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Current radiotracers for positron emission tomography (PET) imaging of choline metabolism have poor systemic metabolic stability in vivo. We describe a novel radiotracer, [18F]fluoromethyl-[1,2-2H4]-choline (D4-FCH), that employs deuterium isotope effect to improve metabolic stability. D4-FCH proved more resistant to oxidation than its non-deuterated analog, [18F]fluoromethylcholine (FCH), in plasma, kidneys, liver and tumor, while retaining phosphorylation potential. Tumor radiotracer levels, a determinant of sensitivity in imaging studies, was improved by deuterium substitution; tumor uptake values expressed as %injected dose/voxel at 60 min were 7.43 ± 0.47 and 5.50 ± 0.49 for D4-FCH and FCH, respectively, (P = 0.04). D4-FCH was also found to be a useful response biomarker. Treatment with the mitogenic extracellular kinase inhibitor, PD0325901, resulted in a reduction in tumor radiotracer uptake that occurred in parallel with reductions in choline kinase A expression. In conclusion, D4-FCH is a very promising metabolically stable radiotracer for imaging choline metabolism in tumors.
The biosynthetic product of choline kinase (EC 126.96.36.199) activity, phosphocholine, is elevated in several cancers and is a precursor for membrane phosphatidylcholine (1-4). Over-expression of choline kinase and increased enzyme activity have been reported in prostate, breast, lung, ovarian and colon cancers (5-10) and are largely responsible for the increased phosphocholine levels with malignant transformation and progression; the increased phosphocholine levels in cancer cells are also due to increased breakdown via phospholipase C (6). Because of this phenotype, together with reduced urinary excretion, [11C]choline has become a prominent radiotracer for positron emission tomography (PET) and PET-Computed Tomography (PET-CT) imaging of prostate cancer, and to a lesser extent imaging of brain, esophageal, and lung cancer (11-16). The specific PET signal is due to transport and phosphorylation of the radiotracer to [11C]phosphocholine by choline kinase. [18F]Fluoromethylcholine (FCH) was developed to overcome the short physical half-life of carbon-11 (20.4 min) (17) and a number of PET and PET-CT studies with this relatively new radiotracer have been published (18-21). The longer half-life of fluorine-18 (109.8 min) was deemed potentially advantageous in permitting late imaging of tumors when sufficient clearance of parent tracer in systemic circulation had occurred (22). Of interest, however, [11C]choline (and fluoro-analog) is oxidized to [11C]betaine by choline oxidase (EC 188.8.131.52) mainly in kidney and liver tissues, with metabolites detectable in plasma soon after injection of the radiotracer (23). This makes discrimination of the relative contributions of parent radiotracer and catabolites difficult when a late imaging protocol is used. In this article we have developed a more metabolically stable FCH analog, [18F]fluoromethyl-[1,2-2H4]-choline (D4-FCH), based on the deuterium isotope effect (24-27). This novel radiotracer has a number of potential advantages: (i) due to improved stability it should better enable late imaging of tumors after sufficient clearance of the radiotracer from systemic circulation and (ii) it should enhance the sensitivity of tumor imaging through increased availability of substrate. In this article, we report for the first time, the development of D4-FCH for imaging tumors and for monitoring therapeutic response.
No-carrier-added FCH and D4-FCH were synthesized by reacting [18F]fluorobromomethane with N, N-dimethylaminoethanol or D4-N,N-dimethylaminoethanol, respectively, as shown in Fig. 1a. [18F]Fluorobromomethane was synthesized from dibromomethane by substitution of bromine with [18F]fluoride based on the method reported by Bergman (28). After trapping the [18F]fluorobromomethane into a 2.5ml conical glass vial containing 150μl of dimethylaminoethanol or D4-N,N-dimethylaminoethanol in dry acetonitrile (1.0ml) pre-cooled to 0°C, the vial was sealed and heated to 100°C for 10 min. The solvent was removed by a stream of nitrogen. Following this, the residue containing FCH or D4-FCH was dissolved in 5% ethanol solution (10ml), loaded onto a cation exchange Sep Pak Cartridge (Waters, Accell CM light) which had been pre-conditioned with 2M HCl and water (5ml each). After further washing of the CM cartridge with ethanol and water (10 ml each), the FCH or D4-FCH was eluted with sterile isotonic saline (0.5 to 2.0ml) and sterilized by filtration (0.22 μm sterile filter; Millipore, Waters).
