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Theranostics 2017; 7(19):4791-4804. doi:10.7150/thno.20767 This issue Cite

Research Paper

Multimodality Imaging of Angiogenesis in a Rabbit Atherosclerotic Model by GEBP11 Peptide Targeted Nanoparticles

Tao Su^{1, 3*}, Ya-Bin Wang^1*, Dong Han^{1, 2*}, Jing Wang⁵, Shun Qi⁴, Lei Gao¹, Ya-Hui Shao⁵, Hong-Yu Qiao², Jiang-Wei Chen², Shu-Hui Liang⁶, Yong-Zhan Nie⁶, Jia-Yi Li², Feng Cao¹

1. Department of Cardiology, Chinese PLA General Hospital, Beijing 100853, China;
2. Department of Cardiology, Xijing Hospital, Fourth Military Medical University, Xi'an 710032, China;
3. Department of Cardiology, the 94th Hospital of Chinese PLA, Nanchang 330000, China;
4. Department of Radiology, Xijing Hospital, Fourth Military Medical University, Xi'an 710032, China;
5. Department of Nuclear Medicine, Xijing Hospital, Fourth Military Medical University, Xi'an 710032, China;
6. Institute of Digestive Diseases, Xijing Hospital, Fourth Military Medical University, Xi'an 710032, China.
* These authors contributed equally to this work

✉ Corresponding author: Feng Cao, M.D., Ph.D. FACC, Department of Cardiology, Chinese PLA General Hospital, 28# Fuxing Road, Beijing 100853, China Tel: +86-10-55499138 E-mail: wind8828com or fengcaoedu.cn or fengcao8828com

Abstract

Background and Aims: Angiogenesis is an important pathological process during progression of plaque formation, which can result in plaque hemorrhage and vulnerability. This study aims to explore non-invasive imaging of angiogenesis in atherosclerotic plaque through magnetic resonance imaging (MRI) and positron emission tomography (PET) by using GEBP11 peptide targeted magnetic iron oxide nanoparticles in a rabbit model of atherosclerosis.

Methods: The dual-modality imaging probe was constructed by coupling 2, 3-dimercaptosuccinnic acid-coated paramagnetic nanoparticles (DMSA-MNPs) and the PET ⁶⁸Ga chelator 1,4,7-triazacyclononane-N, N', N''-triacetic acid (NOTA) to GEBP11 peptide. The atherosclerosis model was induced in New Zealand white rabbits by abdominal aorta balloon de-endothelialization and atherogenic diet for 12 weeks. The plaque areas in abdominal artery were detected by ultrasound imaging and Oil Red O staining. Immunofluorescence staining and Prussian blue staining were applied respectively to investigate the affinity of GEBP11 peptide. MTT and flow cytometric analysis were performed to detect the effects of NGD-MNPs on cell proliferation, cell cycle and apoptosis in Human umbilical vein endothelial cells (HUVECs). In vivo MRI and PET imaging of atherosclerotic plaque were carried out at different time points after intravenous injection of nanoparticles.

Results: The NGD-MNPs with hydrodynamic diameter of 130.8 nm ± 7.1 nm exhibited good imaging properties, high stability, low immunogenicity and little cytotoxicity. In vivo PET/MR imaging revealed that ⁶⁸Ga-NGD-MNPs were successfully applied to visualize atherosclerotic plaque angiogenesis in the rabbit abdominal aorta. Prussian blue and CD31 immunohistochemical staining confirmed that NGD-MNPs were well co-localized within the blood vessels' plaques.

Conclusion: ⁶⁸Ga-NGD-MNPs might be a promising MR and PET dual imaging probe for visualizing the vulnerable plaques.

Keywords: Atherosclerosis, GEBP11 peptide, Magnetic nanoparticles, Multimodality imaging.

Introduction

Cardiovascular disease (CVD) is the leading cause of mortality worldwide and 17.5 million people died from CVD in 2012, representing 31% of all global deaths [1]. Atherosclerotic plaque rupture with thrombosis is responsible for the vast majority of heart attacks and strokes [2]. The plaque stability is mainly determined by its macroscopic structure and microscopic composition [3]. The vulnerable atherosclerotic plaque, characterized by immune cells infiltration, necrotic core, lipid pools, spotty calcification and intra-plaque neovascularization, is prone to rupture suddenly and cause a fatal event [4]. Thus, there is a considerable need for early detecting and accurately stratifying patients with high risk of CVD.

The traditional anatomic imaging techniques such as X-ray angiography (CAG) or coronary computed tomography angiography (CCTA) can detect the plaque morphology and provide an ideal strategy for therapeutic interventions [5]. Some advanced imaging modalities, including intravascular ultrasonography (IVUS) and optical coherence tomography (OCT) are able to provide higher resolution images with in-depth analysis about plaque composition [6]. All these techniques are more dependent on contrast analysis, rather than reflecting the cellular and molecular mechanism by which a stable plaque becomes more vulnerable [7]. Molecular imaging provides an invaluable tool to identify the biological aspects of atherosclerotic plaque in real-time [8].

