- Original research
- Open Access
[18F]Fluoromisonidazole PET in rectal cancer
EJNMMI Research volume 7, Article number: 78 (2017)
There is an increasing interest in developing predictive biomarkers of tissue hypoxia using functional imaging for personalised radiotherapy in patients with rectal cancer that are considered for neoadjuvant chemoradiotherapy (CRT). The study explores [18F]fluoromisonidazole ([18F]FMISO) positron emission tomography (PET) scans for predicting clinical response in rectal cancer patients receiving neoadjuvant CRT.
Patients with biopsy-proven rectal adenocarcinoma were imaged at 0–45 min, 2 and 4 h, at baseline and after 8–10 fractions of CRT (week 2). The first 6 patients did not receive an enema (the non-enema group) and the last 4 patients received an enema before PET-CT scan (the enema group). [18F]FMISO production failed on 2 occasions. Static PET images at 4 h were analysed using tumour-to-muscle (T:M) SUVmax and tumour-to-blood (T:B) SUVmax. The 0–45 min dynamic PET scans were analysed using Casciari model to report hypoxia and perfusion. Akaike information criteria (AIC) were used to compare data fittings for different pharmacokinetic models. Pathological tumour regression grade was scored using American Joint Committee on Cancer (AJCC) 7.0. Shapiro-Wilk test was used to evaluate the normality of the data.
Five out of eleven (5/11) patients were classed as good responders (AJCC 0/1 or good clinical response) and 6/11 as poor responders (AJCC 2/3 or poor clinical response). The median T:M SUVmax was 2.14 (IQR 0.58) at baseline and 1.30 (IQR 0.19) at week 2, and the corresponding median tumour hypoxia volume was 1.08 (IQR 1.31) cm3 and 0 (IQR 0.15) cm3, respectively. The median T:B SUVmax was 2.46 (IQR 1.50) at baseline and 1.61 (IQR 0.14) at week 2, and the corresponding median tumour hypoxia volume was 5.68 (IQR 5.86) cm3 and 0.76 (IQR 0.78) cm3, respectively. For 0–45 min tumour modelling, the median hypoxia was 0.92 (IQR 0.41) min−1 at baseline and 0.70 (IQR 0.10) min−1 at week 2. The median perfusion was 4.10 (IQR 1.71) ml g−1 min−1 at baseline and 2.48 (IQR 3.62) ml g−1 min−1 at week 2. In 9/11 patients with both PET scans, tumour perfusion decreased in non-responders and increased in responders except in one patient. None of the changes in other PET parameters showed any clear trend with clinical outcome.
This pilot study with small number of datasets revealed significant challenges in delivery and interpretation of [18F]FMISO PET scans of rectal cancer. There are two principal problems namely spill-in from non-tumour tracer activity from rectal and bladder contents. Emphasis should be made on reducing spill-in effects from the bladder to improve data quality. This preliminary study has shown fundamental difficulties in the interpretation of [18F]FMISO PET scans for rectal cancer, limiting its clinical applicability.
Hypoxia in cancer cells can lead to radioresistance and influence radiotherapy (RT) response [1,2,3]. Strategies to improve RT outcomes by targeting hypoxia have repeatedly failed due to the inability to reliably identify tumours with severe or non-resolving hypoxia . Thus, attempts to reliably identify such tumours through functional imaging or biochemical analysis are required.
Tumour hypoxia is a consequence of imbalance between oxygen consumption and supply  due to factors mostly related to perfusion, diffusion or anaemia. Briefly, perfusion-related acute (also known as cyclic ) hypoxia is caused by limited oxygen delivery to the tissue due to fluctuations in blood flow as a consequence of poor tumour microvasculature. Acute hypoxia often fluctuates with cycle times that range from a few cycles per hour to many hours or days. Diffusion-related chronic hypoxia is caused by an increase in diffusion distances of oxygen from isolated blood vessels leading to inadequate oxygen supply which lasts from a few hours to many days. The spatial characteristics of cycling hypoxia commonly involve networks of microvessels as opposed to isolated blood vessels. Anaemic hypoxia is tumour-associated or therapy-induced due to reduction in oxygen transport capacity of blood which is exacerbated by the presence of low perfusion. An arterial blood partial pressure (pO2) less than 80 mmHg is considered hypoxemic hypoxia .
The Eppendorf electrode is considered the gold standard for measuring oxygen distribution in tumours  and has been shown to correlate with response to RT [9,10,11,12,13]. This method is invasive and underestimates oxygenation  in heterogeneous tissue due to inability to distinguish between areas of necrosis and viable tumour. Imaging-based non-invasive method to measure distance between tumour tissue and the nearest vessels exists, which can assess the whole tumour [15, 16], but measuring the continuum of diffusion distances is rather challenging .
Increased retention of [18F]fluoromisonidazole ([18F]FMISO) in tumour cells pre-treatment is suggestive of hypoxia  and has been shown to correlate with pO2 polarography defined tumour hypoxia in head and neck (H&N) cancer [8, 19, 20]. [18F]FMISO uptake spatially corresponded with exogenous and endogenous biomarkers of tissue hypoxia in animal models [21, 22]. Decrease in [18F]FMISO uptake was observed in positron emission tomography (PET) images with reduced hypoxia in animal models . However, [18F]FMISO PET showed contradictory results in detecting tumour hypoxia in human soft tissue sarcomas [24,25,26]. Due to the limited spatial resolution of the PET scanner, the image voxels may contain a mixture of acute and chronic hypoxia and an attempt to separate the two has also been reported . This is important because chronic as well as acute hypoxia may play a role in determining the treatment outcome .
There is an increasing interest in developing predictive biomarkers of tissue hypoxia using functional imaging for personalised RT in patients with rectal cancer that are considered for neoadjuvant chemoradiotherapy (CRT). Therefore, the aim was to explore changes in [18F]FMISO PET parameters in human rectal tumours before and after 8–10 fractions of CRT to predict clinical response.
Patients and ethics
Patients were recruited within an ethically approved prospective observational study: modulation of Radiotherapy according to HYpoxia: exploiting changes in the Tumour Microenvironment to improve outcome in rectal cancer (RHYTHM). The trial was registered at ClinicalTrials.gov, URL: https://clinicaltrials.gov/, number: NCT02157246, date of registration: 10 October 2013, date of enrolment of first participant: 20 Dec 2013. All patients provided written informed consent for the study procedures. Patients with histologically confirmed invasive adenocarcinoma of the rectum having neoadjuvant CRT (45 Gy in 25 fractions over 5 weeks plus capecitabine chemotherapy (900 mg/m2 twice a day)), prior to planned curative rectal resection, were recruited between October 2013 and April 2016.
