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Basic Science Investigations |
vß3 Expression Using 64Cu-Labeled Tetrameric RGD Peptide
1 Molecular Imaging Program at Stanford (MIPS), Department of Radiology and Bio-X Program, Stanford University, Stanford, California
2 Radioisotopes Program, Pacific Northwest National Laboratory, Richland, Washington
3 Industrial and Physical Pharmacy, School of Health Sciences, Purdue University, West Lafayette, Indiana
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ABSTRACT |
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 TOP ABSTRACT INTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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vß3 plays a critical role in tumor-induced angiogenesis and metastasis and has become a promising diagnostic indicator and therapeutic target for various solid tumors. Radiolabeled RGD peptides that are integrin specific can be used for noninvasive imaging of integrin expression level as well as for integrin-targeted radionuclide therapy. Methods: In this study we developed a tetrameric RGD peptide tracer 64Cu-DOTA-E{E[c(RGDfK)]2}2 (DOTA is 1,4,7,10-tetraazacyclododecane-N,N',N'',N'''-tetraacetic acid) for PET imaging of integrin vß3 expression in female athymic nude mice bearing the subcutaneous UG87MG glioma xenografts. Results: The RGD tetramer showed significantly higher integrin binding affinity than the corresponding monomeric and dimeric RGD analogs, most likely due to a polyvalency effect. The radiolabeled peptide showed rapid blood clearance (0.61 ± 0.01 %ID/g at 30 min and 0.21 ± 0.01 %ID/g at 4 h after injection, respectively [%ID/g is percentage injected dose per gram]) and predominantly renal excretion. Tumor uptake was rapid and high, and the tumor washout was slow (9.93 ± 1.05 %ID/g at 30 min after injection and 4.56 ± 0.51 %ID/g at 24 h after injection). The metabolic stability of 64Cu-DOTA-E{E[c(RGDfK)]2}2 was determined in mouse blood, urine, and liver and kidney homogenates at different times after tracer injection. The average fractions of intact tracer in these organs at 1 h were approximately 70%, 58%, 51%, and 26%, respectively. Noninvasive microPET studies showed significant tumor uptake and good contrast in the subcutaneous tumor-bearing mice, which agreed well with the biodistribution results. Integrin vß3 specificity was demonstrated by successful blocking of tumor uptake of 64Cu-DOTA-E{E[c(RGDfK)]2}2 in the presence of excess c(RGDyK) at 1 h after injection. The highest absorbed radiation doses determined for the human reference adult were received by the urinary bladder wall (0.262 mGy/MBq), kidneys (0.0296 mGy/MBq), and liver (0.0242 mGy/MBq). The average effective dose resulting from a single 64Cu-DOTA-E{E[c(RGDfK)]2}2 injection was estimated to be 0.0164 mSv/MBq. Conclusion: The high integrin and avidity and favorable biokinetics make 64Cu-DOTA-E{E[c(RGDfK)]2}2 a promising agent for peptide receptor radionuclide imaging and therapy of integrin-positive tumors.
Key Words: tumor angiogenesis • integrin • RGD peptide • microPET • multimeric peptide • 64Cu
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INTRODUCTION |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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vß3, which is not readily detectable in quiescent vessels but becomes highly expressed in angiogenic vessels and tumor cells (8,9). The vß3 integrin is necessary for the formation, survival, and maturation of newly formed blood vessels (10) and its expression correlates with tumor grade and histologic type (11).
Recent data both in preclinical tumor models and in phase I/II clinical trials suggest that antagonists of vß3 integrin inhibit tumor angiogenesis and metastasis (12,13). The ability to noninvasively visualize and quantify vß3 integrin expression level provides opportunities to document tumor (tumor cells and sprouting tumor vasculature) receptor expression, to more appropriately select patients considered for antiintegrin treatment, and to monitor treatment efficacy in integrin-positive patients. Several molecular probes have been developed for MRI (14), ultrasound (15), optical imaging (16), PET, and SPECT applications (17). Although most of the RGD peptide-based probes could target tumors by binding integrin vß3, they suffer from modest tumor uptake and unfavorable pharmacokinetics that limit their applications for imaging and internal radiotherapy.
