- Original research
- Open Access
Hybrid PET/optical imaging of integrin αVβ3 receptor expression using a 64Cu-labeled streptavidin/biotin-based dimeric RGD peptide
© Kang et al. 2015
Received: 12 August 2015
Accepted: 19 October 2015
Published: 31 October 2015
Hybrid PET/optical imaging provides quantitative and complementary information for diagnosis of tumors. Herein, we developed a 64Cu-labeled AlexaFluor 680-streptavidin ((AF)SAv)/biotin-based dimeric cyclic RGD peptide (RGD2) for hybrid PET/optical imaging of integrin αVβ3 expression.
64Cu-1,4,7,10-tetraazacyclododecane-N,N′,N′′,N′′′-tetraacetic acid (DOTA)-(AF)SAv/biotin-PEG-RGD2 was prepared by formation of a complex comprising DOTA-(AF)SAv and biotin-PEG-RGD2, followed by radiolabeling with 64Cu. Receptor binding studies of DOTA-(AF)SAv/biotin-PEG-RGD2 were performed using U87MG cells and 125I-RGDyK as the radioligand, and cellular uptake studies of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 were also performed. MicroPET imaging followed by optical imaging of U87MG tumor-bearing mice was acquired after injection of the hybrid probe, and region of interest (ROI) analysis of tumors was performed. Ex vivo PET/optical imaging and biodistribution studies of the major tissues were performed after the in vivo imaging, and immunofluorescence staining of the tumor tissue sections was carried out.
64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 was prepared in 52.1 ± 5.4 % radiochemical yield and with specific activity of 1.0 ± 0.1 GBq/mg. Receptor binding studies showed that DOTA-(AF)SAv/biotin-PEG-RGD2 had higher binding affinity for integrin αVβ3 than RGD2, reflecting a possible polyvalency effect. Moreover, the hybrid probe revealed time-dependent uptake by U87MG cells. In a microPET/optical imaging study, the hybrid probe demonstrated high accumulation in tumors; ROI analysis revealed 2.7 ± 0.2 % ID/g at 1 h and 4.7 ± 0.2 % ID/g at 21 h after injection, and subsequently acquired optical images showed tumors with strong fluorescence intensity. Ex vivo PET/optical images of the major tissues confirmed the in vivo imaging data, and biodistribution studies demonstrated high and specific uptake in tumors (4.8 ± 0.1 % ID/g). Immunofluorescence staining showed the formation of new blood vessels in tumor tissues, suggesting that the tumor uptake was due to specific binding of the hybrid probe to integrin αVβ3 expressed on tumor cells.
These results indicate that a 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 is able to provide quantitative information on hybrid PET/optical imaging of integrin αVβ3 expression.
Demand for hybrid imaging probes has been growing with advances in hybrid imaging systems such as PET/CT, SPECT/CT, and PET/MRI, and expansion of their clinical uses . PET provides sensitive and quantitative information, and moreover, PET probes are easily translated for clinical use compared with probes used for other modalities . However, PET has the disadvantage of low spatial resolution. MRI offers the highest spatial resolution but has low sensitivity . Optical imaging has the advantages of real-time imaging with high sensitivity and can potentially be used in intraoperative image-guided surgery [2, 3]. However, it is mainly limited to small animal imaging due to low depth penetration. Therefore, hybrid imaging, by compensating for the drawbacks of single imaging modalities, is more accurate and allows for earlier diagnosis of diseases. This has spurred the development of hybrid imaging probes containing diverse functionalities for application in hybrid PET/optical, PET/MR, and other combinations of imaging modalities.