Pathological tumour regression grade (TRG) was scored using American Joint Committee on Cancer (AJCC 7.0) criteria that have been shown to predict prognosis and was considered the reference for comparison against PET outcome. Response is defined as good where patients had AJCC TRG score 0/1 with N0/1 disease post-CRT or good clinical response where surgery was not undertaken. Poor responders had AJCC TRG score 2/3 or N2 nodes on resection, or poor clinical response. Clinical response is based upon imaging, endoscopy and biopsy post CRT.
Patients were scanned with [18F]FMISO PET at baseline (scan 1) and after receiving 8–10 fractions of CRT within approximately 2–3 weeks of the baseline scan (scan 2). [18F]FMISO was provided by the Radiochemistry Laboratory, Wolfson Brain imaging Centre, University of Cambridge, and produced based on the synthesis methods developed by Oh et al.  and Lim and Berridge . Production failed on two occasions. In one patient, scan 2 was not obtained, and in another patient, the baseline scan could not be done and so scan 2 was omitted. Patients were asked to empty their bladder before the start of the scan and positioned head-in-first. The injection arm was raised then folded during acquisition such that the tumour site was within the centre of the field of view (FOV). The PET-CT scans were acquired on a Discovery PET-CT 690 (General Electric Medical Systems, GEMS, Milwaukee, WI) with 157 mm axial FOV . Scans were started 30 s before the administration of [18F]FMISO with a prescribed dose of 370 (range 333–397) MBq. Dynamic PET images were acquired at 0–45 min in list-mode and static images at 2 and 4 h. Each PET scan was preceded by a CT scan, which resulted in 512 × 512 × 61 voxels of size 0.98 × 0.98 × 2.53 mm at all stages of scanning (dynamic, 2 and 4 h). PET datasets were reconstructed using time-of-flight ordered subset expectation maximisation (OSEM) protocol (GE’s VPFX) in 3D mode with two iterations, 24 subsets and 6.4 mm Gaussian filter (~ 7 mm PET spatial resolution ) in accordance with the standard clinical protocol at our centre . Dynamic PET resulted in 128 × 128 × 47 voxels of size 5.47 × 5.47 × 3.27 mm for each of the 40 frames (1 × 30 s, 12 × 5 s, 6 × 10 s, 5 × 30 s, 10 × 60 s, 6 × 300 s). Static PET at 2 h (600 s) and 4 h (600 s) resulted in 256 × 256 × 47 voxels of size 2.47 × 2.47 × 3.27 mm. PET images were corrected for radioactive decay and for attenuation using CT. Arterialised-venous blood samples were acquired at 45 min and 2 and 4 h time-points post tracer injection . Patients underwent magnetic resonance (MR) scan on the same day prior to PET.
The data split into two cohorts; the first six patients did not receive enema, and the last five were planned to receive MICROLAX® micro-enema before the 4 h PET-CT scan. The former will be referred to as the non-enema group and the latter as the enema group throughout this manuscript.
The muscle regions of interest (ROImuscle) were drawn over the gluteus maximus muscle (Additional file 1: Figure S1) on the CT component of PET-CT on the 4 h scan with PMOD image processing software (PMOD Technologies (v3.6) Ltd., Zurich, Switzerland). The tumour regions of interest (ROItumour) were manually delineated on MR scans by JF (a Radiologist with 7 years’ experience reporting rectal MR scans), JW and TG and transferred to the PET-CT using rigid registration in Eclipse radiation treatment planning software (Varian Medical Systems (version 10), Inc., Palo Alto, CA). The ROItumour were transferred to PMOD for analysis (Additional file 1: Figure S1). The tumour regions were again modified by TP in PMOD to ensure the exclusion of bladder from the ROItumour. All ROIs were propagated to the earlier scans using rigid registration in PMOD.
Static PET quantification
The 4 h static [18F]FMISO PET images were analysed using tumour volume, tumour-to-muscle standardised uptake value maximum (T:M SUVmax), tumour-to-blood standardised uptake value maximum (T:B SUVmax), tumour hypoxic volume based on the threshold value of T:M SUVmax > 1.3 and T:B SUVmax > 1.3 and the corresponding percentage (%) of the total tumour volume that is hypoxic based on the corresponding threshold values.
Dynamic PET quantification
A small ROI within the femoral arteries (ROIartery) was manually placed on 3–5 consecutive transaxial slices (Additional file 1: Figure S1) within PMOD, and the combined counts from both arteries were used to define the [18F]FMISO blood curve calibrated to the plasma concentrations. An example of a 0–4 h time activity curve (TAC) from tumour, blood and muscle is shown in Additional file 1: Figure S2. The 0–45 min data was analysed using a standard 3-tissue compartmental model (TCM) with 7 parameters (V b as fractional blood volume; K 1 , k 3 and k 5 as forward; k 2 , k 4 and k 6 as backward tracer transfer rates between the compartments and K i describing the net influx of tracer to the inner-most cellular compartment), a 2-tissue compartmental model (TCM) with 5 parameters (including V b , K 1 , k 2 , k 3 , k 4 , K i ), 1-TCM with 3 parameters (including V b , K 1 , k 2 ) in PMOD, and the Casciari model in MATLAB (The MathWorks (R2013b), Inc., Natick, USA). The Casciari model provided 8 parameters with the most relevant parameters including blood perfusion (F) and hypoxia (K a ) (see Appendix for details). For physiological relevance, the lower-limit of fitting parameters was set at 0, the upper-limit for η and α was set to unity as these were fractional values and the upper-bound of other parameters was set at 5 to obtain results in per second units.
Akaike information criteria (AIC) (for n < 40) were used to compare the data fittings between different pharmacokinetic models , where the lowest AIC value provides the best model fit. The percentage changes between different measurements pre- and during CRT were assessed from static and dynamic [18F]FMISO PET scans. It was assumed that the calculation of % changes pre- and during CRT may reduce systematic bias by cancelling some of the systematic errors on two occasions. The Shapiro-Wilk test  was used to evaluate the normality of data.
A total of 11 patients undergoing neoadjuvant chemoradiotherapy for locally advanced rectal cancer were recruited. All patients received 45 Gy in 25 fractions with concurrent capecitabine chemotherapy (1 patient had capecitabine withheld for 10 days due to low platelets). PET scans were done in 10/11 patients at baseline and 9/11 patients after 8–10 fractions of CRT. The patient characteristics are outlined in Table 1.
Eight patients underwent total mesorectal excision. Of the 3 patients who have not had surgery, 2 had a good clinical response and remain in remission on follow-up. The other declined surgery despite residual disease and subsequently had progressive disease. Five patients were classed as good responders (AJCC TRG 0/1 with N0/1 post-CRT or good clinical response) and 6 as poor responders (AJCC 2/3, N2 disease post-CRT, or poor clinical response) as outlined in Table 1.
The PET parameters failed the Shapiro-Wilk normality test on a number of occasions, and therefore, non-parametric median and inter quartile ranges (IQR) were reported.
