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Dose painting is the prescription of a non-uniform radiation dose distribution to the target volume based on functional or molecular images shown to be indicative of the local risk of relapse. Two prototypical strategies for implementing this novel paradigm in radiation oncology are reviewed: sub-volume boosting and dose painting by numbers. Sub-volume boosting involves the selection of a “target within the target”, defined by image segmentation on the basis of the quantitative information in the image or morphologically, and this is related to image based target volume selection and delineation. Dose painting by numbers is a voxel-level prescription of dose based on a mathematical transformation of the image intensity of individual pixels. Quantitative use of images to decide both where and how to delivery radiation therapy in an individual case is also called theragnostic imaging. Dose painting targets are imaging surrogates for cellular or microenvironmental phenotypes associated with poor radioresponsiveness. In this review, the focus is on positron emission tomography (PET) tracers: FDG and choline as surrogates for tumor burden, FLT as a surrogate for proliferation (or cellular growth fraction) and hypoxia sensitive tracers including FMISO, EF3, EF5 and Cu-ATSM as surrogates of cellular hypoxia. Research advances supporting the clinico-biological rationale for dose painting are reviewed as are studies of the technical feasibility of optimizing and delivering realistic dose painted radiation therapy plans. Challenges and research priorities in this exciting research field are defined and a possible design for a randomized clinical trial of dose painting is presented.
Imaging-based dose painting, the prescription and delivery of a non-uniform dose to the clinical target volume (CTV) is a novel paradigm for prescribing radiation therapy1–3. The basic idea is to replace, completely or in part, the morphologically or anatomically defined target volume with a map of the spatial distribution of a specific tumor phenotype that is hypothesized or has been shown to be related to local tumor control after radiotherapy. A dose prescription function is then used to transform this map into a map of prescribed doses that can be used as input to an inverse planning optimizer. Two prototypical strategies have been considered in the literature: sub-volume boosting1, where an imaging-defined discrete volume is given an additional ‘boost’ radiation dose (in which case the prescription function takes only two discrete dose values), or dose painting by numbers2, where a dose is prescribed at the voxel level, and it is left for the dose plan optimizer to arrive at a physically deliverable dose distribution that approximates the desired dose distribution. In the latter case, the prescription function maps a range of image intensities onto a range of doses. Hybrids between the two strategies use a series of nested volumes, often about five or so, with a prescribed dose assigned to each of them.
Theragnostic imaging2 is the application of the quantitative information in biomedical images to produce a prescribed dose map, i.e. not just a map of where to treat but ideally also of the local dose fractionation that will optimize tumor control under specified normal-tissue constraints. Dose painting by numbers relies directly on theragnostic imaging whereas sub-volume boosting could include morphologic as well as image intensities in the definition of the boost volume. However, in practice there is a continuum of dose prescription strategies ranging between these two ideal cases. In this review, the emphasis will be on theragnostic imaging but large parts of the discussion will apply to the case of sub-volume boosting as well.
Throughout the first half of the history of cancer radiation therapy, the dosimetric challenge was to deliver a sufficiently high dose to the distal aspect of the tumor seen from the direction of the beam. With the advent of megavoltage radiation therapy technology soon after World War II, parallel opposing fields or non-collinear wedged fields allowed delivery of a near-uniform dose to a fairly large target volume. Target volume selection was generally based on structures identifiable on normal x-rays or during fluoroscopy, often bony landmarks or even on the patient’s external anatomy. These target regions were typically rationalized as “…having a high risk of microscopic spread of the disease” and in general no attempt was made to directly visualize the tumor mass. What this meant in effect was that margins around the macroscopic tumor volume were liberal, set-up accuracy and motion management were less of a concern but this relative robustness came at a price: it was difficult to push the prescribed dose much above 60 Gy in 2 Gy fractions without excessive toxicity because of the large volume of normal tissue irradiated.
