation with size for either subline based on electrode oximetry, but 31PNMR did show metabolic hypoxiation in larger AT tumors . Interlaboratory comparison must recognize differences in techniques and procedures. The histology of our tumors is very similar to that of Yeh et al.  and Thorndyke et al. , and growth of the H tumors is comparable. However, we work with the AT1 subline , as opposed to the AT, and we find a VDT of 5 days as opposed to 2 or 3 days . In comparing our own previous data, we have now altered our anesthesia protocol to a baseline of air/isoflurane as opposed to 33% oxygen in nitrous oxide with metafane [8,21]. Nonetheless, the pO2 distributions appear very similar.
In addition to providing tumor baseline pO2, the FREDOM technique allows the study of oxygen dynamics in response to interventions (e.g., respiratory challenge). Our results show that oxygen breathing produced significant increase in mean pO2 in all the H tumors and the small AT1 tumors, whereas the change was only borderline significant in the larger AT1 tumors (Table 1). Most interestingly, the initially hypoxic regions in the H tumors responded significantly to become well oxygenated with oxygen challenge, whereas no distinct reduction in hypoxic fractions was observed in the large AT1 tumors (Table 1 and Figure 4, a and b). The AT1 tumor data coincide with our previous observations in this subline .
There is increasing evidence that tumor malignant progression may be associated with a hypoxic microenvironment [5,6,24]. Several recent clinical studies have demonstrated a positive relationship between the presence of hypoxia and poor outcome associated with malignant progression and metastasis in several cancers (e.g., advanced squamous cell carcinoma of the cervix [3,25,26], and sarcomas and carcinomas from head, neck, and soft tissue ). Studies of breast cancer have not all been consistent. For example, early work by Vaupel et al.  showed no correlation between grade or stage and pO2 using the Eppendorf Histograph. By contrast, a recent report from Hohenberger et al.  indicated that mean pO2 and hypoxic fraction in breast tumors were associated with both grade and stage. The results of Höckel et al.  in advanced cervical cancer patients showed a lack of correlation between tumor oxygenation and differentiation or stage, but a significantly positive correlation of tumor oxygenation and malignant progression. In an animal model, Thews et al.  reported that a higher differentiated rhabdomyosarcoma subline, F1, of the BA-HAN-1 was less well oxygenated than the undifferentiated G8 subline. Although the results of Thews et al. show the opposite trend to the observations we report here, it is important to note that the F1 and G8 tumors grow relatively rapidly. In our studies, the higher differentiated tumors grow much more slowly. Several other studies have shown evidence that tumor malignant progression (e.g., local invasion, destructive growth and metastasis) may be associated with hypoxic microenvironment in both experimental models [5,24,31,32] and the clinic [25,26,33]. A recent study by Movsas et al.  using the Eppendorf Histograph showed that increasing levels of hypoxia were related to increasing clinical stage of human prostate carcinomas, but trends with respect to grade did not reach significance. Eble et al.  found that the moderately welldifferentiated Dunning rat prostate HI subline was better oxygenated than the anaplastic AT1 subline, and Yeh et al.  found that the well-differentiated H subline was better oxygenated than the anaplastic AT. Our previous study of two other Dunning prostate R3327 rat tumor sublines showed that the poorly differentiated and faster-growing (VDT=2.7 days) and metastatic MAT-Lu tumors were less well oxygenated than the moderately differentiated and slower-growing (VDT=9 days) HI tumors. Similar to the results here, breathing hyperoxic gas (oxygen or carbogen) significantly increased the oxygenation and reduced the hypoxic fraction in the HI tumors, but to a much lesser extent in the metastatic MAT-Lu tumors . This would tend to support the hypothesis that tumor hypoxia is associated with parameters such as increased growth rate and level of differentiation (grade). As in our previous studies [9,22,23] of various tumor types, tumor size, which is a major component of tumor staging, showed a strongly inverse relationship to oxygenation.