Analysis of static [18F]FMISO PET scans at 4 h
(a)T:M SUVmax: Tumour hypoxic volume was defined using a threshold of T:M SUVmax ratio > 1.3 and the corresponding percentage of tumour volume that is hypoxic are outlined in Table 2. In 3 patients, T:M SUVmax (Fig. 1) rose by up to 27% (range 0.17–27.05%), whereas it fell in 6 patients with a range of 25.43 to 58.96%. The median T:M SUVmax was 2.14 (IQR 0.58) at baseline and decreased by 33% to 1.30 (IQR 0.19) by week 2. The corresponding median tumour hypoxic volume was 1.08 (IQR 1.31) cm3 and decreased by 95% to 0 (IQR 0.15) cm3 by week 2. A hypoxic tumour volume was identified in all but one patient who underwent baseline [18F]FMISO PET, with a range of 0–13.16%. It increased in 3 patients and reduced in 5 by week 2 CRT.
(b)T:B SUVmax: Tumour hypoxic volume was defined using a threshold of T:B SUVmax ratio > 1.3 and the corresponding percentage of tumour volume that is hypoxic are outlined in Table 3. T:B SUVmax (Fig. 1) rose in 2 of 9 patients, but by less than 2%. These patients also demonstrated an increase in T:M SUVmax at week 2 CRT. For those whose values fell, the range of % change was 10.94 to 71.01%. The median T:B SUVmax was 2.46 (IQR 1.50) at baseline and decreased by 29% to 1.61 (IQR 0.14) by week 2. The corresponding median tumour hypoxic volume was 5.68 (IQR 5.86) cm3 and decreased by 56% to 0.76 (IQR 0.78) cm3 by week 2. All patients scan demonstrated a hypoxic volume at baseline (range 0.48–36.25%), which fell in 6 patients (including the 5 with a reduction in T:M SUVmax -defined hypoxic volume) at week 2.
Analysis of 0–45 min dynamic [18F]FMISO PET scans
When the 0–45 min dynamic PET data were fitted to the mathematical models, the AIC results showed that the Casciari model fitted the data better compared to 1-, 2- and 3-TCM for 17 out of 19 times in tumour (Additional file 1: Table S1) and 18 out of 19 times in muscle (Additional file 1: Table S2). An example of dynamic data fitted with different mathematical models is shown in Additional file 1: Figure S3 for tumour and Additional file 1: Figure S4 for muscle. The lower AIC values for the Casciari model corresponded to better fits, which is also visually evident from these figures.
(a) Tumour: The most meaningful parameters, hypoxia (K a ) and perfusion (F), from the Casciari model are presented in Fig. 2 (Table 4 for details). For tumour data, the median K a was 0.92 (IQR 0.41) min-1 at baseline and decreased by 24% to 0.70 (0.10) min-1 by week 2. The median F was 4.10 (IQR 1.71) millilitres/gram/minute ( ml g−1 min−1) at baseline and decreased by 29% to 2.48 (IQR 3.62) ml g−1 min−1 by week 2 (which is in concordance with earlier studies in solid tumours of rectal cancer (17)). In 9/11 patients that were scanned twice, the tumour perfusion decreased in non-responders and increased in responders except in one patient. None of the other changes in PET parameters between baseline and week 2 showed any clear trend with clinical outcome.
(b) Muscle: The K a and F from Casciari model in muscle are reported in Fig. 2 (Table 4 for details). The median F was 0.12 (IQR 0.04) ml g−1 min−1 at baseline and increased by 376% to 0.60 (0.12) ml g−1 min−1 by week 2. The median K a was 0.02 (IQR 0.03) min-1 at baseline and increased by 3073% to 0.86 (0.76) min-1 by week 2. These values were higher than those reported by Schwartz et al.  perhaps due to differences in model or muscle region used. None of these changes in PET parameters between baseline and week 2 showed any clear trend with clinical outcome.
Impact of bladder activity accumulation
It is impossible to avoid bladder emptying at some point prior to the 4 h scan. [18F]FMISO starts being excreted in urine by 10 min post injection leading to a high activity concentration within the bladder by the end of the study (Fig. 3 ).
The tumour ROI can be seen in close proximity to the bladder in patient 1 as shown in Fig. 4a–c, and non-tumour accumulation of tracer posterior to bladder in patient 2 as shown in Fig. 4d–f. This suggests that the tumour TAC within the non-enema group may include contributions from spill-in from non-tumour activity in the bladder as well as rectum, in addition to hypoxic cells within the tumour. The TACs in Fig. 5a, b correspond to images in Fig. 4a–c, showing the effect of accumulated bladder activity on the tumour TAC between 45 min and 4 h, where the TAC shows a continuously increasing trend. The TAC in Fig. 5c, d corresponds to images in Fig. 4d–f showing that although the patient emptied their bladder before the 2 h scan, the activity reaccumulated at 4 h and consequently the activities in both bladder and tumour first dropped at 2 h (compared to 45 min) and then increased again at 4 h (compared to 2 h). This shows the effect of changes in bladder and non-tumour activity in rectum on the changes in tumour TAC at each time point in the non-enema group.
Impact of rectal activity accumulation and the effect of enema
The trial protocol was changed following the first 6 participants to mandate use of a MICROLAX® enema to be administered and the rectum emptied prior to the 4 h scan to reduce error due to excreted tracer in the rectal lumen. Four patients scanned at baseline and three scanned at week 2 underwent a microenema.
Figures 6a–c show the non-tumour accumulation of tracer in rectum adjacent to tumour at 2 h and the removal of this activity at 4 h post enema. This suggests that the 4 h PET images post-enema may be better for quantification purposes compared to those at 2 h from enema group or those at 4 h from non-enema group due to the exclusion of non-tumour activity in rectum (i.e. one less source of error). Figure 7 shows TACs derived from the images in Fig. 6 and shows the combined effect of bladder activity, non-tumour activity in rectum and hypoxic cells within tumour between 45 min and 2 h, and the effect of the enema (i.e. with non-tumour activity removed from the rectum) on 4 h PET scan and the tumour TAC. Since the patient also emptied their bladder between 2 and 4 h, the bladder activity showed an increase of only 6% and correspondingly an increase of 6.25% in tumour activity was observed. That is why it is still unclear if this increase in tumour activity in Figs. 6 and 7 post enema is due to the spill-in from bladder or accumulation of tracer in hypoxic cells or both. Alternatively, it is possible that the [18F]FMISO in hypoxic cells reached an equilibrium state at 4 h post injection, and the increase in tumour activity could be purely an effect of increased bladder activity.
Imaging with [18F]FMISO PET has been a valuable research tool in assessing hypoxia in various cancer types for predicting response to radiotherapy treatment in H&N and lung cancer [37,38,39,40]. In this study, we assessed the changes in [18F]FMISO PET parameters from static and dynamic imaging of rectal tumours before and after 8–10 fractions of CRT and reported the associated challenges.