The development of computed tomography provided an unprecedented capability to visualize the gross tumor volume and this gave the opportunity to test the so-called 3D hypothesis, namely that increasing the conformality between the high-dose and the target volume, it would be possible to increase local tumor control without increasing (late) toxicity4. This led to a flurry of phase I, II and III radiation dose escalation trials. The broad conclusion of these have been that dose can be pushed higher to some extent but that at least for some late endpoints there has been an associated increase in toxicity as well.
This raises the question whether more advanced dose escalation strategies are more likely to provide a therapeutic gain? One compelling clinico-biological hypothesis is the dose painting hypothesis: 1) local recurrences arise from cellular or micro-environmental niches that are (relatively) resistant at the radiation dose level that can safely be routinely delivered using a uniform dose distribution; 2) molecular and functional imaging will allow spatio-temporal mapping of these regions of relative radioresistance; and 3) advances in radiation therapy planning and delivery technologies facilitates delivery of a graded boost to such regions which in turn should lead to improved local tumor control with acceptable side effects.
Support for the dose painting hypothesis comes in part from mathematical modeling studies. It has been shown that for a fixed integral dose to a tumor with a uniform spatial radiosensitivity distribution, delivering a uniform dose of radiation will maximize the tumor control probability5–7. However, for a non-uniform radiosensitivity distribution, a uniform dose distribution is inferior to a distribution that delivers a relatively higher proportion of the integral tumor dose to the more resistant regions of the tumor 8, i.e. by dose painting. Numerous modeling studies, evaluating dose painting strategies under various radiobiological assumptions, have consistently shown large gains in tumor control probability, in the order of 50% or more3, 8–13. It should be emphasized that none of these modeling exercises are assumption free. Proving a clinical gain from dose painting will ultimately require evidence from clinical trials. However, there is a large body of experimental and clinical data providing indirect support for the dose painting hypothesis and thereby informing the design and encouraging the conduct of dose painting trials. Also, advances in pre-clinical and theoretical research into dose painting provide an increasingly firm base for rational design of clinical trials that are likely to be informative once they are completed.
Validation of a dose painting target does not necessarily require a mechanistic understanding of the relationship between dose response and expression of the target. It is a sufficient – and from a bioethical standpoint probably also a necessary – condition that an empirical relationship has been demonstrated between target expression and worse local outcome of radiation therapy. The current interest focuses on three evidence based causes of radiation therapy failure in the clinic: tumor burden, tumor cell proliferation and hypoxia (figure 1).
Clinical outcome data shows the importance of volume of cancer as a driver of local outcome after radiation therapy. It was hypothesized already in the 1970’s that microscopic disease could be sterilized with a lower dose; the rule of thumb proposed by Fletcher was that roughly 2/3 of the dose needed to control gross disease would suffice14. At the other end of the scale, bulky disease might need a radiation boost dose of 10 to 15 Gy in order to produce a reasonable tumor control probability. The volume of cancer hypothesis gave rise to boost field techniques, now an integral part of radiation therapy practice, for instance in post-operative radiotherapy for breast cancer, or elective irradiation of regions with suspected sub-clinical disease to a lower dose level, for example irradiation of the clinically negative neck in patients with squamous cell carcinoma of the head and neck.
Until recently, CT and MRI, were the only imaging modalities used to delineate the tumor burden or Gross Tumor Volume (GTV) for radiotherapy planning purposes. With the rising availability of PET scanners, more and more studies have been conducted to assess the added value of functional imaging in radiotherapy planning. Among the available tracers for clinical use, FDG is by far the most widely used. Its availability, its high signal-to-background ratio (SBR) and the wide clinical experience accumulated over the years make FDG an attractive tracer for clinical research compared to the other available PET tracers. FDG uptake is commonly considered a good surrogate for tumor cell burden, although various parameters influence FDG uptake and retention, such as the rate of glycolysis, tumor perfusion, proliferation, inflammation and hypoxia15, 16.