The radiochemical purity for both FCH and D4-FCH was ~ 99% as analyzed with radiochemical detection (radio-HPLC). The radioactive species were confirmed as the desired choline analogs by co-elution with a commercial fluorocholine chloride standard (obtained from ABCR Gmbh & Co, Karlsruhe, Germany) by HPLC on an Agilent 1100 series HPLC system equipped with a Bioscan Flowcount FC-3400 Pin diode detector (for radioactivity detection) and an Agilent G1362A refractive index detector for detection of non-radioactive species. The stationary phase comprised of a Phenomenex Luna C18 reverse-phase column (150 mm × 4.6 mm) and the mobile phase comprised 5 mM heptanesulfonic acid (pH 8.0) and acetonitrile (90:10 v/v), delivered at a flow rate 1 mL/min. [11C]Choline was synthesized by Hammersmith Imanet Limited using a previously described method (29). PD0325901 (N-((R)-2,3-dihydroxy-propoxy)-3,4-difluoro-2-(2-fluoro-4-iodo-phenylamino)-benzamide) was obtained from the Division of Signal Transduction Therapy, University of Dundee, Dundee, Scotland.
All animal experiments were done by licensed investigators in accordance with the United Kingdom Home Office Guidance on the Operation of the Animal (Scientific Procedures) Act 1986 and within guidelines set out by the United Kingdom Coordinating Committee for Cancer Research's Ad hoc Committee on Welfare of Animals in Experimental Neoplasia (30). Both tumor-bearing (Balb/c nude mice) and non-tumor bearing (Balb/c mice) animals were used. Human melanoma, SKMEL-28, and human colon, HCT116, tumors were grown in Balb/c nu/nu mice (Harlan) as previously reported (31). Tumor dimensions were measured continuously using a caliper and tumor volumes were calculated by the equation: volume = (π/6) × a × b × c, where a, b, and c represent three orthogonal axes of the tumor. Mice were used when their tumors reached approximately 100 mm3.
FCH or D4-FCH (~4.8MBq) was injected via the tail vein into anesthetized non-tumor bearing Balb/c mice or HCT116 tumor bearing Balb/c nude mice; isofluorane/O2/N2O anesthesia was used. In a limited number of cases [11C]choline (~9MBq) was used for comparison. Plasma samples were obtained at 2, 15, 30 and 60 min after injection; liver, kidney and tumor samples were obtained at 30 min. All samples were snap-frozen in liquid nitrogen. For analysis, samples were thawed and kept at 4°C immediately prior to use. To approximately 0.2 mL of plasma was added ice-cold methanol (1.5 mL). The mixture was then centrifuged (3 minutes, 15,493 × g; 4°C). The supernatant was evaporated to dryness using a rotary evaporator (Heidoloph Instruments GMBH & C0, Schwabach, Germany) at a bath temperature of 40°C. The residue was suspended in mobile phase (1.1 mL), clarified (0.2 μm filter) and analyzed by HPLC. Liver, kidney and tumor samples were homogenized in ice-cold methanol (1.5 mL) using an IKA Ultra-Turrax T-25 homogenizer and subsequently treated as per plasma samples. All samples were analyzed by radio-HPLC on an Agilent 1100 series HPLC system (Agilent Technologies, Stockport, UK) equipped with a γ-RAM Model 3 gamma-detector (IN/US Systems inc., Florida, USA) and Laura 3 software (Lablogic, Sheffield, UK). The stationary phase comprised of a Waters μBondapak C18 reverse-phase column (300 mm × 7.8 mm). Samples were analyzed using a mobile phase comprising of Solvent A (acetonitrile/water/ethanol/acetic acid/1.0 M ammonium acetate/0.1 M sodium phosphate) (800/127/68/2/3/10) and Solvent B (acetonitrile/water/ethanol/acetic acid/1.0 M ammonium acetate/0.1 M sodium phosphate) (400/400/68/44/88/10) with a gradient of 0% B for 6 min, then 0 → 100% B in 10 min, 100% B for 0.5 min, 100 → 0% B in 1.5 min then 0% B for 2 min, delivered at a flow rate of 3 ml/min. The analysis was based on that originally described by DeGrado and co-workers (17).
HCT116 cells were grown in T150 flasks in triplicate until they reached 70% confluent and then treated with vehicle (1% DMSO in growth media) or 1μM PD0325901 in vehicle for 24 h. Cells were pulsed for 1 hr with 1.1 MBq of D4-FCH or FCH. The cells were washed 3 times in ice cold PBS, scraped into 5 ml PBS and centrifuged at 500 × g for 3 min and then re-suspended in 2 ml of ice cold methanol for HPLC analysis as described above for tissue samples.
