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The role of the multivalent effect has been well recognized in the design of molecular imaging probes towards the desired imaging signal amplification. Recently we reported a bifunctional chelator (BFC) scaffold design, which provides a simple and versatile approach to impart multivalency to radiometal based nuclear imaging probes. In this work, we report a series of BFC scaffolds (tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3) constructed on the framework of 1,4,7-triazacyclononane-1,4,7-triacetic acid (NOTA) for 68Ga-based PET probe design and signal amplification via multivalent effect. For proof of principle, a known integrin αvβ3 specific ligand (c(RGDyK)) was used to build the corresponding NOTA conjugates (H31, H32, and H33), which present 1 – 3 copies of c(RGDyK) peptide, respectively, in a systematic manner. Using the integrin αvβ3 binding affinities (IC50 values), the enhanced specific binding was observed for multivalent conjugates (H32: 43.9 ± 16.1 nM; H33: 14.7 ± 5.0 nM) as compared to their monovalent counterpart (H31: 171 ± 60 nM) and the intact c(RGDyK) peptide (204 ± 76 nM). The obtained conjugates were efficiently labeled with 68Ga3+ within 30 min at room temperature in high radiochemical yields (> 95%). The in vivo evaluation of the labeled conjugates, 68Ga-1, 68Ga-2 and 68Ga-3, was performed using male severe combined immunodeficiency (SCID) mice bearing integrin αvβ3 positive PC-3 tumor xenografts (n = 3). All 68Ga -labeled conjugates showed high in vivo stability with no detectable metabolites found by radio-HPLC within 2 h post-injection (p.i.). The PET signal amplification in PC-3 tumor by multivalent effect was clearly displayed by the tumor uptake of the 68Ga-labeled conjugates (68Ga-3: 2.55 ± 0.50%ID/g; 68Ga-2: 1.90 ± 0.10 %ID/g; 68Ga-1: 1.66 ± 0.15 %ID/g) at 2 h p.i. In summary, we have designed and synthesized a series of NOTA-based BFC scaffolds with signal amplification properties, which may find potential applications in diagnostic gallium radiopharmaceuticals.
Positron emission tomography (PET), a nuclear imaging technique, has become a standard-of-care tool for diagnosis, staging treatment planning, and therapeutic efficacy monitoring of patients with cancer or other diseases.1–5 In addition to clinical applications, PET is also widely used in laboratory research to study the underlying mechanisms of diseases and to facilitate the discovery of new treatments.6 Development and application of PET imaging probes from the standard PET radionuclides (15O: t1/2 = 2.04 min; 13N: t1/2 = 9.96 min; 11C: t1/2 = 20.4 min; and 18F: t1/2 = 110 min) suffer from the short half-lives of the radionuclides, which mandates the presence of a radiochemistry laboratory in the close proximity of a cyclotron facility.7 To date, PET probe development using non-standard PET radionuclides (e.g. 64Cu, 68Ga, 89Zr, 124I) has drawn considerable interest given its independence to a cyclotron facility.8, 9 Among the non-standard PET radionuclides, 68Ga (t1/2 = 68 min, 89% β+, Eβ+ max =1.92 MeV, 11% EC) has the most clinical significance as it can be obtained on as needed basis from a bench-top 68 Ge/68Ga generator system thereby negating the onsite cyclotron requirement.10–14 Compared to 18F, the shorter half-life of 68Ga is not necessarily a hindrance in preclinical or clinical applications because its well-established coordination chemistry enables a rapid radiolabeling with high radiochemical yields,15, 16 which provides an opportunity to develop commercial kits to prepare PET probes onsite for diagnostic and prognostic imaging of diseases.
A macrocyclic chelator, 1,4,7-triazacyclononane-1,4,7-triacetic acid (NOTA), and its derivatives are particularly suitable for 68Ga incorporation due to their fast and efficient radiolabeling and in vivo stability (Figure 1).10, 11, 16 The stability of Ga(III)-NOTA complex results from the perfect hole-size match between the NOTA cavity and Ga3+ metal ion, which is accentuated by the tight embrace of the three coordinating carboxylate groups (Figure 1).17–23 However, application of NOTA for a targeted PET probe design is restricted because of its limited bifunctionality. Once the pendent carboxylic acid of the NOTA is conjugated with a targeting vector, the coordinating ability of the NOTA with 68Ga is compromised due to the loss of a coordinating pendent carboxylate group. Several NOTA derivatives such as S-2-(4-Isothiocyanatobenzyl)-1,4,7-triazacyclononane-1,4,7-triaceticacid (NOTA-Bn-SCN), 1,4,7-triazacyclononane-1-succinic acid-4,7-diacetic acid (NODASA) and 1-(1-Carboxy-3-carbo-tert-butoxypropyl)-4,7-(carbotert-butoxymethyl)-1,4,7-triazacyclononane (NODAGA) have been designed to circumvent this problem.15, 18, 19, 23, 24 The general concept of these modifications is the presence of an additional functionality on the macrocylic core for vector conjugation, while preserving NOTA’s capability of stable Ga3+ chelation (Figure 1).
A PET probe design is aimed to facilitate the accurate detection and quantitative analysis of a disease state, which requires high imaging sensitivity and specificity of the designed probe towards the target. To date, the multivalent effect has become a well-accepted concept in the design of molecular imaging probes for specific signal amplification by enhancing the binding affinity of a probe to the specific cell surface receptor.25 The most common way to incorporate the multivalent effect into a PET probe design is through the conjugation of a multimeric targeting vector on a bifunctional chelator (BFC). For instance, dimeric, tetrameric and octameric forms of a cyclic-RGD (Arginine-Glycine-Aspartic Acid) peptide have been used to enhance the in vivo imaging properties of PET probes by the resulting multivalent effect.26, 27
Recently, we reported a BFC scaffold design, which provides a simple and effective way to impart multivalency to PET imaging probes labeled with 64Cu.28 This unique design of BFC scaffolds provides multiple peripheral functional points for multi-presentation of targeting vectors in a BFC without compromising the metal chelate stability of the chelating core. In this work, we have extended this approach to NOTA-based radiopharmaceuticals by synthesizing a series of NOTA BFC scaffolds, tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3. The NOTA BFC scaffold design maintains the intact Ga3+ chelating NOTA core (after tBu deprotection) and varies the number of peripheral carboxylate groups from 1 – 3 to anchor the corresponding number of targeting molecules. This allows us to investigate the multivalent effect on 68Ga-labeled PET probe design in a systematic way. In this study, a well-validated integrin ανβ3 ligand (c(RGDyK)) was used as a model targeting molecule to generate monovalent H31, divalent H32, and trivalent H33 (Figure 3). For comparison, a monovalent analog (H31a) made from the commercial available NOTA-Bn-SCN was used as a positive control (Figure 3).26
All reactions were carried out under N2 atmosphere in degassed dried solvents. Commercially available starting materials were purchased from commercial vendors and used directly without further purification unless otherwise stated. Milli-Q water (18 MΩ-cm) was obtained from a Millipore Gradient Milli-Q water system (Billerica, MA). All aqueous solutions were prepared with Milli-Q water. Silica gel 60 (70–230 mesh, Merck) was used for column chromatography. Analytical thin-layer chromatography (TLC) was performed using Merck 60 F254 silica gel (precoated sheets, 0.2 mm thick) (Lawrence, KS). The 1H and 13C NMR spectra were recorded on a Varian 400 or 500 MHz spectrometer; chemical shifts are expressed in ppm relative to TMS as reference peak (0.0 ppm). Matrix-assisted laser desorption/ionization (MALDI) mass spectra were acquired on an Applied Biosystems Voyager-6115 mass spectrometer. Radiolabeled conjugates were purified by Light C-18 Sep-Pak cartridges (Waters, Milford, MA). Radioactivity of tissue samples and radioactive standards were counted by an automated Gamma Counter, Wizard2 3″ (PerkinElmer).