Pathological angiogenesis of the vessel wall is a consistent feature of atherosclerotic plaque development and progression of the disease [8, 9]. The angiogenic microvessels not only provide an additional gateway for immune cells to infiltrate into plaques, but also lead to intraplaque hemorrhage [10, 11]. A variety of studies demonstrate that increased density of plaque microvessel is an independent risk factor for plaque rupture and inhibition of plaque angiogenesis provides a therapeutic strategy to stabilize atherosclerotic lesions [12-14]. Therefore, more effective targeting moieties are urgently needed for molecular imaging and targeted therapy of angiogenesis in atherosclerosis. We previously screened a nine-amino acid cyclic peptide (CTKNSYLMC, GEBP11) via phage display technology by co-culturing tumor cells SGC-7901 with Human umbilical vein endothelial cells (HUVECs) [15]. GEBP11 peptide holds high affinity and specificity to neovascularization of endothelial cells and is of great value in monitoring angiogenesis processes in vivo [16-18]. We hypothesized that GEBP11 peptide can serve as a target molecule for visualization of vulnerable plaque in vivo by monitoring the process of angiogenesis.

Herein, we conjugated GEBP11 peptide to Fe₃O₄ magnetic nanoparticles and radiolabeled with ⁶⁸Ga. The physicochemical characteristics, magnetic properties, binding affinity and cytotoxicity of ⁶⁸Ga-NGD-MNPs were investigated in this study. Positron emission tomography (PET) and magnetic resonance (MR) dual-modality imaging methods were applied to analyze ⁶⁸Ga-NGD-MNPs distribution, pharmacokinetics and targeting efficacy in rabbit atherosclerotic model.

Materials and Methods

Animals

All animal studies were performed according to a protocol approved by the Chinese PLA General Hospital Animal Care and Use Committee. Thirty male New Zealand white rabbits, weighing ~3.0 kg were fed an atherogenic diet containing 1% cholesterol. After 3 weeks, the rabbits underwent abdominal aorta balloon de-endothelialization. Each rabbit was anesthetized using an intravenous mixture of ketamine (5 mg/kg) and xylazine (35 mg/kg) [19]. A 5-Fr sheath was inserted into the right iliac artery and a 4.0 mm × 15 mm angioplasty balloon was advanced into the abdominal aorta. The balloon was inflated with a 50% mixture of contrast agent and saline and then pulled back three times at 14 atm. Rabbits were fed with atherogenic diet for additional 12 weeks prior to being divided into various study groups.

Twelve-week-old female C57BL/6 mice (Vital River, Beijing, China) were maintained in the PLA animal facility and used to detect the potential toxicity, biodistribution and immunogenicity of the nanoparticles, respectively.

Cell culture

The cell lines Human umbilical vein endothelial cells (HUVECs) and EAhy926 were purchased from American Type Culture Collection center (Menassas, USA) and cultured in M200 basal culture medium supplemented with low serum growth supplement, obtained from Gibco biosciences (Grand Island, USA).

Preparation of NGD-MNPs

Firstly, Fe₃O₄ magnetic nanoparticles (MNPs) with average diameters between 8 nm and 12 nm were synthesized by thermal decomposition of iron (III) acetylacetonate (Sigma-Aldrich, St. Louis, USA) in the presence of oleic and oleylamine as surfactant [20]. Secondly, ligand exchange reaction of oleic acid for meso-2,3-dimercaptosuccinic acid (DMSA) (Sigma-Aldrich, St. Louis, USA) was adopted to transform hydrophobic MNPs into hydrophilic ones as reported previously [21]. After that, GEBP11 peptide was attached to DSMA-MNPs via amide bond formation between the carboxyl of DMSA and amine group of GEBP11 peptide in the presence of 1-ethyl-3-(3-dimethyaminopropyl) carbodiimide (EDC) and N-hydroxysuccinimide (NHS) (Sigma-Aldrich, St. Louis, USA) [22]. Briefly, 5 mg of EDC (10 mg/mL) and 5 mg NHS (10 mg/mL) were mixed in 10 mL aqueous solution of DMSA-MNPs (1 mg/mL) at room temperature. After 30 min, 12 mg GEBP11 (10 mg/mL) was slowly added to the mixture and the reaction solution was continuously stirred for 12 h at 4 ℃. The GEBP11-DMSA-MNPs were collected by centrifuging at 13,000 rpm for 20 min and the supernatant was discarded. Finally, 1 mg of EDC (10 mg/mL), 0.5 mg NHS (10 mg/mL) and 1 mg NOTA (Macrocyclics, Dallas, USA) were mixed in 10 mL borate saline buffer (pH=8.4, 20 mg/mL) at room temperature. After 30 min, 5 mL GEBP11-DMSA-MNPs (1 mg/mL) were added. After 4 h at room temperature, the resultant NOTA-GEBP11-DMSA-MNPs (NGD-MNPs) were collected by centrifuging at 13,000 rpm for 20 min and stored at 4 ℃. The surplus sample was lyophilized for long-term storage.

Radiolabeling with ⁶⁸Ga

⁶⁸GaCl₃ (1110 MBq) was eluted from a ⁶⁸Ge/⁶⁸Ga generator using 0.05 M HCl. NGD-MNPs (1 mg) was dissolved in water (1 mg/mL) and 500 μL of ⁶⁸GaCl₃ (600 MBq) was added. Finally, we adjusted the pH to 3.7 using sodium acetate (1.25 M). Then, the reaction mixture was incubated at room temperature for 30 min. The radiolabeling efficiency was measured by radio-thin-layer chromatography (TLC) using a 1:1 mixture of 10% ammonium acetate and methanol as the developing solvent system. The product was collected by centrifuging at 13,000 rpm for 5 min and sterilized through a 0.22 μm Millipore filter for later use [23].

