Research Progress of Radiolabeled Asn-Gly-Arg (NGR) Peptides for Imaging and Therapy.

Asn-Gly-Arg (NGR) motifs have vasculature-homing properties via interactions with the aminopeptidase N (CD13) expressed on tumor neovasculature. Numerous NGR peptides with different molecular scaffolds have been exploited for targeted delivery of different compounds for imaging and therapy. When conjugated with NGR, complexes recognize the CD13 receptor expressed on the tumor vasculature, which improves the specificity to tumor and avoids systematic toxic reactions. Both preclinical and clinical studies performed with these products suggest that NGR-mediated vascular targeting is an effective strategy for delivering bioactive amounts of cytokines to tumor endothelial cells. For molecular imaging, radiolabeled peptides have been the most successful approach and have been translated into clinic. This review describes current data on radiolabeled tumor vasculature-homing NGR peptides for imaging and therapy.

Introduction

New blood vessels recruit from the preexisting vasculature by neoangiogenesis in the tumor stroma. This is a fundamental process in tumor cell survival, proliferation, and invasion, and it is a multistep process involving growth factors, adhesion molecules, and cellular receptors. Among these, CD13 (also referred to as aminopeptidase N [APN], a zinc-dependent membrane-bound ectopeptidase) is a critical regulator of angiogenesis. CD13 is expressed on activated blood vessels induced by angiogenic signals. The high expression level of CD13 is associated with the progression of tumors, including lung, prostate, and ovarian cancers.[1] Therefore, efforts have been made to identify biomarkers that interact with CD13 expressed in angiogenic vessels to generate new antiangiogenic agents or to obtain ligands for targeted delivery of drugs or imaging agents to tumors.

Asparagine-glycine-arginine (NGR)-containing peptides target the tumor vasculature via interactions with CD13 as seen in peptide-phage library panning in tumor-bearing mice.[2] CD13 is also expressed in normal tissues, including myeloid cells, antigen-presenting cells, mast cells, epithelial cells from renal proximal tubules, small intestine, keratinocytes, prostate, and bile duct canaliculi.[3] However, experiments have suggested that the NGR-containing peptides can bind CD13-positive vessels in tumors, but not other CD13-rich tissues. This may be due to the expression of different forms of CD13. These results further show the feasibility of using NGR-containing peptides as a potential and promising diagnostic and therapeutic agent.[4] Therefore, numerous efforts have been made to explore the NGR tripeptide motif as vehicle for delivering chemotherapeutic drugs, nanoparticles, and radioisotopes to the tumor. Both the preclinical experiments and clinical trials have shown its utility for imaging the tumor vasculature.[5]

NGR is a promising target for cancer therapy, and it is important to develop an approach for noninvasively imaging CD13 receptor levels in living subjects to identify responsive patients, monitor therapy, and estimate prognosis. NGR-based molecular radioimaging is an optimal method for assessing the expression of CD13 receptor in vivo noninvasively and accurately. In this review, we comprehensively summarize the current status of NGR peptide–directed drug delivery and highlight molecular radioimaging in cancer.

Structures of Common NGR Peptides

Initial reports revealed that a pentapeptide of NGR was sufficient to be the minimum binding motif with an NGR sequence flanked by 1 amino acid at both ends[6] (Figure 1). The results show the different molecular scaffolds of NGR peptides that have been coupled to drugs and particles through the N-terminal or C-terminal.[3,5,7] Although it is generally assumed that all of these peptides could bind to CD13 on the tumor neovasculature, different molecular scaffolds of NGR motifs confer different biochemical and biological properties such as the binding affinity to CD13-positive endothelial cells and different degradation patterns.

Figure 1.

Structure of common NGR peptides.

Numerous experiments have further confirmed that cyclic NGR (cNGR) displayed stronger affinity and higher specificity toward the CD13 receptors than linear ones.[7,8] First-generation linear forms of the NGR peptides suffered from low selectivity and stability. The improvement and reforming were achieved by developing the cyclic pentapeptides, including NGR cyclized through the disulfide bond (named cCNGRC).[7] To further improve the stability of NGR toward chemical and enzymatic reactions, more robust cyclizations have been introduced such as the amide linkage made by direct conjugation or the triazole linkage resulting from click chemistry.[8,9] The cNGR ligand, cKNGRE, was cyclized by the amide bond and displayed 3.6-fold greater affinity than linear KNGRG in CD13 cancer cells.[8] When both linear NGR and disulfide-bonded cNGR were coupled with the tumor necrosis factor (TNF) α, the cNGR-TNF-α exhibited more than 10-fold higher antitumor activity compared to the linear NGR derivative.[7] Except for these, using multimeric cNGR peptides could improve the binding affinity to tumor cells.[10]

Furthermore, the main degradation product of cNGR peptides is characterized by a gain of 1 Da, while the main degradation product of linear NGR is characterized by a loss of 17 Da versus the original peptide. The different degradation patterns of cyclic and linear peptides can be explained by the fact that the disulfide bridge reduces peptide bond flexibility and decreases the potential reactivity of the α-amino group with the Asn side chain or with the succinimide intermediate.[11] The Asn residue of linear NGR tends to spontaneously deamidate and generate Asp and isoAsp residues.[12] This reaction occurs by nucleophilic attack of the backbone amino-group on the Asn side chain, leading to the formation of mixtures of isoDGR and DGR with changes in peptide bond length and charge. As a consequence, the change in NGR to isoDGR/DGR caused a loss of CD13-binding affinity and gain of αvβ3-integrin-binding activity.[12]

Considering the biochemical and biological characteristics of different molecular scaffolds such as peptide stability and receptor binding specificity, NGR drug conjugates and fusion proteins should be carefully designed, produced, stabilized, and developed to further stimulate investigation.