Analysis of static [18F]FMISO PET scans at 4 h
Low cellular uptake of [18F]FMISO in hypoxic cells and slow cellular washout from non-hypoxic tissue limits the contrast between the tissue of interest and the background at early time points post injection [41, 42]. The static PET scans at 2 and 4 h post-injection were obtained to allow tracer washout from non-hypoxic tissue  including muscle, which is expected to improve the characterisation between oxic and hypoxic regions inside the tumour. Timing variations occurred in acquiring 2 and 4 h PET scans with largest variation in a patient from the enema group whose 2 h PET scan was delayed by 45 min and 4 h scan delayed by 59 min.
For pixels in the tumour ROI, a tissue to blood (T:B) ratio ≥ 1.2 was considered to indicate significant hypoxia as first described by Rajendran et al. . Thereafter, various authors have used T:B ratio ≥ 1.2, 1.3 or 1.4 to indicate hypoxia. There is currently no consensus on which of these values to use. Since [18F]FMISO concentrations in blood and muscle are nearly identical by a few minutes after tracer injection, T:M ratios were considered equivalent to T:B ratios with the benefit that no blood sampling is required. Since T:M SUVmax represented SUVmax of tumour divided by SUVmax of muscle, and since the normalisation factors in numerator and denominator cancel each other, the numerical outcome of T:M SUVmax is mathematically equivalent to the T:M ratio which is approximately equivalent to the T:B ratio (as evident from results in Fig. 1a, b). Therefore, we thought it was appropriate to use both T:M SUVmax and T:B SUVmax to define tumour hypoxia volumes.
Our tumour SUVmax values appeared higher than those obtained by Havelund et al.  who imaged rectal tumours with [18F]FAZA PET at 2 h. Tumour hypoxic volumes obtained in this study were difficult to compare with those shown by Roels et al. , who based rectal tumour ROI on [18F]FDG PET. Our T:M ratio values are however similar to those obtained in other solid tumour types such as head and neck squamous cell carcinoma [45,46,47,48] and non-small cell lung cancer . Where quoted, hypoxic tumour fraction appeared higher in these tumours than in rectal cancer [48, 50].
Analysis of 0–45 min dynamic [18F]FMISO PET scans
Dynamic [18F]FMISO PET data allows the measurement of hypoxic cells and blood perfusion simultaneously  which is not possible with static PET imaging at a single time point. In addition, T:B ratios from static PET scans at 4 h are likely to underestimate the hypoxia volume within a tumour, and for these reasons dynamic PET analysis was employed .
Selection of 0–45 min data
Imaging at 2 h may not be sufficient for [18F]FMISO to reach equilibrium within hypoxic cells . The tracer cleared from the muscle at 4 h at the same time that tumour uptake starts to increase (as shown in Additional file 1: Figure S2). This was the principal reason we first planned to analyse 0–4 h data. However, for the enema group, it was not deemed appropriate to concatenate the 0–2 h and 4 h data to obtain a combined 0–4 h tumour TAC or to combine 0–4 h data from the enema and non-enema group. This is due to the external intervention made in the enema group before the 4 h PET scan. It meant that the tumour activity at 4 h in the enema group included contributions from hypoxic cells and spill-in from bladder activity. In the non-enema group, the contributions came from hypoxic cells, bladder activity and non-tumour rectal activity. Therefore, only three 0–4 h PET datasets from the non-enema group were considered suitable for the dynamic analysis. For this reason, we decided to report the results from 0–45 min dynamic PET scans where all the datasets could be included within the analysis.
Arterial input function
The outcomes of mathematical modelling are sensitive to the arterial input function (AIF) [51, 52]. Since 92–96% of the [18F]FMISO in plasma has been shown to be intact by 90 min post-injection , it was thought unnecessary to correct AIF for the presence of metabolites. Continuous arterial blood sampling was not obtained in this study, and therefore, it was not possible to validate the image-derived input function from the femoral artery, which may cause bias in the estimated model parameters .
Selection of Casciari model
A few tumour and muscle TACs failed to fit using 1-, 2- and 3-TCM which could either be due to an inappropriate [18F]FMISO pharmacokinetic model or due to inconsistencies in the TACs. Therefore, fitting gluteus muscle data successfully to the Casciari model suggested that the tumour data needed further analysis and it was absolutely necessary to seek a pharmacokinetic model that fitted the tumour data successfully. Even though more parameters may be required to fit more complex data successfully, this does not mean that the outcome is more meaningful just because the data has been fitted by a more complex model . The use of the Casciari model was based on previous recommendations [21, 55] that assumed an inverse relationship between hypoxia and perfusion within the tumour.
This was a critical step in model fitting, and we used the Casciari recommended initial values. However, in some cases, different initial values were attempted to obtain better fit. It was also observed that multiple solutions existed. Nonlinear optimization may suffer from local minima and initialisation which may be minimised using stochastic sampling as suggested by Shi et al. .
The parameter fixing was undertaken to improve the precision of model parameters [21, 56]. In our case, parameter fixing either failed or gave different results and therefore was not considered any further. In the absence of true physiological values of these parameters, fixing may bias model estimates, for example, in case of rats, a large η value of 0.90 was obtained by Casciari .
Baseline median K a in tumour was 46 times higher than in muscle suggesting that tumour is likely to contain hypoxia cells whereas resting muscle is well oxygenated. On the other hand, baseline median F in tumour was 34 times higher than in muscle suggesting difference in tumour and muscular vasculature.
(a) Tumour showed a median 29% and 24% decrease in F and K a respectively after 2 weeks of CRT. However, a reduction in K a post treatment can be indicative of reduced tracer delivery due to damaged capillary bed rather than a reduction in tumour hypoxia . Tumour K a did not show any relationship with F. This suggests that the changes in median K a in tumour during treatment were not due to the direct consequence of changes in perfusion and may suggest a radiotherapy-induced reoxygenation [50, 58] as it starts early during CRT and has been previously shown to correlate with outcome in H&N tumours [59, 60]. In our study, the alterations in tumour perfusion trend with response highlighted the importance of changes in vasculature-related functional parameters during radiotherapy, its important role in understanding hypoxia  and its relation with outcome [59, 62, 63].
At baseline, tumour F showed a weak relationship with T:M SUVmax and T:B SUVmax at 4 h and none after 2 weeks of CRT, suggesting that these parameters from static PET may primarily exhibit chronic hypoxia. The K a showed poor relationship with T:M SUVmax and T:B SUVmax at baseline and after 2 weeks of CRT suggesting that the semi-quantitative and quantitative method of measuring hypoxia from static and dynamic PET, respectively, are not equivalent .