Characterization of NGD-MNPs

The morphology and size distribution of DMSA-MNPs and NGD-MNPs were characterized by transmission electronic microscopy (TEM, JEM-2100, JEOL, Tokyo, Japan) at an accelerating voltage of 100 kV. The hydrodynamic diameters and Zeta potentials of these particles were determined by dynamic light scattering (DLS, Zetasizer Nano ZS90, Malvern Instruments, Worcestershire, UK) equipped with 4 mW He-Ne laser (λ = 633 nm). The magnetic properties of powder samples were analyzed in a vibrating sample magnetometer (VSM JDM-13, China).

Immunofluorescence staining of GEBP11 in cells and plaque tissue

Human umbilical vein endothelial cells (HUVECs) and EAhy926 cells (ATCC, Rockville, USA) were prepared as described previously [24, 25]. An in vitro cell chemical hypoxia model was established by adding 300 μM cobalt chloride (CoCl₂) to culture medium and cells were harvested after 4 h. The binding affinity and specificity of GEBP11 were assessed by cell immunofluorescence studies. The cells, after hypoxia treatment, were incubated with FITC-GBPE11 (1 mg/mL) for 30 min, fixed in 4% paraformaldehyde and washed by PBS as described above. Nuclei were stained by 4', 6-diamidino-2-phenylindole (DAPI) for 3 min. The cells were imaged by a confocal fluorescence microscope (Olympus, Tokyo, Japan) using filters specific for DAPI and FITC. An unrelated peptide (URP, CNLKNTHHC) was used as negative control.

The plaque tissue from rabbits before nanoparticle injection was processed routinely into paraffin and sectioned. The tissue sections were dewaxed, rehydrated and heat-induced antigen was retrieved in citrate buffer (0.01 M, pH 6.0). After incubating overnight with a goat anti-rabbit CD31 antibody (Abcam, Cambridge, UK) and FITC-GEBP11 peptide at 4 °C, the slides were washed and incubated with DyLight^TM 488-conjugated Donkey Anti-Mouse IgG as secondary antibody for 30 min at room temperature. Nuclei were stained by 4', 6-diamidino-2-phenylindole (DAPI) for 3 min. The sections were imaged by an Olympus FV 10i confocal fluorescence microscope.

In vitro MR imaging

To determine the relaxivity, NGD-MNPs were diluted in 500 μL distilled water at various concentration levels (0, 2.5, 5, 7.5 and 10 μg/mL) and then transferred to 1.5 mL Eppendorf tubes. High resolution T₂-weighted MRI scans were acquired using an 8-channel wrist joint coil on a 3.0 T MRI system (Siemens, Germany). The imaging parameters were as follows: field of view (FOV) 120 mm, base resolution 384 × 384, slice thickness 3 mm, multiple echo times (TE) 20, 40, 60, 80, 100, 120, 140 ms, repetition time (TR) 2000 ms. T₂ relaxation rates were plotted against iron concentrations in the particle dilutions. The relaxivity was determined by a linear fit.

Cell culture and cell MR imaging

To reveal the T_2-signal decay value of the HUVECs treated with NGD-MNPs, 1×10⁵ HUVECs were seed onto sterile 24-well plates and incubated overnight in a humidified incubator at 37 °C with 5% CO₂. When the cells reached 70-80% confluency, HUVECs chemical hypoxia model was prepared as described previously. Fresh M200 complete medium supplemented with different concentrations of NGD-MNPs (0, 5, 10, 15 and 20 μg/mL) were added to the culture plates. The cells were incubated with nanoparticles for 6 h and washed three times with phosphate buffered saline (PBS, 0.1 M, pH 7.4). The cells were detached by trypsin/ethylenediaminetetraacetic acid (EDTA), suspended in 500 μL 0.5% agarose gel and then transferred to 1.5 mL Eppendorf tubes. MR images were acquired using a 3.0 T MRI system with the same parameters mentioned above.

Prussian blue staining and iron uptake assay

To confirm the cellular uptake of nanoparticles, 1×10⁶ HUVECs were incubated with NGD-MNPs at a concentration of 20 μg/mL for 6 h. The cells were washed with PBS and fixed in 4% paraformaldehyde for 15 min. After removing the fixative, 1 mL of solution containing 5 wt% potassium ferrocyanide and 10 vol% HCl were added to each well and incubated at room temperature for 15 min. After washing with distilled water three times, the cells were counterstained with nuclear fast red solution (Sigma Chemical Co, St. Louis, MO) for 3 min. Images were obtained under Olympus BX51 microscope (Olympus, Tokyo, Japan).

The quantitative analysis of iron content internalized by HUVECs was determined by an atomic absorption spectrophotometer (AAS, Shimadzu Corp, Kyoto, Japan). 1×10⁶ HUVECs were treated with CoCl₂ as described above and then incubated with nanoparticles (20 μg/mL) for 6 h. The cells were lysed with 200 μL of concentrated HCl and the lysate was transferred into a micro reaction tube. After an appropriate dilution of lysate with distilled water, intracellular iron content was measured by AAS.

