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Theranostics 2017; 7(4):805-813. doi:10.7150/thno.17117 This issue Cite

Research Paper

Preclinical Melanoma Imaging with ⁶⁸Ga-Labeled α-Melanocyte-Stimulating Hormone Derivatives Using PET

Chengcheng Zhang¹, Zhengxing Zhang¹, Kuo-Shyan Lin^1,2, Jinhe Pan¹, Iulia Dude¹, Navjit Hundal-Jabal¹, Nadine Colpo¹, François Bénard^1,2,

1. Department of Molecular Oncology, BC Cancer Agency, Vancouver, BC, Canada
2. Department of Radiology, University of British Columbia, Vancouver, BC, Canada

✉ Corresponding author: Dr. François Bénard. Address: Department of Molecular Oncology, BC Cancer Agency, 675 West 10th Avenue, Rm 14-111, Vancouver, BC V5Z 1L3, Canada. Phone: 604-675-8206. Fax: 604-675-8218. E-mail: fbenardca.

Abstract

It is estimated that melanoma accounted for 76,380 new cases and 10,130 deaths in the United States in 2016. The melanocortin 1 receptor (MC1R) is highly expressed in the vast majority of melanomas, which makes it an attractive target for molecular imaging and radionuclide therapy. Lactam bridge-cyclized α-melanocyte-stimulating hormone (Ac-Nle⁴-cyclo[Asp⁵-His-D-Phe⁷-Arg-Trp-Lys¹⁰]-NH₂, or Nle-CycMSH_hex) analogues have been successfully developed and studied for MC1R-targeted imaging, predominantly with single-photon emission computed tomography (SPECT). The goal of this study was to design and evaluate novel peptides for melanoma imaging with positron emission tomography (PET). We designed and synthesized three peptides, DOTA-PEG₂-Nle-CycMSH_hex (CCZ01047), DOTA-4-amino-(1-carboxymethyl) piperidine (Pip)-Nle-CycMSH_hex (CCZ01048), and DOTA-Pip-Pip-Nle-CycMSH_hex (CCZ01056). All three peptides exhibited high binding affinity to MC1R with sub-nanomolar K_i values, rapid internalization into B16F10 melanoma cells and high in vivo stability with more than 93% remaining intact at 15 min post-injection (p.i.) in blood plasma. All three ⁶⁸Ga-labeled tracers produced high contrast PET images in C57BL/6J mice bearing B16F10 tumors, and their respective tumor uptakes were 8.0 ± 3.0, 12.3 ± 3.3, and 6.5 ± 1.4 %ID/g at 1 h p.i. Minimal normal organ activity was observed at 1 h p.i., except for kidneys (5.1 ± 1.4, 4.7 ± 0.5, and 6.2 ± 2.0 %ID/g, respectively), and thyroid (4.1 ± 0.6 %ID/g for CCZ01047 and 2.4 ± 0.6 %ID/g for CCZ01048). Due to high accumulation at tumor sites and rapid background clearance of ⁶⁸Ga-CCZ01048, we further evaluated it at 2 h p.i., and a tumor uptake of 21.9 ± 4.6 %ID/g was observed, with background activity further decreased. Exceptional image contrast was also achieved, i.e. tumor-to-blood, tumor-to-muscle, tumor-to-bone and tumor-to-kidney ratios were 96.4 ± 13.9, 210.9 ± 20.9, 39.6 ± 11.9 and 4.0 ± 0.9, respectively. A blocking study was also performed by co-injection of excess amount of non-radioactive Ga-coupled of CCZ01048, which confirmed that the tumor uptake was MC1R mediated. In conclusion, the introduction of a cationic Pip linker to Nle-CycMSH_hex, CCZ01048, not only improved tumor uptake, but also generated high tumor-to-normal tissue contrast with PET imaging in a preclinical melanoma model. Therefore, CCZ01048 is a promising candidate for PET imaging of melanoma, and potentially as a theranostic agent for radionuclide therapy of melanoma when labeled with α or β emitters.