NGR Peptide-Based Drug Delivery Systems

Due to their neovasculature homing properties, NGR peptides have been exploited for targeted delivering of different compounds to tumors including cytokines, chemotherapeutic drugs, liposomes, antiangiogenic agents, imaging agents, and nucleic acid to CD13-positive tumor neovasculature.[3] NGR-based chemotherapeutic agents such as NGR-liposomal doxorubicin, docetaxel-loaded polymeric micelles, platinum (IV), carboplatin, 5-fluorouracil prodrug, and 5-fluoro-2′-deoxyuridine prodrug showed selectively toxicity for angiogenic endothelial cells and anticancer activity in mice.[13,14] NGR-based cytokines such as tumor necrosis factor α (hTNFα), interferon-γ (IFNγ), IFN α2a, endostatin, a tumstatin fragment 35-135, and truncated tissue factor also have antiangiogenic activity[3,15-17]

Of these, NGR-based tumor necrosis factor α (NGR-hTNF) is the most widely studied molecule. It has been studied in phase I-III clinical trials.[18] Tumor necrosis factor α, an inflammatory cytokine, was initially identified for its impressive antitumor activity in a variety of tumors. It destroys tumor-associated vessels and activates the immunogenic response rather than by directly damaging tumors. However, despite the significant antitumor effects observed in animal models, phase I-II clinical trials showed that TNF induced toxic effects and extremely low antitumor activity.[19] Tumor necrosis factor combined with NGR had stronger antitumor activity and less toxicity than TNF alone. The dose–response curve showed microgram doses of TNF were necessary to induce antitumor effects, while a wider range of NGR-TNF doses (from picograms to micrograms) showed antitumor activity.[19]

A phase I study (EORTC 16041) investigated dose-limiting toxicities, maximum tolerated dose (MTD), pharmacodynamics, pharmacokinetics, and vascular response in solid tumors. Here, NGR-hTNF were administered within 20 or 60 minutes in the range of 0.2 to 60 g/m2. The MTD was 45 g/m2 when administered in 1 hour, and the most frequently observed toxicities were chills and fever.[20] A later phase I study defined the optimal biological dose of NGR-hTNF to be 0.8 g/m2 in the low dose range (0.2-1.6 g/m2, 1-hour infusion).[21] A randomized, double-blind, placebo-controlled phase 3 trial has been conducted to investigate its efficacy and safety in patients with malignant pleural mesothelioma who progressed during or after the first-line treatment: 200 patients were selected to receive NGR-hTNF plus best investigator choice and 200 patients received placebo plus best investigator choice. Although the overall survival did not differ between the NGR-hTNF group and the placebo group (median: 8.5 months, 95% CI: 7.2-9.9 vs 8.0 months, 95% CI: 6.6-8.9; P = .58), subgroup analyses suggest patients with shorter treatment intervals may benefit from NGR-hTNF.[22] In addition, NGR-hTNF has been performed on hepatocellular carcinoma (HCC), malignant pleural mesothelioma (MPM), metastatic melanoma, small cell lung cancer, relapsed ovarian cancer, and colorectal cancer (CRC) both alone and in combination with chemotherapy in different phases of clinical trials. All these studies showed that NGR-hTNF was well tolerated with significant disease control at low dose.[22-27] Thus, NGR-hTNF deserves further investigation in MPM, HCC, and CRC. These findings suggest an improved antitumor activity by the NGR-mediated vascular targeting approach.

Monomeric Compounds of NGR for Tumor Radioimaging

Different NGR motifs have been labeled with different radionuclides through different bifunctional chelators. The most studied nuclides were 68Ga and 64Cu for positron emission tomography (PET) imaging and 99mTc for single-photon emission computed tomography (SPECT) imaging. Positron emission tomography provides higher spatial resolution than SPECT.