To provide biochemical evidence that the 5′ – phosphate, was the peak identified on the HPLC chromatogram, cultured cells were treated with alkaline phosphatase as described previously (32). Briefly, HCT116 cells were grown in 100mm dishes in triplicate and incubated with 5.0 MBq of FCH for 60 min at 37°C to form the putative FCH-phosphate. The cells were washed with 5 ml ice cold PBS twice and then scraped and centrifuged at 750 × g (4°C, 3 min) in 5 ml PBS. Cells were homogenized in 1 ml 5 mM Tris-HCl buffer solution (pH 7.4) containing 50% (v/v) glycerol, 0.5 mM MgCl2, and 0.5 mM ZnCl2, and incubated with 10 units of bacterial (type III) alkaline phosphatase (Sigma) at 37°C in a shaking water bath for 30 min to dephosphorylate the FCH-phosphate. The reaction was terminated by adding ice cold methanol. Samples were processed as per plasma above and analyzed by radio-HPLC. Control experiments were performed without alkaline phosphatase.
Size-matched HCT116 tumor-bearing mice were randomised to receive daily treatment by oral gavage of vehicle (0.5% hydroxypropyl methylcellulose plus 0.2% Tween 80) or 25mg/kg (0.005 ml/g mouse) of the mitogenic extracellular kinase inhibitor, PD0325901, prepared in vehicle. D4-FCH-PET scanning was performed after 10 daily treatments with the last dose administered 1 h before scanning. After imaging, tumors were snap-frozen in liquid nitrogen and stored at −80°C for analysis of choline kinase A (CHKA) expression.
Dynamic FCH and D4-FCH imaging scans were carried out on a dedicated small animal PET scanner, quad-HIDAC (Oxford Positron Systems, Weston-on-the-Green, United Kingdom). The features of this instrument have been described previously (32). For scanning the tail veins of vehicle- or drug-treated mice were cannulated after induction of anesthesia (isofluorane/O2/N2O). The animals were placed within a thermostatically controlled jig (calibrated to provide a rectal temperature of ~37°C) and positioned prone in the scanner. FCH or D4-FCH (2.96-3.7 MBq) was injected via the tail vein cannula and scanning commenced. Dynamic scans were acquired in list-mode format over a 60 min period as previously reported (33). The acquired data were sorted into 0.5-mm sinogram bins and 19 time frames (0.5 × 0.5 × 0.5 mm voxels; 4 × 15 s, 4 × 60 s, and 11 × 300 s) for image reconstruction, which was performed by filtered back-projection using a two-dimensional Hamming filter (cut-off 0.6). The image data-sets were visualized using the Analyze software (version 6.0; Biomedical Imaging Resource, Mayo Clinic, Rochester, MN).
Cumulative images of 30-60 min dynamic data were used for visualization of radiotracer uptake and to draw regions of interest (ROI). ROI were defined manually on five adjacent tumor regions (each 0.5 mm thickness). Dynamic data from these slices were averaged for each tissue (liver, kidney, muscle, urine and tumor) and at each of the 19 time points to obtain time versus radioactivity curves (TACs). Corresponding whole body TACs representing injected radioactivity were obtained by adding together radioactivity in all 200 × 160 × 160 reconstructed voxels. Tumor radioactivity was normalized to whole body radioactivity and expressed as percentage injected dose per voxel (%ID/vox). The normalized uptake of radiotracer at 60 min (%ID/vox60) was used for subsequent comparisons. The average of the normalized maximum voxel intensity across five slices of tumor %IDvox60max was also use for comparison to account for tumor heterogeneity and existence of necrotic regions in tumor. The area under the curve (AUC) was calculated as the integral of %ID/vox from 0-60 min.
Statistical analyses were performed using the software GraphPad Prism, version 4 (GraphPad, San Diego, CA). Between-group comparisons were made using the nonparametric Mann-Whitney test. Two-tailed P value ≤ 0.05 were considered significant.