We and others have reported radiolabeled RGD-containing peptide dimers as radiopharmaceuticals for diagnosis of rapidly growing solid tumors (18–23). It was hypothesized that the receptor binding of one RGD cyclic peptide will significantly enhance the "local concentration" of the other RGD peptide in the vicinity of the receptor, which may lead to a faster rate of receptor binding or a slower rate of dissociation of radiolabeled RGD dimer from the integrin vß3 and result in higher uptake and longer retention time in the tumor. A multimeric RGD peptide with >2 repeating cyclic RGD units is thus expected to further enhance the affinity of the receptor–ligand interactions even more significantly through the phenomenon of a polyvalency effect. The apparent increase in molecular size may also prolong circulation time of the multimer and consequently reduce tumor washout rate.
In this investigation we applied the polyvalency principle and developed a novel tetrameric RGD peptide using glutamate as the branching unit. The resulting RGD peptide tetramer was conjugated with the macrocylic chelator 1,4,7,10-tetraazacyclododecane-N,N',N'',N'''-tetraacetic acid (DOTA) and labeled with 64Cu for microPET imaging of integrin expression in a subcutaneous U87MG glioblastoma xenograft model in female athymic nude mice. The aim of this study was to investigate integrin targeting characteristics of 64Cu-DOTA-E{E[c(RGDfK)]2}2 as a potential agent for diagnosis and receptor-mediated internal radiotherapy of integrin receptor–expressing tumors.
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MATERIALS AND METHODS |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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Analytic as well as semipreparative reversed-phase high-performance liquid chromatography (RP-HPLC) were performed on a Dionex 680 chromatography system with a UVD 170U absorbance detector and model 105S single-channel radiation detector (Carroll & Ramsey Associates). The recorded data were processed using Chromeleon version 6.50 software. Isolation of DOTA-conjugated peptide and 64Cu-labeled peptide was performed using a Vydac protein and peptide column (218TP510; 5 µm, 250 x 10 mm). The flow was 5 mL/min, with the mobile phase starting from 95% solvent A (0.1% TFA in water) and 5% solvent B (0.1% TFA in acetonitrile) (0–3 min) to 35% solvent A and 65% solvent B at 33 min. The analytic HPLC was performed using the same gradient system, but with a Vydac 218TP54 column (5 µm, 250 x 4.6 mm) and flow of 1 mL/min. Ultraviolet (UV) absorbance was monitored at 218 nm.
Preparation of Boc-Glu(OSu)-OSu
To a solution of the Boc-protected glutamic acid (0.247 g, 1.0 mmol) in 5 mL of N,N-dimethylforamide (DMF) were added N-hydroxysuccinimide (NHS) (0.253 g, 2.2 mmol) and DCC (0.453 g, 2.2 mmol). The resulting mixture was stirred at room temperature for 10 h. The dicyclohexylurea (DCU) by-product was filtered off. The filtrate was evaporated to dryness under vacuum to give a crude product, which was then taken up in 3 mL of methylene chloride. The insoluble solid was filtered off. The filtrate was concentrated to about 1 mL. The solution was added dropwise into 30 mL of ether. The desired product was precipitated as white solid, which was dried in vacuo. The yield was 0.27 g (
61%). 1H NMR (CDCl3) 
-5.23 (br s, 1H, NH), 4.82 (m, 1H, CH), 2.85 (m, 8H, succinimide group), 2.44–2.25 (m, 2H, CH2CO), 1.52 (m, 2H, CH2CH2CO), 1.46 (s, 9H, t-Bu).
Preparation of Cyclic RGD Peptide Tetramer: E{E[c(RGDfK)]2}2
To a solution of the Boc-protected glutamic acid activated ester Boc-E(OSu)2 (4.4 mg, 0.01 mmol) in anhydrous DMF (1 mL) was added the cyclic RGD peptide dimer E[c(RGDfK)]2 (39.4 mg, 0.03 mmol). The pH of the resulting mixture was adjusted to 8.5–9.0 with diisopropylethyl amine (DIPEA). The reaction was stirred at room temperature overnight and the desired product, Boc-E{E[c(RGDfK)]2}2, was isolated by semipreparative HPLC. The collected fractions were combined and lyophilized to give a fluffy white powder. The yield was 15 mg (53%). Electrospray ionization mass spectroscopy (ESI-MS) (positive mode): m/z = 2,848 for [M + H]+ (C128H187N39O56, calculated molecular weight [MW] = 2,847). The Boc-group was readily removed by treating Boc-E{E[c(RGDfK)]2}2 with anhydrous TFA for 5 min. The crude product was purified by HPLC. The collected fractions were combined and lyophilized to afford E{E[c(RGDfK)]2}2 as a white powder. The yield was 98%. ESI-MS (positive mode): m/z = 2,748 for [M + H]+ (C123H181N39O34, calculated MW = 2,747).