(b) At baseline, the muscle showed low F values and negligible K a levels as expected. Despite a median increase of 376% in F at week 2 CRT, the median F in muscle was 4 times lower compared to that in tumour. The K a in muscle increased by a median value of 3076% at week 2, but the median K a in muscle was of the order obtained in the tumour. Acute effects of radiotherapy include reversible inflammation occurring in actively proliferating cells . It is therefore likely that the muscle underwent radiation response causing inflammation in this region [64, 65]. The mechanism between inflammation and hypoxia is not well understood [66, 67], but increased perfusion due to inflammatory changes secondary to radiotherapy have been reported in rectal cancer . It is also known that the [18F]FMISO reduction to nitro radical is reversible in the presence of oxygen. It is possible that the prolonged duration of increased blood perfusion beyond 45 min increased the accumulation of tracer in muscle during the first 2 h post tracer injection which then reversed between 2 and 4 h when we observed a large washout of tracer suggesting that the trapping mechanism is rather time dependent and fluctuating. The pattern of blood perfusion in acute hypoxia can alter on a 20 min time scale , which is less than our experiment time of 45 min for dynamic analysis. In our study, muscle K a and F showed weak relationship suggesting that the muscle [18F]FMISO uptake was not affected by the changes in muscle perfusion .
Impact of bladder activity accumulation
The accumulation of [18F]FMISO in bladder starts 10–15 min post-tracer injection (Fig. 3) due to variable urinary excretion and may affect tumour uptake by a phenomenon called spill-in which can affect both lesion detectability [70, 71] and quantification . Additional file 1: Figure S5 shows the phenomenon of spill-in count from bladder into the tumour due to scatter and random photons. The false lines of responses are accepted as true events leading to overestimation of activity concentration in the surrounding region leading to an error during image reconstruction. Bettinardi et al.  assessed random/scatter characteristics over a range of 0–60 kBq/cm3 within the PET field of view. However, it should be noted that we observed much higher activity concentrations (undecay corrected activity of up to 150 kBq/cm3) within human bladder at 2 and 4 h post injection which would lead to an increase in random/scatters in a non-linear fashion. Additionally, the regions within very close proximity of the bladder gets further affected during image reconstruction by the spill-in of activity from bladder due to the limited spatial resolution of the PET scanner. The PET quantitative values within tumour may further get affected depending upon, but not limited to, the rate of urine excretion to bladder, the activity concentration within the bladder, its volume and proximity to the tumour at the time of imaging, the accuracy of attenuation correction, etc.
Catheterization of the bladder has been suggested as an invasive alternative to this problem, but it is a potential source of infection and uncomfortable for patients . In addition, for radiotherapy planning purposes, a full bladder is required and so this would be unhelpful if these scans were to be used for guidance. Even though some preliminary phantom work has been done to minimise this problem by restricting the bladder counts in image reconstruction process, but it is still at an early stage to be translated to clinical data . More work is required to address the PET image reconstruction [74,75,76] related issues before [18F]FMISO PET can be employed for the quantification of rectal cancer.
Impact of rectal activity accumulation and the effect of enema
[18F]FMISO is excreted through the biliary tract into the gastrointestinal tract as well as through the urine. When rectal lumen contains high [18F]FMISO activity and it is within close proximity of the tumour, the spill-in of activity from rectal lumen into the tumour is unavoidable due to the limited resolution of the PET scanner. The use of an enema shortly prior to the 4 h scan may reduce this non-tumour luminal activity as shown in Figs. 6 and 8.
Variability of ROI due to image co-registration
Tumours are generally adjacent to normal rectal wall and therefore difficult to outline on CT. Therefore, tumours were first outlined on MR scans and then modified to match 4 h PET uptake since there is inevitable time difference between the PET-CT and MR scans obtained on the same day. Rigid registration was used to transfer the ROI between dynamic and static scans. This should be done with caution as the internal organ motion due to air, rectal peristalsis or other reasons may not allow accurate delineation of the tumour (Additional file 1: Figure S6). Since the tracer uptake in tumour changes over time, the data may benefit from careful delineation of tumour region at each time point, albeit controversial due to the time and cost involved. In the case of Additional file 1: Figure S6, it was possible to visually identify the tumour on the 4 h scans but not the 2 h scans due to the patient empting their bladder and the clearance of air in at least one patient. PET-MR may be useful in such situations.
Other PET tracers
[18F]FMISO has been shown to have lower tumour uptake compared to other hypoxia tracers  and therefore at a disadvantage, providing lower tumour to background contrast. The PET tracers that show clearance to bladder or gut lumen are likely to have similar issues as presented within this work. A recent report  summarised clinical image finding for PET hypoxia tracers and suggested the use of variety of tracers in tumours of the brain, H&N, breast, lung and lymphoma. On the basis of favourable preclinical or metabolic data, the use of [18F]HX4 for imaging liver and [xCu]Cu-ATSM for imaging bladder was also recommended even though the retention of radio-copper in animal models at early time post-injection has been shown to partially reflect processing of copper rather than a sole hypoxia marker . However, limited use of most PET tracers was suggested for the assessment of hypoxia in the tumours of the renal, liver, colorectal, bladder and prostate, with the exception of [18F]FAZA and [xCu]Cu-ATSM for colorectal tumours for visualisation purposes, though semi-quantitative methods were attempted [44, 80]. [18F]FMISO in colorectal was not recommended and our finding suggest the same . [18F]FDG PET has been useful in the management of rectal cancer as a marker of glucose metabolism but not hypoxia directly and therefore is not discussed here.
Since the TRG scores were obtained in 8 patients and clinical response in 3 patients who did not undergo surgery, the conclusions drawn from this study are limited by the small number of subjects. The acceptability of procedures to patients and clinical implementation is a major challenge in clinical imaging trials. Despite these challenges, some problems are solvable, for example, the spill-in from non-tumour accumulation of [18F]FMISO was improved using enema, while other problems may not be currently solvable, for example, the spill-in from bladder. Given the high activity regions within the pelvis, similar challenges in analysing and interpreting [18F]FMISO uptake may exist for other tumours, such as cervix and prostate cancer. Frusemide may be considered to aid rapid urinary excretion and dilute the residual radioactivity in the bladder. Another solution may be to keep patients well hydrated and request bladder emptying immediately before the PET scan. However, for target delineation purposes, it is preferred that the bladder has the same size and shape as on scans acquired for radiotherapy planning i.e. ‘comfortably full’ for the registration algorithm to work well. Since CT is unable to provide a good contrast in the soft tissue within the pelvis, PET-MR may be potentially beneficial albeit controversial due to the lack of attenuation correction in the bone.