To develop hybrid imaging probes, nanoparticles are commonly used as platforms because of the ease of addition of diverse functional groups including tumor-targeting compounds. For tumor angiogenesis targeting, cyclic Arg-Gly-Asp (RGD) peptides, selective antagonists of integrin αVβ3, have been radiolabeled with various radioisotopes. The most well-characterized ligand, 18F-labeled galacto-RGD peptide, has shown promise for tumor imaging of melanoma M21 tumor-bearing mice and diagnosis of cancer patients [4, 5]. With its longer half-life, 64Cu-labeled RGD peptide showed prolonged tumor uptake in MDA-MB-435 tumor-bearing mice . In addition, PEGylation of RGD peptides improved in vivo pharmacokinetics; 64Cu-labeled PEGylated RGD peptide accumulated in tumors at early time points and rapidly washed out from the blood of U87MG tumor-bearing mice compared with 64Cu-labeled RGD peptide [7, 8]. Multimeric RGD peptides, such as 64Cu-labeled RGD dimer and tetramer, were shown to possess not only higher integrin binding affinity compared with the corresponding monomer but also prolonged tumor retention and increased renal excretion in tumor-bearing mice, which were possibly attributed to a polyvalency effect [9, 10]. Other dimeric RGD peptides, labeled with 18F, 68Ga, and 99mTc, have also been shown to have superior in vivo properties than their corresponding monomers [11–14].
Nanoparticles such as liposomes, quantum dots, gold nanoparticles, carbon nanotubes, and others have been conjugated with RGD peptides and utilized for hybrid imaging or improved tumor targeting. 111In-DTPA-labeled liposomes conjugated with RGD peptide were designed for hybrid SPECT/MR imaging of integrin αVβ3. Although 111In-labeled liposomes exhibited low tumor uptake in U87MG tumor-bearing mice, Gd-labeled liposomes were taken up by the tumors of both U87MG and M21 tumor-bearing mice, based on R1 values . 64Cu-labeled quantum dots (Qdots) modified with RGD peptides were developed for PET and near-infrared fluorescence (NIRF) imaging, and the tumor vasculature was visualized by both PET and ex vivo NIRF imaging . In another study, RGD peptides and DOTA were conjugated to polyaspartic acid-coated iron oxide nanoparticles, which were then labeled with 64Cu. Hybrid PET/MR imaging of the particles in U87MG tumor-bearing mice showed integrin αVβ3 expression in the tumor . 125I-labeled RGD-PEG-gold nanoparticles were prepared by conjugating PEG to the gold particles and RGD peptide to PEG, and then finally radiolabeling the particles with 125I. RGD-PEG-gold nanoparticles exhibited much higher binding affinity for integrin αVβ3 on U87MG cells than free RGDyC peptide. SPECT/CT images of U87MG tumor-bearing mice showed fast tumor uptake of the gold particles . Single-walled carbon nanotubes have also been used as a platform for tumor angiogenesis imaging; carbon nanotubes coated with RGD- and DOTA-conjugated PEG-phospholipids were labeled with 64Cu, and then the resulting nanotubes had a high tumor uptake in U87MG tumor-bearing mice. Ex vivo Raman spectroscopy data of the major tissues confirmed the microPET imaging data .
Previously, we and others showed that a streptavidin (SAv) and biotin complex can serve as a useful platform for the development of hybrid imaging probes due to the strong interaction between SAv and biotin, with a dissociation constant of approximately 10−14 M . Examples of these probes include 99mTc-HYNIC-labeled quantum dots (Qdots)-SAv/biotin-PEG-EGF, SAv/three biotinylated 111In-DOTA, Cy5.5 and anti-Her2 antibody, and 64Cu-DOTA-(AF)SAv/biotin-PEG-VEGF121 [21–23]. Unlike most nanoparticles, antibody-conjugated SAv and 90Y-DOTA-biotin have been used clinically for pretargeted radioimmunotherapy, which was shown to be safe .
In this study, we extended application of the SAv/biotin platform to the development of an E[cyclic(RGDyK)]2 (RGD2)-based hybrid imaging probe for tumor angiogenesis imaging. Therefore, 64Cu-DOTA-(AlexaFluor680; AF)SAv/biotin-PEG-RGD2 was prepared and evaluated for hybrid PET/optical imaging of integrin αVβ3 receptor expression in U87MG tumor-bearing mice.
