Methods
Tumor model
Fresh tumor fragments of the syngeneic Dunning prostate adenocarcinoma sublines R3327-H, -HI and -AT1 [
17] were implanted subcutaneously into the distal thigh of male Copenhagen rats (weight 180-200 g, Charles River Laboratories, Wilmington, Massachusetts, USA). During irradiation of H- and HI-tumors, rats were always kept under inhalation anesthesia with a mixture of 2.5% sevoflurane (Abbott, Wiesbaden, Germany) and oxygen at 2 l/min using an inhalation mask. For AT1-irradiations, animals were anesthetized with an intraperitoneal injection of Ketamine hydrochloride (125 mg/kg, Pfizer Deutschland, Berlin, Germany) mixed with Xylazine hydrochloride (20 mg/kg, Bayer HealthCare, Leverkusen, Germany) and breathed air [
13]. Imaging studies were performed with 3-3.5% sevoflurane and 1 l/min oxygen. All experiments were approved by the governmental review committee on animal care, and animals were kept under standard laboratory conditions.
Irradiation setup
The general experimental setup has been described previously [
6,
13,
14]. Briefly, for tumor irradiations, rats were placed in a special device for accurate positioning. Tumors of two different sizes were irradiated: Small tumors with a mean diameter at treatment of 10.5 mm (range 9.0 to 12.0 mm) were irradiated with carbon ions at the center of a single 20 mm SOBP (dose-averaged LET in the tumor: 75 keV/μm, range 64-96 keV/ μm) having a field diameter of 18 mm (90% isodose). Large tumors had a mean diameter at treatment of 16.5 mm (range 15.5 to 18.5 mm) and were irradiated either with carbon or oxygen ions (
16O-ions) at the center of a single 30 mm spread-out Bragg-peak (SOBP) (dose-averaged LET in the tumor: 65 keV/μm, range 52-91 keV/μm for carbon and 101 keV/μm, range 82-142 keV/μm for oxygen ions, respectively) having a field diameter of 25 mm (90% isodose). The range of the ions was adjusted by a polymethyl methacrylate (PMMA)-bolus of appropriate thickness. A second PMMA-plate was positioned behind the tumor.
Photon irradiations were performed under identical conditions using a single 6 MV beam of a linear accelerator (Siemens Artiste, Erlangen, Germany) and a PMMA-bolus in front and behind the tumor. Irradiation fields were produced with a cylindrical collimator for the small tumors (90% isodose: 15 mm) and with a multi-leaf collimator for the larger tumors (90% isodose: 24 mm), respectively.
Dose response studies
For small tumors, dose response experiments were performed for all three tumor-sublines (AT1, HI and H) with either 1, 2 or 6 fractions using increasing dose levels of either carbon ions or photons. In total, this experimental series contained 859 animals (374 for carbon ions and 405 for photons) including 80 sham-treated controls.
In a second series, large tumors of the HI-subline were treated with single doses under oxic as well as under hypoxic conditions using increasing dose levels of either carbon ions, oxygen ions or photons. Hypoxic conditions were realized by clamping the tumor-supplying artery 10 min before and during treatment. In total, this experimental series contained 280 animals (45/44 for carbon ions, 37/36 for oxygen ions and 47/48 for photons under oxic/hypoxic conditions); 23 sham-treated animals served as controls.
Following irradiation, tumor volume was measured twice weekly in both experimental series using a caliper. Primary endpoint was local tumor control at 300 days, defined as no detectable tumor regrowth. As the H-subline exhibited residual nodules, they were harvested and analyzed histologically for fibrosis (Hematoxylin/Eosin; H&E) and proliferation 5-bromo-2′-desoxyuridine (BrdU). A fibrotic pattern without proliferation was considered as secondary endpoint for locally controlled H-tumors.
For the primary endpoint, actuarial control rates were calculated and the logistic dose-response model was fitted using the maximum likelihood fitting procedure of the software STATISTICA (version 10.0, Statsoft Inc.,
www.statsoft.com) (see [
6] for details). For the secondary endpoint, no actuarial approach was required as surviving tumor cells were directly detected with a proliferation marker. For both endpoints, the RBE was calculated as the ratio of the TCD
50-values (dose at 50% tumor control probability) for photons and
12C-ions.