Keywords: Melanocortin 1 receptor, Melanoma, α-melanocyte-stimulating hormone, PET imaging, Ga-68.

Introduction

It is estimated that melanoma accounted for 76,380 new cases and 10,130 deaths in the United States in 2016 [1]. Despite the fact that novel therapies such as immune checkpoint inhibitors [2], BRAF inhibitors [3], adoptive T-cell therapies [4] and oncolytic viruses [5] have shown promising results, the majority of patients with advanced metastatic melanoma will eventually die from disease progression. Therefore, accurate staging remains a key aspect in managing melanoma. With high sensitivity and spatial resolution, positron emission tomography (PET) has emerged as a powerful imaging technique for such purpose. While 2-[¹⁸F]Fluorodeoxyglucose PET coupled with computed tomography (CT) is highly accurate in detecting metastatic disease in cutaneous melanomas [6], this modality lacks sensitivity for early nodal metastases, and liver metastases in uveal melanomas [7, 8].

The melanocortin 1 receptor (MC1R) is highly expressed in malignant melanomas. It has been shown to be expressed in 83% of melanoma cell lines, all tissue samples from primary and metastatic melanomas (n = 26) [9], and 95% of uveal melanomas [10]. In addition, low levels of MC1R expression in normal tissues make this protein an attractive target for molecular imaging. Indeed, radiolabeled peptide ligands based on the sequence of α-melanocyte-stimulating hormone (α-MSH) have been studied extensively for MC1R-targeted imaging, summarized in a review article [11]. α-MSH, a tridecapeptide, is prone to proteolysis by peptidase in vivo. Unnatural amino acid substitutions at position 4 with Nle and position 7 with D-Phe not only increased in vivo stability, but also improved binding affinity to MC1R. Furthermore, His-Phe-Arg-Trp has been identified as a key sequence for biological activity and binding with MC1R. With this core sequence, cyclized α-MSH analogues have been designed, which further improved both stability and affinity. The most successful analogues to date are based on lactam bridge-cyclized α-MSH (Ac-Nle⁴-cyclo[Asp⁵-His-D-Phe⁷-Arg-Trp-Lys¹⁰]-NH₂, or Nle-CycMSH_hex), which have shown promising results in animal models predominately with single-photon emission computed tomography (SPECT) over the past few years [12-20].

The goal of this study was to develop and optimize Nle-CycMSH_hex-based agents and evaluate their potential for PET imaging of melanoma. We designed a series of imaging probes by attaching a PEG₂ linker, a cationic linker (4-amino-(1-carboxymethyl) piperidine, or Pip), or dual Pip linkers to Nle⁴. A chelator, 1, 4, 7, 10-tetraazacyclododecane-1, 4, 7, 10-tetraacetic acid (DOTA) was then coupled to enable radiometal coupling. In this paper, we report the synthesis of these peptides, namely CCZ01047, CCZ01048 and CCZ01056 respectively, radiolabeling with ⁶⁸Ga, in vitro receptor binding and internalization assay, and in vivo biodistribution and PET imaging results in a preclinical melanoma model.