Zhang et al[28] investigated the feasibility of 68Ga-labeled linear NGR for the detection of the CD13-positive tumors. MicroPET imaging showed high focal accumulation of 68Ga-DOTA-NGR visualized at the tumor site at 1 hour in A549 tumor xenografts. The maximum uptake of 68Ga-DOTA-NGR in A549 tumors was nearly 1% ID/g, and the maximum tumor/lung ratios were 12.58 ± 1.26 at 1.5 hours. Immunohistochemistry confirmed that radioactivity was correlated with expression of CD13 in A549 xenografts and confirmed that NGR is a promising molecular probe for CD13. Although tumor uptake was higher than the APN-negative MDA-MB231 tumor group, the tumor uptake of 68Ga-labeled linear NGR is not optimal for tumor radioimaging. While 18F-fluorodeoxyglucose PET/computed tomography (CT) is effective for early detection in various malignant diseases, it was limited in detecting well-differentiated HCCs. This may be caused by the overexpressed glucose-6-phosphatase (G6Pase) and the low expressed glucose transporter 1.[29] In terms of the high expression rate of CD13 in a variety of HCC cell lines, Gao et al[30] compared 68Ga-DOTA-G3-cNGR (cycled by disulfide bond) and [18]F-FDG to image well-differentiated SMMC-7721 HCC xenografts (positive for both CD13 and G6Pase). The extra 3 glycines were added to protect the core motif NGR and increase peptide half-life and stability. In vivo microPET/CT imaging studies indicated the uptake of 68Ga-DOTA-G3-cNGR in SMMC-7721 tumors was similar to that in the CD13-positive control HT-1080 tumors (2.17% ± 0.21% ID/g vs 2.46% ± 0.23% ID/g, P = .18 > .05) and was obviously higher than that in the CD13-negative control HT-29 malignancy (2.17% ± 0.21% ID/g vs 0.67% ± 0.20% ID/g, P = .0148 < .05). The uptake of 68Ga-DOTA-G3-cNGR in SMMC-7721-derived tumors was 2.97-fold higher than that of [18]F-FDG (2.17% ± 0.21% ID/g vs 0.73% ± 0.26% ID/g). The tumor/liver ratio of 68Ga-DOTA-G3-cNGR was 2-fold higher than that of [18]F-FDG in the SMMC-7721 HCC models. In terms of high uptake and T/L ratio in well-differentiated HCC tumor, 68Ga-DOTA-G3-cNGR was more suitable for imaging well-differentiated HCC as compared to [18]F-FDG. As compared to the linear 68Ga-DOTA-NGR studied by Zhang et al., the circular structure indeed significantly improves the uptake of tumors.[28]

Although there are multiple studies using DOTA as a chelator for 68Ga, 68Ga-NOTA system has been shown to have higher stability than that of 68Ga-DOTA system.[31] Shao et al[32] developed 68Ga-NOTA-G3-cNGR for noninvasive imaging of CD13 expression in vivo by PET. The disulfide bond cycled cNGR radioprobe exhibited rapid and significant tumor uptake and good tumor-to-background contrast in a subcutaneous HT-1080 fibrosarcoma mouse model. HT-1080 tumor uptake of 68Ga-NOTA-G3-NGR was 6.30% ± 2.27%, 5.03% ± 1.95%, and 3.84% ± 2.32% ID/g at 0.5, 1, and 2 hours, respectively. The ratios of HT-1080 tumor uptake to muscle, liver, kidney, and blood at 1 hours were 7.39 ± 2.20, 3.14 ± 0.35, 0.57 ± 0.02, and 4.78 ± 1.14, respectively. Versus uptake of 68Ga-DOTA-G3-cNGR studied by Gao et al[30] in HT-1080 tumors, 68Ga-NOTA-G3-cNGR shows significantly higher uptake (6.30% ± 2.27% ID/g vs 2.46% ± 0.23% ID/g) in HT-1080 tumor and higher tumor/muscle ratios (7.39 ± 2.20 vs 2.14 ± 0.43), suggesting better chelation of 68Ga-NOTA system.

Poor uptake and short retention time due to the smaller molecular weight are the most common problems for small-molecule peptide probes.[33] The most important reason for the short half-life time of peptides and proteins is their rapid renal excretion and enzymatic degradation. In general, molecules with a mass below 5 kDa are not bound to plasma proteins and could be completely excreted through renal pathways. Molecules with a mass greater than 50 kDa cannot be found in the glomerular ultrafiltrate. Zhao et al[34] introduced CendR into the NGR peptide (denoted as iNGR) and then compared the efficacy of 68Ga-DOTA-iNGR and 68Ga-DOTA-NGR (cycled by disulfide bond) as a new molecular probe for microPET imaging of CD13-positive xenografts. The CendR motif (R/KXXR/K), a C-terminal sequence containing a C-terminal arginine or lysine with a free carboxyl group, can increase the residence time, increase the flow of the peptide through blood vessels, and direct the peptide to pass through biological barriers by interacting with neuropilin-1 (NRP-1).[35] In vivo microPET imaging studies showed that the tumor uptake values were 3.41 ± 0.28, 2.97 ± 0.30, and 2.64 ± 0.31% ID/g at 0.5, 1, and 1.5 hours for 68Ga-DOTA-iNGR and 2.68 ± 0.35, 1.91 ± 0.32, and 1.45 ± 0.30% ID/g for 68Ga-DOTA-NGR, respectively (P < .05). The maximum uptake rate of 68Ga-DOTA-iNGR in HT-1080 cells was about 2-fold higher than 68Ga-DOTA-NGR (1.78% ± 0.14% vs 0.90% ± 0.12%) at 2 hours. Furthermore, the uptake rate of 68Ga-DOTA-iNGR was similar to that of 68Ga-DOTA-NGR after being blocked by NRP-1 antibody. Tumor uptake of 68Ga-DOTA-iNGR could be completely blocked by cold NGR and partially blocked by neutralizing NRP-1 antibody, indicating that the enhancement was attributed to the interaction of CendR and NRP-1. The uptake of 68Ga-DOTA-iNGR in HT-1080 tumors was significantly higher than that of 68Ga-DOTA-NGR at all time points and with longer retention time. The CendR motif modification is a promising method for improving NGR peptide performance.