Positron-Emission-Tomography (PET)
Dynamic PET measurements with different radiofluorinated 2-nitroimidazole derivatives on a patient scanner (Biograph™ mCT, 128 S, Siemens, Erlangen, Germany) were performed to characterize the hypoxic status of small (0.8 ± 0.5 cm
3) and very large (4.4 ± 2.8 cm
3) H-, HI- and AT1-tumors prior to irradiation. For this, 15-53 MBq of [
18F]fluoromisonidazole ([
18F]FMISO) were injected into the tail vein of the animals and PET images were recorded over a time period of 60 min using a 28-frame protocol (for details, see [
16]). In total, this study included 30 tumors (10 AT1, 12 HI and 8 H).
Additional static measurements in 12 HI-tumors (diameter 16 mm) were performed on a PET/CT (Inveon Micro-PET/SPECT/CT, Siemens Medical Solutions, Knoxville, USA) before and 2, 9, and 21d after carbon ion or photon irradiation, respectively. In these measurements, 38-52 MBq [18F]fluoroazomycin arabinoside ([18F]FAZA) were administered into the tail vein and images were evaluated at 2 h post-injection.
T1-weighted dynamic contrast enhanced magnetic resonance imaging (DCE-MRI)
T1-weighted DCE-MRI measurements were performed in 17 small HI-tumors before as well as 3, 7, 14 and 21 days after single doses (isoeffective doses 18 Gy 12C-ions vs. 37 Gy photons and 37 Gy 12C-ions vs. 75 Gy photons, respectively) using a clinical 1.5 T MRI (Symphony, Siemens, Erlangen, Germany) together with an in-house built small animal coil. Irradiations were carried out either with carbon ions or photons using the same absorbed as well as the same RBE-weighted doses. Each animal had a sham-treated tumor on the contralateral side as internal control.
A T2-weighted turbo spin echo sequence (TR 3240 ms, TE 81 ms, slice thickness 1.5 mm, pixel size 0.35 mm) was used to position the image slice of the DCE-MRI measurement (TR 373 ms, TE 1,67 ms, slice thickness 4.5 mm, pixel size 0.99 mm) at the center of the tumor. 30 s after starting the DCE-MRI measurement, 0.1 mmol/kg Gd-DTPA (Magnevist
®, Bayer Healthcare Pharmaceuticals, Berlin, Germany) was injected into the tail vein. Tumor volume and the kinetics of the contrast agent were analyzed using the in-house software “Medical Imaging Interaction Toolkit” (dkfz, Heidelberg, Germany [
18,
19]).
Doppler-Ultrasound imaging
Ultrasound imaging was performed for 16 small HI-tumors from different dose-groups of the carbon ion and photon single fraction dose-response studies using a Power Doppler Ultrasound of 30 MHz and the RMV-704 transducer (slice thickness 200 μm, VEVO770, VisualSonics, Toronto, Canada). Animals were measured before and weekly or 2-weekly after irradiation.
Flow cytometric analysis
DNA-index and cell cycle distribution as well as potential surface stem cell marker of untreated tumors were identified with flow cytometry. Single cell suspensions obtained from frozen tissue were incubated with 2.1% citric acid including 0.5% tween 20 and shaking for 20 min at room temperature. Afterwards, 700 μl of the cell suspension supernatant were transferred into a vial, containing 4 ml phosphate buffer (Na
2HPO
4 7.1 g/100 ml dH
2O, pH 8.0) with 2 μg/ml 4′,6-diamidino-2-phenylindole (DAPI) and analyzed on a PAS II flow cytometer (PARTEC, Münster, Germany). For details see [
15]. Cryo-preserved tumor tissue was prepared as single cell suspension using isolation buffer. Afterwards cells were stained for CD24-PE, CD44-FITC, CD133-PE, CD326-FITC, cytokeratin 5/8 and 19 labelled with an Alexa Fluor 488 secondary antibody and measured in the Galaxy pro Flow cytometer (PARTEC, Münster, Germany). Flow cytometric analysis was confirmed with staining of cryo-preserved and FFPE tumor tissue (for details, see [
15]).