Materials and Methods

Peptide synthesis

Solid phase peptide synthesis was performed via standard Fmoc chemistry on an Endeavor 90 peptide synthesizer (Aapptec). Fmoc-Rink-Amide-MBHA resin was swelled in dichloromethane (DCM), and the Fmoc protecting group was removed by treating the resin with 20% piperidine in dimethylformamide (DMF). Fmoc-protected amino acids (3 equivalents), Fmoc-Lys(Mtt)-OH, Fmoc-Trp(Boc)-OH, Fmoc-Arg(Pbf)-OH, Fmoc-D-Phe-OH, Fmoc-His(Trt)-OH, and Fmoc-Asp(O-2-PhiPr)-OH, were coupled to the resin in presence of HBTU (3 equivalents), HOBt (3 equivalents) and DIEA (6 equivalents). Before deprotection of the Fmoc on the Asp, the Mtt group on the Lys and the O-2-PhiPr group on the Asp were removed by 2.5% trifluoroacetic acid (TFA). Subsequently, the Lys and the Asp were cyclized in presence of benzotriazole-1-yl-oxy-trispyrrolidinophosphonium hexafluorophosphate (PyBOP, 4 equivalents) and DIEA (4 equivalents). Then, the Fmoc protecting group was removed, and Fmoc-Nle-OH was coupled, and the Fmoc was removed. For CCZ01047, CCZ01048 and CCZ01056, Fmoc-PEG₂-OH, Fmoc-Pip-OH, and two sequential Fmoc-Pip-OH linkers were coupled, respectively. Finally, the last Fmoc was removed, and the DOTA chelator (3 equivalents) was coupled, which was pre-activated with N-hydroxysuccinimide (3.6 equivalents) and N,N'-Dicyclohexylcarbodiimide (DCC, 3 equivalents). The peptide was simultaneously deprotected and cleaved from the resin by incubating with 90/2.5/2.5/2.5/2.5 TFA/phenol/H₂O/triisopropylsilane/1, 2-ethanedithiol for 3 h at room temperature. The solution was filtered and the peptide was precipitated in diethyl ether, and purified on a semi-preparative column using 23% acetonitrile containing 0.1% TFA at a flow rate of 4.5 mL/min using high-performance liquid chromatography (HPLC, Agilent). The HPLC eluate was collected and lyophilized, and the purity of the peptides was > 97%. Mass analysis was performed on a 5600 mass spectrometer (AB/Sciex). For gallium complexation, the purified peptide and GaCl₃ (5 equivalents) in sodium acetate buffer (0.1 M, pH 4.0) was incubated at 80°C for 15 min. The mixture was purified by HPLC using the same condition as described above.

Radiochemistry

⁶⁸Ga was obtained from a ⁶⁸Ge/⁶⁸Ga generator (iThemba Labs), by eluting with 0.6 M HCl. The eluate was mixed with concentrated metal-free 34-37% HCl. The mixture was passed through a DGA resin column (Eichrom), and washed by 5 M HCl. After the column was air-dried, ⁶⁸Ga was eluted off with deionized water. The purified ⁶⁸Ga solution was mixed with HEPES buffer (2 M, pH 5.0) and the DOTA conjugated peptides. The radiolabeling reaction was carried out under microwave heating for 1 min as described previously [21]. HPLC purification was then performed to remove free ⁶⁸Ga, and to separate radiolabeled product from precursor to ensure high specific activity of the final product for preclinical imaging studies. The reaction mixture was separated by HPLC using a semi-preparative column eluted with 24% acetonitrile containing 0.1% TFA for ⁶⁸Ga-CCZ01047, 21% acetonitrile containing 0.1% TFA for ⁶⁸Ga-CCZ01048 and 25% acetonitrile in phosphate-buffered saline (PBS) solution for ⁶⁸Ga-CCZ01056, at a flow rate of 4.5 mL/min. The retention times were 17.6, 24.4 and 18.7 min, respectively. The collected radiolabeled peptides were diluted with deionized water and retained on C18 SepPak cartridges (Waters) to remove acetonitrile and TFA/PBS. The purified peptides were eluted with ethanol and diluted with 0.9% NaCl saline. Quality control was performed on analytical column eluted with 24% acetonitrile containing 0.1% TFA for ⁶⁸Ga-CCZ01047, 23% acetonitrile containing 0.1% TFA for ⁶⁸Ga-CCZ01048 and 25% acetonitrile in PBS solution for ⁶⁸Ga-CCZ01056, at a flow rate of 2 mL/min. The retention times were 11.1, 7.0 and 6.7 min, respectively. Peptides with radiochemical purity of > 95% were used for subsequent experiments.

In vivo stability in mouse plasma

In vivo stability was characterized according to previously published procedures [22]. Briefly, mice were sedated with 2% isoflurane, and 8-12 MBq of ⁶⁸Ga-labeled peptide was injected via tail vein. At 5 or 15 min p.i., mice were euthanized and the blood was promptly withdrawn, which was mixed with equal volume of acetonitrile. After centrifugation for 15 min, the supernatant was collected and analyzed using radio-HPLC.