In addition to radionuclide 68Ga for PET imaging, 99mTc has been used to label NGR peptides for SPECT. NGR peptide (cyclic via a disulfide bond) was synthesized and directly labeled with 99mTc and then subjected to SPECT imaging of CD13 expression in a CD13 receptor-positive HepG2 hepatoma xenograft mouse model. A SPECT imaging also showed significant uptake in tumor and dominant renal and hepatic clearance. The highest tumor uptake of 99mTc-cNGR was 3.26% ± 0.63% ID/g, with the highest tumor-to-normal tissue (T/NT) ratio 7.58 ± 1.92 at 8 hours. However, the tumor/liver at 1 hour was 0.63 ± 0.33, which could limit applications in abdominal diseases.[36] NGR peptides could be conjugated with the most commonly used bifunctional technetium chelators mercaptoacetylglycylglycylglycine (MAG3). Faintuch et al[37] evaluated the in vitro and in vivo performance of 99mTc radiolabeled pegylated cNGR peptide 99mTc-MAG3-PEG8-cNGR (cycled through the amide bond) as a marker of imaging angiogenesis in lung (A549), prostate (PC-3), and ovarian (OVCAR-3) tumors. PEGylation protects peptides from enzymatic degradation and enhances overall hydrophilicity of the compounds. This increases the peptide half-life and stability and decreases immunogenicity. Lung and ovarian cancer cells show promising results, but prostate cancer cells do not. This may be caused by the different receptor expression levels in tumor cells.

Glutamic acid-cysteine-glycine (ECG) is a tripeptide containing a sulfur and multiple nitrogen atoms. It shows strong chelation ability with 99mTc.[38] Through using peptides ECG as bifunctional coupling agent, Kim et al[39] developed 2 NGR-containing hexapeptides, ECG-NGR and NGR-ECG, as molecular imaging agents to target APN/CD13 in HT-1080 fibrosarcoma. The tumor/muscle uptake ratio of 99mTc-ECG-NGR reached 5.7 ± 0.4 at 4 hours, which is comparable to dimeric NGR-based peptides 99mTc-NGR2 in HepG2 hepatoma xenografts model (6.06 at 4 hours).[40] In contrast, the tumor/muscle uptake ratio of 99mTc-NGR-ECG was only 2.9 ± 0.5 at 4 hours, which is lower than that of 99mTc-ECG-NGR. In vitro and in vivo studies showed that 99mTc-ECG-NGR has a better specific binding ability for the tumor cells and tumor tissue than 99mTc-NGR-ECG. This may be because the asparagine residue of NGR-ECG is not protected by other amino acids and could be easily deamidated by a nucleophilic attack. A series reaction after nucleophilic attack of the backbone NH center on the asparagine side chain leads to the formation of mixtures of isoDGR/DGR, which lead to a loss of CD13-binding affinity and lower tumor uptake.[11,12] We concluded that different molecular scaffolds have a significant influence on peptide-binding properties of APN/CD13 in tumor neovasculature. Modification of the N-terminus seems crucial to improving the in vitro and in vivo performance of NGR peptides.

Chlorambucil (CLB), a DNA-alkylating nitrogen mustard, is widely used to treat chronic lymphocytic leukemia, lymphomas, breast, and ovarian carcinoma and a variety of other solid tumors. To address the systemic toxicity and various other side effects caused by its low specificity, Vats K et al[41] explored the targeted chemotherapy ability of CLB-cNGR and used 99mTc to monitor its pharmacokinetics and biodistribution through the chelator 6-hydra-zinonicotinic acid (HYNIC). Drugs conjugated with the targeting vectors NGR peptides can act as conduits for site-specific delivery and can then overcome the nonspecific accumulation in normal tissues.[42] The cytotoxicity studies demonstrated that CLB-cNGR significantly inhibits B16F10 cell growth at all concentrations versus CLB or cNGR. A ∼25-fold excess concentration of CLB could achieve similar cytotoxicity as CLB-cNGR. In vivo biodistribution studies showed that the maximum tumor uptake was 2.45% ± 0.28% ID/g at 30 minutes and maximum tumor to muscle ratio was 4.23 ± 0.57 at 180 minutes in C57BL6 mice bearing melanoma tumors. This suggests that the systemic exposure and side effects of drugs can be reduced by conjugation to the targeting peptide. In addition, radiolabeled peptide drug conjugates contribute can help track the pharmacokinetics of the drug. In general, 99mTc-labeled NGR peptides have similar tumor uptake as 68Ga but also have higher liver uptake, which limits their use in abdominal diseases.