Bulk solvents were removed by rotary evaporator under reduced pressure, and trace solvents were removed by vacuum pump. The α-Bromoglutaric acid-1-tertbutylester- 4-benzyl ester (4) was synthesized according to the published procedure.29 The 1,4,7-triazacyclononane (TACN) and p-SCN-Bn-NOTA were purchase from Macrocyclics (Dallas, TX); and L-glutamic acid-5-benzylester was purchased from Sigma-Aldrich. The 68Ge/68Ga generator system was purchased from iThemba LABS (Somerset west, South Africa).
HPLC separation was performed on a Waters 600 Multisolvent Delivery System equipped with a Waters 2996 Photodiode Array detector. The mobile phase consisted of H2O with 0.1% TFA (solvent A) and acetonitrile with 0.1% TFA (solvent B). The analytical HPLC was performed on an XTerra RP18 column (150 × 4.6 mm) with a gradient of 0 % B to 100 % B in 50 min at a flow rate of 1.0 mL/min. The HPLC separation was performed on a semi-preparative XTerra RP18 Column (250 × 10 mm) with a gradient of 0% B to 100 % B in 50 min at a flow rate of 4.0 mL/min.
The ανβ3 integrin-binding affinities of c(RGDyK), H31, H31a, H32, and H33 were determined by a competitive cell-binding assay using 125I-echistatin (PerkinElmer) as the α νβ3-specific radioligand. The experiments were performed on U87MG human glioblastoma cells following a previously reported method.28 Briefly, U87MG cells were grown in RPMI 1640 medium supplemented with penicillin, streptomycin, and 10% (v/v) fetal bovine serum (FBS) at 37°C under 5% CO2. Suspended U87MG cells in binding buffer (20 mM Tris, pH 7.4,150 mM NaCl, 2 mM CaCl2, 1 mM MgCl2, 1 mM MnCl2, 0.1% bovine serum albumin) were seeded on multi-well DV plates (Millipore) with 5 × 104 cells per well and then incubated with 125I-echistatin (10,000 cpm/well) in the presence of increasing concentrations (0 – 5,000 nM) of c(RGDyK) peptide conjugates for 2 h. The final volume in each well was maintained at 200 μL. At the end of incubation, unbound 125I-echistatin was removed by filtration followed by three rinses with cold binding buffer. The retentate was collected and the radioactivity was measured using a γ-counter. The best-fit IC50 values (inhibitory concentration where 50% of the 125I-echistatin bound on U87MG cells are displaced) of c(RGDyK), H31, H32, and H33 were calculated by fitting the data with nonlinear regression using GraphPad Prism (GraphPadSoftware, Inc.). Experiments were duplicated with quintuplicate samples.
All animal studies were performed in compliance with guidelines set by the UT Southwestern Institutional Animal Care and Use Committee (IACUC). The PC-3 cell line was obtained from the American Type Culture Collection (ATCC, Manassas, VA), and was cultured in T-media (Invitrogen, Carlsbad, CA) at 37 °C in an atmosphere of 5% CO2 and were passaged at 75 % confluence in P150 plates. T-media was supplemented with 5% Fetal Bovine Serum (FBS) and 1 × Penicillin/Streptomycin. PC-3 cells were harvested from monolayer using PBS and trypsin/EDTA, and suspended in T-media with 5% FBS. The cell suspension was then injected subcutaneously (5 × 104 cells in 100 μL media) into the front left flanks of male SCID (Severe combined immunodeficiency) mice. After injection, animals were monitored three times a week by general observations. The tumor was allowed to grow three weeks to reach a palpable size (50 – 150 mm3) for biodistribution and microPET-CT imaging studies.
Male SCID mice bearing PC-3 prostate tumor xenograft were injected with 15–20 μCi of a 68Ga labeled conjugate to evaluate the tissue distribution of the tracer in mice. All mice were sacrificed at 30 min and 2 h p.i. The organs of interest (tumor, blood, heart, lung, liver, spleen, kidneys, fat, bone, muscle, brain, small intestine, large intestine, and stomach) were harvested, weighed, and radioactivity was quantified using a γ-counter. Standards were prepared and counted along with the tissue samples to calculate the percent injected dose per gram (%ID/g) and percent injected dose per organ (%ID/organ). To determine the pharmacokinetic parameters, mice injected with the tracer were blood sampled from the retro-orbital sinus at 2, 5, 10, 30, 60, and 120 min. The pharmacokinetic parameters were calculated based on a two-compartment open model.30 For in vivo stability evaluation, three SCID mice were used for each conjugate; each mouse was injected with 150 – 200 μCi of a 68Ga labeled conjugate in 150 μL of saline via the tail vein. The mouse urine was collected within 2 h post injection (p.i.) and the lower part of the abdomen was pressed as necessary. The collected urine was filtered and analyzed by radio-HPLC.