Encouraging data support the use of FDG-PET in target definition and dose painting. In HNSCC, methodological studies have demonstrated that the use of pre-radiotherapy FDG-PET led to a better estimate of the true tumor volume, as defined by the pathological specimens, compared with CT and MRI17, 18. Interestingly, when validated segmentation tools were used, the mean FDG-PET-based GTV was consistently smaller than the GTV defined from morphological imaging in all investigated tumor locations and at all time points during radiotherapy, see figure 219–21. This finding probably reflects the limited soft tissue discrimination of morphological imaging. The reduction of target volumes defined from FDG-PET translated into significant normal tissue sparing with either 3D-CRT or helical IMRT in “proof of concept” HNSCC studies18, 20. This effect was even more impressive when FDG-PET was performed weekly during treatment to allow for dose adaptation as shown in figure 3.
FDG-PET has been used as a dose painting target for sub-volume boosting in a phase I study in locally advanced HNSCC22. This approach was proven to be feasible and safe. De Neve’s group has also demonstrated that FDG avidity could be used as a target for dose painting by numbers, with a clear dosimetric advantage relative to sub-volume boosting due to a better capability to create peak-dose regions inside the planning target volume23.
Similar encouraging data have also been reported for non-small-cell lung cancer (NSCLC) where studies have found that FDG-PET volumes were smaller in general than CT-defined GTVs, thus reducing the incidental radiation exposure of the healthy lungs and the esophagus sufficiently to allow a radiation dose escalation24, 25. FDG-PET scans also help in tumor delineation in the presence of atelectasis or intra-tumor heterogeneity, and has shown a remarkably good correlation with surgical pathology and patient data26–28.
Limited data are available on GTV delineation and dose adaptation with metabolic tracers other than FDG. In the brain, amino-acids such as methionine (MET) and fluoroethyl-L-tyrosine (FET) have been used for GTV delineation in gliomas and for the differentiation between treatment related changes (pseudo-progression or pseudo-regression) and residual/recurrent tumor29. Some data support the use of MET and (DOTATOC) as PET tracers for GTV delineation in meningiomas and glomus tumours29. Yet, no data are available on dose adaptation in these tumors. Limited data are available on the use of 11C-choline-PET for volume selection and delineation in adenocarcinoma of the prostate. Because of its low sensitivity, choline-PET has a limited role in routine clinical practice for defining target volumes in patients with intra-prostatic lesions or with metastatic/recurrent disease30. Yet, there are promising preliminary data on the use of choline-PET for target selection and as a means of guiding high dose radiation therapy for recurring nodal disease31.
A modeling study found that using choline-PET to boost the radiation dose within the prostate resulted in only a modest increase in local control32. This modest gain stems from the lack of knowledge of the exact PET sensitivity as well as the fractionation sensitivity, quantified by the α/β ratio, of prostate cancer33.
Tumor cell proliferation is a well established cause of local failure after radiation therapy for many tumor types, most convincingly supported by the evidence from randomized controlled trials of a benefit from accelerated radiation therapy in head and neck squamous cell carcinoma34 and non-small cell lung cancer35. It is likely that patient-to-patient variability in accelerated proliferation seen after cytotoxic insults explains at least some of the variability in treatment outcome seen in the clinic 36, 37. Intensive research and development has gone into developing 11C-labelled thymidine – initially meant for use as an in vivo parallel to the classical tritiated thymidine assay – and several radiolabelled halogenated pyrimidine deoxynucleosides as PET imaging tracers of DNA synthesis. However, rapid biodegradation of these compounds leads to radiolabelled metabolites in the blood which complicates image analysis and interpretation38, 39. Most current interest centers on another radiofluorinated thymidine analog: 3'-Deoxy-3'-[18F]fluorothymidine (FLT). FLT is a terminator of the growing DNA chain and is therefore only incorporated into DNA during synthesis to a very limited extent. However, it is retained in cells after phosphorylation by the thymidine kinase 1 (TK1) enzyme40. TK1 is differentially expressed in the late G1 and S phases but is practically absent in G0 cells41. Thus, although FLT is often referred to as a “proliferation tracer”, it actually provides a map of the local growth fraction of tumor cells. Consistent with this, the SUV of FLT has been shown in several clinical studies to correlate with the cell-cycle specific Ki-67 index as assessed by immunohistochemistry in biopsies42–48. One negative study failed to detect such a correlation in 8 patients with esophageal cancer49. However, in addition to the issue of limited statistical power, the range of Ki-67 indices in the tumors included in this particular study seems atypically narrow and concentrated in the upper end of the range seen in larger series of patients with this disease50. In addition to the data showing that FLT is an imaging surrogate for the tumor cell growth fraction, there are data from animal studies demonstrating sensitivity of FLT PET to detect the growth inhibitory response induced by molecular targeted agents, cytotoxic drugs or ionizing radiation in mouse tumor models (for a recent review see Barwick et al.51), and of androgen ablation in a hormone-sensitive murine prostate tumor model52.