Dimeric Compounds of NGR for Tumor Radioimaging

Although most NGR peptide-based probes can target tumors by binding to the CD13 receptor, they usually show moderate tumor uptake and unfavorable pharmacokinetics, which limit their applications in tumor imaging and therapy. Dimerization of a ligand can be an effective approach to enhance the binding affinity to specific receptor leading to higher tumor uptake through multivalency effects (multivalency effects refer to the synthesis of more than one targeting ligand in a single reagent to simultaneously bind multiple receptors and enhance the overall binding affinity).[43]

The most common multivalent system is the dimer. It has been reported that dimeric RGD peptides can markedly improve the binding affinity of the RGD ligand to integrin αvβ3 receptor.[43] CD13 receptor and integrin αvβ3 receptors are both cell surface targets of tumor angiogenesis: Dimeric NGR peptides with 2 repeating cNGR may also lead to higher affinity of the receptor and uptake in the tumor. The increased molecular size can prolong circulation time, reduce tumor washout rate, and lead to longer retention time in the tumor.

64Cu-labeled monomeric and dimeric NGR peptides (cycled by disulfide bond) for microPET imaging of CD13 receptor expression have also been explored. The HT-1080 tumor uptake was 3.33% ± 0.10%, 3.09% ± 0.20%, 2.32% ± 0.17%, and 1.79% ± 0.27% ID/g at 1, 2, 4, and 24 hours for 64Cu-DOTA-NGR1; the corresponding values were 6.53% ± 0.20%, 6.09% ± 0.18%, 5.22% ± 0.17%, and 3.60% ± 0.23% ID/g at 1, 2, 4, and 24 hours, respectively, for 64Cu-DOTA-NGR2. The tumor to muscle ratio at 4 hours was calculated to be 3.91 ± 0.19, while the corresponding values for 64Cu-DOTA-NGR2 were 7.57 ± 0.15 (Figure 2). Both the cell-based binding assay and microPET imaging suggested a nearly 2-fold higher CD13 avidity of 64Cu-DOTA-NGR2 than the corresponding monomeric 64Cu-DOTA-NGR1 in HT-1080 cells. Both 64Cu-DOTA-NGR1 and 64Cu-DOTA-NGR2 showed predominant uptake in liver and kidneys at all time points.[44] High accumulation and retention in the liver may result from the slow dissociation of 64Cu from the DOTA chelator. The instability of 64Cu-DOTA can lead to de-metalation and subsequent accumulation in nontarget tissues and organs such as in the liver. This is a common problem for 64Cu-DOTA probes. Except for trapping of 64Cu in the mouse liver, another important reason for liver uptake may be caused by CD13 expression in mouse liver. Thus, characterizing the CD13 expression levels in normal organs and tissues, such as in liver and kidneys, will promote clinical imaging applications of NGR-containing probes.

Figure 2.

Representative micro positron emission tomography images of mice bearing HT-1080 or HT-29 tumors. Right front flank images shown 4 hours after intravenous (IV) administration of 64Cu-DOTA-NGR1 or 64Cu-DOTA-NGR2. The blocking study was performed by IV injection of 64Cu-DOTA-NGR1 or 64Cu-DOTA-NGR2 with coinjection of NGR peptide [c(CNGRC)] in HT-1080 tumor xenografts. It suggested a nearly 2-fold higher CD13 avidity of 64Cu-DOTA-NGR2 than the corresponding monomeric 64Cu-DOTA-NGR1 in HT-1080 cells. Adapted with permission from Kai Chen et al.44 Copyright (2019) America Chemical Society.

In other research, a 64Cu-labeled dimeric disulfide bond with a cNGR peptide based on the sarcophagine cage has been studied to decrease Cu2+ dissociation. The sarcophagine cage (denoted as “Sar”) is a macrocyclic chelator. Although it has excellent binding ability and a higher radiolabeling efficiency for 64Cu2+ than other chelators, it has also failed to address the problem of significant uptake in liver in this study. The liver uptake values were calculated to be 9.81% ± 0.62% ID/g at 1 hour; the ratio of HT-1080 tumor uptake to liver at 4 hours was 0.79 ± 0.27, which is comparable to the value of 64Cu-DOTA-NGR2.[44] The cell-based binding assay, microPET imaging, and biodistribution studies indicated that 64Cu-Sar-NGR2 has a similar CD13 affinity and comparable biodistribution as previously reported as 64Cu-DOTA-NGR2. This confirmed that the multimerization of NGR peptides enhances CD13-binding affinity.[44,45]

Another study was carried out to compare 99mTc-labeled monomeric and dimeric linear NGR peptides NGR1 and NGR2 for SPECT imaging of CD13 expression in HepG2 hepatoma xenografts. Similar to 64Cu-labeled monomeric and dimeric NGR peptides, the dimeric 99mTc-NGR2 exhibited overall better properties in vitro and in vivo versus the monomeric 99m Tc-NGR1 in terms of binding avidity, cellular uptake, tumor uptake and retention, tumor to background contrast ratio, and pharmacokinetics. However, 99mTc-NGR1 and 99mTc-NGR2 both showed significant liver uptake: 15.87% ± 1.76% ID/g for 99mTc-NGR2 and 10.30% ± 1.32% ID/g for 99mTc-NGR1 at 1 hour; this indicates that they are not suitable for abdominal tumors.[40]

In terms of tumor uptake and tumor/muscle ratio, dimeric compounds demonstrated better pharmacokinetics with a higher tumor to nontarget ratio versus the corresponding monomeric. Although 64Cu- and 99mTc-labeled NGR peptides have obvious tumor uptake, they both suffered from significant liver uptake. 68Ga-labeled dimeric compounds discussed next could be the most ideal radioactive probes. They can reduce the liver uptake with comparable tumor uptake with 64Cu- and 99mTc-labeled NGR peptides.