The imaging studies were performed on a Siemens Inveon Multimodality PET/CT system (Siemens Medical Solutions Inc., Knoxville, TN, USA). Ten minutes prior to imaging, the animals were anesthetized using 3% isofluorane at room temperature until stable vitals were established. Once the animal was sedated, the animal was placed onto the imaging bed under 2% Isofluorane anesthesia for the duration of the imaging. The CT imaging was acquired at 80kV and 500 μA with a focal spot of 58 μm. The total rotation of the gantry was 360° with 360 rotation steps obtained at an exposure time of approximately 180 ms/frame. The images were attained using CCD readout of 4096 × 3098 with a binning factor of 4 and an average frame of 1. Under low magnification the effective pixel size was 103.03 μm. Total microCT scan time was approximately 6 minutes. The CT images were reconstructed with a down sample factor of 2 using Cobra Reconstruction Software. The PET imaging was acquired directly following the acquisition of CT data. Each PC-3 tumor bearing mouse was injected with 100 – 125 μCi of a 68Ga labeled conjugate in 100 μL of saline via tail vein. Immediately after the injection, a dynamic PET scan was performed from 0 – 30 min. The 0–30 min dynamic imaging data were reconstructed into six frames (5 min each frame), where each frame represented the average value of the respective 5 min interval. At 2 h p.i., a 15-min static scan was performed. PET images were reconstructed using Fourier Rebinning and Ordered Subsets Expectation Maximization 3D (OSEM3D) algorithm. Reconstructed CT and PET images were fused and analyzed using Inveon Research Workplace (IRW) software. For quantification, regions of interest were placed in the areas expressing the highest 68Ga-labeled conjugate activity as determined by PET and guided by visual inspection of CT images. The tissues examined include the tumor, heart, liver, lung, kidney, and muscle. The resulting quantitative data were expressed in %ID/g.
A solution of α-bromoglutaric acid 1-tert-butyl ester 5-benzyl ester29 (4, 0.40 g, 1.12 mmol) in 30 mL of chloroform was added over a period of 3 h to a solution of 1,4,7-triazacyclononane (TACN, 0.29 g, 2.24 mmol) in 40 mL of chloroform. The mixture was stirred over 3 d at room temperature and concentrated to give yellow oil. The crude product was purified by column chromatography (silica gel, CHCl3/EtOH/NH4OH 7:3:0.5) to give 5 (0.15 g, 50%) and 6 (40 mg, 15%) as colorless oil.
1H NMR (CDCl3, 500 MHz) δ1.5 (s, 9H, C(CH3)3); 2.2–1.85 (m, 2H, CHNCH2); 2.9–2.5 (m, 14H, NCH2, CH2COOBzl); 3.25 (dd, 1H, CHBr); 5.1 (s, 2H, CH2Ph); 7.35 (m, 5H, Ph); MALDI-TOF/MS calcd for C22H35N3O4 [M+H]+: 406.23. Found: 406.40.
1H NMR (CDCl3, 500 MHz) δ1.4 (s, 18H, C(CH3)3); 1.9 (m, 2H); 2.05 (m, 2H); 2.45 (m, 2H); 2.55 (m, 2H); 2.8 (d, 2H); 3.0 (bs, 4H); 3.25 (m, 6H); 5.17 (s, 4H, CH2Ph); 7.28 (m, 10H, Ph); MALDI-TOF/MS calcd for C38H55N3O8 [M+H]+: 682.40. Found: 682.28.
The mixture of 5 (0.300 g, 0.740 mmol) and K2CO3 (0.20 g, 1.45 mmol) in 50 mL of anhydrous MeCN was cooled to 0 °C. To the above solution t-butyl-2-bromoacetate (0.26 g, 1.35 mmol) in 20 mL of anhydrous MeCN was added dropwise for 4 h. The reaction mixture was stirred at 0 °C for 6 h and at room temperature for 24 h. The mixture was filtered over Celite and the filtrate was evaporated to dryness. The crude product was purified by column chromatography (silica gel, CH3Cl:EtOH 95:5) to provide tBu3-1-Bn as yellow oil (0.27 g, 57%). 1H NMR (CDCl3, 500 MHz) δ 1.5 (s, 27H, C(CH3)3); 1.85–3.6 (m, 21H, CHNCH2, NCH2, CH2-COOBn, CH2COOtBu); 5.1 (s, 2H, CH2Ph); 7.35 (m, 5H, Ph); MALDI-TOF/MS calcd for C34H55N3O8 [M+H]+: 635.40. Found: 635.75.
Compound tBu3-1-Bn (150 mg, 0.237 mmol) was dissolved in 20 mL of 2-propanol and the solution was degassed (N2) for 5 min. To the above solution was added 10% Pd/C (50 mg) suspended in 0.5 mL of H2O. The suspension was shaken in a hydrogenator (Parr, Moline, Illionis) at room temperature for 16 h under a H2 atmosphere (60 psi). The suspension was filtered through Celite and the solvent was evaporated under vacuum. The obtained crude was purified by column chromatography (silica gel, 2-propanol/ammonia 95:5) to provide tBu3-1-COOH (85 mg, 66%) as yellow oil. 1H NMR (CDCl3, 500 MHz) δ1.5 (s, 27H, C(CH3)3); 2.0 (m, 2H); 2.5 (m, 2H); 2.8–3.2 (m, 12H); 3.45–3.75 (m, 5H); MALDI-TOF/MS calcd for C27H49N3O8 [M+H]+: 544.35. Found: 544.68.
To a mixture of compound tBu3-1-COOH (5.0 mg, 9.0 μmol), N- hydroxysuccinimide (NHS, 10.0 mg, 88.7 μmol) and EDC·HCl (15.0 mg, 90.0 μmol) in 800 μL of anhydrous MeCN was added 20 μL of N, N-diisopropylethylamine (DIPEA). The mixture was then stirred under N2 for 24 hours. After removal of the solvent under reduced pressure, the resulting residue was redissolved in CHCl3 (1.0 mL) and then promptly washed with water (3 × 2 mL). The organic layer was evaporated, and the residue was dried by a lyophilizer to yield the NHS-activated ester as pale yellow solid (MALDI-TOF/MS calcd for C31H52N4O10 [M+H]+: 641.37. Found: 641.42), The NHS-activated ester was used directly for the next step without further purification. Cyclic RGD peptide [c(RGDyK)] (7.0 mg, 11 μmol) was mixed with the NHS-activated ester in 500 μL of anhydrous DMF, to which 50 μL of DIPEA was added. The mixture was then stirred at room temperature for two days under N2. After removal of the solvent, the crude product was purified by semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were combined and lyophilized to afford 2.0 mg of t-butyl protected H31 as white powder. MALDI-TOF/MS calcd for C54H88N12O15 [M+H]+: 1144.65. Found: 1144.37. The t-butyl protected H31 (2.0 mg, 1.74 μmol) was dissolved in 95% of TFA and stirred at room temperature for 12 h. After evaporation of the solvent, the residue was purified by semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were pooled and lyophilized to afford H31 as white solid in quantitative yield. MALDI-TOF/MS calcd for C42H64N12O15 ([M+H]+: 976.46. Found: 976.43.