Many experimental and clinical studies have demonstrated that reoxygenation of hypoxic tumor cells contributes to improved radiation sensitivity for tumor therapy [36,37]. Whether initially hypoxic regions of a tumor can be modified to become better oxygenated has long been considered a key indicator for outcome of irradiation. Examining the initially hypoxic regions (pO2<10 Torr) showed that more than 90% of the hypoxic regions in the H tumors became better oxygenated in response to oxygen breathing. In contrast, about 60% of such regions from the AT1 tumors remained unchanged (Figure 4b). Thus, one would expect that radiosensitivity of the H tumors might be significantly improved with pretreatment oxygen breathing, whereas beneficial effect in the AT1 tumors would be less. In fact, measurements in HI tumors with respect to our recent experimental radiotherapy have validated the hypothesis. We found that oxygen breathing before and during a 30-Gy single-dose irradiation significantly enhanced the radiosensitivity by prolonging the tumor growth delay in large HI tumors . Intriguingly, breathing oxygen had no benefit in small HI tumors coinciding with a very small baseline hypoxic fraction. By analogy, one would expect that patients with hypoxic tumors like the large H and HI would show enhanced local control by irradiation in combination with oxygen breathing. Actually, recent clinical data have shown promising results in advanced head and neck cancers accomplished by accelerated radiotherapy with the carbogen and nicotinamide (ARCON) schedule. The phase II trial demonstrated that the ARCON has significantly improved 3- year local control rates to 80% for larynx, 69% for hypopharynx, 88% for oropharynx cancers , and those patients with hypoxic tumors received the greatest benefit from the ARCON paradigm .
Comparison of Figure 4, a and b shows that the mean pO2 in the initially hypoxic regions from both the H and the AT1 tumors continued to increase during the course of 40-minute oxygen breathing, whereas the corresponding hypoxic fraction in both sublines dropped to a minimum value within 24 minutes and then remained stable. This discrepancy suggests that hypoxic regions may be divided into two categories: those that are modulated by oxygen within 24 minutes and continue to show increase at later times, versus those that are unresponsive. This information could be valuable for guiding and planning radiotherapy. In our previous studies of the Dunning prostate rat tumors, we found that oxygen or carbogen breathing produced a similar effect on tumor oxygenation across all the sublines MAT-Lu, AT1, and HI [8,9,21,22,40]. Our irradiation study validated that oxygen breathing significantly improved radiosensitivity in initially hypoxic large HI tumors .
HFB has many strengths as a reporter molecule: MR interrogation is nondestructive, and HFB exhibits remarkably low toxicity and is readily available. From an MR perspective, HFB is ideal, having a single resonance, high sensitivity to pO2, and minimal sensitivity to temperature . The high vapor pressure produces a short biological half-life (T1/2~600 minutes) , but there is little macroscopic redistribution over a period of 2.5 hours allowing effective investigations of acute interventions . The Hamilton syringe with a custom-made fine sharp needle (32 gauge) was designed to minimize tissue damage. Our current data, as well as our previous observations, have demonstrated the stability of local pO2 measurements under baseline conditions. FREDOM oximetry has been validated by various techniques in previous studies (e.g., similar baseline pO2 distribution in the AT1 tumors acquired by Eppendorf Histograph  and comparable oxygen dynamics with oxygen or carbogen challenge observed in HI tumors using the fiber optic OxyLite  or oxygen electrodes ).
Tumor oxygenation may be investigated at many levels, ranging from induced gene expression to cellular microscopy and macroscopic techniques. Ultimately, correlation with outcome is relevant to clinical application, as has been demonstrated for measurements using the Eppendorf Histograph [3,26,27] and, most recently, pimonidazole binding . We have previously shown that pO2 measurements using FREDOM were similar to the Histograph and now we show that hypoxic fractions are commensurate with pimonidazole binding. The anaplastic and faster-growing AT1 tumors had significantly higher pimonidazole binding (18%) than the well-differentiated and slower-growing H tumors (5%, P<.05), consistent with the FREDOM measurements. However, as shown in Table 2, the hypoxic fractions HF2.5,5,10 measured by FREDOM for the large AT1 tumors were far greater than the extent of pimonidazole binding. Others have also reported such discrepancies using Histograph or OxyLite [12,42]. Histograph assessment of oxygenation does not differentiate hypoxic live tissues from necrotic regions, leading to overestimation of tumor hypoxia [43,44]. However, in our tumors, the level of necrosis is relatively small and would not account for the disparity. It has also been suggested that diffusion may limit the distribution of bioreductive hypoxia markers, leading to underestimation of tumor hypoxia  and, in addition, nitroimidazole binding may be influenced by levels of both nitroreductase and thiol . Furthermore, a pO2 threshold value for hypoxic marker binding is not clearly defined in vivo. There may also be differences in sensitivity to chronic versus acute hypoxia and the time required for efficient pimonidazole labeling. Bennewith et al.  have now shown significantly greater pimonidazole binding when assessed following 96 hours of continuous oral availability, as opposed to a single intravenous or intraperitoneal dose followed by tissue harvest after 6 hours. Here, we followed the manufacturer's recommendations of a 90- minute delay between intravenous administration and sacrifice. Despite the lack of absolute correspondence, a general positive correlation in assessments of tumor hypoxia has been reported between Histograph or OxyLite and pimonidazole binding by others [12,44], and now by us here.