Comparative Experiments of NGR and RGD-Based Radioimaging

Among the various peptides identified by phage-display to target the tumor vessels in a mouse model, 2 peptide motifs have been well characterized with known recognition sites. One of them contains the sequence Asn-Gly-Arg (NGR) and was found to bind the CD13 receptor isoform upregulated in the tumor vasculature. Another peptide contains the sequence Arg-Gly-Asp (RGD) and specifically recognizes the upregulated αvβ3 and αvβ5 integrins in tumor endothelial cells.[46] Both RGD and NGR tripeptide motifs have been explored as vehicles for delivering chemotherapeutic drugs, radioisotopes, and nanoparticles to angiogenic tumors. There are numerous studies into RGD-radiolabeled peptides such as SPECT isotope 99mTc and PET with [18]F, 64Cu, and 68 Ga; however, there are few reports on 68Ga- and 64Cu-labeled NGR peptides so far. Although the NGR peptide shows higher selectivity toward tumor cells and has a 3-fold higher specificity than the RGD peptides, several direct comparisons between radiolabeled NGR and RGD peptides have different conclusions.[43,47]

Shao et al[46] directly compared 68Ga-NOTA-G3-NGR2 and 68Ga-NOTA-G3-RGD2 probes for imaging tumor angiogenesis in HT-1080 tumor xenografts coexpressing high levels of CD13 and ανβ3/ανβ5 integrin. The linker and chelator remained the same. RGD was cyclized by the amino group (N-terminus of phenylalanine) with the carboxyl branch in lysine residue; the cyclization of CNGRC used a disulfide bridge. Figure 3 shows no significant difference between the 2 probes in terms of tumor uptake based on microPET imaging (7.84% ± 1.94% ID/g for 68Ga-NOTA-G3-RGD2 vs 6.42% ± 2.21% ID/g for 68Ga-NOTA-G3-NGR2 at 0.5 hour); the tumor/muscle ratio was 8.12 ± 1.69 for 68Ga-NOTA-G3-RGD2 vs 7.76 ± 1.16 for 68Ga-NOTA-G3-NGR2.[46] The liver uptake of 68Ga-NOTA-G3-NGR2 and 68Ga-NOTA-G3-RGD2 were 2.33% ± 0.42% and 2.94% ± 0.35% ID/g at 0.5 hour, and the tumor to liver ratio of HT-1080 was 3.47 ± 0.69 for 68Ga-NOTA-G3-NGR2 and 3.26 ± 1.23 for 68Ga-NOTA-G3-RGD2 at 1 hour. The liver accumulation of 68Ga-NOTA-G3-NGR2 and 68Ga-NOTA-G3-RGD2 was significantly lower than previously reported for 64Cu- or 99mTc-labeled NGR peptides.[40,44,45] This result suggests that these 2 probes can be an alternative for PET imaging in patients with fibrosarcoma.

Figure 3.

Representative image of mice bearing HT-1080 or HT-29 tumors after intravenous administration of 68Ga-NOTA-G3-NGR2 or 68Ga-NOTA-G3-RGD2 at 1 hour postinjection, and the coinjection of nonlabeled NOTA-G3-NGR2 or NOTA-G3-RGD2 as blocking agents. Tumors are indicated using circles. There is no significant difference between the 2 probes in terms of tumor uptake based on micro positron emission tomography imaging. Adapted with permission from Yahui Shao et al.46 Copyright (2019) America Chemical Society.

Another study compared 68Ga-NOTA-cNGR and 68Ga-NODAGA-c(RGD)2 in subcutaneously injected and subrenal (SRCA) implanted mesoblastic nephroma (NeDe) tumor cells but with different conclusions.[48] In contrast to Shao et al,[46] this study selected c[KNGRE]-NH2(cyclic(lysine-asparagine-glycine-arginine-glutamic acid amide)) cyclic peptides because the cNGR peptides with a succinimide ring closure are more stable and can prevent deamidation versus the disulfide-bridged cNGR. Although there was no significant increase in mean standardized uptake value (SUV)mean (1.73 ± 0.39 for 68 Ga-NOTA-cNGR and 1.31 ± 0.24 for 68Ga-NODAGA-c(RGD)2, respectively), the SUVmax and T/M SUVmax of 68Ga-NOTA-cNGR were nearly 2-fold higher than 68Ga-NODAGA-c(RGD)2 in NeDe tumor-bearing rats with a subcutaneous tumor model (11.47 ± 1.37 and 12.47 ± 2.19 for 68Ga-NOTA-cNGR and 4.96 ± 0.47 and 6.98 ± 0.55 for 68Ga-NODAGA-c(RGD)2). In summary, this study revealed that 68Ga-NOTA-cNGR performs better than dimeric RGD tracers in NeDe tumor cell lines. This might be due to the differences in the structure and stability of the cNGR peptides.[48]

99mTc-MAG3-PEG8-cRGD and 99mTc-MAG3-PEG8-cNGR (both were cyclic PEGylated pentapeptides) were compared in a SKMEL28 melanoma model and B16F10 melanoma model for angiogenesis detection.[49] RGD performs better than NGR in SKMEL28 human melanoma-bearing mice in terms of tumor uptake, tumor/blood ratio, and tumor/muscle ratio; the difference was not remarkable in B16F10 human melanoma-bearing mice. The structure of the targeted peptides influences the performance of radiotracers, and this experiment suggested that expression level of the markers in different cells also has a greater impact.