DOTA Conjugation and 64Cu Radiolabeling
DOTA-E{E[c(RGDfK)]2}2 was synthesized in a manner similar to that described before (18,26,28,29). Briefly, DOTA was activated by EDC and SNHS at pH 5.5 for 30 min with a molar ratio of DOTA:EDC:SNHS = 10:5:4. The DOTA-OSSu reaction mixture (15 µmol, calculated on the basis of SNHS) was cooled to 4°C and added to E{E[c(RGDfK)]2}2 (2 mg, 0.6 µmol) dissolved in 500 µL of water. The reaction mixture was adjusted to pH 8.5 with 0.1N of NaOH and was allowed to incubate overnight at 4°C. The DOTA-coupled peptide was purified by semipreparative HPLC. The peak containing the tetramer conjugate was collected, lyophilized, and dissolved in water (2 mg/mL) for use in radiolabeling reactions. The yield was 1.4 mg (75%). Matrix-assisted laser desorption ionization time-of-flight mass spectroscopy (MALDI-TOF MS): m/z = 3,135.3 for [M + H]+ (C139H205N43O41, calculated MW = 3,135.5)
DOTA-E{E[c(RGDfK)]2}2 was radiolabeled with 64Cu to obtain 64Cu-DOTA-E{E[c(RGDfK)]2}2. In brief, 64CuCl2 (74 MBq) was diluted in 400 µL of 0.1 mol/L sodium acetate and added to the DOTA conjugate (5 µg peptide per mCi 64Cu). The reaction mixture was incubated for 1 h at 50°C. 64Cu-DOTA-E{E[c(RGDfK)]2}2 was then purified by semipreparative HPLC. The radioactive peak containing 64Cu-DOTA-E{E[c(RGDfK)]2}2 was collected, the solvent was evaporated, and the activity was reconstituted in phosphate-buffered saline (PBS) and passed through a 0.22-µm syringe filter for in vivo animal experiments.
Octanol–Water Partition Coefficient
Approximately 111 kBq of 64Cu-DOTA-E{E[c(RGDfK)]2}2 in 500 µL of PBS (pH 7.4) were added to 500 µL of octanol in an Eppendorf microcentrifuge tube. The 2 layers were mixed for 5 min at room temperature, the tubes were centrifuged at 12,500 rpm for 5 min (model 5415R Eppendorf microcentrifuge; Brinkman), and 200-µL aliquots of both layers were counted in a 
-counter (Packard Instruments). The experiment was repeated 3 times.
Cell Integrin Receptor-Binding Assay
In vitro integrin-binding affinities and specificities of DOTA-conjugated RGD peptides were assessed via displacement cell-binding assays using 125I-echistatin as the integrin-specific radioligand. Experiments were performed on human glioblastoma U87MG cell line by modification of a method previously described (28). Cells were grown in Dulbecco’s medium (Gibco) supplemented with 10% fetal bovine serum (FBS), 100 IU/mL penicillin, and 100 µg/mL streptomycin (Invitrogen Co.), at 37°C in a humidified atmosphere containing 5% CO2. During the cell-binding assay experiment, the cells were harvested, washed twice with PBS, and resuspended (2 x 106 cells/mL) in binding buffer (20 mmol/L Tris, pH 7.4, 150 mmol/L NaCl, 2 mmol/L CaCl2, 1 mmol/L MgCl2, 1 mmol/L MnCl2, 0.1% bovine serum albumin). Filter multiscreen DV plates (96-well; pore size, 0.65 µm; Millipore) were seeded with 105 cells and incubated with 125I-echistatin (30,000 cpm/well) in the presence of increasing concentrations of different RGD peptide analogs (0–1,000 nmol/L). The total incubation volume was adjusted to 200 µL. After the cells were incubated for 2 h at room temperature, the plates were filtered through a multiscreen vacuum manifold and washed twice with cold binding buffer. The hydrophilic polyvinylidenedifluoride (PVDF) filters were collected and the radioactivity was determined using a NaI(Tl) -counter (Packard Instruments). The best-fit 50% inhibitory concentration (IC50) values for the U87MG cells were calculated by fitting the data by nonlinear regression using GraphPad Prism (GraphPad Software, Inc.). Experiments were performed twice with triplicate samples.