Cytotoxicity assay of nanoparticles

MTT assay was used for cell viability study. 1×10⁴ HUVECs were seed in 96-well plates under different concentrations of NGD-MNPs (0, 5, 10, 50, 100 and 250 μg/mL). After 48 h incubation, the relative cell viability was assessed by MTT assay. 20 μL MTT solution (5 mg/mL) was added to each well and incubated for 4 h. The formazan crystal was dissolved in 150 μL DMSO completely and then the plates were read on a Microplate Reader at 490 nm wavelength (TECAN, Switzerland).

The cell cycle and apoptosis were analyzed by flow cytometry (Becton Dickinson, San Jose, CA). 1×10⁵ HUVECs were seed in sterile 24-well plates and incubated with NGD-MNPs at a concentration of 20 μg/mL for 48 h. Cells were washed with PBS, harvested with trypsinization and then treated with a set of reagents provided by the CycleTEST^TM PLUS DNA Reagent Kit (BD biosciences, San Diego, USA). Nuclei were then stained with a 50 μg/mL PI solution for 30 min at 4 ℃ in the dark. The distributions of cell-cycle phases were analyzed by flow cytometry. Treated or untreated cells were stained with propidium iodide (PI) and Annexin V (eBioscience, San Diego, USA) for the apoptosis tests.

Mice (n=3/group) received 4 intravenous injections of 200 μL PBS or NGD-MNPs (20 mg Fe/kg/injection) in two weeks. 4 weeks and 12 weeks after the last injection, mice were euthanized and the spleen, liver, lungs, heart and kidneys were harvested for histopathological analysis.

Mice (n=3/group) received a single intravenous injection of 100 μL PBS or NGD-MNPs (5 mg Fe/kg/injection). At several time points (0, 0.5, 1, 3, 7 and 15 day) after the administration of the NGD-MNPs, mice were euthanized and 3 mL blood sample was sent to the clinical laboratory of Xijing hospital for alanine aminotransferase (ALT), aspartate aminotransferase (AST) and creatinine assay.

Immunogenicity assay of nanoparticles

Mice (n=3/group) received 3 intravenous injections of 100 μL PBS or NGD-MNPs (5 mg Fe/kg/injection) every two weeks. Mice were euthanized 10 days after the last immunization [26]. T lymphocyte proliferation was determined by the MTT assay. Briefly, 1×10⁴ spleen cells isolated from the vaccinated mice were seeded in 96-well plates and stimulated with the NGD-MNPs (10 μg/mL) for 48 h. 20 μL MTT solution (5 mg/mL) was added to each well and incubated for 4 h. The formazan crystal was dissolved in 150 μL DMSO completely, followed by measurement of the optical density (OD) value using a microplate reader. The stimulation index (SI) was calculated as follows: SI = (OD of stimulated culture)/(OD of unstimulated culture). SI > 2 was considered significant [27].

Relative proportions of CD4+ T and CD8+ T cells in the spleen cells of mice were analyzed by flow cytometry. Briefly, 1×10⁶ splenocytes were cultured in complete RPMI-1640 alone or co-cultured with NGD-MNPs (10 μg/mL) for 4 h. 10 μL of FITC-conjugated rat anti-mouse CD8 antibody (Ebioscience, San Diego, USA) and PE-conjugated rat anti-mouse CD4 antibody (Ebioscience, San Diego, USA) were incubated with the spleen cells in a 200 μL volume for 20 min at room temperature. The spleen cells were washed twice with PBS and resuspended in 500 μL PBS for flow cytometry.

Blood retention time and biodistribution of nanoparticle

Mice (n=3/group) received a single intravenous injection of 100 μL NGD-MNPs (5 mg Fe/kg/injection). At different time points (0.1, 2, 6, 12, 24 and 48 h) after the injection, 3 mL of blood sample was collected to obtain serum immediately. Then iron contents in serum were determined by a fast sequential AAS (Shimadzu Corp, Kyoto, Japan) and analyzed to calculate a half-life period.

Mice (n=3/group) received a single intravenous injection of 100 μL PBS or NGD-MNPs (5 mg Fe/kg/injection). At several time points (0.5, 7 and 15 days) after the injection, mice were euthanized and the spleen, liver, lungs and kidneys were harvested for Prussian blue staining analysis.

Intravascular and ultrasound imaging

IVUS was carried out after administration of 20 μg nitroglycerin using a 40 MHz catheter (Atlantis SR Pro, Boston Scientific, Natick, MA, USA) and an automatic pullback device at 0.5 mm/s. All IVUS images were obtained at 30 frames/s and recorded on high-resolution super VHS videotapes.

In vivo PET/MR imaging

PET/CT scans were performed on a Biograph 64 HR PET-CT (Siemens, Germany). ⁶⁸Ga-NGD-MNPs or ⁶⁸Ga-NUD-MNPs (52.4 MBq in 500 μL) were respectively injected into rabbits under anesthesia via a marginal ear vein. A 10 min static scan was acquired at 60 min. The images were reconstructed by a two-dimensional ordered-subsets exception maximum algorithm. For each PET/CT scan, regions of interest (ROIs) were drawn over the vassal wall, muscle, liver and kidneys on the decay-corrected whole-body coronal images.