Rapid radiometalation kinetics at low concentration and ambient temperature make N, N′-bis-[2-hydroxy-5-(carboxyethyl)benzyl]ethylenediamine-N, N′-diacetic acid (HBED-CC) an attractive chelator for 68Ga radiolabeling. Therefore, Satpati D[50] investigated the potential of 68Ga-HBED-CC-cNGR (cyclized by the disulfide bond) and 68Ga-HBED-CC-cRGD as tumor targeting radiotracers. The 68Ga-HBED-CC-cRGD displayed higher specificity in integrin αvβ3-positive B16F10 cells and higher uptake in B16F10 tumors versus 68Ga-HBED-CC-cNGR; the 2 radiotracers exhibited similar uptake in HT-1080 tumor xenografts. In terms of the tracer uptake in HT-1080 tumors, 68Ga-NOTA-G3-cNGR (5.03% ± 1.95% ID/g at 1 hour)[32] and 64Cu-DOTA-NGR (3.33% ± 0.10% ID/g at 24 h)[44] show higher retention in HT-1080 tumors than 68Ga-HBED-CC-c(NGR) (1.5% ± 0.1% ID/g at 1 hour). This may be due to different chelators and the absence of a spacer (3 glycine units) in the 68Ga-HBED-CC-cNGR radiotracer.[50]

These experiments show that different tumors with different expression levels of CD13 are best imaged with different structures of peptides and chelating agents. They can dramatically affect tumor uptake.

NGR-Based Radiopharmaceuticals for Tumor Therapy

NGR-based peptides can specifically bind to overexpressed CD13 receptor in angiogenic blood vessels and tumor cells. NGR peptides are useful for preparing anticancer agents by delivering cytotoxic drugs, proapoptotic peptides, and TNF to the tumor vasculature.[3] The tumor-homing characteristic can be used in radiotherapy that relies on β− particle decay.

Ma W[51] designed a novel fusion NGR-VEGI protein and labeled it with Rhenium-188 (188Re) for SPECT tumor imaging and tumor therapy in mice bearing human fibrosarcoma HT-1080 xenografts. The goal of the fusion protein was to increase the tumor specificity of vascular endothelial growth inhibitor (VEGI). The VEGI is a member of the TNF family and is correlated with lower tumor recurrence, longer survival time, and better prognosis in patients with breast cancer. It can activate multiple signaling pathways and inhibit endothelial cell proliferation, angiogenesis, and tumor growth. In tandem with NGR peptides, it could improve the tumor specificity and reduce adverse side effects of VEGI.[52,53] Here, 188Re (T 1/2 = 16.98 hours) could emit γ-rays for radioimaging and β− particles for radiotherapy. The biodistribution study suggested relatively good radioactivity in tumor (1.66% ± 0.32% ID/g) and good tumor to muscle ratio (4.98 ± 0.25) of 188Re-NGR–VEGI at 24 hours. The in vivo radiotherapy effect indicated that 18.5 MBq of 188Re-NGR–VEGI obviously inhibits tumor growth in HT-1080 tumor-bearing mice versus saline, NGR treatment, and NGR-VEGI treatment alone. No toxicity was observed, which concurs with the in vitro inhibitory effect. The results demonstrated that 188Re-NGR-VEGI can significantly induce HT-1080 tumor cell death. However, HT-1080 tumor growth slowly recurred after 18 days of treatment due to the relatively short half-life of 188Re. This could be solved by replacing 188Re with longer half-life radionuclides such as 177Lu (T 1/2 = 6.7 days) and 90Y (T 1/2 = 2.7 days) or multiple administration.

Vats K et al[54] evaluated the potential of 177Lu-labeled carbon nanospheres (CNS) as nano radiopharmaceuticals for molecular imaging and therapy. Carbon nanospheres are composed of the nontoxic carbon and have been broadly explored in the field of cancer nanomedicine. Their small size, large surface area, spherical shape, and reactive functionalities of CNS lead to high biocompatibility and facile chemical conjugation. They can be tagged with targeting vectors (peptides or antibodies), chemotherapeutic drugs, or imaging entities (dyes or radioisotopes) to combine diagnostic and therapeutic modalities in a single nanoplatform. Furthermore, enhanced surface reactivity can also facilitate multimeric nanosphere systems with multivalent displays of ligands (peptides/drugs) to amplify the concentration at the target and improve its specificity. According to the biodistribution studies, the 177Lu-labeled nanosphere−peptide conjugate 177Lu-DOTA-CNS-cNGR exhibited 2.3-fold higher tumor accumulation than 177Lu-DOTA-cNGR (without CNS); however, this was lower than 177Lu-DOTA-CNS without the peptide. Rapid clearance of 177Lu-DOTA-CNS-G3-cNGR resulted in significantly higher tumor to blood and tumor to muscle ratios versus 177Lu-DOTA-cNGR and 177Lu-DOTA-CNS. These results suggested that CNS combined with NGR peptides form an important part of the targeted radio-nanoprobes in the future.