FLT PET scans at baseline and 2 weeks into fractionated radiotherapy have been used to define targets for sub-volume boosting in a recent radiation therapy planning study53. In the absence of direct clinical evidence for an association between these regions and a subsequent local treatment failure, the biological rationale for this boost strategy is still not completely clear. Part of the concern arises from our current understanding of the biology of accelerated proliferation. There is emerging evidence from experimental and clinical studies that accelerated tumor cell repopulation is an actively-controlled biological response to a trauma rather than a simple consequence of high proliferative activity at the onset of therapy. A study by Begg et al.54 of 476 patients with head and neck squamous cell carcinoma (HNSCC) showed that pre-treatment cell kinetics was not predictive of outcome of fractionated radiation therapy. Furthermore, a separate study of the pre-treatment tumor cell growth fraction, assessed by the Ki-67 labeling index from immunohistochemistry (IHC) on biopsies from 402 patients with HNSCC, found this to be inversely associated with a benefit from randomized allocation to strongly accelerated radiation therapy55. These observations discourage the use of proliferation at baseline as a theragnostic target for dose painting. Redefining the boost volume after two weeks of radiation therapy may help overcome this issue, but it is not clear if this is a valid strategy either.
In contrast to simple cell kinetics at baseline, strong expression of the epidermal growth factor receptor (EGFR) was statistically significantly associated with a favorable outcome after randomization to strongly accelerated RT in 304 patients with HNSCC56. This finding is consistent with data from the Danish Head and Neck Cancer study group57, 58, although these studies did not rely exclusively on randomized treatment allocation. Further evidence for the central role of the EGF signaling pathway in the response of HNSCC to fractionated RT comes from the randomized controlled trial showing a clinical benefit from combining radiation therapy with cetuximab, a monoclonal antibody against the EGF receptor59.
Synthesizing all of the above evidence, two promising avenues for proliferation-targeting dose painting are being pursued. One is to assess the proliferative response to therapy rather than proliferation at baseline as a dose painting target. However, serial FLT scans during a course of therapy should be interpreted with some care. This is in part because of the competition between cell killing and (compensatory) proliferation and in part because FLT uptake requires progression in the cell cycle. Studies have demonstrated that inhibition of cell cycle progression prevents FLT uptake40 and that FLT uptake in vivo is reduced 24 and 48 hours after single doses of radiation of 8 to 20 Gy60, 61, consistent with the well-established mitotic delay after irradiation. While a shorter delay is to be expected after clinically relevant fraction sizes, the mitotic delay could cause a biased assessment of the tumor cell growth fraction if measured shortly after a dose of radiation. The other avenue is direct PET imaging of a major proliferative response pathway, the obvious prime candidate being the EGFR pathway, at least in case of HNSCC where a substantial body of evidence shows that this is a master switch for accelerated repopulation. EGFR expression can be PET imaged using radiolabelled tyrosine kinase inhibitors or antibodies against the extra-cellular domain of the receptor62. Also of potential interest in a radiation oncology context is the emerging possibility63 to image constitutively active mutant EGFR using 124I-labelled chimeric antibodies that bind to an EGFR epitope exposed only on mutant, overexpressed or activated forms of the receptor.