Animal Models
Animal procedures were performed according to a protocol approved by Stanford University Institutional Animal Care and Use Committee. Human brain cancer carcinoma xenografts were induced by subcutaneous injection of 107 U87MG cells into the right front leg of female athymic nude mice. Three weeks after inoculation of the tumor cells, when the tumor reached 0.4–0.6 cm in diameter, the mice were used for biodistribution and microPET (Concorde Microsystems Inc.) experiments.
In Vivo Metabolic Stability Studies
The metabolic stability of 64Cu-DOTA-E{E[c(RGDfK)]2}2 was evaluated in normal athymic nude mice using the method described in the literature with some modifications (29). Animals were sacrificed and dissected at 30 min, 1 h, and 2 h after injection of 7.4 MBq of activity into the tail vein. Blood was immediately centrifuged for 5 min at 15,000g. Liver and kidneys were homogenized, extracted with 500 µL PBS, and centrifuged at 15,000g for 5 min. After removal of the supernatants, the pellets were washed with 1 mL PBS. For each sample, supernatants of both centrifugation steps of blood, liver, and kidneys were combined and passed through Sep-Pak C-18 cartridges. The urine sample was diluted with 1 mL PBS and passed through a C-18 cartridge. The cartridges were washed with 2 mL of water and eluted with 2 mL acetonitrile containing 0.1% TFA. After evaporation of the solvent, the residues were redissolved in 1 mL PBS. Aliquots of 400 µL were injected onto analytic RP-HPLC.
Biodistribution Studies
Female nude mice bearing tumor xenography of human glioblastoma U87MG were injected with 0.74–1.11 MBq of 64Cu-DOTA-E{E[c(RGDfK)]2}2. The mice were sacrificed and dissected at 30 min, 1, 2, 4, and 24 h after injection of 64Cu-labeled tetrameric RGD peptide. The blocking experiment was performed by coinjecting radiotracer with a saturating dose of c(RGDyK) (10 mg/kg) and sacrificed at 1 h after injection. Blood, tumor, major organs, and tissues were collected and wet weighted. The radioactivity in the tissues was measured using a -counter. The results are presented as the percentage injected dose per gram (%ID/g). For each mouse, the radioactivity of the tissue samples was calibrated against a known aliquot of the injectate and normalized to a body mass of 20 g. Values are expressed as mean ± SD for a group of 3 animals.
Calibration of microPET
Scanner activity calibration was performed to map between microPET image units and units of radioactivity concentration. A preweighed 50-mL centrifuge tube was filled with distilled water and 64CuCl2 (9.3 MBq [250 µCi] as determined by the dose calibrator) was used to simulate the whole body of the mouse. This tube was weighed, centered in the scanner aperture, and imaged for a 30-min static image, single bed position. From the sample weight and assuming a density of 1 g/mL, the activity concentration in the bottle was calculated in units of µCi/mL. Eight planes were acquired in the coronal section. A rectangular region of interest (ROI) (counts/pixel/s) was drawn on the middle of 8 coronal planes. Using these data, a calibration factor (C) was obtained by dividing the known radioactivity in the cylinder (µCi/mL) by the image ROI. This calibration factor was determined periodically and did not vary significantly with time.