The mixture of 6 (85 mg, 0.12 mmol) and K2CO3 (86 mg, 0.62 mmol) in 40 ml of anhydrous MeCN was cooled to 0 °C. To the above solution t-butyl-2-bromoacetate (24 mg, 0.125 mmol) in 10 ml of anhydrous MeCN was added dropwise for 3 h. The reaction was stirred at 0 °C for 6 h and room temperature for 24 h. The mixture was filtered over Celite and the filtrate was evaporated to dryness. The crude product was purified by column chromatography (silica gel, CHCl3/EtOH, 95: 5) to give tBu3-2-Bn2 (80 mg, 80%) as yellow oil. 1H NMR (CDCl3, 500 MHz) δ 1.5–1.7 (s, 27H, C(CH3)3); 1.91–2.10 (m, 4H); 2.42–2.61 (m, 4H); 2.83 (bs, 3H); 3.1 (bs, 5H); 3.3 (bs, 3H); 3.5 (bs, 2H); 3.80–4.14 (m, 3H); 5.1 (s, 4H, CH2Ph); 7.25 (m, 10H, Ph); 13 25.20, 28.16, 31.05, 53.38, 55.28, 58.59, 64.46, C NMR (CDCl3,100 MHz) δ77.00, 80.90, 81.97, 85.21, 126.79, 128.08, 135.92, 171.99, 172.87. MALDI-TOF/MS calcd for C44H65N3O10 [M+H]+: 796.47. Found: 796.67.
Compound tBu3-2-Bn2 (50 mg, 0.15 mmol) was dissolved in 20 mL of 2-propanol and the solution was degassed (N2) for 5 min. To the above solution was added 10% Pd/C (30 mg) suspended in 0.5 mL of H2O. The suspension was shaken in a hydrogenator (Parr, Moline, Illionis) at room temperature for 16 h under a H2 atmosphere (60 psi). The suspension was filtered through Celite and the solvent was evaporated under vacuum. The obtained crude was purified by column chromatography (silica gel, 2-propanol/ammonia 95:5) to provide tBu3-2-(COOH)2 (30 mg, 66%) as yellow oil. 1H NMR (CDCl3, 500 MHz) δ1.6 (s, 27H, C(CH3)3); 2.4–2.8 (m, 7H); 3.0–3.3 (m, 12H); 3.45–3.75 (m, 5H); MALDI-TOF/MS calcd for C30H53N3O10 [M+H]+: 615.37. Found: 615.56.
To a mixture of compound tBu3-2-(COOH)2 (5.0 mg, 8.5 μmol), N-hydroxysuccinimide (10.0 mg, 80.0 μmol) and EDC·HCl (10.5 mg, 55.0 μmol) in 500 μL of dry MeCN was added 20 μL of N, N-diisopropylethylamine (DIPEA), which was then stirred under N2 for 24 hours. Solvent was removed under reduced pressure, the residue was redissolved in CHCl3 (1 mL) and then promptly washed with water (3 × 2 mL). The CHCl3 was evaporated, the residue was dried by a lyophilizer to yield NHS-activated ester as pale yellow solid (MALDI-TOF/MS calcd for C38H59N5O14 [M+H]+: 808.41. Found: 808.18), NHS-activated ester was used directly for the next step without further purification. Cyclic RGD peptide [c(RGDyK)] (10.5 mg, 17 μmol) was mixed with the above yellow solid in 500 μL of anhydrous DMF, to which 50 μL of DIPEA was added. The mixture was then stirred at room temperature for two days under N2. After evaporation of the solvent under vacuum, the crude product was purified by a semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were combined and lyophilized to afford t-butyl protected H32 as white powder. MALDI-TOF/MS calcd for C84H131N21O24 [M+H]+: 1818.97. Found: 1818.74. The t-butyl protected H32 (3.5 mg, 1.9 μmol) was dissolved in 95% of TFA and stirred at room temperature for 12 h. After evaporation of the solvent, the residue was purified by semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were pooled and lyophilized to afford a white solid H32 in quantitative yield. MALDI-TOF/MS calcd for C72H107N21O24 ([M+H]+: 1649.78. Found: 1649.38.
To a suspension of TACN (68 mg, 0.525 mmol) and K2CO3 (1.2 g, 8.68 mmol) in 3 mL of anhydrous MeCN at room temperature, compound 4 (620 mg, 1.74 mmol) in 3 mL of anhydrous MeCN was added dropwise. After the addition, the reaction was allowed to proceed at room temperature for 24 h and then at 55 °C for 24 h. The solids were removed by filtration and washed with chloroform (2 × 20 mL). The combined filtrate was concentrated under vacuum and purified by column chromatography (silica gel, 60- 230 mesh) using using CHCl3 to EtOAc for elution. Compound tBu3-3-Bn3 was obtained as a sticky oil (350mg; Yield, 70%): 1H NMR (CDCl3, 400 MHz) δ 1.42 (s, 27H), 1.76–1.88 (m, 3H), 1.90–2.04 (m, 3H), 2.38–2.58 (m, 8H), 2.64–2.84 (m, 8H), 2.86–2.96 (m, 2H), 3.04–3.14 (m, 3H), 5.08 (s, 6H), 7.32 (s, 15H); 13C NMR (CDCl3, 100 MHz) δ 25.63, 28.55, 31.31, 52.61–54.42 (br), 66.42, 67.22, 81.08, 128.41, 128.47, 128.77, 136.28, 172.74, 173.47. MALDI-TOF/MS calcd for C54H75N3O12 [M+H]+: 958.54. Found: 958.77. Anal. Calcd for C54H75N3O12·H2O: C, 66.44; H, 7.95; N, 4.30. Found: C, 66.41; H, 7.65; N, 4.30.
To a solution of tBu3-3-Bn3 (100 mg, 0.128 mmol) in 5 mL of 2-propanol was added portion wise 10 mg of 10% Pd/C. The suspension was shaken in a hydrogenator (Parr, Moline, Illionis) at room temperature for 16 h under a H2 atmosphere (60 psi). After removal of the solids, evaporation of solvent under vacuum gave the target compound tBu3-3-(COOH)3 as white solid in nearly quantitative yield. 1H NMR (CDCl3, 400 MHz) δ 1.48 (s, 27H), 2.07 (br, 6H), 2.50 (br, 8H), 3.15 (br, 10H), 3.62 (br, 3H), 8.35 (br. 3H); 13C NMR (CD3OD, 100 MHz) δ 25.16, 27.34, 31.27, 45.55, 63.39, 82.89, 171.41, 15.24; MALDI-TOF/MS calcd for C33H57N3O12 [M+H]+: 687.39. Found: 688.89. Anal. Calcd for C33H54N3Na3 O12: C, 52.58; H, 7.22; N, 5.57. Found: C, 52.58; H, 7.22; N, 5.59.