LogD_7.4 measurements

LogD_7.4 values of ⁶⁸Ga-labeled peptides were assessed using published procedures [23].

Cell culture

The B16F10 melanoma cell line (Mus musculus) used in the tumor model was obtained commercially from ATTC (CRL-6475). The cell line was confirmed pathogen-free by the IMPACT 1 mouse profile test (IDEXX BioResearch). Cells were cultured in Dulbecco's Modified Eagle's Medium (DMEM, StemCell Technologies) supplemented by 10% FBS, 100 U/mL penicillin and 100 μg/mL streptomycin at 37°C in a humidified incubator containing 5% CO₂. Cells grown to approximately 90% confluence were washed with sterile 1× PBS (pH 7.4), followed by trypsinization.

Receptor binding assays

In vitro competitive binding assays were performed using B16F10 cells. 500,000 cells/well were seeded onto a 24 well poly-D-lysine coated plate (Corning) overnight. Growth media was removed, and reaction buffer containing 4.8 mg/mL HEPES, 100 U/mL penicillin, 1,000 µg/mL streptomycin and 2 mg/mL BSA was added, and allowed to incubate with cells at 37°C for at least an hour. Non-radioactive Ga-coupled peptides and ¹²⁵I-[Nle⁴, D-Phe⁷]-alpha-MSH (PerkinElmer) were added to each well. The binding of ¹²⁵I-[Nle⁴, D-Phe⁷]-alpha-MSH was competed by the ligand of interest at increasing concentrations from 0.5 pM to 5 µM. The reaction mixture was incubated at 25°C with gentle agitation for 1 h. After the incubation, the reaction mixture was removed, and cells were washed with ice-cold PBS twice. 0.25% Trypsin solution was used to harvest the cells and radioactivity was measured on a WIZARD 2480 gamma counter (PerkinElmer).

Internalization assay

In vitro internalization assays were performed using B16F10 cells on 24 well poly-D-lysine coated plate (Corning) according to previously published procedures [24]. Briefly, approximately 500,000 cpm of ⁶⁸Ga-labeled peptide was added to the cells and allowed to incubate for 30, 60, 90 and 120 min at 37°C. After the incubation, cells were washed with ice-cold PBS. Two acid washes (0.2M Acetic acid, 0.5M NaCl, pH 2.6) were performed and collected to measure the membrane-bound fraction. The cells were subsequently trypsinized and collected to measure the internalized fraction. These fractions were counted for radioactivity using a WIZARD 2480 gamma counter (PerkinElmer).

Tumor implantation

All animal experiments were conducted according to the guidelines established by Canadian Council on Animal Care and approved by Animal Ethics Committee of the University of British Columbia. Mice were housed under pathogen-free conditions and kept on twelve-hour light and dark cycles in the Animal Resource Centre, BC Cancer Research Centre, Vancouver, Canada. PET imaging and biodistribution studies were performed using male C57BL/6J mice. For tumor implantation, mice were anesthetized by inhalation with 2% isoflurane in 2.0 L/min of oxygen, and 1×10⁶ B16F10 cells were implanted subcutaneously on the right back at the level of the forelimbs. Mice were imaged or used in biodistribution studies once the tumor grew to reach 8-10 mm in diameter in 8-10 days.