microPET Studies
PET of tumor-bearing mice was performed on a microPET R4 rodent model scanner (Concorde Microsystems Inc.). The scanner has computer-controlled vertical and horizontal bed motion, with an effective axial field of view (FOV) of 7.8 cm and a transaxial FOV of 10 cm. U87MG tumor-bearing mice (n = 3) were imaged in the prone position in the microPET scanner. The mice were injected with about 9.3 MBq of 64Cu-DOTA-E{E[c(RGDfK)]2}2 via the tail vein and then anesthetized with 2% isoflurane and placed near the center of the FOV of the microPET where the highest image resolution and sensitivity are obtained. The 10-min static scans were obtained at 15 min, 30 min and 1, 2, 4, and 18 h after injection. The images were reconstructed by a 2-dimensional ordered-subsets expectation maximum (OSEM) algorithm. No correction was necessary for attenuation and scattering. At each microPET scan, ROIs were drawn over each tumor, normal tissue, and major organs on decay-corrected whole-body coronal images. The average radioactivity concentration (accumulation) within a tumor or an organ was obtained from mean pixel values within the multiple ROI volumes, which were converted to counts/mL/min by using the calibration constant C. Assuming a tissue density of 1 g/mL, the ROIs were then converted to counts/g/min, and then divided by the administered activity to obtain an imaging ROI-derived percentage administered activity per gram of tissue (%ID/g). For a receptor-blocking experiment, mice bearing U87MG tumors on the right front leg were imaged at 1 h (10-min static scan) after administration of 9.3 MBq of 64Cu-DOTA-E{E[c(RGDfK)]2}2 coinjected with 10 mg/kg c(RGDyK).
Radiation Dose Extrapolations to the Human
Radiation-absorbed doses were not estimated for our U87MG tumor-bearing mice. However, the mouse biodistribution data (uptake, retention, and clearance) were used to project radiation-absorbed doses that could be expected in human subjects administered 64Cu-DOTA-E{E[c(RGDfK)]2}2. Projected radiation-absorbed doses for humans were made by assuming that, for the purpose of this exercise, the metabolism rates and pharmacokinetics of 64Cu-DOTA-E{E[c(RGDfK)]2}2 in man and mouse were equivalent. Therefore, the biodistribution data were assumed to apply to a reference adult human subject. Time–activity curves were generated from the mean values obtained in mice for each organ of interest. We then calculated source organ residence times for the human model by integrating a monoexponential fit to the experimental biodistribution data for each organ or tissue by standard methods. The whole-body time–activity curve was integrated by fitting the whole-body retention data to a biphasic exponential decay curve, which represented the retention data more closely than a single exponential equation. The source organ residence times obtained forthwith were used with a standard quantitation platform Organ Level Internal Dose Assessment (OLINDA; Vanderbilt University) (30). Note that the residence time for the urinary bladder was calculated without incorporating a dynamic bladder model.
Statistical Analysis
The data were expressed as means ± SD. One-way ANOVA was used for statistical evaluation. Means were compared using the Student t test. P values < 0.05 were considered significant.
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RESULTS |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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v integrin were performed using v integrin–positive U87MG cells rather than isolated receptors vß3. Binding on the cell membrane allows cross-linking and integrin receptor multimerization, by which multivalent binding and clustering of receptor is studied in the natural context of the integrin (31). We compared the receptor-binding affinity of DOTA conjugated tetrameric RGD peptide with that of unlabeled echistatin, E{E[c(RGDfK)]2}2, E[c(RGDfK)]2, and DOTA-E[c(RGDfK)]2 by performing competitive displacement studies with 125I-echistatin (Fig. 2). All the peptides inhibited the binding of 125I-echistatin to v integrin–positive U87MG cells. The IC50 values for echistatin, E{E[c(RGDfK)]2}2, and E[c(RGDfK)]2, were 1.2 ± 0.1, 15.0 ± 1.1, and 32.2 ± 2.1 nmol/L, respectively. DOTA chelation had minimal effect on the receptor avidity of dimeric and tetrameric RGDs. The IC50 values for DOTA-E{E[c(RGDfK)]2}2 and DOTA-E[c(RGDfK)]2 were 16.6 ± 1.3 and 48.4 ± 2.8 nmol/L, respectively. The cell-binding assay demonstrated that RGD tetramer had about 3-fold and almost 10-fold higher integrin avidity than the corresponding dimeric (19) and monomeric (25) RGD peptide analogs, respectively.