To a mixture of compound tBu3-3-(COOH)3 (3.8 mg, 5.5 μmol), N-hydroxysuccinimide (6.2 mg, 55.0 μmol) and EDC HCl (10.5 mg, 55.0 μmol) in 500 μL of dry MeCN was added 20 μL of N, N-diisopropylethylamine (DIPEA), which was then stirred under N2 for 24 hours. After the solvent was removed under reduced pressure, the residue was redissolved in CHCl3 (1 mL) and then washed 3 times (3 × 2 mL) with water promptly. The organic layer was evaporated to remove CHCl3, the resulting residue was then dried by a lyophilizer to NHS-activated ester as pale yellow solid (MALDI-TOF/MS calcd for C45H60N6O18 [M+H]+: 979.44. Found: 979.40), NHS-activated ester was used directly for the next reaction without further purification. Cyclic RGD peptide [c(RGDyK)] (10.5 mg, 17 μmol) was mixed with the above yellow solid in 500 μL of anhydrous DMF, to which 50 μL of DIPEA was added. The mixture was then stirred at room temperature for two days under N2. After evaporation of the solvent under vacuum, the crude product was purified by a semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were combined and lyophilized to afford 4.5 mg of t-butyl protected H33 as white powder (33%). MALDI-TOF/MS calcd for C114H174N30O33 [M+H]+: 2490.29. Found: 2490.21. The t-butyl protected H33 (2.0 mg, 0.80 μmol) was dissolved in 95% of TFA and stirred at room temperature for 12 h. After evaporation of the solvent, the residue was purified by semi-preparative reverse-phase HPLC. The collected fractions of multiple runs were pooled and lyophilized to afford a white solid H33 in quantitative yield. MALDI-TOF/MS calcd for C102H150N30O33 [M+H]+: 2321.10. Found: 2321.43.
To a solution of p-SCN-Bn-NOTA (10 mg, 22 μmol) in 200 μL of anhydrous DMF was added a mixture of [c(RGDyK)] (3.3 mg, 5 μmol) and DIPEA (20 μL) in 200 μL of anhydrous DMF. The mixture was then stirred at room temperature for 24 h. After evaporation of the solvent, the residue was purified by semi-preparative reverse-phase HPLC. The collected fractions from multiple runs were pooled and lyophilized to afford 5.0 mg of H31a as white solid (88%). MALDI-TOF/MS calcd for C47H67N13O14 [M+H]+: 1070.47. Found: 1070.48.
To a 2.0 mL vial containing 5–10 μg of respective conjugate in 1400 μL of 1 M 4-(2-hydroxyethyl)-1-piperazineethanesulfonic acid (HEPES, pH = 6.5) solution, 2 – 3 mCi of 68GaCl3 in 0.6 N HCl was added. The reaction mixture was shaken and incubated at 75°C for 0.5 h. Then, 2 μL of 5 mM ethylendiaminetetraacetic acid (EDTA) was added to the reaction mixture, which was allowed to incubate for another 5 min (EDTA was used to remove non-specifically bound or free 68Ga from the 68Ga-labeled conjugate). The purification of 68Ga-labeled conjugate was carried out by passing the mixture through a preconditioned Sep-Pak C-18 light cartridge. After thorough rinsing (3 × 3 mL, water) of the cartridge, the 68Ga -labeled conjugate was eluted by an ethanol-water mixture (70:30). The product was first analyzed by a Rita Star Radioisotope TLC Analyzer (Straubenhardt, Germany) on instant thin-layer chromatography (ITLC-SG) plates (Pall Life Sciences, East Hills, NY) and then by radio-HPLC to determine the radiochemical purity of the product.
Quantitative data were expressed as the mean ± SD. Unpaired t test (two-tailed, confidence intervals: 95%) was performed using GraphPad Prism. P values of <0.05 were considered statistically significant.
The synthesis of H31, H32 and H33 tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3; second, conjugation of c(RGDyK) with tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3, followed by the deprotection of the t-butyl protected carboxylate groups. The side-arm, α-bromoglutaric acid-1-tertbutylester-4-benzyl ester 4 was synthesized by two steps from commercially available L-glutamic acid-5-benzylester.29 Alkylation of the commercially available TACN with 4 in CHCl3 at room temperature gave both mono- (5, 50%) and di-alkylated (6, 15%) products. Compounds 5 and 6 were separated using column chromatography, where compound 6 was eluted first. Further alkylation of 5 and 6 with bromo-t-butylester afforded tBu3-1-Bn (57%) and tBu3-2-Bn2 (80%), respectively. Over-alkylation was observed during the reaction between 5 or 6 with bromo-t-butylester, which led to the respective quaternary ammonium salt. However, the salt formation was avoided by slow addition of bromo-t-butylester to the diluted solution of 5 or 6. Alkylation of TACN with 4 (3.3 equivalents) afforded tBu3-3-Bn3 in a yield of over 70% without formation of mono- or di-substituted analogs under the given reaction conditions.
The protected BFC scaffolds, tBu3-1-Bn, tBu3-2-Bn2 and tBu3-3-Bn3, contains two protected carboxylate groups at α and γ positions of the side-arm. The benzyl protected γ-carboxylate groups in tBu3-1-Bn, tBu3-2-Bn2 and tBu3-3-Bn3 were selectively deprotected and reserved for peptide (c(RGDyK)) conjugation. Catalytic debenzylation of tBu3-1-Bn, tBu3-2-Bn2 and tBu3-3-Bn3 was achieved using 10% Pd/C in 2-propanol under hydrogen atmosphere to afford tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3 in quantitative yield. The obtained γ-carboxylic acids were then activated by N-hydroxysuccinimide (NHS) for acid-amine conjugation chemistry and used as received for further conjugation. The conjugation of NHS-activated tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3 with 1 – 3 equivalents of c(RGDyK) in the presence of DIPEA provided the t-butyl protected conjugates in 30 – 45 % yields. Finally, the α-carboxylate group was deprotected using 95% trifluoroacetic acid to provide H31, H32, and H33, each containing three internal carboxylic acids for 68Ga labeling. The H31a conjugate was prepared by directly reacting p-SCN-Bn-NOTA with c(RGDyK) peptide at room temperature in aqueous media using a reported procedure.15, 26
All the intermediates and final products were characterized by 1H NMR, mass spectroscopy and HPLC. Analysis of 1H NMR spectra was facilitated by addition or removal of characteristic t-butyl and/or benzyl groups. Also, these compounds were characterized by their molecular ion peak by MALDI-mass spectrometry, and the purity of these conjugates was assured by observing a single peak in the reverse-phase HPLC.
The 68Ga labeling efficiencies were evaluated under an acidic condition (pH = 3.0 – 3.5)31 for all the conjugates by varying the reaction temperature and time. At room temperature, conjugates H31, and H31a showed a high 68Ga incorporation rate (> 90%) within 10 min of the radiochemical reaction, while H32 and H33 only had 71% and 84%, respectively. When the reaction proceeded to 30-min, all the conjugates were radiolabeled with > 95% of 68Ga. At 70°C, all conjugates showed nearly instant labeling with 68Ga. The 68Ga labeled conjugates were purified in one step using a pre-activated C-18 Sep-Pak light cartridge with a > 90% recovery rate. The radiochemical purity of the 68Ga-labeled conjugates after cartridge purification was > 99% as determined by radio-HPLC. The overall radiochemical procedure including the purification and HPLC steps took less than 45 min and gave a decay-corrected radiochemical yield of > 90%. The specific activity of the purified 68Ga-labeled conjugates was in the range of 33 – 44 MBq/nmol. The 68Ga-labeled conjugates were eluted from HPLC less than one min earlier than their respective conjugate.