Tumor induction analysis via limiting dilution assay
CD24+/CD45− and CD24−/CD45− untreated AT1-, HI- and H-tumor cells were enriched and sorted (FACS Aria, BD, Heidelberg, Germany) from freshly prepared tumor tissue. 500.000 CD24−/CD45− cells and various cell numbers between 10 to 200.000 CD24+/CD45− cells were injected in a Matrigel suspension (BD, Heidelberg, Germany) subcutaneously into the right and left thigh of animals. The tumor induction was monitored for 300 days.
Histological and molecular studies
Before and at several time points after single dose irradiation (8 h, 18 h, 72 h, 7 d, 14 d, 21 d) tumor tissue was cryo-preserved, cut into 7 μm cryo-sections (Mikrom HM560, Thermo Fisher Scientific, Dreieich, Germany) and fixed in methanol/acetone for immunofluorescence stainings. Alternatively, formalin-fixed paraffin-embedded (FFPE) tissue was processed with the Microtom (Microm STS Section-Transfer-System, Thermo Fisher Scientific, Dreieich, Germany) and used for H&E staining.
To analyze the secondary endpoint in the H-tumor, cryo-preserved sections of the residual nodules were stained for proliferating cells using a BrdU antibody (Roche Diagnostics, Mannheim, Germany), which was injected intraperitoneally (100 mg/kg, Sigma-Aldrich, Taufkirchen, Germany) prior to sacrificing the animal. Vessel architecture (CD31), pericytes (smooth muscle actin) and perfusion as well as hypoxic fraction (pimonidazole) was stained using published protocols [
6,
16].
For gene expression analysis, HI-tumor tissue was minced in liquid nitrogen using a Potter S with a Teflon tube extruder (B. Braun, Melsungen, Germany) and RNA was extracted immediately with the NucleoSpin® RNA L Kit (Macherey-Nagel, Düren, Germany). RNA-quantity (NanoDrop® ND-1000 Peqlab, Erlangen, Germany) and quality (Agilent RNA 6000 Nano Kit and Agilent Bioanalyzer 2100, Agilent, Waldbronn, Germany) were verified. Gene expression profiling was performed according to the manufacturers’ protocol (Agilent) using the Whole Rat Genome Kit 4x44k, Low Input Quick Amp Labeling Kit One-Color, gene expression hybridization Kit, RNA-Spike In Kit One-Color, SSPE washing buffer and stabilization and drying solutions.
Discussion
Preclinical studies in normal tissues are preferentially performed to evaluate potential side effects of carbon ions and to validate RBE-models. In contrast, tumor experiments aim to decipher biological factors, which influence the tumor response differently for photons and ion beams, and to identify, which tumor entities might benefit most likely from high-LET irradiations. In this context, a systematic study was initiated to quantitatively assess the treatment response of three different tumor lines to photons and 12C-ions using a local tumor control assay.
In summary, the following clinically relevant results (Fig.
1) were obtained: (i) For photons, a considerably heterogeneous treatment response was found, documented by a broad range of TCD
50-values for the three tumor-sublines. (ii) For carbon ions, the respective dose-response curves were located much closer to each other. (iii) In addition, the slope of the dose-response curve for each tumor subline was comparable or steeper for
12C-ions than for photons, and (iv) the resulting RBE increased with tumor grading (i.e. H vs. HI vs. AT1). This increase of RBE predominantly results from a rise of TCD
50 with tumor grading in photon treatments while the variation of the treatment response to
12C-ions is only small. This supports the conclusion that certain tumor-associated factors might be responsible to render tumors more resistant to photons than to
12C-ions. Clearly, these factors are depending on tumor grade. Moreover, also intra-tumoral heterogeneity seems to possess minor impact as documented by the increased slope of the dose-response curve of
12C-ions for the very heterogeneous HI-subline as compared to the respective curve for photons. These results allow the conclusion that the response to
12C-ions is also less dependent on intra-tumor heterogeneity. Regarding the effectiveness, the highest RBE of
12C-ions can be expected for undifferentiated tumors, showing the highest resistance against photon irradiations. A first report on prostate cancer patients in Japan confirmed our results showing very high tumor control rates with reduced toxicity and a comparable 5-year local control rate for carbon ions between low, intermediate and high-risk prostate cancer patients [
20].