Preclinical PET/CT imaging

PET/CT imaging studies were carried out on a microPET/CT scanner (Inveon, Siemens) following the same procedures as previously published [21]. Briefly, for static PET scans, each tumor bearing mouse was injected with 4-6 MBq of ⁶⁸Ga-labeled peptides for the one hour time point, or 8-10 MBq for the two hour time point, via the caudal lateral tail vein under isoflurane sedation. After injection, the mice were allowed to recover and roam freely in their cages. After 1 or 2 hours, the mice were sedated again and positioned in the scanner. A baseline CT scan was obtained for localization and attenuation correction. This was followed by a 10 min static PET scan. For dynamic PET scans, a 60 min list-mode acquisition was started at the time of intravenous injection with 4-6 MBq of ⁶⁸Ga-labeled peptides following a baseline CT scan. The mice were kept warm by a heating pad during acquisition. The mice were euthanized using CO₂ inhalation after static PET imaging followed by biodistribution. The PET images were reconstructed using the ordered subset expectation maximization and maximum a posteriori algorithm (OSEM3D/MAP), using 2 OSEM3D iterations followed by 18 MAP iterations, with a requested resolution of 1.5 mm.

Biodistribution studies

Mice not used for imaging studies were anesthetized by 2% isoflurane inhalation, and injected with 1-2 MBq of ⁶⁸Ga-labeled peptides. For blocking studies, 100 μg of non-radioactive Ga-coupled peptides was co-injected with the radioactive compound. After injection, the mice were allowed to recover and roam freely in their cages, and euthanized by CO₂ inhalation 1 h or 2 h later. Blood was promptly withdrawn, and the organs of interest were harvested, rinsed with 1× PBS (pH 7.4), and blotted dry. Each organ was weighed and the radioactivity of the collected tissue was measured using a WIZARD 2480 (PerkinElmer) or a Cobra II gamma counter (Packard), normalized to the injected dose using a standard curve and expressed as the percentage of the injected dose per gram of tissue (%ID/g).

Autoradiography

Mice were sedated by 2% isoflurane inhalation, and injected with 6-8 MBq of ⁶⁸Ga-CCZ01048 with or without co-injection of 100 μg of non-radioactive Ga-coupled peptides. At 1 h p.i., mice were euthanized, and tumor, muscle and thyroid were harvested and frozen in isopentane/dry-ice bath. Autoradiography was performed according to previously published procedures [24]. Ten μm-thick sections were acquired for the organs of interest using a cryostat (Leica), thaw-mounted onto Superfrost Plus microscope slides (Fisherbrand). These sections along with a set of ⁶⁸Ga-peptide standards, were exposed to a phosphor screen overnight and imaged on a Typhoon FLA 9500 scanner (GE Healthcare).

Statistical analysis

Data analysis was performed using GraphPad Prism 6.0h. Multiple t tests were performed for all organs in the biodistribution studies; multiple comparisons were corrected using the Holm-Sidak method. Outliers were removed using the ROUT method with Q = 1%. The difference was considered statistically significant when the adjusted p value was < 0.05. Blood half-life of radiotracers was calculated using non-linear regression assuming one phase decay.

Results

Chemical properties and in vitro binding affinity

All three α-MSH analogues, CCZ01047, CCZ01048 and CCZ01056, were prepared with high purity (> 97%, Figure S1), and the molecular weight was verified by mass spectrometry (Table 1, Figure S2). The chemical structures of the tracers are shown in Figure 1. The inhibition constant (K_i) of these α -MSH analogues to MC1R was measured using competitive binding assays. All three peptides showed sub-nanomolar K_i (Figure 2, Table 1).

Radiochemical characteristics, in vivo plasma stability and in vitro internalization

The radiochemical data for the three tracers are summarized in Table 2. The ⁶⁸Ga-labeled CCZ01047, CCZ01048 and CCZ01056 were prepared with > 96% radiochemical purity in average decay-corrected radiochemical yields ranging from 50-61%. High specific activity was achieved with the average > 236.8 MBq / nmol. All three ⁶⁸Ga-labeled tracers were fairly hydrophilic with average LogD_7.4 values ranging from -3.14 to -3.07. Furthermore, all three tracers were shown to be considerably stable in vivo with > 93% remaining intact at 15 min p.i. in blood plasma in mice (Table 2, Figure S3). In addition, all three tracers were shown to be rapidly internalized into B16F10 cells with 36%-52% of total bound activity being internalized after 30 min incubation, and increased to 55%-62% after 120 min (Figure S4).