The in vitro αvβ3 binding affinities of c(RGDyK), H31, H32, and H33 were determined by a competitive cell-binding assay using 125I-echistatin as the integrin-specific radioligand.32 The receptor binding experiments were performed using αvβ3 integrin-positive U87MG human glioma cells containing a high αvβ3 integrin density on its cell surface.33 All the conjugates inhibited the binding of 125I-echistatin to the αvβ3 integrin-positive U87MG cells in a dose-dependent manner (Figure S1). Calculated IC50 values expressed by the 50% inhibitory concentration of the 125I-echistatin binding were 204 ± 76 nM (c(RGDyK)), 218 nM (H31a),26 171 ± 60 nM (H31), 43.9 ± 16.1 nM (H32) and 14.7 ± 5.0 nM (H33). The in vitro αvβ3 binding affinity of c(RGDyK) was used as a reference. The binding affinity of H31 is similar to that of c(RGDyK), indicating that the conjugation of a NOTA scaffold to c(RGDyK) had minimal effect on the receptor binding affinity of c(RGDyK). The multivalent enhancement ratio (MVE) calculated by dividing the IC50 value of H31 by that of H32 or H33 and the respective number of c(RGDyK) molecules, was 3.9 for H32 and 11.6 for H33, indicative of the anticipated multivalent effect.28, 34
The metabolic stability of 68Ga-1, 68Ga-1a, 68Ga-2 and 68Ga-3 in SCID mice was evaluated by examining their metabolites in urine at 2 h p.i. Impressively, no metabolites were detected for any of the conjugates by radio-HPLC analysis (Figure S2), indicating high in vivo stability of 68Ga-labeled conjugates.
The pharmacokinetics (PK) parameters for 68Ga-1, 68Ga-1a, 68Ga-2, and 68Ga-3 were evaluated in SCID mice using a two-compartment open model. The time-activity curves of the 68Ga-labeled conjugates in blood showed a biphasic clearance (Figure 4). As shown in Table 1, all the 68Ga-labeled conjugates displayed a rapid distribution half-life (t1/2(α) < 5 min) and a short terminal half-life (t1/2(β) < 50 min).
The tissue distribution profiles of 68Ga-1, 68Ga-1a, 68Ga-2 and 68Ga-3 in SCID mice bearing the αvβ3 integrin-positive PC-3 tumor are summarized in Figure 5 and Table S3. Among the organs evaluated, kidney showed the highest uptake (68Ga-1a: 6.25 ± 0.61 %ID/g; 68Ga-1: 5.40 ± 0.61 %ID/g; 68Ga-2: 3.18 ± 2.76 %ID/g; 68Ga-3: 8.41 ± 0.99 %ID/g) at 30 min p.i., indicating that all the conjugates were primarily excreted through the renal route. At 2 h p.i., less than 60% of the kidney uptake was retained for monovalent conjugates (68Ga-1a: 2.95 ± 0.76 %ID/g; 68Ga-1: 3.14 ± 0.13 %ID/g), while the divalent and trivalent ones showed a > 90% retention (68Ga-2:3.86 ± 1.80 %ID/g; 68Ga-3: 7.50 ± 0.95 %ID/g). At 30 min p.i., no significant difference was observed for the liver uptake of the conjugates (68Ga-1a: 1.98 ± 0.29 %ID/g; 68Ga-1: 1.91 ± 0.30 %ID/g; 68Ga-2: 2.07 ± 0.05 %ID/g; 68Ga-3: 3.10 ± 0.77 %ID/g). Interestingly, the liver uptake retention was independent of the valency of the conjugates at 2 h p.i. However, the tumor uptake of the conjugates showed a positive correlation with the valency (68Ga-1a: 1.63 ± 0.19 %ID/g; 68Ga-1: 1.67 ± 0.16 %ID/g; 68Ga-2: 1.94 ± 0.32 %ID/g; 68Ga-3: 4.41±1.00 %ID/g) at 2 h p.i., which clearly reflects the multivalent effect and is consistent with the cell binding affinities of the conjugates. Impressively, the tumor retention rate of the uptake shown at 2 h p.i. was in the order of trivalent 68Ga-3 (79%) > divalent 68Ga-2 (61%) > monovalent 68Ga-1 (55%) monovalent 68Ga-1a (57%) at 2 h p.i.
The PET-CT imaging was performed on SCID mice bearing integrin αvβ3-positive PC-3 prostate cancer xenograft. Representative decay-corrected coronal images at 30 min (dynamic frame of 25 – 30 min) and 2 h p.i. are shown in Figure 6a. The PC-3 tumors were clearly visualized by all four probes at 30 min p.i. but without significant tumor uptake difference observed among the conjugates (68Ga-1a: 3.24 ± 0.41 %ID/g; 68Ga-1: 3.26 ± 0.70 %ID/g; 68Ga-2; 3.06 ± 0.21 %ID/g; and 68Ga-3: 3.55 ± 0.85 %ID/g) (Table S1). Uptake of 68Ga-1, 68Ga-1a, 68Ga-2 and 68Ga-3 at 30 min p.i. in other organs, especially muscle and blood, was also high, which resulted in the low tumor-to-background contrast. At 2 h p.i., the tumor-to-background contrast clearly increased as the 68Ga-labeled conjugate was cleared from the non-target organs (Figure 6d). Of the 68Ga-labeled conjugates, 68Ga-3 showed the highest tumor uptake at 2 h p.i. (2.55 ± 0.50 %ID/g), which is significantly (p < 0.05) higher than all other 68Ga-labeled conjugates (68Ga-2: 1.90 ± 0.10 %ID/g; 68Ga-1: 1.66 ± 0.15 %ID/g; and 68Ga-1a:1.40 ± 0.36 %ID/g) (Figure 6c). This observation can be explained by the enhanced binding affinity of the trivalent 68Ga-3 conjugate, which led to its prolonged retention in the target, integrin αvβ3-positive tumor. Compared to the corresponding 30-min uptake value, the tumor uptake retention at 2 h p.i. follows the same order as observed in the biodistribution result: trivalent 68Ga-3 (72%) > divalent 68Ga-2 (62%) > monovalent 68Ga-1 (51%) ~ monovalent 68Ga-1a (43%). A blockade experiment was performed by co-injecting the 68Ga-labeled conjugate with the blocking dose of c(RGDyK) (10 mg/kg). The drastic reduction of tumor uptake for all 68Ga-labeled conjugates unequivocally indicated their imaging specificity of integrin αvβ3 (Table S1).