The relative rates of oxidation of the two isotopically radiolabeled choline species, FCH and D4-FCH (see structural formula in Fig. 1a) to their respective metabolites, FCH-betaine and D4-FCH-betaine was evaluated by high performance liquid chromatography (HPLC) in mouse plasma after intravenous injection of the radiotracers; the chromatographic method previously described by DeGrado and co-workers was used (17). As shown in Fig. 1b D4-FCH was markedly more stable to oxidation than FCH with ~40% conversion of D4-FCH to D4-FCH-betaine at 15 min after intravenous injection into mice compared to ~80% conversion of FCH to FCH-betaine. The time-course for in vivo oxidation is shown in Fig. 1c demonstrating overall improved stability of D4-FCH over FCH. Metabolite analysis of tissues including liver, kidney and tumor by HPLC was also accomplished. Typical HPLC chromatograms of FCH and D4-FCH and their respective metabolites in tissues are shown in Fig. S1. Choline and its metabolites lack any UV chromophore to permit presentation of chromatograms of the cold unlabelled compound simultaneously with the radioactivity chromatograms. Thus, we validated the presence of metabolites by other (chemical and biological) means. Of note the same chromatographic conditions were used for characterization of the metabolites and retention times were similar. We confirmed the identity of the phosphocholine peak biochemically by incubation of the putative phosphocholine formed in untreated HCT116 tumor cells with alkaline phosphatase Fig. S2. Chemical (potassium permanganate) and enzymatic (choline oxidase) methods were used to confirm the identity of the betaine peak (23) (data not shown). A high proportion of liver radioactivity was present as phosphocholine at 30 min post injection for both FCH and D4-FCH (Fig. 2a). An unknown metabolite (possibly the aldehyde intermediate) was observed in both the liver (7.4 ± 2.3%) and kidney (8.8 ± 0.2%) samples of D4-FCH treated mice. In contrast, this unknown metabolite was not found in liver samples of FCH treated mice and only to a smaller extent (3.3 ± 0.6%) in kidney samples. Notably 60.6 ± 3.7% of D4-FCH derived kidney radioactivity was phosphocholine compared to 31.8 ± 9.8% from FCH (P = 0.03). Conversely, most of the FCH-derived radioactivity in the kidney was in the form of FCH-betaine; 53.5 ± 5.3% compared to 20.6 ± 6.2% for D4-FCH (Fig. 2b). It could be argued that levels of betaine in plasma reflected levels in tissues such as liver and kidneys. Tumors showed a different HPLC profile compared to liver and kidneys; typical radio-HPLC chromatograms obtained from the analysis of tumor samples (30 min after intravenous injection of FCH, D4-FCH and [11C]choline) are shown in Fig. S3. In tumors, radioactivity was mainly in the form of phosphocholine in the case of D4-FCH (Fig. 2c). In contrast, both FCH and [11C]choline showed significant levels of FCH-betaine and [11C]betaine. In the context of late imaging, these results indicate that D4-FCH will be the superior radiotracer for PET imaging with an uptake profile that is easier to interpret.
FCH and D4-FCH were both rapidly taken up into tissues and retained (Fig. 3a and 3b). Tissue radioactivity increased in the order: muscle < urine < kidney < liver. Given the predominance of phosphorylation over oxidation in the liver (Fig. 2a), we found little differences in overall liver radioactivity levels between the two radiotracers. Liver radioactivity at levels 60 min after D4-FCH or FCH injection, %ID/vox60, was 20.92 ± 4.24 and 18.75 ± 4.28, respectively (Fig. 3a and b). This is also in keeping with the lower levels betaine with D4-FCH injection than with FCH injection (Fig. 2a). Thus, pharmacokinetics of the two radiotracers in liver determined by PET (which lacks chemical resolution) were similar. The lower kidney radioactivity levels for D4-FCH compared to FCH (Fig. 3a and b), on the other hand, reflect the lower oxidation potential of D4-FCH in kidneys (Fig 2b). The %ID/vox60 for FCH and D4-FCH were 15.97 ± 4.65 and 7.59 ± 3.91, respectively in kidneys (Fig. 3a and b). Urinary excretion was similar between the radiotracers. ROIs that were drawn over the bladder showed %ID/vox60 values of 5.20 ± 1.71 and 6.70 ± 0.71 for D4-FCH and FCH, respectively. Urinary metabolites comprised mainly of the unmetabolized radiotracers (data not shown). Muscle showed the lowest radiotracer levels of any tissue.