 Figure 1 

Chemical structures of gallium-labeled A. CCZ01047, B. CCZ01048, and C. CCZ01056.

 Figure 2 

Representative competitive binding curves for the natural gallium-labeled A. CCZ01047, B. CCZ01048, and C. CCZ01056.

 Figure 3 

PET images of A. ⁶⁸Ga-CCZ01047 B. ⁶⁸Ga-CCZ01048 and C. ⁶⁸Ga-CCZ01056 at 1 h p.i., in mice bearing B16F10 tumor. The scale bar unit is %ID/g. Tumors are indicated by arrows.

 Figure 4 

Tumor-to-kidneys uptake ratios for ⁶⁸Ga-CCZ01047 and ⁶⁸Ga-CCZ01056 at 1 h p.i., and ⁶⁸Ga-CCZ01048 at 1 h p.i. with and without co-injection of 100 μg of non-radioactive Ga-labeled CCZ01048 and at 2 h p.i.

PET/CT imaging, biodistribution and autoradiography

For all three tracers, tumors were clearly visualized with high contrast on the PET images at 1 h p.i. (Figure 3). Biodistribution studies revealed tumor uptake at 1 h p.i. for ⁶⁸Ga-labeled CCZ01047, CCZ01048 and CCZ01056 was 8.0 ± 3.0, 12.3 ± 3.3, and 6.5 ± 1.4 %ID/g, respectively (Table 3). Minimal normal organ activity was observed at 1 h p.i., except for kidney (5.1 ± 1.4, 4.7 ± 0.5, and 6.2 ± 2.0 %ID/g, respectively), and thyroid (4.1 ± 0.6 %ID/g for CCZ01047 and 2.4 ± 0.6 %ID/g for CCZ01048). Tumor-to-kidney uptake ratios were 1.6 ± 0.6, 2.7 ± 0.9 and 1.1 ± 0.3, respectively (Figure 4). Dynamic PET scans were performed to characterize the time activity curves of the three tracers. For CCZ01047 and CCZ01048, tumor uptake was sustained and increased over time; but for CCZ01056, tumor uptake slightly decreased (Figure 5). Moreover, activity clearance was much faster in normal tissues with CCZ01048 compared to CCZ01047. Therefore, CCZ01048 was further evaluated at 2 h p.i., and a higher tumor uptake of 21.9 ± 4.6 %ID/g was observed, with background activity further decreased compared to the one hour time point (Figure 6, Table 3). Excellent image contrast was achieved for CCZ01048 at 2 h p.i. Tumor-to-blood, tumor-to-muscle, tumor-to-bone and tumor-to-kidney ratios were all increased compared to 1 h p.i., reaching 96.4 ± 13.9, 210.9 ± 20.9, 39.6 ± 11.9, and 4.0 ± 0.9, respectively. A blocking study was performed for CCZ01048 at 1 h p.i. with co-injection of 100 µg of non-radioactive Ga-labeled CCZ01048 (Figure 6C, Table 3). Tumor uptake significantly decreased (p < 0.001) by more than 80%, to 2.3 ± 1.1 %ID/g, which was comparable to the blood activity at 2.8 ± 1.3 %ID/g. Kidney accumulation was higher in the blocking study, at 24.4 ± 13.5 %ID/g. Autoradiography was also performed to further evaluate the in vivo radioactivity distribution of ⁶⁸Ga-CCZ01048 at 1 h p.i. (Figure S5). Strong intensity was observed for tumor slices, and minimal intensity for background muscle and thyroid slices. Moreover, with co-injection of 100 µg of non-radioactive Ga-labeled CCZ01048, tumor slices showed largely reduced signal intensity and comparable to that of muscle slices.

 Figure 5 

Time activity curves of A. ⁶⁸Ga-CCZ01047, B. ⁶⁸Ga-CCZ01048 and C. ⁶⁸Ga-CCZ01056 using region-of-interest located around the tumor, muscle, blood (from left ventricle), and bone. %ID/g is in log scale. The blood half-life of the radiotracers was 9.0, 4.0 and 4.1 min, respectively.