Consistent with the biodistribution data, all 68Ga-labeled conjugates showed efficient clearance from the kidney (Table S1). Possibly due to the multivalent effect, 68Ga-3 showed the highest kidney uptake (4.03 ± 1.75 %ID/g) at 2 h p.i., which is significantly higher than other 68Ga-labeled conjugates (p < 0.01) (Figure 6b, Table S1). In the liver, no significant uptake and retention difference was observed for the 68Ga-labeled conjugates at either 30 min or 2 h p.i. Low to negligible level (< 1.14 %ID/g) of uptake was observed in other major organs (e.g. heart, lungs, muscle) at 2 h p.i.
The design of a BFC for metal-based radiopharmaceuticals is largely influenced by the ability of the BFC to form a kinetically inert chelate with a metal radionuclide and the ease to covalently anchor a targeting vector. To date, both cyclic and acyclic BFCs containing coordinating atoms (e.g. nitrogen, oxygen and sulfur) have been reported for Ga(III) chelation.35–38 For a BFC to be considered for nuclear imaging probe design, its complex with the metal ion of interest must have desirable thermodynamic and in vivo kinetic stability, specifically resistance to trans-metalation with serum proteins. The most commonly used macrocyclic chelator, 1, 4, 7, 10-tetraazacyclododecanetetraacetic acid (DOTA), is a choice of convenience for 68Ga PET imaging design due to its commercial availability and the fact that it is in the composition of several FDA-approved agents. However, the DOTA complex with Ga(III) has a thermodynamic stability constant (log K = 21.33)39 comparable to that of the transferrin complex with Fe(III) (log K = 20.3),40 which may lead to in vivo transmetalation.40 Also, the complexation kinetics of DOTA with Ga(III) often require an elevated temperature and a long reaction time, which could be detrimental to the activity of the biomolecule and not advantageous to 68Ga, a radionuclide with a decay half-life barely longer than one hour. Given the small ionic radius of Ga(III) (76 pm),18 NOTA, a nine-membered triazamacrocyclic chelator, would provide a perfect cavity size match for Ga(III) coordination. Indeed, the thermodynamic stability constant of Ga(III)-NOTA complex (log K = 30.98)22, 24 is approximately 10 orders of magnitude higher than that of its DOTA counterpart. More impressively, the neutral Ga(III)-NOTA complex was reported to stay inert against the acid-catalyzed dissociation in 6N HNO3 for 6 days.20 When NOTA is used without modification as a BFC, however, one of its three pendent coordinating carboxylic acids would be consumed to form an amide linkage with the targeting vector. Although the coordinating atoms (N3O3) stay the same before and after the conjugation, the stability of the metal complex moiety is compromised due to the formation of an amide linkage.41, 42 In order for NOTA to keep its three coordinating acetate arms intact for Ga(III) chelation, an additional functional group is necessary. Indeed, various C- or N-functionalized NOTA derivatives have been reported as modified NOTA for gallium radiopharmaceuticals.23, 43–46 Of the reported methods, the N-functionalization of TACN provides a simple and versatile way of introducing additional functionalities to the triazamacrocyclic ring, which makes the NOTA derivatives bifunctional.23, 24
The multivalent effect is widely used to enhance the desired biological potency of a bioactive molecule.47–50 For instance, the tumor targeting efficacy of a targeting vector can be enhanced by orders of magnitude through the strengthened specific ligand-receptor binding.28, 34, 51–54 In principle, multimeric presentation of a ligand increases its local concentration on the cell surface thus increasing the probability of the specific ligand-receptor interaction, which results in enhanced target accumulation. Furthermore, the juxtaposition of the conjoined ligands can facilitate the desired ligand-receptor interaction. In the field of molecular imaging, multivalent effect can certainly be exploited to amplify the imaging signal in target organs or tissues in the same manner. Indeed, several groups have reported that imaging contrast can be significantly improved by taking advantage of multivalent effect in the imaging probe design.27, 28, 32, 55–58 For instance, multivalent PET imaging probes featuring multimeric peptides have demonstrated better imaging properties than their monomeric counterpart.32, 55, 59–64
Recently, we reported a BFC scaffold design for 64Cu-based PET imaging probes, which provides multiple peripheral functional points for multi-presentation of targeting vectors in a BFC without compromising the metal chelate stability of the chelating core.28 An important role of such a BFC scaffold is to provide PET signal enhancement through the resulted multivalent effect. Similarly, we designed a series of NOTA-based scaffolds for 68Ga PET imaging probes, tBu3-1-Bn,23 tBu3-2-Bn2 and tBu3-3-Bn3, which contain two orthogonally protected carboxylic acid groups on each side-arm. All three BFC scaffolds have three t-butyl protected α-carboxylic acid groups intended for Ga(III) coordination, while the number of the terminal benzyl protected γ-carboxylic acid differs to systematically vary the valency of a targeting vector from 1 – 3. The orthogonality of the protecting groups on the side-arm enables the selective deprotection of the γcarboxylate and α-carboxylate groups by different procedures at the corresponding step. Further, the four-carbon alkyl chain is incorporated as a spacer between the NOTA core and the peripheral carboxylate groups so as to minimize the interference of the NOTA motif with the properties of the targeting vector. Indeed it was reported that replacing one of the acetic acid side arms of NOTA with succinic acid, a 4-carbon spacer, has a negligible effect on the geometry or the thermodynamic stability of the resulting Ga(III) complex (Ga-NODASA: log K = 30.9; Ga-NOTA: log K = 30.98).24 Impressively, the exchange kinetics of 67Ga-NODASA with transferrin at the physiological pH and temperature showed no metal transchelation over the period of 5 days.24 Therefore, we believe the replacement of the acetate side-arm with α-bromoglutaric acid 1-tert-butyl ester 5-benzyl ester (4) would not adversely influence the structural integrity and thermodynamic stability of the resulting Ga-complexes.
The NOTA BFC scaffolds, tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3, were synthesized by alkylation of TACN using appropriate equivalents of 4. Synthesis of tBu3-1-COOH and tBu3-2-(COOH)2 was performed in a three-step route with the first step determining the overall yield. The alkylation of TACN with 4 afforded both 5 and 6. The subsequent two steps were quantitative. Synthesis of tBu3-3-(COOH)3 was straightforward, which can be scaled to produce grams of the product. The NOTA scaffolds (tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3) possess one, two and three peripheral catboxylate groups, respectively, for the covalent attachment of a targeting vector in a systematic fashion. For proof of concept, a well-validated integrin αvβ3 ligand, c(RGDyK), was conjugated to tBu3-1-COOH, tBu3-2-(COOH)2 and tBu3-3-(COOH)3 to yield tBu-protected monvalent, divalent, and trivalent peptide conjugates. The tBu-protected α-carboxylate was later deprotected in 95% TFA to give H31, H32, and H33 in quantitative yield as peptide conjugates ready for labeling with 68Ga.