From a technical point of view, assessment of local control was most difficult in the slow-growing and well differentiated H-tumor because of frequently occurring residual tissue nodules at the end of the follow-up time. This problem was solved by additional histological analysis using lack of proliferative activity within these nodules as secondary endpoint. Interestingly, as the corresponding TCD
50-values increased for both, photons and
12C-ions, there was only a minor difference in RBE and the above conclusion remains unchanged [
6].
While this report refers to single dose irradiations only, the identical study was conducted for 2 and 6 fractions, already published for the AT1-tumor [
14]. Although still under evaluation for the HI- and the H-tumor, there is a clear trend that fractionation increases the TCD
50-values in all three tumor cell lines and both irradiation modalities. Again, the shift is larger for photons than for carbon ions, indicating an increasing RBE with decreasing dose per fraction and decreasing differentiation status. The highest RBE for 6 daily fractions (2.67 ± 0.15) was found for the anaplastic AT1-subline [
14]. Details on the complete fractionated studies, including the dose dependence of the RBE and the determination of α/β-ratios will be published separately. An interesting side observation of the published study [
14] was that in the fast growing AT1-tumor the metastatic rate increased, when the number of fractions raised from 2 to 6. Yet, at least for the given treatment schedules (1, 2 and 6 fractions) the results were not dependent on radiation quality [
21].
There is significant evidence in the literature that resistance to photon therapy is associated with both, intrinsic cellular factors conditioned by the evolutionary capacity of cancer phenotypes as well as epigenetic parameters, or the temporal and spatial heterogeneity of the tumor microenvironment caused by structural abnormalities and density of tumor microvessels, dysfunctional blood flow, low pH leading to either chronic or acute hypoxic conditions [
22‐
25].
For further clarification, a detailed structural and functional characterization of all three tumor lines prior to irradiation was undertaken. As highly aneuploidic subpopulations were present in all three tumor lines, the ploidic status was not considered as a relevant tumor-associated intrinsic factor for the differential radiation response [
15]. In contrast, differences were detected with respect to putative cancer stem-like cells characterized as CD24
+/CD45
− cells, which were positively tested for the ability to form new tumors in a functional limiting dilution assays (Glowa et al., unpublished data). The fact that stem-cell properties were detected in H- and HI- but not in AT1-tumors needs further analysis which is presently ongoing.
Dramatic differences were found with respect to the structure and quality of the tumor vascularization and in correlation with the tumor microenvironment, inasmuch as a range of differently oxygenated tumors were detected, with the highest hypoxic fraction in the poorly differentiated AT1-tumors and nearly no detectable hypoxia in the well differentiated H-tumors. These results are in line with a previous report on the same tumor model using TOLD-MRI [
10]. In addition, the [
18F]FMISO-TAC-curves in PET were extremely variable between the three tumor sublines indicating also large differences in perfusion [
5]. Thus, the investigated tumor-sublines represent a wide range of differently oxygenated tumors allowing dedicated investigation of the role of oxygenation on the radiation response.
To further exploit the role of
12C-ions to overcome hypoxia, which is presumably the most important resistance factor in photon therapy, a four-armed dose-response study was performed. Larger moderately differentiated HI-tumors were selected as model tumors because of its proven hypoxia and its extensive heterogeneous treatment response to photons. For larger HI-tumors treated with photons either under ambient or complete hypoxic (clamping) conditions, the detected oxygen enhancement ratio (OER) was clearly below 2, which is in line with previously published in vivo studies [
26,
27]. Generally, OERs for single dose irradiations in solid tumors under clamping conditions were found to be lower than in cell culture studies [
3,
28], presumably because tumor cells in intact tissues are not only impacted by the intrinsic cellular radioresistance but also by additional factors like cell to cell communication, bystander effects, and the immune response. Moreover, clamping does not only create a transient severe hypoxic state but also reduces the nutrient supply and induces a strong extracellular pressure to the capillaries which might increase secondary tumor cell death and therefore masks the potentially higher OER to some degree. When
12C-ions (dose average LET: 65 keV/μm) were applied under identical experimental conditions an up to 15% lower OER was found for larger HI-tumors. The detected decrease of OER for
12C-ions is relevant and if confirmed in patients would increase effectiveness dramatically. With this respect, the only available study, which compares the impact of tumor oxygenation for
12C-ions and photons in patients, is inconclusive [
29].