MRI was performed on the 3.0 T MRI system with a knee coil before and 4 h after intravenous administration of NGD-MNPs (5 mg Fe/kg body weight). The parameters were as follows: field of view (FOV) 80 mm, base resolution 192 × 192, slice thickness 1 mm, multiple echo times (TE) 114 ms, repetition time (TR) 3500 ms. The T₂-weighted signal change of the plaque was calculated by using the following formula: (SIpre-SIpost)/SIpre × 100%, where SIpre and SIpost were the signal intensity of the plaque before and after administration of the nanoparticles, respectively.

Histology staining

After the MR images were acquired, the plaque tissues were processed routinely into paraffin and sectioned. The tissue sections were dewaxed, rehydrated and heat-induced antigen was retrieved in citrate buffer (0.01 M, pH 6.0). After incubation overnight with goat anti-rabbit CD31 primary antibody (dilution 1:100) at 4 °C, the slides were washed and incubated with mouse anti-goat IgG (dilution 1:200, Zymed) as secondary antibody for 30 min at room temperature. After washing again with PBS, horseradish peroxidase (HRP)-conjugated streptavidin (Zymed) was incubated for 10 min. Subsequently, CD31 location was visualized by 3,3-diaminobenzidine (DAB) solution for 3 min and counterstained by hematoxylin for 2 min. Then tissues were dehydrated, mounted and photographed for Olympus BX51 microscope (Olympus, Tokyo, Japan) evaluation. Prussian blue staining was performed to the serial sections as described above.

Statistical Analysis

Data are expressed as mean ± standard deviation (SD). SPSS17.0 (SPSS Inc, USA) and Prism 5.0 (GraphPad Software, USA) were used to perform the one-way analysis of variance (ANOVA). A two-tailed P-value < 0.05 was considered statistically significant.

Results

Characterization of nanoparticles

The schematic structures of ⁶⁸Ga-GEBP11-DMSA-MNPs are shown in Fig. 1. Transmission electron microscopy (TEM) images showed DMSA-MNPs and NGD-MNPs with average iron core sizes of 10 nm and 12 nm, respectively (Fig. 2A, D). Both the DMSA-MNPs and NGD-MNPs had a narrow size range (Fig. 2B, E). The results of DLS revealed that the NGD-MNPs dispersed in distilled water had a hydrodynamic diameter of 130.8 nm ± 7.1 nm, larger than 63.2 ± 4.1 nm of the DMSA-MNPs (Fig. 2C, F). Zeta potential of MNPs was -33.7 ± 1.5 mV, which changed to -45.2 mV ± 2.3 mV after coupling with NOTA (Fig. 2G). The magnetic properties of DMSA-MNPs and NGD-MNPs measured by VSM showed that the two kinds of particles were superparamagnetic and the saturation magnetization of DMSA-MNPs was 58.1 emu/g, larger than 47.6 emu/g of NGD-MNPs (Fig. 2H). The relaxivity (r²) of NGD-MNPs was calculated to be 109.7 mM^-1s^-1, slightly lower than that of DMSA-MNPs (128.4 mM^-1s^-1) (Fig. 2I). The MRI results showed that the T₂ relaxation time was significantly affected by NGD-MNPs and there was a strong linear correlation between the nanoparticle concentration and the signal intensity change. As expected, HUVECs treated with NGD-MNPs showed a gradual MR signal decay with increasing concentration of iron (Fig. 3C).

 Figure 1 

Schematic diagram depicting the structure and manufacture of ⁶⁸Ga-NOTA-GEBP11-DMSA-MNPs (⁶⁸Ga-NGD-MNPs).

 Figure 2 

The characterizations of MNPs. (A, D) TEM micrograph (the scale bar is 20 nm). (B, E) The size distribution of MNPs. (C, F) The hydrodynamic diameters and dispersive stability of MNPs measured by DLS. (G) The zeta potential of MNPs measured by DLS. (H) The magnetization curves of MNPs. (I) The relaxivities (r₂) of MNPs.

Cellular uptake of nanoparticles

The targeting ability of GEBP11 peptide was examined by confocal laser microscopy. Fluorescence signals from cellular cytoplasm could be easily detected in HUVECs (Fig. 3A). In addition, we found high binding affinity of GEBP11 peptide to EAhy926 cells after hypoxia treatment by immunofluorescence staining study (Fig. S1). GEBP11 peptide was well co-localized with CD31-positive plaque neovascularization and vasa vasorum in the plaque section (Fig. 3B). After Prussian blue staining, the intra-cytoplasmic inclusions containing MNPs presented as dense blue stained vesicles under light microscopy. Prussian blue staining results showed that the iron uptake of HUVECs increased significantly in NGD-MNPs group compared with that in DMSA-MNPs group or unrelated peptide control group (NRD-MNPs) (Fig. 3D). The quantitative evaluation of the cellular uptake of MNPs is in agreement with that observed with Prussian blue staining and the cellular iron loading increased with the dosage of MNPs (Fig. 3E).

 Figure 3 

The binding affinity of GEBP11 peptide and NGD-MNPs to HUVECs. (A) Immunofluorescence images of FITC-labeled GEBP11 peptide or un-related peptide (URP) incubated HUVECs (the scale bar is 50 μm). (B) Confocal images showing GBEP11 peptide ligand and CD31 expression in plaque region (the scale bar is 100 μm). (C) The T₂ weighted MR images of NGD-MNPs or HUVECs after incubation with NGD-MNPs at various iron concentrations. (D) Prussian blue staining images of HUVECs after incubation with MNPs (the scale bar is 50 μm). (E) Iron uptake curves of HUVECs.