Radiolabeling of the conjugates of H31, H32, and H33 with 68Ga was tested by varying reaction conditions, such as pH, temperature, and time, in order to reach the highest achievable specific activity of the labeled tracers within a short time, given the 68-min half-life of 68Ga. Because radiolabeling of NOTA with 68Ga is pH sensitive, HEPES was used as the reaction buffer to provide the optimal labeling pH (3.0 – 3.5).16 At room temperature, we were able to label the conjugates in high radiochemical yields (RCY > 95%) within 30 min. Comparatively speaking, the 68Ga labeling of multivalent conjugates (H32, and H33) was slower than that of the monvalent ones (H31 and H31a) in part due to the steric hindrance by the additional copies of c(RGDyK) peptide. However, the difference virtually disappeared when the radiolabeling was conducted at 70°C. One of the desired features of a PET imaging agent for clinical application is the ease of post-labeling purification. By a simple separation procedure through a C-18 cartridge, all the radiolabeled conjugates reached > 99% radiochemical purity as determined by radio-HPLC.
Both H31 and H31a have one copy of c(RGDyK) peptide while H32 and H33 have two and three copies of c(RGDyK), respectively. The multi-presentation of the c(RGDyK) peptide in H32 and H33 is expected to enhance the affinity of the receptor-ligand interaction through the phenomenon of multivalent effect. By a competitive cell-binding assay using 125I-echistatin as the integrin-specific radioligand,32 multivalent effect, as measured by the enhanced specific ligand-receptor binding affinity was evaluated. The determined IC50 values of monvalent H31 (171 ± 60 nM), divalent H32 (43.9 ± 16.1 nM), and trivalent H33 (14.7 ± 5.0 nM) were found to be similar to the measurements reported for the monovalent (H31a, 218 nM), divalent (60 nM) and tetravalent (16 nM) conjugates constructed from peptide multimerization of c(RGDyK).26 The cell-binding assay clearly demonstrated the anticipated multivalent effect of H32 and H33 as compared to their monovalent counterpart (H31). Of note, the multivalent effect resulted from the BFC scaffold-based multivalency (H33, 13 nM) is similar to that resulted from the tetramerization of c(RGDyK) (NOTA-Bn-SCN–tetramer, 16 nM).26
The in vivo behavior of 68Ga-1, 68Ga-1a, 68Ga-2 and 68Ga-3, was evaluated in SCID mice bearing integrin αvβ3-positive PC-3 prostate cancer xenograft. Like other c(RGDyK) based agents, all the 68Ga-labeled conjugates were efficiently cleared from the kidneys, while the excretion through feces was negligible within 2 h p.i. The radio- HPLC analysis of collected urine demonstrated that the 68Ga-labeled conjugates stayed intact (> 99%) within 2 h p.i, which is roughly two times of the physical half-life of 68Ga. This high metabolic stability of the 68Ga-labeled conjugates likely resulted from the kinetic inertness of the Ga-NOTA complex.
The integrin αvβ3 positive PC-3 tumor was visualized with 68Ga-1, 68Ga-1a, 68Ga-2, and 68Ga-3 at 30 min and 2 h p.i. (Figure 6a). Irrespective of the valency, all the 68Ga-labeled conjugates showed similar tumor uptake with poor contrast at 30 min p.i. due to their relatively high level of presence in the non-target organs (e.g. blood and muscle. Table S3). At 2 h p.i., the enhanced tumor uptake and retention of 68Ga-2 and 68GA-3 can be partially attributed to their increased binding affinities resulting from multivalent effect. Interestingly, the tumor PET signal amplification level by the multivalent effect (68Ga-3: 2.55 ± 0.50 %ID/g; 68Ga-2: 1.90 ± 0.10 %ID/g; 68Ga-1: 1.66 ± 0.15 %ID/g) is similar to that in a published work using peptide multimerization of c(RGDyK) as an approach to realize multivalent effect for PET probe design (tetramer: 2.1 %ID/g; dimer: 1.9 %ID/g; monomer: 1.1 %ID/g).26 In addition to the increased binding affinity, the prolonged in vivo half-life of multivalent conjugates, resulting from the molecule size increase, may also contribute to the enhanced tumor uptake over the time course. The prolonged in vivo half-life of multivalent conjugate is believed to be able to sustain the desired tumor accumulation and retention.26, 65 However, similar distribution and elimination half-lives were observed for all radiolabeled conjugates. Therefore we think that the observed tumor uptake increase and PET signal amplification was predominately caused by the multivalency of 68Ga-2 and 68Ga-3. It is important to note that the imaging specificity is not compromised because of the added multivalency as it is shown by the complete signal loss in the blockade experiment (Figure 6a and Table S2). The liver signal intensity difference between 2 h and 2 h blockade was likely caused by the diluting effect of the excess cold ligand. However, we acknowledge that the kidney uptake was also increased by the multivalent effect, which might affect how the peptide conjugates are handled in the proximal tubule and their binding to megalin. While the same phenomenon is common in peptide-based radiopharmaceuticals, the exact mechanism for such an increase is unknown. To evaluate the statistic correlation between the biodistribution and quantitative imaging data, we calculated the Pearson correlation coefficients for all four conjugates. The results (r: 68Ga-1a > 0.77; 68Ga-1 > 0.85; 68Ga-2 > 0.90; 68Ga-3 > 0.87) clearly demonstrate a strong correlation.
A series of NOTA-based BFC scaffolds were synthesized to take advantage of multivalent effect for 68Ga PET imaging probe design. Using a well-validated integrin αvβ3 ligand, c(RGDyK), peptide conjugates varying multivalency from 1 to 3 were prepared. The in vitro and in vivo evaluations of the peptide conjugates demonstrated that the preservation of the intact NOTA core in the BFC scaffold design guaranteed rapid and efficient 68Ga incorporation and high in vivo stability, while the multivalency rendered by the BFC scaffold design was able to significantly enhance the specific imaging of the targeted αvβ3 receptor in a prostate cancer xenograft mouse model. Together with our previously reported BFC scaffold design for 64Cu PET imaging probes, we have validated the design concept that multivalent effect can be realized on a simple BFC scaffold to amplify the desired imaging signal. It is noteworthy that the peptide multimerization method reported by others can be combined with our BFC scaffold design to achieve multi-layered multivalency if necessary. Further, our design allows enhanced specific targeting to heteromeric receptors by incorporating mutually independent targeting molecules on the BFC scaffold.
This work was partially supported by a USAMRMC grant (W81XWH-08-1-0305) and two NIH grants (P01 DK058398; U24 CA126608). The authors acknowledge the generous support of a private donor that allowed the purchase of the Inveon PET-CT system.