Hypoxia plays a double role as a consequence and as a driver of malignant progression64. As early as 1936, JC Mottram at Mount Vernon Hospital in Northwood, England demonstrated that tumor hypoxia is associated with a poor response to radiation therapy65. Large clinical studies have confirmed that hypoxia, assessed by polarographic micro-electrode measurements of partial oxygen pressure or assessed by immunohistochemistry of hypoxia-related endogenous biomarkers in diagnostic biopsies, is associated with malignant progression and a poor outcome after therapy. The strongest evidence exists for squamous cell carcinoma of the head and neck66, 67, but there is also evidence for several other tumor sites68 in particular prostate69–72 and uterine cervix73, 74.
A number of PET tracers have been developed as hypoxia surrogates for imaging and several new ones are in various stages of preclinical or clinical development75, 76. The two tracers with most extensive clinical experience are [18F]fluoromisonidazole (FMISO) and 60Cu-, 61Cu- or 64Cu-labeled Copper(II) diacetyl-di(N4-methylthiosemicarbazone) (Cu-ATSM). The overall conclusion from about a dozen correlative clinical studies is that there is a statistically significant association between PET-assessed hypoxia at baseline, i.e. before treatment start, and tumor outcome after radiation therapy13.
Development of new hypoxia sensitive tracers is partly driven by mechanistic considerations of uptake and retention mechanisms. Like FMISO, several of these tracers are [18F]-labeled nitroimidazoles such as FETNIM ([18F]Fluoroerythronitroimidazole), EF5 (2-(2-nitro-1H-imidazol-1-yl)-N-(2,2,3,3,3-[18F]pentafluoropropyl)acetamide), EF3 (2-(2-Nitroimidazol-1H-yl)-N-(3,3,3-trifluoropropyl)acetamide) and [18F]Fluoroazomycinarabinofuranoside (FAZA). There are potentially interesting differences between these tracers77, as an example FETNIM and FMISO are more hydrophilic than EF3 or EF5; and there is more non-hypoxia related bioreduction of FMISO compared with EF3. Some studies in rodent tumor models also show differences from one tumor type to another as well as an influence of the interval from administration of the tracer to performing the PET scan. It is not clear to what extent these tracers will have clinically relevant differences in performance when used for PET imaging of human tumors in a population of patients. It is likely that there is no consistently superior hypoxia tracer and it is even possible that some of these tracers could provide complementary information. However, in our view, the potential utility of various tracers for defining dose painting targets can only be established from clinical correlative studies, and it is time to conduct such studies to bring the field forward.
As discussed above, FDG may be a valid dose painting target in itself, but it is not a good imaging surrogate of hypoxia. Clinical studies have found no or very limited correlations between FDG uptake and various PET hypoxia tracers78 and this is consistent with several small animal tumor studies showing a lack of co-localization between FDG on one hand and Cu-ATSM79, FAZA80 or EF381 on the other, see figure 4.
One concern in the development of hypoxia directed dose painting is the spatio-temporal stability of the PET hypoxia map. Already the pioneering FMISO PET study by Janet Rasey and colleagues82, 83 showed PET detected reoxygenation in some but not all tumors investigated. It remains a research question whether the initially hypoxic region should be boosted or whether the plan should be adapted to change in hypoxic regions. Spatial variability has also been demonstrated in a subset of HNSCC tumors in scan-rescan studies conducted before the onset of radiation therapy84. However, Lee et al.85 found that boosting the dose to the hypoxic sub-volume on one scan would still lead to a substantial additional dose to the sub-volume that was found to be hypoxic on the repeat scan.
The magnitude of the required dose to control disease in PET hypoxic regions is not clear. Simplistic back-of-an-envelope estimates based on in vitro oxygen enhancement ratios (OER) are likely to be gross overestimates of the dose required in human tumors. Interestingly in this context, Lee et al.86 found excellent loco-regional tumor control in a series of 20 patients after standard chemoradiation therapy despite the presence of PET detected hypoxia in the primary tumor or in positive nodes at baseline or during fractionated therapy in 18 of these cases.