Given the relatively high systemic stability of D4-FCH and high proportion of phosphocholine metabolites, it was reassuring to observe higher tumor radiotracer uptake by PET in mice that were injected with D4-FCH compared to the FCH group. Fig. 4a shows typical (0.5 mm) transverse PET image slices demonstrating accumulation of FCH and D4-FCH in human melanoma SKMEL-28 xenografts. In this mouse model, the tumor signal-to-background contrast was qualitatively superior in the D4-FCH PET images compared to FCH images. Both radiotracers had similar tumor kinetic profiles detected by PET (Fig. 4b). The kinetics were characterized by rapid tumor influx with peak radioactivity at ~1 min (Fig. 4b). Tumor levels then equilibrated until ~5 min followed by a plateau. The delivery and retention of D4-FCH were quantitatively higher than those for FCH (Fig. 4c). The %ID/vox60 for D4-FCH and FCH were 7.43 ± 0.47 and 5.50 ± 0.49, respectively (P=0.04). Because tumors often present with heterogeneous population of cells, we exploited another imaging variable that is probably less sensitive to experimental noise – an average of the maximum pixel %ID/vox60 across 5 slices (%IDvox60max). This variable was also significantly higher for D4-FCH (P=0.05; Fig. 4c). Furthermore, tumor area under the time versus radioactivity curve (AUC) was higher for D4-FCH mice than FCH (P =0.02). Although the 30 min time point was selected for a more detailed analysis of tissue samples, it should be noted that the percentage of parent compound in plasma was consistently higher for D4-FCH compared to FCH at earlier time points. Regarding imaging, tumor uptake for both radiotracers was similar at the early (15 min) and late (60 min) time points (Supplementary Table1). The earlier time points may be appropriate for pelvic imaging.
Having demonstrated that D4-FCH was a more stable fluorinated-choline analog for in vivo studies, we wanted to investigate if this radiotracer could be used to measure response to therapy. We chose to perform these studies in a reproducible tumor model system in which treatment outcomes have been previously characterized, i.e., the human colon carcinoma xenograft HCT116 treated with PD0325901 daily for 10 days (31). Drug treatment led to tumor stasis (reduction in tumor size by only 12.2% at day 10 compared to the pretreatment group); tumors of vehicle-treated mice increased by 375%. Tumor D4-FCH levels in PD0325901-treated mice peaked at approximately the same time as those of vehicle-treated ones, however, there was a marked reduction in radiotracer retention in the treated tumors (Fig. 5a). All imaging variables decreased after 10 days of drug treatment (P=0.05, Fig. 5b). This indicates that D4-FCH can be used to detect treatment response even under conditions where large changes in tumor size reduction are not seen (31). To understand the biomarker changes, we examined the intrinsic cellular effect of PD0325901 on D4-FCH-phosphocholine formation by treating exponentially growing HCT116 cells in culture with PD0325901 for 24 h and measuring the 60-min uptake of D4-FCH in vitro. As shown in Fig. 5c., PD0325901 significantly inhibited D4-FCH-phosphocholine formation in drug-treated cells demonstrating that the effect of the drug in tumors is likely due to cellular effects on choline metabolism rather than hemodynamic effects.
To understand further the mechanisms regulating D4-FCH uptake with drug treatment, we assessed changes in CHKA expression in PD0325901- and vehicle-treated tumors excised after PET scanning. A significant reduction in CHKA protein expression was seen in vivo at day 10 (P=0.03) following PD0325901 treatment (Fig. 6) indicating that reduced CHKA expression contributed to the lower D4-FCH uptake in drug-treated tumors. The drug-induced reduction of CHKA expression also occurred in vitro in exponentially growing cells treated with PD0325901 (data not shown).