Cytotoxicity assay of nanoparticles

Intracellular nanoparticle accumulation might induce cell death or apoptosis. TUNEL staining result revealed that there was no significant increase in cell apoptosis between NGD-MNPs group and negative control group (3.9% vs 3.0%, P > 0.05) (Fig. 4A, B). MTT assay demonstrated that the HUVECs incubated with different concentrations (5, 10, 50, 100 and 250 μg/mL) of NGD-MNPs exhibited no significant difference in cell viability compared with negative control groups (P > 0.05) (Fig. 4C). It is clear that NGD-MNPs produced no significant effect on cell cycle of HUVECs after 48 h treatment (P > 0.05) (Fig. 4D). Prussian blue staining of major organs showed iron agglomeration at 1 and 3 months after multiple dose administration of NGD-MNPs, but we found no structural or histopathological changes in any of the tissues (Fig. 4E). We found transient and moderate increases in ALT, AST and creatinine levels 1 day after NGD-MNPs injection as compared to controls, while the levels nearly fell back to baseline at 15 days post-treatment (Fig. 4F, G and H).

Immunogenicity assay of nanoparticles

Splenic lymphocytes were sorted from mice immunized with NGD-MNPs or PBS and analyzed using a proliferation assay. The SI value of the NGD-MNPs immunized group (1.313 ± 0.09) was higher than that of the PBS control group, but the difference was not significant. These results indicate that NGD-NPs do not strongly stimulate T-cell proliferative response in mice (Fig. 4I). The percentages of CD4+ and CD8+ T cell subsets in spleen cells were slightly higher in mice immunized with NGD-MNPs than that immunized with PBS, but the difference was not significant (P > 0.05) (Fig. 4J). These flow cytometry assays demonstrated that the NGD-MNPs have little influence on the activation of T cells.

 Figure 4 

Biocompatibility and immunogenicity of NGD-MNPs. (A) The flow cytometry assay and (B) the apoptosis index of HUVECs after incubation with NGD-MNPs. (C) The cell viability of HUVECs after incubation with NGD-MNPs at various iron concentrations. (D) The cell cycle of HUVECs after incubation with NGD-MNPs. (E) Representative Prussian blue staining of major visceral organs (heart, lungs, liver, spleen and kidneys) harvested from mice at 4 or 12 weeks after injection of NGD-MNPs or PBS (the scale bar is 50 μm). (F) Blood samples were collected from PBS or NGD-MNPs treated groups at different time points, and serum concentrations of AST, (G) ALT and (H) CREAT were analyzed. (I) Splenocytes from the immunized mice were incubated with NGD-MNPs for 2 days and then measured by the MTT assay to calculate the SI. (J) Splenocytes were isolated from immunized mice 10 days after the last immunization and the relative percentages of CD4+ T cells or CD8+ T cells were analyzed by flow cytometry.

Blood retention time and biodistribution of nanoparticles

The half-life period of the nanoparticles, calculated from the iron content in the serum of mice, was 6.2 h (Fig. 5A). The biodistribution of the nanoparticles in vivo was evaluated by Prussian blue staining of major organs sectioned at different time points after a single intravenous administration. We observed a preferential accumulation of nanoparticles in liver, lungs, kidneys and spleen rather than in heart or brain. Overall, the clearance process of nanoparticles in tissue lasted for 15 days, which was much slower than that in serum. The temporal biodistribution varied according to the different organ. There was a greater reduction of nanoparticle in kidneys and lungs than in liver and spleen (Fig. 5B).

 Figure 5 

Biodistribution of NGD-MNPs in mice. (A) Blood retention time of NGD-MNPs in mice. (B) Representative Prussian blue staining of major visceral organs (lungs, liver, spleen and kidneys) harvested at 12 h, 1 week and 2 weeks after injection of NGD-MNPs (the scale bar is 50 μm).

Intravascular and ultrasound imaging

As a consequence of abdominal aorta balloon de-endothelialization (Fig. 6A), vessel enlargement and plaque formation were observed compared to control group by ultrasound imaging (Fig. 6B, C). Meanwhile, an eccentric plaque with hypoechoic region was observed in the IVUS image, whereas no obvious atherosclerotic plaque was observed in control group (Fig. 6D, E). Extensive yellow-white plaques were observed at the injured site of rabbit abdominal aorta on a macroscopic image (Fig. 6F). The lipid-rich plaques were observed by oil red O staining compared to control group (Fig. 6G).

In vivo PET/CT and MR imaging

The targeting efficacy of ⁶⁸Ga-NGD-MNPs in atherosclerotic plaque was evaluated with static scans. The uptake of probe in plaque tissue and major organs were quantified based on ROI analysis of the PET images (Fig. 7A). The plaque was clearly visible with high contrast relative to background at 60 min after ⁶⁸Ga-NGD-MNPs injection. Predominant uptake of ⁶⁸Ga-NGD-MNPs was also visualized in the lungs, liver and kidneys. Meanwhile, there was little plaque uptake in ⁶⁸Ga-NUD-MNPs control group. Standard uptake value (SUVs) of ⁶⁸Ga-NGD-MNPs was higher than ⁶⁸Ga-NUD-MNPs in atherosclerotic abdominal aorta (SUVmax = 2.34 vs 0.47, P < 0.05) (Fig. 7B).