Materials and equipment
RGD2 was purchased from Peptide International (Louisville, KY, USA), biotin-PEG(3400)-NHS ester was from Nanocs (New York, NY, USA), (AF)SAv was from Life Technologies (Carlsbad, CA, USA), and DOTA-NHS ester was from Macrocyclics (Dallas, TX, USA). 64CuCl2 was kindly provided by KIRAMS (Seoul, Korea). PD-10 columns were purchased from Amersham Biosciences (Piscataway, NJ, USA), Amicon filters were from Millipore (Billerica, MA, USA), and spin columns were from Thermo Scientific (Rockford, IL, USA). Chelex 100 resin (50–100 mesh) and other chemicals were purchased from Sigma-Aldrich (St. Louis, MO, USA), and BCA protein assay kits were from Pierce (Rockford, IL, USA). All buffers used for synthesis and radiolabeling were pretreated with Chelex 100 resin to ensure that they were metal-free. Matrix-assisted laser desorption ionization time of flight (MALDI-TOF) mass spectrometry was performed on a Voyager-DETM STR Biospectrometry Workstation (Applied Biosystems, Foster City, CA, USA). Purification and analysis of products were performed by HPLC (Thermo Scientific, Waltham, MA, USA), and eluates were monitored using a UV detector (218 nm).
Radioactivity was measured using a dose calibrator (Biodex Medical Systems, Shirley, NY, USA), and tissue radioactivity was counted using an automatic gamma counter (PerkinElmer, Waltham, MA, USA). MicroPET and optical images were acquired at the Center for Molecular and Cellular Imaging, Samsung Biomedical Research Institute (SBRI, Seoul, Korea) using an Inveon microPET/CT scanner (Siemens Medical Solutions, Malvern, PA, USA) and a Xenogen IVIS Spectrum (Caliper Life Sciences, Hopkinton, MA, USA), respectively.
Preparation of DOTA-(AF)SAv
(AF)SAv (1.3 mg) and 20 equivalents of DOTA-NHS ester (400 μg, 481.9 nmol) were dissolved in 800 μL of 0.1 M sodium carbonate buffer (pH 8.5), which was then stirred at room temperature for 18 h in the dark. At the end of the reaction, the reaction mixture was purified using a PD-10 column, concentrated using an Amicon filter (cut-off: 10 kDa), and then lyophilized. DOTA-(AF)SAv was obtained at 97.3 % yield, quantified using a BCA protein assay kit, and then analyzed by MALDI-TOF mass spectrometry.
Preparation of biotin-PEG-RGD2
RGD2 (1.7 mg, 1.3 μmol) and biotin-PEG(3400)-NHS ester (2.4 mg, 0.6 μmol) were dissolved in 500 μL of 0.1 M sodium carbonate buffer (pH 8.5), which was then stirred at room temperature for 19 h. At the end of the reaction, the reaction mixture was purified by HPLC using a C18 column (YMC, 5 μm, 10 × 250 mm) with sequential programs using a mixture of 0.1 % trifluoroacetic acid (TFA) in water and CH3CN. The first isocratic program was a 90:10 mixture over 10 min, and the second gradient program was from a 90:10 mixture to a 35:65 mixture over 30 min. The flow rate was 3 mL/min. After lyophilization, biotin-PEG-RGD2 was analyzed by MALDI-TOF mass spectrometry.
Preparation of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2
Biotin-PEG-RGD2 (91.2 μg, 18.2 nmol) dissolved in acetate buffer (pH 6) was added to DOTA-(AF)SAv (201.9 μg, 3.6 nmol) in the same buffer. The reaction mixture (total volume of 200 μL) was stirred at room temperature for 1 h, and then incubated with 64CuCl2 (377 MBq) at 40 °C for 30 min with constant shaking. Unreacted 64CuCl2 and biotin-PEG-RGD2 in the reaction mixture were removed by centrifugation using a spin column (molecular weight (mw) cut-off 7 kDa).