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vß3-positive U87MG tumors was observed at early time points (9.93 ± 1.05 %ID/g at 30 min after injection). Tumor uptake slowly decreased to 7.61 ± 0.68 %ID/g at 2 h after injection, and 4.56 ± 0.51 %ID/g over 24 h. The biologic retention half-time t1/2 of the 64Cu-labeled tetrameric RGD peptide tracer was 4.3 h (R2 = 0.99) in the tumor. The renal associated activity was initially high (9.02 ± 0.56 %ID/g, 30 min after injection), but fell to 2.83 ± 0.22 %ID/g at the end of 24 h (biologic retention t1/2 = 1.72 h, R2 = 0.99) (Table 1). Moderate liver activity accumulation (e.g., 4.38 ± 0.39 %ID/g at 1 h and 2.34 ± 0.18 %ID/g, respectively) was also observed at all times.
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vß3 positive, with 64Cu-DOTA-E{E[c(RGDfK)]2}2 and measuring the biodistribution at 1 h after injection A significant decrease of radioactivity in all dissected tissues is shown in Figure 4B. Uptake in tumor was reduced most markedly from 9.70 %ID/g to 1.75 %ID/g. This experiment showed that the uptake and retention of 64Cu-DOTA-E{E[c(RGDfK)]2}2 can be blocked in the presence of excess of nonradioactive RGD peptide in the U87MG tumor as well as in other organs, except blood and kidney. This simple blocking experiment does not allow us to conclude with absolute certainty that tumor uptake of 64Cu-DOTA-E{E[c(RGDfK)]2}2 is attributed to specific peptide–receptor interaction unless dose-dependent inhibition of tumor uptake is observed by coinjecting varying amounts of competing agents. A comparison of the kinetics of excretion of 64Cu-DOTA-E[c(RGDfK)]2 and 64Cu-DOTA-E{E[c(RGDfK)]2}2 from the blood, liver, kidneys, and U87MG tumors is shown in Figure 5. Both tracers demonstrated rapid blood clearance with the tetramer (biologic t1/2 = 0.56 h; R2 = 0.99) slower than the dimer (biologic t1/2 = 0.20 h; R2 = 0.99). The renal uptake of the tetramer was significantly higher than that of the dimer at all time points (P < 0.0001), presumably because of the charge differences of these 2 conjugates. No significant difference was seen between 2 tracers in the liver uptake at early time points (P > 0.1), but the tetramer displayed persistent activity accumulation in the liver while liver activity for the dimer was slowly excreted. The relatively lipophilic character of the cyclic RGDfK tetramer (log P = –1.6 ± 0.1) may be responsible for the hepatic residualization of this tracer. The uptake for 64Cu-DOTA-E{E[c(RGDfK)]2}2 in the integrin-positive U87MG tumor was more than 2-fold higher than for 64Cu-DOTA-E[c(RGDfK)]2 (P < 0.001). Altogether, the prolonged tumor retention and rapid clearance from nontarget organs led to very high tumor-to-nontumor ratios for the tetrameric RGD peptide tracer (e.g., at 2 h time point, tumor-to-blood ratio = 34.8 ± 2.7; tumor-to-muscle ratio = 15.9 ± 1.2; tumor-to-liver ratio = 2.32 ± 0.18; tumor-to-kidney ratio = 1.54 ± 0.12; and tumor-to-small intestine ratio = 3.95 ± 0.30).
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v integrin expression level and an intact blood–brain barrier (BBB). Comparison of tumor uptakes in mice with and without coinjection of blocking dose of nonradioactive RGD peptide c(RGDyK) is illustrated in Figure 6C. Tumor-to-background contrasts at 1 h after injection for the control group and blocked group were 8.7 ± 1.5 and 2.3 ± 0.6, respectively.
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DISCUSSION |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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vß3–positive tumors.
A variety of radiolabeled peptides are being evaluated for tumor localization and therapy. Radiolabeled RGD peptides are of particular interest because they bind to the integrin vß3 overexpressed on newly formed blood vessels and cells of many common cancer types. However, most small cyclic RGD peptides tracers result in fast blood clearance accompanied by low tumor uptake and rapid tumor washout, presumably due to suboptimal receptor-binding affinity and inadequate contact with cell-surface integrin receptors (17,24–29,32–34).