In conclusion, this pilot study with small datasets revealed significant challenges in delivery and interpretation of [18F]FMISO PET scanning for rectal cancer. Preliminary data does not support the hypothesis that a reduction in [18F]FMISO uptake is predictive of clinical response. There are two principal problems namely spill-in from non-tumour activity in the rectum and from bladder into the surrounds that encompass tumour. Careful consideration should be given to PET acquisition and reconstruction to minimise spill-in counts from the bladder. This preliminary study has shown fundamental difficulties in interpretation of [18F]FMISO PET for rectal cancer, limiting clinical applicability.
Thomlinson RH, Gray LH. The histological structure of some human lung cancers and the possible implications for radiotherapy. Br J Cancer. 1955;9:539–49.
Gray LH, Conger AD, Ebert M, Hornsey S, Scott OCA. The concentration of oxygen dissolved in tissues at the time of irradiation as a factor in radiotherapy. Br J Radiol. 1953;26:638–48.
Mottram JC. A factor of importance in the radio sensitivity of tumours. Br J Radiol. 1936;9:606–14.
Horsman MR, Overgaard J. The impact of hypoxia and its modification of the outcome of radiotherapy. J Radiat Res. 2016;57:i90–8.
Vaupel P, Briest S, Höckel M. Hypoxia in breast cancer: pathogenesis, characterization and biological/therapeutic implications. Wien Med Wochenschr. 2002;152:334–42.
Dewhirst MW. Relationships between cycling hypoxia, HIF-1, angiogenesis and oxidative stress. Radiat Res. 2009;172:653–65.
Samuel J, Franklin C. Common Surgical Diseases. In: Myers JA, Millikan KW, Saclarides TJ, editors. An algorithmic approach to problem solving. New York, NY: Springer New York; 2008. p. 391–4.
Zimny M, et al. FDG—a marker of tumour hypoxia? A comparison with [18F]fluoromisonidazole and pO2-polarography in metastatic head and neck cancer. Eur J Nucl Med Mol Imaging. 2006;33:1426–31.
Movsas B, et al. Hypoxic prostate/muscle po2 ratio predicts for biochemical failure in patients with prostate cancer: preliminary findings. Urology. 2002;60:634–9.
Höckel M, et al. Intratumoral pO2 predicts survival in advanced cancer of the uterine cervix. Radiother Oncol. 1993;26:45–50.
Nordsmark M, Overgaard M, Overgaard J. Pretreatment oxygenation predicts radiation response in advanced squamous cell carcinoma of the head and neck. Radiother Oncol. 1996;41:31–9.
Nordsmark M, et al. The relationship between tumor oxygenation and cell proliferation in human soft tissue sarcomas. Int J Radiat Oncol Biol Phys. 1996;35:701–8.
Okunieff P, et al. Oxygen tension distributions are sufficient to explain the local response of human breast tumors treated with radiation alone. Int J Radiat Oncol Biol Phys. 1993;26:631–6.
Mortensen LS, et al. Identifying hypoxia in human tumors: a correlation study between 18F-FMISO PET and the Eppendorf oxygen-sensitive electrode. Acta Oncol. 2010;49:934–40.
Haustermans K, et al. Diffusion limited hypoxia estimated by vascular image analysis: comparison with pimonidazole staining in human tumors. Radiother Oncol. 2000;55:325–33.
McGowan DR, Macpherson RE, Hackett SL, Liu D, Gleeson FV, McKenna WG, Higgins GS, Fenwick JD. 18 F-fluoromisonidazole uptake in advanced stage non-small cell lung cancer: A voxel-by-voxel PET kinetics study. Med Phys. 2017. doi:10.1002/mp.12416.
Vaupel P. Tumor microenvironmental physiology and its implications for radiation oncology. Semin Radiat Oncol. 2004;14:198–206.
Nehmeh SA, et al. Reproducibility of intratumor distribution of (18)F-fluoromisonidazole in head and neck cancer. Int J Radiat Oncol Biol Phys. 2008;70:235–42.
Gagel B, et al. pO polarography, contrast enhanced color duplex sonography (CDS), [18F] fluoromisonidazole and [18F] fluorodeoxyglucose positron emission tomography: validated methods for the evaluation of therapy-relevant tumor oxygenation or only bricks in the puzzle of tumor hypoxia? BMC Cancer. 2007;7:1–9.
Gagel B, et al. pO2 polarography versus positron emission tomography ([18F] fluoromisonidazole, [18F]-2-fluoro-2′-deoxyglucose). Strahlenther Onkol. 2004;180:616–22.
Shi K, et al. Quantitative analysis of [18F]FMISO PET for tumor hypoxia: correlation of modeling results with immunohistochemistry. Mol Imaging Biol. 2016:1–10.
Dubois L, et al. Evaluation of hypoxia in an experimental rat tumour model by [(18)F]Fluoromisonidazole PET and immunohistochemistry. Br J Cancer. 2004;91:1947–54.
Peeters SG, et al. A comparative study of the hypoxia PET tracers [18F]HX4, [18F]FAZA, and [18F]FMISO in a preclinical tumor model. Int J Radiat Oncol Biol Phys. 2015;91:351–9.
Bentzen L, et al. Tumour oxygenation assessed by 18F-fluoromisonidazole PET and polarographic needle electrodes in human soft tissue tumours. Radiother Oncol. 2003;67:339–44.
Rajendran JG, et al. [18F]FMISO and [18F]FDG PET imaging in soft tissue sarcomas: correlation of hypoxia, metabolism and VEGF expression. Eur J Nucl Med Mol Imaging. 2003;30:695–704.
Rajendran JG, et al. Hypoxia and glucose metabolism in malignant tumors. Clin Cancer Res. 2004;10:2245–52.
Wang K, Yorke E, Nehmeh SA, Humm JL, Ling CC. Modeling acute and chronic hypoxia using serial images of (18)F-FMISO PET. Med Phys. 2009;36:4400–8.
Brown M. The remarkable yin and yang of tumour hypoxia. Int J Radiat Biol. 2010;86:907–17.
Oh SJ, et al. Fully automated synthesis of [18F]fluoromisonidazole using a conventional [18F]FDG module. Nucl Med Biol. 2005;32:899–905.
Lim J-L, Berridge MS. An efficient radiosynthesis of [18F]fluoromisonidazole. Appl Radiat Isot. 1993;44:1085–91.
Bettinardi V, et al. Physical performance of the new hybrid PET/CT Discovery-690. Med Phys. 2011;38:5394–411.
Teoh EJ, McGowan DR, Macpherson RE, Bradley KM, Gleeson FV. Phantom and clinical evaluation of the Bayesian penalized likelihood reconstruction algorithm Q. Clear on an LYSO PET/CT system. Journal of nuclear medicine : official publication, Society of Nuclear Medicine. 2015;56:1447–52.
Phelps M, et al. Tomographic measurement of local cerebral glucose metabolic rate in humans with (F-18) 2-fluoro-2-deoxy-D-glucose: validation of method. Ann Neurol. 1979;6:371–88.