 Figure 6 

PET images of ⁶⁸Ga-CCZ01048 at A. 1 h p.i., B. 2 h p.i. and C. 1 h p.i. with co-injection of 100 μg of non-radioactive Ga-labeled CCZ01048, in mice bearing B16F10 tumors. The scale bar unit is %ID/g. Tumors are indicated by arrows.

Discussion

MC1R has been studied extensively for melanoma imaging in the preclinical setting, based on the sequence of α-MSH peptide, predominantly for radiolabeling using single photon emitters. A few generations of tracers have been designed and evolved from linear to cyclized peptides, which were further improved by shortening the ring to six amino acids, i.e. CycMSH_hex. Guo and colleagues introduced ¹¹¹In-DOTA-Nle-CycMSH_hex, which showed tumor uptake of 19.4 ± 1.7 %ID/g, with tumor-to-kidneys uptake ratio of 2.0 at 2 h p.i. [19]. Introduction of a -GlyGly- or a -GlyGlu- linker between the DOTA and the Nle-CycMSH_hex resulted in tumor uptake of 19.1 ± 5.0 and 9.0 ± 1.9 %ID/g at 2 h p.i., respectively [16]. Moreover, ¹¹¹In-DOTA-GlyGly-Nle-CycMSH_hex had a slightly increased tumor-to-kidney uptake ratio of 2.8 at 2 h p.i. Interestingly, the addition of the negatively charged amino acid glutamate in the linker significantly decreased tumor uptake. In previous studies, we observed that introduction of a cationic Pip linker not only improved receptor binding affinity, but also generated approximately two-fold increase in tumor uptake for radiotracers targeting the bradykinin 1 receptor [22], similar to observations made by others with gastrin-releasing peptide receptor radioligands [25]. Therefore, in this study, based on the previously reported core structure, DOTA-Nle-CycMSH_hex, we synthesized three new tracers with a neutral PEG₂ linker (CCZ01047), a cationic Pip linker (CCZ01048), and dual Pip linkers (CCZ01056).

All three peptides exhibited high binding affinity, with sub-nanomolar inhibition constants to MC1R on B16F10 cells, which is an established model for melanoma imaging [26-28]. For CCZ01048, which has a single cationic Pip linker, the inhibition constant improved more than 2-fold compared to CCZ01047 with the neutral PEG₂ linker. The peptide with the dual Pip linkers (CCZ01056) further improved the binding affinity approximately 2-fold. Also, all ⁶⁸Ga-labeled peptides were fairly stable in vivo with more than 93% remaining intact at 15 min p.i. in mice. Due to the fast blood clearance of the radiotracers in vivo, stability tests at longer time points resulted in low radioactivity of the remaining peptides, which were comparable to background, and thus cannot be quantified. Moreover, all three tracers were rapidly internalized into cells with 55%-62% after 120 min incubation. The high in vivo stability and high level of internalization is consistent with a ^99mTc(CO)₃-labeled peptide, which has the same core structure of Nle-CycMSH_hex [18].