We and others (18–23) have previously applied the concept of bivalency to develop dimeric RGD peptides for improved tumor targeting over that of the corresponding monomeric RGD peptide analogs. In principle, the introduction of the homogeneous dimeric RGD peptide system is expected to improve integrin targeting by cooperative receptor interactions and receptor shielding to endogenous competition. Dimeric RGD peptide E[c(RGDfK)]2 was conjugated with DOTA or HYNIC, which enables labeling with 111In (21), 90Y (21,23), 64Cu (19), and 99mTc (18,22). The dimeric RGD peptide tracer showed higher receptor-binding affinity and specificity for integrin vß3 in vitro and enhanced tumor uptake and retention in vivo as compared with the monomeric RGD peptide analog. A single injection of 90Y-DOTA-E[c(RGDfK)]2 at maximum tolerated dose caused a significant delay in tumor growth in a small subcutaneous OVCAR-3 ovarian xenograft tumor model (21). We found that replacing D-phenylalanine with D-tyrosine increased the hydrophilicity of the dimeric RGD peptide and, consequently, resulted in increased integrin-mediated tumor uptake and more favorable biokinetics in an orthotopic MDA-MB-435 breast cancer model (19). E[c(RGDyK)]2 was also labeled with 18F by using a prosthetic 4-18F-fluorobenzoyl group and showed significantly higher tumor uptake and prolonged tumor retention in comparison with the 18F-labeled monomeric RGD peptide because of the synergistic effect of bivalency and improved pharmacokinetics (20).
Although the dimeric RGD peptide tracers had some incremental improvement on tumor targeting and pharmacokinetics as compared with the monomeric RGD peptide analogs, the intermediate tumor uptake and persistent renal activity accumulation of this type of radioligand prevent their translation into human beings for diagnostic or therapeutic applications.
We hypothesize that multimerization to introduce tetrameric RGD peptides might further increase the receptor-binding affinity presumably because of the polyvalency effect. In this study, we designed a new tetrameric RGD peptide with repeating c(RGDfK) units connected through glutamate linkers. A cell receptor–binding assay using integrin-positive U87MG cells and 125I-echistatin as the radioligand found integrin avidity of E{E[c(RGDfK)]2}2 > E[c(RGDfK)]2 > c(RGDfK) (Fig. 2). DOTA conjugation had a minimal effect on the integrin affinity of the RGD peptides. When applied to the subcutaneous U87MG glioblastoma xenogarft model, 64Cu-DOTA-E{E[c(RGDfK)]2}2 showed high tumor uptake and primarily renal and secondarily hepatic excretion routes (Figs. 4 and 6). The initial high tumor uptake might be attributed to the high integrin affinity of the tracer. The increased molecular size resulting in longer blood circulation time might be responsible for the prolonged tumor retention. At any given time, the in vivo tumor signal not only is attributed to specific binding but also presents contributions from nonspecific binding, free ligand in tissue, and intravascular activity. Kinetic modeling (e.g., Logan plot) (35) of the noninvasive dynamic PET data may be applied to directly measure affinity constants and binding potential in vivo.
Kidney retention of 64Cu was much longer for 64Cu-DOTA-E{E[c(RGDfK)]2}2 than for 64Cu-DOTA-E[c(RGDfK)]2 (Fig. 5). Differences in renal uptake and excretion may be related to the charge differences of these 2 conjugates. The tetrameric RGD peptide tracer is more positively charged than the dimeric RGD peptide tracer because of the presence of more secondary amino groups, similar to what is observed for the difference between dimers and monomers (18–23). The positively charged radiopeptides or metabolites are usually retained in the kidney after resorption by renal tubular cells and lysosomal proteolysis (36). We also note from Figure 5 that the enhanced tumor uptake of the tetramer compared with the dimer is accompanied by a similar increase in renal uptake. Thus, tumor-to-kidney ratios do not increase significantly when using the tetrameric RGD peptide tracer and, consequently, the therapeutic window may not be increased and the advantage of a tetramer over a dimer might be modest. Blocking cationic binding sites in the kidneys with cationic amino acid infusion was reported to reduce renal uptake without compromising the tumor activity accumulation in both mice and humans (37). We expect that renal uptake of 64Cu-DOTA-E{E[c(RGDfK)]2}2 may be blocked by coadministration of D- or L-lysines (37). Modification of DOTA-E{E[c(RGDfK)]2}2 conjugation by inserting a pharmacokinetic modifier to make the 64Cu-labeled complex neutral or negatively charged may also improve the biokinetics of the tracer. Tetrameric RGD peptide tracer had moderate but persistent liver uptake. Although the factors that exert this influence are not fully understood, it is clear that the charge, lipophilicity, and stability of the copper complex play major roles. Our pervious experience with 64Cu-labeled dimeric RGD peptide found that replacing D-Phe with D-Tyr increased the hydrophilicity of the resulting radiotracer and subsequently reduced liver uptake (19). We suggest that 64Cu-DOTA-E{E[c(RGDyK)]2}2 may exhibit less liver uptake than 64Cu-DOTA-E{E[c(RGDfK)]2}2.