We have designed, synthesized and established utility of a novel radiolabeled choline analog for tumor imaging. Many cancers have elevated phospholipid biosynthesis to meet the demand of rapid tumor cell growth, and in these cancers, phosphocholine serves as an important mediator of transmembrane signaling (34, 35). Choline is taken into cells by a specific transport mechanism and phosphorylated by choline kinase which is constitutively active in many cancer cells (10, 36, 37). This metabolic process serves to trap choline in cells as phosphocholine, thus, radiolabeled analogs of choline are being explored as radiotracers for imaging tumors by PET. FCH, originally developed by De Grado and co-workers, is currently been evaluated for imaging prostate cancer, and other malignancies (17, 22, 38, 39). In this study, we report the development of a more stable FCH analog, D4-FCH, for cancer detection in which substitution of deuterium for hydrogen on the ethyl alcohol portion of choline results in a large observed isotope effect in the oxidation of choline to betaine by choline oxidase (25-27). Kinetic studies indicate that the magnitude of the 1H/2D isotope effect is the result of environmentally enhanced quantum tunneling involving a highly pre-organized enzyme active site, where the probability of tunneling decreases with the increased mass of deuterium in a molecule (24). The biological effect of this substitution is to reduce oxidation and increase the net availability of the parent tracer for phosphorylation and trapping within cells leading to improved signal-to-background contrast for PET imaging of tumors in vivo (40-42)
Improved stability of D4-FCH over FCH for late imaging after clearance was supported initially (0-30 min) by the higher proportion of parent radiotracer in plasma, but this difference appeared to have been lost by 60 min when the parent radiotracers had been completely metabolized (Fig. 1c). We interpret this finding as a model limitation: the capacity of rodents to metabolize choline analogs (43) is substantially higher than that of humans (23) and so we expect the early differential between the two radiotracers to be maintained in humans. Improved stability of D4-FCH over FCH was demonstrated as reduced levels of D4-FCH oxidation products in plasma of mice injected intravenously with the radiotracers. The oxidation product of D4-FCH was also lower in at least one of two major organs responsible for choline oxidation/choline oxidase activity - liver and kidney (23, 39, 43). The reduced oxidation of D4-FCH resulted, for instance, in a 2-fold lower total radioactivity level in kidney. Tissue HPLC analysis also confirmed that most of the D4-FCH was trapped specifically in the form of phosphocholine whereas betaine was the main metabolite from FCH in kidneys. It is possible that kidneys have a lower capacity for phosphorylating the free D4-FCH. In liver, on the other hand, unmetabolized FCH and D4-FCH were rapidly phosphorylated and the predominance of phosphorylation may explain the similar levels of liver radioactivity for both radiotracers. Notably, betaine levels in liver were higher for FCH than D4-FCH. Betaine, like phosphocholine, is a charged molecule and is also expected to be trapped in cells to a reasonable extent; unlike phosphocholine, however, it is exported into circulation as shown in this study.
One advantage of using radiolabeled choline analogs for pelvic imaging is their low renal elimination. Urine levels of choline analogs result largely from unmetabolized parent radiotracer (data not shown) as betaine analogs are efficiently reabsorbed in the kidney tubules (44, 45). Due to their ionization properties, oxidation intermediates (such as aldehyde) are unlikely to be re-absorbed efficiently within the kidney tubules and could contribute to urinary radioactivity (45). It was a concern that the high stability of D4-FCH, and hence higher levels of parent radiotracer in plasma will lead to high levels of radioactivity in the urine. Compared to [11C]choline, FCH was found to have less desirable urinary excretion properties. We have not been able to demonstrate that D4-FCH used under the same conditions will overcome this limitation. It may be possible, however, for patients to void urine at late time points to reduce bladder radioactivity.
Of interest, both FCH and [11C]choline showed high levels of betaine metabolites in tumor, whereas very little betaine metabolite was found following D4-FCH injection. The improved stability of D4-FCH will permit late imaging to be performed with confidence since metabolism will be less of a concern. In a late imaging protocol, voiding can further reduce the spill-over contribution of bladder radioactivity. Improved stability of D4-FCH also led to increased tumor radioactivity by 1.3-fold compared to FCH. This increased tumor retention could be ascribed to increased availability of substrate for phosphorylation and reduced competing (oxidation) reactions that leads to betaine formation and elimination of the latter. Having demonstrated superior pharmacokinetics, we further established utility of D4-FCH for response monitoring. D4-FCH was found to be a useful radiotracer for monitoring the effect of MEK inhibition by PD0325901 in a model where the drug effects are largely cytostatic at the dose used. The reduction in radiotracer uptake following drug treatment in vivo was intrinsic to changes in cellular biochemistry as demonstrated in vitro and could be ascribed at least in part to reduced CHKA expression.
In translating our findings into clinical imaging, it should be noted that oxidation of choline is faster in rodents (38) compared to humans (23). Thus, we expect the rate of D4-FCH oxidation to be even lower in humans; this may lead to further improvements in detection sensitivity in humans consequent to the higher overall levels of phosphorylated D4-FCH. In conclusion, we have demonstrated that the novel radiotracer, D4-FCH, has improved stability and sensitivity for detection of choline metabolism in vivo. The radiotracer also has potential for detecting response to anti-cancer drug treatment. These promising attributes warrant further pre-clinical and clinical development of D4-FCH.
Funding support from Cancer Research UK & Engineering & Physical Sciences Research Council (C2536/A10337), and the UK Medical Research Council (U1200.005.00001.01).
Disclosure of Potential Conflict of Interest
The authors are considering filing a patent on this invention.