In a separate experiment, an aliquot of DOTA-(AF)SAv/biotin-PEG-RGD2 was purified using a spin column (cut-off 7 kDa) and its purity was determined by HPLC using a Superdex™ 75 GL column (10 × 300 mm, GE Healthcare Life Sciences, Marlborough, MA, USA) and 0.01 M phosphate buffer as the eluent at a flow rate of 0.7 mL/min.
64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 (98.4 MBq) in 0.01 M PBS (pH 7.4) was added to 50 % fetal bovine serum (FBS; Gibco, Brooklyn, NY, USA) and incubated at 37 °C for 0, 1, 3, 16, and 24 h. At the indicated time points, each sample was loaded onto a PD-10 column, and fractions were eluted using PBS (pH 7.4) and counted using a dose calibrator.
Cell integrin receptor binding
The integrin αVβ3 receptor binding study was performed using a previously reported procedure with a slight modification . 125I-RGDyK was used as the radioligand and prepared immediately before use. U87MG cells (2 × 106 cells/100 μL) cultured in minimum essential media (MEM; Gibco) were re-suspended in binding buffer (20 mM Tris–HCl buffer with 150 mM NaCl, 2 mM CaCl2, 1 mM MgCl2, 1 mM MnCl2, and 0.1 % bovine serum albumin (BSA); pH 7.4). 125I-RGDyK (2.7 kBq/80 μL of binding buffer) was added to tubes containing U87MG cells in the presence of different concentrations (0.1, 1, 10, 102, 103, 104, and 105 nM; 20 μL) of either DOTA-(AF)SAv/biotin-PEG-RGD2 or RGD2 at room temperature for 1 h. After incubation, the cells were washed three times with PBS for 5 min, re-suspended with PBS (1 mL), and then counted using a gamma counter. All experiments were performed in triplicate. IC50 values were determined using GraphPad Prism software 5.
U87MG cells were cultured in MEM supplemented with 10 % FBS, streptomycin (100 μg/mL), and penicillin (100 units/mL). Cells were maintained at 37 °C in a humidified 5 % CO2 incubator. U87MG cells were seeded in 12-well plates at 5 × 105 cells/well and cultured for 2 days. 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 (111 kBq/2 μL) was added to each well, and the cells in a total volume of 0.5 mL were incubated at 37 °C for 1, 2, 16, and 21 h. After incubation, the cells were washed three times with PBS. Cell lysis was then carried out using 0.1 N NaOH, and the resulting lysate was counted using a gamma counter. For the blocking study, cells were incubated with the hybrid probe in the presence of RGD2 (10 μM) at 37 °C for 21 h and then treated as described above. All experiments were performed in triplicate.
This study was reviewed and approved by the Institutional Animal Care and Use Committee of SBRI. SBRI is an Association for Assessment and Accreditation of Laboratory Animal Care International accredited facility and abide by the Institute of Laboratory Animal Resources guide.
In vivo microPET/optical imaging
U87MG tumor-bearing mice were prepared by subcutaneously inoculating U87MG cells (5 × 106) into the right hind legs of 5-week-old BALB/c nude mice (male). When tumor size reached 407.4 ± 58.6 mm3 at 3 weeks after inoculation, the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 (6.9 ± 0.3 MBq/200 μL) was injected intravenously without (n = 3) or with RGD2 (20 mg/kg, n = 3) through the tail vein. MicroPET static images were acquired for 10 min at 1, 2, 16, and 21 h after injection. Immediately after microPET imaging, optical images of the mice were acquired (excitation: 675 nm, emission 720 nm) for 1 s.
The images obtained were reconstructed using three-dimensional ordered subset expectation maximization and then processed using Siemens Inveon Research Workplace 4.2. Regions of interest (ROIs) were drawn over tumors in the right legs, and the average signal levels in the ROIs were measured. Data are expressed as percent injected dose per gram of tissue (% ID/g). ROIs of optical images were drawn over tumors, and signal levels were measured using Living Image 3.2 software. These data are presented as photons per second per square centimeter per steradian (photons/s/cm2/sr).