Adaptive dose painting aims to use imaging as a biomarker of (local) response, typically derived from repeat imaging during radiotherapy compared with a scan at baseline, i.e. before treatment commences. This response map is then used as the input map to adapt the delineated target volume or, in case of dose painting by numbers, the dose distribution so that relatively more dose is applied in regions showing poor response.
A few studies have been conducted so far on FDG-PET-based adaptive treatment in NSCLC. A pilot study of 14 cases reported that an FDG PET scan performed at mid-treatment showed a 44% reduction in GTV in 6 compared with a reduction of 26% on CT87. An FDG-PET-based boost dose of 30–102 Gy (mean 58 Gy), or alternatively, a reduction in normal tissue complication probability (NTCP) of 0.4–3% (mean 2%), was deemed clinically feasible in 5 of these 6 patients. However, in a similarly designed study, Gillham et al.88 concluded that despite tumor shrinkage determined by FDG-PET/CT during treatment, the adaptive-targeting strategy tested in their study would only allow a modest dose escalation.
Response-adaptive dose painting immediately raises the question: When to image? With FDG in HNSCC the signal is weak after 30–40 Gy of chemo-radiation and is not visible after 50 Gy. Similar observations have been made for other tracers. It is likely that useful differentiation according to patient-to-patient variability in response to therapy will have to be assessed after one to three weeks of treatment.
Even after one week of therapy, the PET signal would conceivably mainly reflect doomed cells! No imaging modality can currently distinguish between viable cells that are doomed or not. However, as mentioned above, validation of a dose painting target will come from empirical, clinical evidence rather than from mechanistic considerations also in the case of adaptive dose painting strategies.
The simplest, reasonable, voxel-based prescription function is a linear interpolation between a minimum dose, Dmin, and a maximum dose Dmax, as the voxel image intensity, I, varies between its lower and upper bound, Imin and Imax within the target volume9, 89:
A slightly different formulation was proposed by Flynn et al.90 who proposed a strategy where a voxel-based boost dose was applied to an anatomically defined target sub-volume. The boost was added on top of a uniform dose to the clinical target volume, DCTV such that the mean boost dose was kept equal to a pre-set uniform boost dose, Dboost. Using the same notation as above:
This principle for dose prescription is known as dose redistribution10. Flynn’s formulation still assumes proportionality between image intensity and (boost) dose, but the advantage is that keeping Dboost constant produces a ‘natural’ control dose plan for a hypothetical trial, delivering a uniform boost of the same size but without image guided dose painting. Also Alber and colleagues considered a linear transformation of the image intensity into a prescribed dose but with slightly different constraints on the prescribed dose91.
The optimal mathematical form of the prescription function is unknown92 and will depend on the specific tracer. Ideally it should be estimated empirically from radiation dose-response data as a function of tracer uptake level. Several authors have tried to incorporate mechanistic elements in the prescription function, for example Thorwarth et al.93 who modified the radiosensitivity parameter in a linear-quadratic dose-survival curve according to the retention of FMISO; or Søvik et al.10 who also used an underlying linear quadratic model of cell survival with direct scaling of the a and b parameters using an analytical, approximate, description of the OER.
While these semi-mechanistic prescription functions may represent useful starting points for empirical estimation of the optimal prescription function, they are obviously over-simplifications of the more complex multi-factorial biology underlying local radioresponsiveness at the voxel level.
Numerous planning studies have shown that sub-volume boosting or multi-level dose painting plans can be optimized using commercial software65 and that dose-painting-by-numbers plans can be optimized using research software90, 91, 94. The technical feasibility of optimizing linac based IMRT plans9, 65, 93, 95, 96, helical90, 97 and arc photon98 IMRT plans as well as intensity modulated proton therapy (IMPT) plans90, 97 has been documented. Several of these studies have compared the relative merits of various delivery platforms, and – expectedly – delivery technologies with a high number of degrees of freedom and with intrinsically high spatial resolution do better. Overall, it seems fair to say that success in meeting a given set of dose painting plan objectives is less technology dependent than one would have suspected. IMPT plans may show an advantage for certain configurations of target volumes and critical normal structures, again as one would intuitively expect.