NGR-Based Cardiovascular Radio Imaging

Angiogenesis is a natural repair process in some nonmalignant diseases such as myocardial ischemia, cerebrovascular infarction, and arthritis. RGD peptides can have high tracer uptake in the myocardial infarction.[47] CD13 is also expressed on fibroblasts and inflammatory cells in acute myocardial ischemia. Tillmanns J[55] proved that uptake of 68Ga-NOTA-cNGR was correlated with fibroblast and inflammatory cell infiltration in the infarcted myocardium as well as 68Ga-NOTA-cRGD uptake. The results also revealed that radiolabeled NGR tracers could be used for in vivo imaging of the early wound-healing phase after myocardial infarction.

Radiolabeled monomeric cyclic peptide cyclo (Cys-Asn-Gly-Arg-Gly) (coNGR) and its tetramer co(NGR)4 can be cyclized by native chemical ligation instead of disulfide bridging. Both coNGR-based imaging agents displayed considerably higher SUVs at infarcted areas. Uptake patterns of 111In-coNGR and 111In-co(NGR)4 were coincident with CD13 immunohistochemistry on excised hearts. Here, Co(NGR)4 displayed a significantly higher specific uptake in infarcted myocardium versus coNGR. These studies show that NGR could be a promising sensitive imaging agent for the detection of angiogenesis in infarcted myocardium.[56]

Optical Imaging

NGR-labeled with small molecular fluorophores, quantum dot (QDs), and polymer carriers are widely used methods for optical molecular imaging. Both linear and cyclized NGR peptide can be coupled to a maleimide-modified fluorescent dye Oregon Green 488 (OG488) for optical imaging. In CD13-positive tumor cells, the affinity of OG488 cyclic KNGRE is 3.6-fold higher than that of OG488 linear KNGRG.[16] In addition to OG488 dye, NGR can also be coupled to the fluorescent dye Cy5.5 for optical imaging. Despite the CD13-positive HT-1080 tumor region exhibiting specific accumulation of cNGR-Cy5.5, the overaccumulation of cNGR-Cy5.5 in the kidney and liver can reduce the sensitivity to tumors.[16,17]

Compared to traditional dyes, QDs emission is brighter with narrow emission spectra and is tunable based on its size. Moreover, QD’s optical performance is more stable and durable.[57] cNGR has been combined with OG488 or biotin, and the complex was assessed in a CD13-positive murine endothelial cell line. The biotin-tagged NGR multivalently labeled the QDs, which gave the cNGR-QDs greater intensity and more persistent fluorescence than the cNGR-OG488 dye. In vivo fluorescence microscopy revealed the lower bleaching rate and higher intrinsic fluorescence of QD versus OG488 dye. Thus, the cNGR-QD strongly labeled CD13-rich cells. However, new generations of less toxic and more easily cleared QDs are needed.[58]

Direct conjugation suffers from a low signal/background ratio and in vivo stability of peptides and fluorophores. They can be conjugated to a polymeric carrier such as liposomes that can be encapsulated with multiple probes to produce amplified signals for imaging. Taking advantage of the intrinsic fluorescence properties of DOX, DOX-encapsulated NGR-modified liposome showed a 10-fold enhancement in affinity for CD13-positive cancer cells versus NGR peptide alone.[59] Other fluorescent studies of NGR peptides include fluorescein isothiocyanate (FITC)-labeled N-(hydroxypropyl)methacrylamide copolymer, FITC-labeled cytoskeletal proteins actin, and 1,1′-dioctadecyl-3,3,3′,3′-tetramethylindocarbocyanine perchlorate (DiI)-labeled biodegradable di-block copolymer; PEG-poly (D, L-lactide) also showed promising results for tumor imaging.[16,17]

Conclusion

Peptides containing the NGR motif have been used as a homing agent for delivery of therapeutics, cytokines, peptides, chemicals, liposomes, and polymeric micelles to activated tumor neovascular tissue. This strategy can enhance therapeutic efficacy and reduce systemic toxicity. Various radiolabeled NGR peptides with different molecular scaffolds and chelators exhibit great differences in affinity, specificity, and pharmacokinetics. Dimerizing NGR peptides is a promising strategy to improve pharmacokinetic characteristics and tumor to nontarget ratio. Moreover, the different stability and receptor-binding specificity caused by different molecular scaffolds should be carefully considered. Generally speaking, cNGR displayed a stronger affinity and higher specificity toward the CD13 receptors versus linear ones. 68Ga-labeled dimeric compounds could be the most ideal radioactive probes so far and can greatly reduce liver uptake with comparable tumor uptake as 64Cu and 99mTc. The use of radiolabeled NGR peptides for imaging of CD13 expression has good potential for tumor imaging and therapy.