Ex vivo imaging and biodistribution studies
At the end of the in vivo microPET/optical imaging study, mice were sacrificed, and major tissues (heart, lungs, liver, spleen, kidneys, intestines, muscle, and tumor) were separated immediately and subjected to ex vivo imaging (microPET, 10-min static scan; optical imaging, 1-s exposure). ROIs of ex vivo images were drawn around each tissue, and the average signal level in the ROI was measured. For the biodistribution study, the tissues of interest and blood were then weighed and counted, and data are expressed as percent injected dose per gram of tissue.
Tumor tissues obtained after in vivo imaging were fixed in 4 % paraformaldehyde overnight. Specimens were then dehydrated in graded ethanol, embedded in paraffin, and sectioned at 5 μm on a Reichert microtome. The sections were blocked with 1 % BSA in PBS for 30 min and then incubated with goat anti-β3 (1:100; Santa Cruz Biotechnology, Santa Cruz, CA, USA) and rabbit anti-VEGFR2 antibodies (1:100; Santa Cruz Biotechnology) overnight at 4 °C. Subsequently, sections were stained with FITC-labeled anti-goat and rhodamine-labeled anti-rabbit antibodies (1:200; Santa Cruz Biotechnology). Hoechst 33342 (1 μg/mL; Cell Signaling Technology, Danvers, MA, USA) was used to stain the cell nuclei of tumor tissues. Stained tissue sections were examined under a microscope (×200; Nikon Eclipse 80i).
Data were analyzed with unpaired, two-tailed Student’s t tests. Differences at the 95 % confidence level (P < 0.05) were considered statistically significant.
Preparation of DOTA-(AF)SAv and biotin-PEG-RGD2
DOTA-(AF)SAv prepared from (AF)SAv and DOTA-NHS ester was readily purified using a size-exclusion column. MALDI-TOF mass spectrometric analysis indicated that the average number of DOTA molecules conjugated to (AF)SAv was 3.8 ± 0.6. In contrast, to prepare biotin-PEG-RGD2, excess amounts (2 equivalents) of RGD2 were used to consume as much biotin-PEG-NHS ester as possible, as this NHS ester eluted close to biotin-PEG-RGD2 on HPLC. The resulting biotin-PEG-RGD2 was purified by HPLC, but not using a size-exclusion column because of its similarity in molecular weight to the biotin-PEG-NHS ester. Biotin-PEG-RGD2 was obtained at 87.1 ± 8.1 % yield and identified by MALDI-TOF mass spectrometry: (m/z) [M + H]+ calcd. 5023.77, C225H413N22O98S; found 5024.57.
Preparation of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2
Cell integrin receptor binding
Ex vivo imaging and biodistribution studies
DOTA-(AF)SAv and biotin-PEG-RGD2 were prepared via amide bond formation under basic conditions (pH 8.5). Different methods were applied to purify these two molecules due to differences in their molecular weights from reactants; DOTA-(AF)SAv was purified using a PD-10 column, in which the unconjugated DOTA was easily removed because of its low molecular weight (mw 501.49), whereas biotin-PEG-RGD2 was purified using a centrifugal filter to remove unreacted RGD2 peptide (mw 1350.43), followed by a reverse-phase HPLC column because of the small difference in molecular weight between biotin-PEG-NHS ester (mw 3790.48) and biotin-PEG-RGD2 (mw 5025.83). As a result, there were no molecular ion peaks corresponding to both biotin-PEG-NHS ester and RGD2 detected on MALDI-TOF mass spectrometry, except for the molecular ion peak of biotin-PEG-RGD2. The key to preparing a SAv/biotin complex is to remove unbound biotin-PEG-RGD2 after the complex formation. In this study, we used a spin column (mw cut-off 7 kDa) to rapidly remove molecules with a molecular weight less than 7 kDa from the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2.