Motulsky H, Christopoulos A. Fitting models to biological data using linear and nonlinear regression: a practical guide to curve fitting. In: OUP USA; 2004.
Shapiro SS, Wilk MB. An analysis of variance test for normality (complete samples)†. Biometrika. 1965;52:591–611.
Schwartz J, et al. Pharmacokinetic analysis of dynamic 18F-fluoromisonidazole PET data in non-small cell lung cancer. J Nucl Med. 2017;58:911–9.
Eschmann S-M, et al. Prognostic impact of hypoxia imaging with 18F-misonidazole PET in non-small cell lung cancer and head and neck cancer before radiotherapy. J Nucl Med. 2005;46:253–60.
Thorwarth D, Eschmann S-M, Scheiderbauer J, Paulsen F, Alber M. Kinetic analysis of dynamic (18)F-fluoromisonidazole PET correlates with radiation treatment outcome in head-and-neck cancer. BMC Cancer. 2005;5:152.
Rajendran JG, et al. Tumor hypoxia imaging with [F-18] fluoromisonidazole positron emission tomography in head and neck cancer. American Association for Cancer Research. 2006;12:5435–41.
Dirix P, et al. Dose painting in radiotherapy for head and neck squamous cell carcinoma: value of repeated functional imaging with 18F-FDG PET, 18F-fluoromisonidazole PET, diffusion-weighted MRI, and dynamic contrast-enhanced MRI. J Nucl Med. 2009;50:1020–7.
Loi S, et al. Oxaliplatin combined with infusional 5-fluorouracil and concomitant radiotherapy in inoperable and metastatic rectal cancer: a phase I trial. Br J Cancer. 2005;92:655–61.
Roels S, et al. Biological image-guided radiotherapy in rectal cancer: is there a role for FMISO or FLT, next to FDG? Acta Oncol. 2008;47:1237–48.
Rajendran J, et al. [18F] FMISO and [18F] FDG PET imaging in soft tissue sarcomas: correlation of hypoxia, metabolism and VEGF expression. Eur J Nucl Med Mol Imaging. 2003;30:695–704.
Havelund BM, et al. Tumour hypoxia imaging with 18F-fluoroazomycinarabinofuranoside PET/CT in patients with locally advanced rectal cancer. Nucl Med Commun. 2013;34:155–61.
Okamoto S, et al. The reoxygenation of hypoxia and the reduction of glucose metabolism in head and neck cancer by fractionated radiotherapy with intensity-modulated radiation therapy. Eur J Nucl Med Mol Imaging. 2016;43:2147–54.
Zschaeck S, et al. Spatial distribution of FMISO in head and neck squamous cell carcinomas during radio-chemotherapy and its correlation to pattern of failure. Acta Oncol. 2015;54:1355–63.
Mönnich D, et al. Robustness of quantitative hypoxia PET image analysis for predicting local tumor control. Acta Oncol. 2015;54:1364–9.
Simoncic U, et al. Comparison of DCE-MRI kinetic parameters and FMISO-PET uptake parameters in head and neck cancer patients. Med Phys. 2017;44:2358–68.
Gagel B, et al. [18F] fluoromisonidazole and [18F] fluorodeoxyglucose positron emission tomography in response evaluation after chemo−/radiotherapy of non-small-cell lung cancer: a feasibility study. BMC Cancer. 2006;6:51.
Koh WJ, et al. Evaluation of oxygenation status during fractionated radiotherapy in human nonsmall cell lung cancers using [F-18]fluoromisonidazole positron emission tomography. Int J Radiat Oncol Biol Phys. 1995;33:391–8.
Verwer EE, et al. Pharmacokinetic analysis of [18F]FAZA in non-small cell lung cancer patients. Eur J Nucl Med Mol Imaging. 2013;40:1523–31.
Puri T, Blake GM, Siddique M, Frost ML, Cook GJ, Marsden PK, Fogelman I, Curran KM. Validation of new image-derived arterial input functions at the aorta using 18F-fluoride positron emission tomography. Nucl Med Commun. 2011;32(6):486–95.
Bruehlmeier M, Roelcke U, Schubiger PA, Ametamey SM. Assessment of Hypoxia and Perfusion in Human Brain Tumors Using PET with 18F-Fluoromisonidazole and 15O-H2O. J Nucl Med. 2004;45:1851–9.
Puri T, et al. Validation of image-derived arterial input functions at the femoral artery using 18F-fluoride positron emission tomography. Nucl Med Commun. 2011;32:808–17.
Casciari JJ, Graham MM, Rasey JS. A modeling approach for quantifying tumor hypoxia with [F-18]fluoromisonidazole PET time-activity data. Med Phys. 1995;22:1127–39.
Siddique M, et al. The precision and sensitivity of 18F-fluoride PET for measuring regional bone metabolism: a comparison of quantification methods. In: Journal of Nuclear Medicine; 2011.
Oehler C, et al. 18F-Fluromisonidazole PET imaging as a biomarker for the response to 5,6-dimethylxanthenone-4-acetic acid in colorectal xenograft tumors. J Nucl Med. 2011;52:437–44.
Eschmann SM, et al. Hypoxia-imaging with 18F-misonidazole and PET: changes of kinetics during radiotherapy of head-and-neck cancer. Radiother Oncol. 2007;83:406–10.
Zips D, et al. Exploratory prospective trial of hypoxia-specific PET imaging during radiochemotherapy in patients with locally advanced head-and-neck cancer. Radiother Oncol. 2012;105:21–8.
N. E. Wiedenmann et al., Serial [18F]-fluoromisonidazole PET during radiochemotherapy for locally advanced head and neck cancer and its correlation with outcome. Radiother Oncol 2015 117, 113-117 .
Brown JM, Le Q-T. Tumor hypoxia is important in radiotherapy, but how should we measure it? Int J Radiat Oncol Biol Phys. 2002;54:1299–301.
Pore N, et al. Nelfinavir down-regulates hypoxia-inducible factor 1α and VEGF expression and increases tumor oxygenation: implications for radiotherapy. Cancer Res. 2006;66:9252–9.
Qayum N, et al. Tumor vascular changes mediated by inhibition of oncogenic signaling. Cancer Res. 2009;69:6347–54.
Barnett GC, et al. Normal tissue reactions to radiotherapy: towards tailoring treatment dose by genotype. Nature reviews Cancer. 2009;9:134–42.
Vujaskovic Z, et al. Radiation-induced hypoxia may perpetuate late normal tissue injury. Int J Radiat Oncol Biol Phys. 2001;50:851–5.
D’Ignazio L, Batie M, Rocha S. Hypoxia and inflammation in cancer, focus on HIF and NF-κB. Biomedicine. 2017;5:21.