Tumors were clearly visualized with high tumor-to-background contrast for all three tracers in static PET scans. Also, both ⁶⁸Ga-CCZ01047 and ⁶⁸Ga-CCZ01048 showed increased and sustained tumor uptake in dynamic PET scans, with ⁶⁸Ga-CCZ01048 showing faster background clearance as well as faster accumulation at tumor sites. Moreover, ⁶⁸Ga-CCZ01048 produced the highest tumor uptake at 12.3 ± 3.3 %ID/g at 1 h p.i. in biodistribution studies, compared to 8.0 ± 3.0 %ID/g for ⁶⁸Ga-CCZ01047 and 6.5 ± 1.4 %ID/g for ⁶⁸Ga-CCZ01056. In addition, ⁶⁸Ga-CCZ01048 showed the lowest activity accumulation in kidneys at 4.7 ± 0.5 %ID/g at 1 h p.i., compared to 5.1 ± 1.4 %ID/g for ⁶⁸Ga-CCZ01047 and 6.2 ± 2.0 %ID/g for ⁶⁸Ga-CCZ01056. Therefore, ⁶⁸Ga-CCZ01048 was selected as the best candidate and evaluated further. Interestingly, moderate thyroid accumulation was also observed for ⁶⁸Ga-CCZ01047 and ⁶⁸Ga-CCZ01048. Similar uptake at the region of thyroid was shown for another PET tracer, ⁶⁴Cu-DOTA-GlyGly-Nle-CycMSH_hex [20]. However, no thyroid uptake was reported for CycMSH_hex-based radiopeptides labeled with SPECT isotopes. Furthermore, the decrease in thyroid uptake was not statistically significant following co-injection of excess amount of non-radioactive Ga-coupled CCZ01048. Nonetheless, activity accumulation in thyroid was moderate and lower than kidneys in all conditions tested; therefore, kidneys remain to be the dose-limiting organ for radiotherapy using this peptide. Potential adverse effects due to thyroid damage would still need to be closely monitored. There is extensive experience with radioiodine in diagnosis and treatment of thyroid diseases. Radiation exposure to the thyroid gland can readily be managed with thyroid hormone supplementation. This would be minor in the context of advanced metastatic melanoma treatment.

Blocking studies via PET imaging, biodistribution and autoradiography all confirmed that ⁶⁸Ga-CCZ01048 tumor uptake was MC1R mediated. The excess amount of the non-radioactive counterpart slowed down the clearance of the ⁶⁸Ga-CCZ01048, and thus higher background radioactivity level, including the kidneys, was observed in the static PET image, biodistribution and autoradiography data, which was expected. We further investigated ⁶⁸Ga-CCZ01048 at 2 h p.i., which led to higher tumor uptake at 21.9 ± 4.6 %ID/g, and moderate kidneys uptake of 5.5 ± 0.4 %ID/g. The average tumor-to-kidney uptake ratio of 4.0 at 2 h p.i. is the highest reported to date for all radiopeptides based on the CycMSH_hex. The low kidney uptake is particularly advantageous, since kidney is commonly a major dose-limiting organ when peptide receptor radionuclide therapy is employed. Furthermore, the 21.9 ± 4.6 %ID/g tumor uptake value is the highest among all PET tracers targeting MC1R. This is a notable improvement from 13.4 ± 1.6 %ID/g of ⁶⁴Cu-labeled NOTA-GlyGly-Nle-CycMSH_hex at 2 h p.i. [20]. Therefore, the combination of the rapid internalization, high tumor uptake and excellent tumor-to-normal organ uptake ratios make CCZ01048 a promising candidate for radionuclide therapy, by coupling the same peptide with ¹⁷⁷Lu or ²¹³Bi/²²⁵Ac.

In conclusion, we designed and evaluated three ⁶⁸Ga-labeled peptides based on CycMSH_hex, and observed that the introduction of a cationic Pip linker, CCZ01048, not only improved tumor uptake, but also generated high tumor-to-normal tissue contrast with PET imaging in a preclinical melanoma model. Therefore, CCZ01048 is a promising candidate for PET imaging of malignant melanoma, and potentially as a theranostic compound for radionuclide therapy of melanoma using α or β emitters.

Supplementary Material

Supplementary figures.

Acknowledgements

This work was supported in part by the Canadian Institutes of Health Research (MOP-119361), the BC Cancer Foundation, and the BC Leading Edge Endowment Fund.

Competing Interests

The authors have declared that no competing interest exists.

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Author contact

Corresponding author: Dr. François Bénard. Address: Department of Molecular Oncology, BC Cancer Agency, 675 West 10^th Avenue, Rm 14-111, Vancouver, BC V5Z 1L3, Canada. Phone: 604-675-8206. Fax: 604-675-8218. E-mail: fbenardca.

Received 2016-8-5
Accepted 2016-11-10
Published 2017-2-8

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