Tumor hypoxia results, in part, from inadequate blood vessel development and solid tumors appear not to grow beyond a critical size of ~ 1 mm3 without evoking angiogenesis . Figure 5 shows a typical case of insufficient blood vessels in a region of an AT1 tumor, which results in hypoxia and eventually necrosis with increased distance away from the vessels. The anti-CD31 staining for vascular endothelial cells showed that the more hypoxic AT1 tumors had lower vascular density than the better-oxygenated H tumors (Table 2). This result is in agreement with other reports in various animal or human tumors indicating greater hypoxia at reduced vascular density [11,44]. However, some studies have shown the opposite trend [17,49], may be because hypoxia stimulates angiogenesis, generating greater neovasculature. Here, we have applied histological approaches to assess hypoxia in relation to vascular density. Others have examined additional pertinent parameters including vascular perfusion (e.g., using distribution of the Hoechst 33342 dye) [14,38] and even dynamic changes by applying pairs of distinct hypoxia markers (CCI-103F and pimonidazole) sequentially before and after an intervention to reveal dynamic response (pulse chase double labeling) . Specifically, they were able to detect changes in tumor hypoxia following interventions designed to modulate hypoxia such as breathing hyperoxic gas and hydralazine. Ultimately, dynamic studies will be of great importance, and the availability and correlation of many diverse techniques revealing tissue and cellular properties on various scales from whole tumor to microscopic resolution will be pertinent.
The FREDOM approach to tumor oximetry has the great advantage of facilitating noninvasive assessment of changes in pO2 in response to interventions, as shown here for breathing hyperoxic gases and previously for vasoactive agents, such as hydralazine , or vascular targeting agents . The method is inherently quantitative, but it does require introduction of small quantities (~ 50 µl) of the reporter molecule, HFB. Another drawback for potential clinical application is the current lack of an [19F]NMR channel on most clinical MRI scanners. Currently, we estimate that at least 20 research instruments in the world have a clinical [19F]EPI capability and this will increase dramatically with the popularity of high field systems (e.g., 3 T). Our own institution is installing its first clinical [19F]MRI capability in spring 2003 and we envisage clinical application of the FREDOM in the near future. We are currently investigating Investigational New Drug approval for HFB.
We and others are also searching for alternative noninvasive approaches. Near-infrared reveals changes in vascular oxygenation with high time resolution, but currently little spatial discrimination . BOLD (Blood Oxygen Level- Dependent) contrast [1H]MRI provides spatial resolution and is sensitive to changes in vascular oxygenation, but also is sensitive to changes in tumor blood flow and tumor blood volume (FLOOD) . Moreover, correlations between changes in signal intensity and direct measures of pO2 have shown a qualitative relationship, but poor indication of absolute pO2 [54,55]. In some cases, correlation has been shown between pO2 and dynamic contrast-enhanced (DCE) [1H]MRI [56,57], but although DCE can reveal changes in vascular flow and permeability, it must be recognized that tissue pO2 represents a balance between oxygen delivery and consumption, and thus, such correlations are unlikely to be valid across diverse tumor types.
In conclusion, we have demonstrated that in comparison with the H tumor, the anaplastic and faster-growing AT1 subline of the Dunning R3327 tumor is significantly more hypoxic. Comparable data using histological markers of hypoxia and vascular endothelium further validate the assessment of tumor oxygenation by FREDOM. We believe this approach can provide valuable insight into tumor physiology and response to interventions, assisting in the development of novel therapeutic strategies. Ultimately, FREDOM should have application in the clinical setting.
We are grateful to Matthew Merritt for maintaining the MR system, Maria Sambade for assistance with histology, Peter Peschke (DKFZ) for providing tumor cells, and Philip Thorpe for laboratory facilities.
1This research was supported, in part, by NIH RO1 CA79515 (NCI)/EB002762 (NIBIB) and the DOD Prostate Cancer Initiative Postdoctoral Award (DAMD 170110108) (D.Z.), and performed in conjunction with Cancer Imaging Program P20 CA 86354.