Egners A, Erdem M, Cramer T. The response of macrophages and neutrophils to hypoxia in the context of cancer and other inflammatory diseases. Mediat Inflamm. 2016;2016:10.
R. Garcia-Figueiras et al., in 101st Scientific Assembly and Annual Meeting, Radiological Society of North America. (McCormick Place, Chicago, 2015).
Chaplin DJ, Olive PL, Durand RE. Intermittent blood flow in a murine tumor: radiobiological effects. Cancer Res. 1987;47:597.
Schöder H, Larson SM. Positron emission tomography for prostate, bladder, and renal cancer. Semin Nucl Med. 2004;34:274–92.
Massaro A, et al. Optimising (18)F-choline PET/CT acquisition protocol in prostate cancer patients. N Am J Med Sci. 2012;4:416–20.
Jesús S-R, et al. Impact and correction of the bladder uptake on 18 F-FCH PET quantification: a simulation study using the XCAT2 phantom. Phys Med Biol. 2016;61:758.
Lo E, et al. Strategies to prevent catheter-associated urinary tract infections in acute care hospitals: 2014 update. Infect Control Hosp Epidemiol. 2014;35:464–79.
Boellaard R. Standards for PET image acquisition and quantitative data analysis. J Nucl Med. 2009;50:11S–20S.
Adams MC, Turkington TG, Wilson JM, Wong TZ. A systematic review of the factors affecting accuracy of SUV measurements. Am J Roentgenol. 2010;195:310–20.
Silva-Rodríguez J, Aguiar P, Domínguez-Prado I, Fierro P, Ruibal Á. Simulated FDG-PET studies for the assessment of SUV quantification methods. Revista Española de Medicina Nuclear e Imagen Molecular. 2015;34:13–8.
Wack LJ, et al. Comparison of [18F]-FMISO, [18F]-FAZA and [18F]-HX4 for PET imaging of hypoxia—a simulation study. Acta Oncol. 2015;54:1370–7.
Fleming IN, et al. Imaging tumour hypoxia with positron emission tomography. Br J Cancer. 2015;112:238–50.
Hueting R, et al. A comparison of the behavior of 64Cu-Acetate and 64Cu-ATSM in vitro and in vivo. J Nucl Med. 2014;55:128–34.
Dietz DW, et al. Tumor hypoxia detected by positron emission tomography with 60Cu-ATSM as a predictor of response and survival in patients undergoing neoadjuvant chemoradiotherapy for rectal carcinoma: a pilot study. Dis Colon rectum. 2008;51:1641–8.
Thank you to the patients who took part in the RHYTHM-I study and the Oxford University Hospitals Foundation NHS Trust. This study was supported by the NIHR Oxford Biomedical Research Centre and sponsored by University of Oxford. It was run by Oncology Clinical Trial Office (OCTO), Oxford Clinical Trials Research Unit. Thanks for staffs at OCTO who have been involved in the study and guidance from the Radiotherapy and Imaging Oversight Committee. Thanks to Deborah Whittington, Lead Nurse Endoscopist at the Oxford University Hospitals NHS Foundation Trust. Tanuj Puri (TP) thanks Emeritus Professor Glen Blake at the King’s College London for the valuable discussions and dedicates this manuscript to late Professor Ignac Fogelman (also known as the father of radionuclide bone imaging) who passed away on the 5th of July 2016.
The study is sponsored by the University of Oxford, funded by Cancer Research United Kingdom (CRUK) & Engineering and Physical Sciences Research Council (EPSRC) Cancer Imaging Centre in Oxford, in association with the Medical Research Council (MRC) and Department of Health (DoH). Tanuj Puri is funded by the CRUK Oxford Cancer Research Centre. Tessa Greenhalgh is supported by the National Institute for Health Research (NIHR) Oxford Biomedical Research Centre and the CRUK/EPSRC Oxford Cancer Imaging Centre. Mike Partridge would like to acknowledge grant code C5255/A15935 from Cancer Research UK. CRUK Oxford Cancer Research Centre (OCRC2), CRUK & EPSRC Oxford Cancer Imaging Centre (OCIC1, application reference: C5255/A10339), CRUK & EPSRC Cancer Imaging Centre in Oxford (CICO2, application reference: C5255/A16466) is awarded to Professor Gillies McKenna.
Ethics approval and consent to participate
Informed consent was obtained from all individual participants included in the study. All procedures performed in this study involving human participants were in accordance with the local ethical standards and/or national research committee and with the 1964 Helsinki declaration and its later amendments or comparable ethical standards. The research ethics committee (REC) was the East of England – Essex Research Ethics Committee. Ethics approval reference number is 13/EE/0123. The Radiotherapy & Imaging Trial Oversight Committee (RIOC) fulfilled the roles of the trial steering committee (TSC) and data and safety monitoring committee (DSMC).
The authors declare that they have no competing interests.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Tumour AIC values from fitting 0-45min dynamic [18F]FMISO PET readings at baseline and week 2 to four different pharmacokinetic models. Table S2. Muscle AIC values from fitting 0-45 min dynamic [18F]FMISO PET readings at baseline and week 2 to four different pharmacokinetic models. Figure S1. Example of the ROI from which measurements were taken. Figure S2. Examples of TAC in tumour, blood and muscle at baseline over 0-4 h. Figure S3. Example of 0-45 min tumour TACs fitted to four different pharmacokinetic models. Figure S4. Example of 0-45 min muscle TACs fitted to four different pharmacokinetic models. Figure S5. The artwork shows examples of scatter & random events originating from the activity inside the bladder as a potential cause of spill-in counts inside the tumour. Figure S6. An example from the enema group showing transaxial PET/CT images at 2 and 4 h. AIC=akaike information criteria; min= minute; [18F]FMISO=[18F]fluoromisonidazole; PET=positron emission tomography; CRT=chemoradiotherapy; ROI=region of interest; TAC=time activity curve; h=hour; CT=computed tomography. (PDF 445 kb)
Casciari et al.  developed a compartmental model for [18F]fluoromisonidazole ([18F]FMISO) as following:
The total [18F]FMISO activity A(t) in tissue, F is blood perfusion (microvascular blood flow rate measured per unit volume in units: ml g−1 min−1), K a is the cellular [18F]FMISO reaction rate (inversely related to oxygen concentration) that is related to the fraction of cells in the region that are hypoxic (units: min−1), K b is the rate constant for transport of diffusible products out of the cell (units: min−1), V t is tissue specific volume (units: mlg−1), η is the fraction of V t occupied by extracellular space (units: dimensionless), α is the fraction of the hydroxylamine reactive intermediate that is converted to bound products (units: dimensionless), β 1 (units: dimensionless) and β 2 (unit: dimensionless) were the partial volume and spill-in correction factors.
About this article
- Pharmacokinetic modelling
- Rectal cancer
- Predictive biomarker