MRI was performed before and 4 h after nanoparticle administration. It was clearly observed that T₂ signal intensity of plaque regions in NGD-MNPs group was affected compared to NUD-MNPs group. NGD-MNPs can effectively reduce the T₂ relaxation time and consequently produce negative enhancement effects on T₂-weighted images (Fig. 8A). Signal intensity in MR imaging of plaque declined by 17.5% 4 h post-injection in NGD-MNPs group compared to 3.68% in control group (P < 0.05, Fig. 8B).

Histology

Immunohistochemical analyses showed that a large number of nanoparticles deposited in plaque lesions in NGD-MNPs group compared to NUD-MNPs group (Fig. 8C). Moreover, Prussian blue and CD31 immunohistochemistry serial section staining further confirmed that NGD-MNPs were well co-localized with plaque microvasculature (Fig. 8D).

 Figure 6 

Atherosclerotic lesions. (A) Abdominal aorta balloon denudation model. (C) Representative ultrasound images show the vessel enlargement and plaque formation 8 weeks after injury, (B) but not in control group. (E) Representative intravascular ultrasound images show a greater plaque burden and plaque eccentricity, (D) but not in control group. (F) An advanced plaque was observed at the injured site of rabbit abdominal aorta. (G) Representative macroscopic image shows the lipid-rich plaque by oil red O staining.

 Figure 7 

In vivo PET imaging study. (A) The PET images of rabbits 2 h after ⁶⁸Ga-NGD-MNPs or ⁶⁸Ga-NUD-MNPs injection. (B) Quantification of PET images. Plaque in ⁶⁸Ga-NGD-MNPs group exhibited significantly greater mean standardized uptake value (SUV) than control group.

 Figure 8 

In vivo MR imaging study. (A) The MR images of abdominal aorta before and 4 h after NGD-MNPs or NUD-MNPs injection (the scale bar is 1 cm). (B) Comparison of the relative signal intensity change (NENH%) in the T₂-weighted images of abdominal arterial wall before and 4 h after NGD-MNPs or NUD-MNPs injection. (C) Prussian blue staining images show the accumulation of NGD-MNPs or NUD-MNPs in the plaque tissues extracted from rabbits. (D) CD31 immunohistochemistry images were recorded for showing the co-localization of CD31 and NGD-MNPs in the corresponding tissues (the scale bar is 50 μm).

Discussion

Despite recent therapeutic developments, cardiovascular disorder remains a worldwide health challenge and causes a remarkable need for early diagnosis and sequential treatment. Because morphological imaging has some limitations in early diagnosis of vulnerable plaque, molecular imaging has emerged as a novel tool to identify molecular and cellular events critical for the pathogenesis of atherosclerosis. Accumulating evidence has linked plaque angiogenesis with progressive atherosclerotic disease and acute lesion instability [9, 28, 29]. The plaque microvasculature can act as conduits for cellular and soluble lesion components (such as lipid, cytokines, and growth factors) [30]. Moreover, the fragile structure of the neovasculature is prone to leakage and therefore promotes intra-plaque hemorrhage [31, 32]. As mentioned above, molecular imaging approaches will be critical for monitoring angiogenesis processes in diseases, as well as evaluating physiological consequences of the therapeutic intervention. In this study, we have synthesized and evaluated a GEBP11 peptide-targeted imaging probe for angiogenesis molecular imaging with PET/MRI.

The essence of molecular imaging is the interaction between probes and targeted markers. The targeting ability of the imaging probe is the primary issue of molecular imaging. Successful molecular imaging relies on probes with high affinity, sensitivity and specificity. Peptides containing the integrin-binding motif Arg-Gly-Asp (RGD) can image newly formed microvessels in both tumor tissue and atherosclerotic plaque [12, 33-36]. In spite of the promising results, some researchers hypothesized that the RGD peptide might lack specificity for endothelial cells as macrophages can also express α_vβ₃ integrin in atherosclerotic plaque [37]. Our previous results confirmed that GEBP11 peptide exhibits high affinity to tumor vasculature. In the present study, we clarified that GEBP11 peptide could selectively target endothelial cells rather than macrophages by immunofluorescence staining. The in vitro cell immunofluorescence results showed strong evidence of specific GEBP11 peptide ligand expression in HUVECs. The Prussian blue staining demonstrated a significant increase of ⁶⁸Ga-NGD-MNPs uptake in the plaque with the maximum value at 60 min after the injection of the nanoprobe.

Another challenge for the in vivo imaging is that the size of imaging probe should be accurately controlled. The aorta endothelial tight gap junction associated with the plaque is approximately 20 nm in mice [38]. On the other hand, circulating MNPs less than 10 nm of diameter will be quickly eliminated by renal clearance, while the particles greater than 200 nm are inclined to be captured by the reticuloendothelial system (RES) [39]. Hence, we designed NGD-MNPs, of which inorganic core size is very close to 10 nm and the hydrodynamic diameter is only 130.8 nm ± 7.1 nm. This disparity is attributed to the interaction between coating materials and solvent molecule. Compared with DMSA-MNP, hydrodynamic size of the nanoparticles expressed an increase after their conjugation with GEBP11 peptide and NOTA, but hydrodynamic size of NGD-MNPs could be well controlled under 150 nm by altering the ratio of GEBP11 to DMSA-MNPs. In our previous study, we found that one DMSA-coated nanoparticle could be conjugated with approximately 4 GEBP11 peptides [40]. The change of zeta potential indicated a successful conjugation between nanoparticles and the other segments. Our results revealed that NGD-MNPs had a long blood circulation time, resulting in more opportunities for the interaction between ligands and NGD-MNPs.