Relatively few feasibility studies have taken the crucial step from planning to delivery of realistic dose painting. However, phantom studies by Kissick et al.99 have produced encouraging results. Kissick used film dosimetry on a 4D-motion anthropomorphic lung phantom to test the feasibility of helical tomotherapy delivery of a clinically realistic dose painting plan. The authors concluded that delivery was feasible with a relatively modest degradation of the gamma map compared to delivery of the same plan to a static phantom.
Molecular-imaging guided dose painting is a compelling concept. Based on current research, modulation of the radiation dose distribution according to local phenotypic or microenvironmental variations in an individual tumor is likely to be technically feasible at a level of spatial resolution comparable to the voxel size in clinical PET images. In view of the complexity of dose painting strategies clinical correlative studies and early clinical trials should be initiated and conducted in parallel with continued pre-clinical research.
What would clinical trials of dose painting look like? Probably not very different from other comparative effectiveness trials! Phase I/II studies of dose painting by FDG defined sub-volume boosting have already been published for patients with HNSCC22 and further early trials are in progress in this disease and in NSCLC. Pre-operative radiation therapy for rectal adenocarcinoma is another interesting indication where pathological response could be used as an early surrogate endpoint for tumor effect. Also recurrent rectal carcinomas, among many other tumor sites and histologies, have been considered in this context100. The obvious attraction of FDG-based dose painting is the wide availability and the extensive clinical experience with this tracer.
The boost dose escalation trial from De Neve’s group22, enrolled 41 patients with HNSCC between 2003 and 2005, 23 at dose level I (total physical dose of 72.5 Gy in 32 fractions to the FDG-PET positive volume), and 18 at dose level II (77.5 Gy in 32 fractions to the PET positive volume). With a median follow-up for surviving patients of 14 months, two cases of dose-limiting Grade 4 toxicity occurred at dose level I. A treatment-related death at dose level II led to termination of the trial. Actuarial 1-year local control was 85% and 87% at the two dose levels. However, 4 of the 9 recurrences seen at the time of analysis occurred in the FDG-defined boost region, raising the possibility that dose should be escalated further if possible without exceeding the acceptable toxicity.
Once the feasibility and safety of the dose painting strategy is established, a phase III trial should be launched with time to loco-regional progression and late toxicity as joint primary endpoints (Figure 5). Recording the pattern of failure and its relation to the PET distribution will be important. Again HNSCC would be an attractive tumor site due to the importance of local control for long-term disease control. To avoid under-treating patients in any of the trial arms, a conservative approach would be to do a dose-painted boost dose only on top of a standard curative dose to the clinical target volume. A PET/CT scan should be performed in all cases with the investigational PET tracer and dose painting by numbers or to a PET defined sub-volume should be planned. To compare like with like, in each patient, the PET defined dose painting plan should be matched with a geometrically defined boost plan delivering the same integral dose to the target volume. The actual plan to be used will be decided by randomization. Although modeling has suggested large gains in tumor control from dose painting, the trial should have a sample size allowing detection of a 15 percentage point improvement in loco-regional control with 90% power. The trial sample size would be about 450 patients, but an adaptive design could be considered. Clearly, this would need a multi-center or cooperative group format to finish accrual within a reasonable time. Strong data from the early clinical trials will be required to motivate a phase III trial with this sample size and complexity of the intervention. We anticipate that such a trial will be initiated within the next five years.
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Søren M. Bentzen, University of Wisconsin – Madison, Departments of Human Oncology, Medical Physics, Biostatistics and Medical Informatics, K4/316 Clinical Science Center, 600 Highland Avenue, Madison WI 53792, USA.
Vincent Gregoire, Center for Molecular Imaging and Experimental Radiotherapy & Radiation Oncology Department, Université catholique de Louvain, St-Luc University Hospital, Avenue Hippocrate 10, B-1200 Brussels, Belgium.