In addition to U87MG tumor, 64Cu-labeled RGD tetramer uptake in some normal organs and tissues was also inhibited by coadministration of an excess amount of monomeric RGD peptide c(RGDyK) (Fig. 4B). Western blot analysis of the tissue lysates suggested that these organs express a low amount of integrin vß3 (data not shown). Whether integrin-mediated localization of 64Cu-DOTA-E{E[c(RGDyK)]2}2 in nontumor tissues will affect its imaging as well therapeutic application requires further investigation.
The OLINDA software (30), as a replacement for MIRDOSE3, provides a calculation of the effective dose for human adults as defined in ICRP Publication 60 (38). The urinary bladder received the highest absorbed doses, reflecting rapid clearance of most of the injected 64Cu-DOTA-E{E[c(RGDyK)]2}2 into the bladder and making it the limiting organ as far as the amount of 64Cu-DOTA-E{E[c(RGDyK)]2}2 that can be injected. However, the patient’s voiding interval affects the radiation dose absorbed by the urinary bladder and, because the urinary bladder is the limiting organ, the patient’s frequency of urination will change the bladder dose. Previous nonhuman primate imaging studies with 64Cu-labeled octreotide 64Cu-TETA-Y3-TATE found that the bladder dose could be reduced >7-fold by a normal voiding scheme as compared with no excretion assumption (39). If this is also true for our tetrameric RGD peptide tracer, then the kidneys appear to be the most affected and dose-limiting organs in human studies with regard to toxicity. The human kidney and liver doses of 64Cu-DOTA-E{E[c(RGDfK)]2}2 calculated from mouse biodistribution data (0.030 and 0.024 mGy/MBq, respectively) were significantly lower than those of 64Cu-labeled octreotide 64Cu-DOTA-OC calculated from clinical PET (0.078 and 0.091 mGy/MBq, respectively) (40). The use of rodent biodistribution data is generally thought to give a worst-scenario estimate of absorbed doses to normal organs. Whether this is true for 64Cu-DOTA-E{E[c(RGDfK)]2}2 remains to be tested in human patients. Nevertheless, methods to decrease the uptake of radioligand in the kidneys, such as coadministration of cationic amino acids (37) or modifying the structure to render the overall neutral or negatively charged molecule, may be able to minimize long-term damage to this organ if a particle ray-emitting isotope is used for the therapy.
Previous clinical investigations demonstrated the expression of integrin vß3 in glioma-associated angiogenesis (11). We have also shown that both subcutaneous and orthotopic U87MG glioblastoma xenografts (20,24,26,27) had high level of integrin. However, the subcutaneous tumor model used in this study does not accurately represent the growth, invasion, histology, gene expression profiling, vasculature, and stromal interactions or intracranial tumors.
In addition, the tumor model from the established U87MG glioblastoma cell line does not necessarily reflect the biology, heterogeneity, or therapeutic response of the primary tumor from which it was derived. Genetically accurate animal models for brain tumors such as those described in the Mouse Models of Human Cancers Consortium (MMHCC) (http://emice.nci.nih.gov/) that are more likely to parallel the human situation may be used in the future to test the clinical potential of the tetrameric RGD peptide tracer.
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CONCLUSION |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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ACKNOWLEDGMENTS |
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FOOTNOTES |
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For correspondence or reprints contact: Xiaoyuan Chen, PhD, Molecular Imaging Program at Stanford (MIPS), Stanford University, 1201 Welch Rd., P095, Stanford, CA 94305-5484.
E-mail: shawchen{at}stanford.edu
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTSDISCUSSIONCONCLUSIONREFERENCES |
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) in U87MG tumor-bearing athymic nude mice. Error bars denote SDs (n = 3).