A detailed comparison with the previous dose-response experiments for the small tumors, however, turned out to be difficult as the TCD50-values after photon and 12C-ion irradiations under non-clamping conditions were found to be substantially higher as compared to the previously investigated small tumors. This suggests that larger tumors are not only associated with an increased number of tumor cells but also that volume-dependent alterations of the tumor micromilieu might play a role. To investigate this hypothesis in more detail, the clamping experiments are currently repeated for the small tumors within a new project and a comparison of the response of small and large tumors will be published separately when the results are available.
Radioresistance of tumors due to hypoxia is clinically of highest relevance as oxic tumors have a much higher disease-free survival than hypoxic tumors, as has been shown in head and neck cancer patients [
30]. Therefore, the observed reduction of the OER for
12C-ions is a very important finding for the treatment of hypoxic tumors. In a first patient cohort treated with carbon ions, Japanese colleagues verified a smaller OER of
12C-ions in uterine cancer [
29] and our findings in the experimental prostate carcinomas confirm this, however, further analyses are necessary. Although the obtained promising OERs for
12C-ions might in principal be used to overcome radioresistance evoked by severe hypoxia, the dependence of OER on LET is still an open question. In vitro the OER for high LET irradiations decreases with increasing LET and is expected to be negligible at LETs higher than 200 keV/μm [
31]. Our preliminary results based on dose-response studies with oxygen ions (dose average LET: 101 keV/μm) using the same tumor model also indicates a small OER near to 1.
Finally, structural and functional assessments were performed in HI-tumors to decipher some of the biological mechanisms, responsible for the differential effects of
12C-ions and photons. In-house synthetized [
18F]FAZA in combination with static PET measurements in a dedicated small animal scanner (Inveon Micro-PET/SPECT/CT (Siemens Medical Solutions, Knoxville, USA)) has been established in larger HI-tumors. A significant tracer-uptake prior to treatment followed by a clear reduction 1 week after irradiation was found for photons as well as for
12C-ions in a first pilot study. The hypoxia imaging tracer [
18F]FAZA is a well-established alternative to the first generation tracer [
18F]FMISO and is known to correlate well with both, autoradiography and the hypoxia marker pimonidazole [
32]. Yet, results so far are reported to be ambivalent. No significant general reoxygenation was seen for SiHa cervix tumors in mice after fractionated irradiations with 10 or 25 Gy photons [
32], while reoxygenation has been shown after 2 weeks of fractionated radiotherapy for patients with head and neck cancer in some but not in all cases [
33]. Radiation-induced reoxygenation seems to depend on tumor type and on the intrinsic characteristics of the individual tumor. Tumor cell inactivation, tissue shrinkage, vessel damage and altered perfusion are biological factors associated with oxygenation changes after irradiation. A very striking observation was the extremely fast emerging of vascular disruptions already 18 h after single doses of carbon ions, while similar changes were delayed after photon irradiations. Nevertheless, a clear correlation between vessel integrity and hypoxia or reoxygenation is currently missing.
In spite of existing vascular structures, oxygen delivery to neoplastic and stromal cells is frequently reduced or even abolished by increased vessel distances, severe structural abnormalities of tumor microvessels, disturbed microcirculation and increased interstitial pressure. This can lead to false negative results in PET measurements as the tracer may not reach the hypoxic regions. To independently assess functional microenvironmental disturbations, measurements with doppler ultrasound as well as DCE-MRI were performed. Ultrasound measurements revealed a high blood flow followed by a rapid and dramatic decrease after carbon ions and later a steady state in the first 4 weeks after irradiation. Besides, this initial effect no other significant variation was detected between the two radiation modalities as well as for different dose levels. A further refinement of these results is expected from photoacoustic imaging [
34], which allows assessing the oxygen saturation of tumor vessels based on optical detection of oxy- and deoxyhemoglobin. Similar to the ultrasound measurements, preliminary results of DCE-MRI revealed a faster and higher contrast enhancement after single doses of
12C-ions as compared to photons, which is in line with the more prominent vessel damage observed on the histological level. This first assessment is based on a qualitative rather than quantitative data analysis and a more detailed investigation using pharmacokinetic modeling to extract perfusion-related tissue parameters is ongoing.