SAv/biotin complexes have previously been used to develop imaging probes; IRDye800-SAv/biotin-Avi-VEGF121 and 64Cu-DOTA-(AF)SAv/biotin-PEG-VEGF121 were shown to have potential for NIRF and PET/optical imaging of VEGF receptor expression, respectively [23, 26]. Moreover, SAv bound to biotinylated 111In-DOTA, Cy5.5, and anti-Her2 antibody showed high tumor uptake in SUMI190 tumor-bearing mice . In our study, RGD2 was conjugated to biotin via PEG to improve its in vivo properties and provide flexibility, while 64Cu-DOTA was directly conjugated to SAv(AF). This imaging probe design may be suitable for hybrid imaging of tumor angiogenesis, because RGD2 can be used for αVβ3 receptor binding while the radioisotope and fluorescent dye can be used for PET and optical imaging, respectively. A long PEG chain (mw 3400) was used to allow RGD2 to gain access to the binding site of the integrin receptor, while the radioisotope and fluorescent dye were conjugated directly to SAv not to interfere with binding of RGD2 to the integrin receptor. Furthermore, the hybrid probe was stable for 24 h based on an in vitro serum stability study (Fig. 2). In comparison with in vivo PET imaging of 64Cu-DOTA-(AF)SAv without biotin molecules , the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 showed higher tumor uptake that increased in a time-dependent manner, reflecting its long-term stability in vivo.
To evaluate the receptor binding affinity of the probe, U87MG cells, which are known to express high levels of integrin αVβ3 , were incubated with 125I-RGDyK in the presence of different concentrations of DOTA-(AF)SAv/biotin-PEG-RGD2 or RGD2. IC50 value of DOTA-(AF)SAv/biotin-PEG-RGD2 was 3.1-fold higher than that of RGD2 (Fig. 3). Diverse dimeric and multimeric RGD peptides have been shown to have higher in vitro receptor binding affinity and tumor uptake than monomeric RGD peptides [12, 28]. In this study, four equivalents of the RGD2 peptide were possibly bound to one molecule of SAv because of its tetrameric structure, which might have contributed to the higher binding affinity of the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 than the dimeric RGD peptide probably due to a polyvalency effect [9, 10]. Cellular uptake study exhibited that the hybrid probe was taken up by U87MG cells in a time-dependent manner, and that its levels increased 3.0-fold over a 21-h incubation (Fig. 4a). Cellular uptake was inhibited significantly by RGD2, indicating specificity of the probe to the integrin αVβ3 receptor (Fig. 4b).
In vivo microPET and optical imaging results of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 demonstrated incremental tumor uptake over time. ROI values of tumor uptake obtained from microPET images increased 1.7-fold over 21 h (Fig. 5a). A similar pattern of tumor uptake was observed in optical images, with uptake increasing 1.8-fold over the same period of time (Fig. 5c). Biodistribution data of this hybrid probe demonstrated higher tumor uptake (4.8 ± 0.1 % ID/g at 21 h after injection) than that of 64Cu-DOTA-E[(RGDfK)]2 in U87MG tumor-bearing mice (<4 % ID/g at 4 h after injection) , although 64Cu-DOTA-E[(RGDyK)]2 showed better in vivo kinetics than the D-Phe derivative in MDA-MB-435 tumor-bearing mice . Furthermore, the tumor uptake pattern of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 was similar to that reported for other RGD-conjugated nanoparticles. 64Cu-DOTA-QDot-RGD showed relatively low tumor uptake at 1 h after injection (less than 1 % ID/g), which then increased to 4.3 ± 0.5 % ID/g at 25 h after injection based on ROI analysis of microPET images . Higher tumor uptake was detected in 64Cu-labeled RGD-conjugated iron oxide nanoparticles, which were avidly taken up by U87MG tumors of mice (7.9 ± 0.8 % ID/g at 1 h after injection) and increased to 9.8 ± 3.2 % ID/g at 21 h after injection . Another study showed that 64Cu-DOTA- and RGD-conjugated single-walled carbon nanotubes exhibited significantly high tumor uptake of 10–15 % ID/g at 24 h after injection compared to 3–4 % ID/g uptake of RGD-free nanotubes . The presence of SAv in the hybrid probe may affect tumor uptake, because 111In-labeled SAv was reported to accumulate in tumors in LS174T tumor mice (4.5 ± 0.2 % ID/g at 5 h after injection) . In our previous study, however, 64Cu-DOTA-(AF)SAv without biotin molecules showed low tumor uptake (1.6 ± 0.1 % ID/g at 22 h) . Therefore, tumor uptake of the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 was likely due to the probe itself.
The hybrid probe showed high uptake in the liver and spleen compared with that of 64Cu-DOTA-E[(RGDfK)]2 . This high uptake in the reticuloendothelial system resulted from the presence of the relatively large molecule, SAv, as shown by high liver uptake of 64Cu-DOTA-(AF)SAv (15.7 ± 0.57 % ID/g at 22 h) . A similar uptake pattern was detected in microPET images of U87MG tumor-bearing mice injected with 64Cu-DOTA-QDot-RGD; liver uptake was higher than 40 % ID/g up to 25 h after injection based on ROI analysis . 64Cu-labeled RGD-conjugated iron oxide nanoparticles also showed high liver uptake (31.1 ± 2.5 % ID/g at 1 h and 11.7 ± 1.2 % ID/g at 21 h after injection), probably due to the relatively large size of the particles . Similarly, high liver uptake (17~30 % ID/g at 24 h) was also detected in mice injected with 64Cu-labeled single-walled carbon nanotubes coated with phospholipid-PEG chains conjugated to the RGD peptide . The longer the PEG chain, the lower the liver uptake and the higher the tumor uptake of nanotubes . Therefore, use of longer PEG arms may improve the in vivo properties of the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 by reducing liver uptake. Optical images confirmed the microPET imaging data for the hybrid probe and showed high fluorescence intensity in tumors that increased over time (Fig. 5c, d). While the 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 was taken up by the liver and spleen based on PET imaging, this was not clear from optical images due to the presence of the skeleton and the depth penetration limitations of optical imaging. However, ex vivo optical images revealed that the hybrid probe was taken up by the liver, spleen, and tumor (Fig. 6c, d).
Immunofluorescence staining of tumor tissue sections obtained after microPET/optical imaging demonstrated that β3 receptors were highly expressed on endothelial cells (VEGFR2) of blood vessels (Fig. 8). This result suggests that tumor uptake of the hybrid probe was attributable to its binding to integrin αVβ3.
Our study showed that both microPET and optical imaging data of 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 in U87MG tumor-bearing mice were in good agreement for monitoring integrin αVβ3 expression. This hybrid probe provided real-time detection of tumor as well as quantitative information on tumor and major organs with high specificity and sensitivity. In addition, this hybrid probe may have advantages, because hybrid PET/optical probes may allow for preoperative detection, intraoperative image-guided surgery, and postoperative evaluation of tumors.
We prepared a 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 efficiently using a SAv/biotin complex as a platform. As shown by a receptor binding study, DOTA-(AF)SAv/biotin-PEG-RGD2 exhibited higher binding affinity for the integrin αVβ3 than RGD2 peptide, which we attributed to a possible polyvalency effect by four flexible biotin-PEG-RGD2 arms complexed with one SAv core. PET/optical images of U87MG tumor-bearing mice indicated that the hybrid probe accumulated in tumor with prolonged retention over 21 h. These results demonstrate that 64Cu-DOTA-(AF)SAv/biotin-PEG-RGD2 provides specific and sensitive hybrid PET/optical images for monitoring integrin αVβ3 expression, and that a SAv/biotin complex is a useful platform for developing hybrid imaging probes.
This work was supported by the National Research Foundation of Korea (NRF) grant funded by the Korean government (MEST) (grant code: 2011–0030164).
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