The toxicity of magnetic nanoparticles is one of the most important issues that needs further investigation. Emerging studies suggest that DMSA-MNPs have good biocompatibility for MR imaging both in vitro and in vivo [41-45]. In spite of the greater uptake of nanoparticles mediated by GEBP11 peptide, rare detectable cytotoxic effect was observed in cells and tissues assays. Furthermore, biochemical analysis (AST, ALT and CREA) verified that NGD-MNPs had little effect on these important biological functions of normal rats and showed good biocompatibility for further biomedical application. Immunogenicity is another significant concern for biologic drugs as it can affect both safety and efficacy [46]. In this study, we found that NGD-NPs did not strongly stimulate T-cell proliferative response in mice. The immune response might depend not only on the chemical structure of GEBP11 peptide on the nanoparticle surface, but also on extrinsic factors, such as MNP dose and the MNPs coating modification.

Molecular imaging relies on various imaging technologies, each approach presents advantages and weaknesses. PET provides high sensitivity and allows quantitative measurements, albeit with relatively limited spatial resolution. MRI is good at representing anatomical information, but has limitations for analysis of molecular events. Using hybrid imaging methods allows combination of the benefits of different imaging platforms [3]. The combination of MRI contrast agent DMSA-MNPs and the positron emitter ⁶⁸Ga complements each weakness and maximizes strengths of these two imaging modalities. The macrocyclic chelator NOTA was selected to interact with ⁶⁸Ga because it allows for highly efficient radiolabeling under mild conditions to ensure the biological activity of targeting molecules [47]. Iron oxide magnetic nanoparticles (MNPs) have been widely used not only as negative contrast agent for MR imaging, but also as an effective carrier for peptides to prolong their circulation half-life [48]. The increased cellular uptake of NGD-MNPs confirmed that the chemical conjugation with DMSA-MNPs and NOTA exerted no detrimental effect on the bioactivity of GEBP11 peptide. GEBP11 peptide has ability to facilitate cellular uptake of nanoparticles.

The PET images showed that predominant uptake of ⁶⁸Ga-NGD-MNPs was visualized in the plaque, lungs, liver and kidneys. One possible explanation for this phenomenon is that the probe is metabolized through the liver and kidneys. The Prussian blue and CD31 immunohistochemistry were used to further evaluate the targeting specificity of NGD-MNPs. The co-localization of NGD-MNPs with CD31 is consistent with PET/MR images. The signal change of PET/MR images could serve as a surrogate marker of microvascular density in atherosclerotic plaques. NGD-MNPs may provide a useful tool to assess the atherosclerotic plaque burden and severity.

Despite these encouraging results, there are still some limitations in our research. GEBP11 peptide receptor on vascular endothelial cell is still unclear, but several candidate receptor molecules have been obtained. Further work is underway to provide a detailed structural understanding of the interaction between GEBP11 peptide and its ligand. Whether the probe of NGD-MNPs can serve as a therapeutic intervention vector still requires further investigation.

Conclusions

We developed a novel PET/MR dual-modality imaging probe (NGD-MNPs) for noninvasive assessment of angiogenesis in atherosclerotic plaque in this study. NGD-MNPs could selectively accumulate within the plaque vasculature and was suitable for in vivo molecular imaging of progressive plaque angiogenesis formation with high specificity and sensitivity.

Abbreviations

AAS: atomic absorption spectrophotometer; CAG: coronary X-ray angiography; CCTA: coronary computed tomography angiograpy; CoCl₂: cobalt chloride; CVD: Cardiovascular disease; DAPI: 4', 6-diamidino-2-phenylindole; DLS: dynamic light scattering; DMSA-MNPs: 2, 3-dimercaptosuccinnic acid-coated paramagnetic nanoparticles; EDTA: trypsin/ethylenediaminetetraacetic acid; EPR: enhanced permeability and retention; ⁶⁸Ga-NUD-MNPs: 68Ga-NOTA-unrelated peptide-DMSA-MNPs; ⁶⁸Ga-NGD-MNPs: ⁶⁸Ga-NOTA-GEBP11-DMSA-MNP; HUVECs: human umbilical vein endothelial cells; IVUS: intravascular ultrasonography; MNPs: magnetic nanoparticles; MR: magnetic resonance; OCT: optical coherence tomography; PET: positron emission tomography; PBS: phosphate buffered saline; SUVs: standard uptake values; TLC: radio-thinlayer chromatography; TEM: transmission electronic microscopy; UPR: unrelated peptide; TR: repetition time; TE: echo times

Supplementary Material

Supplementary Figure S1 shows the binding affinity of GEBP11 peptide to EAhy926 cells. Immunofluorescence images of FITC-labeled GEBP11 peptide or un-related peptide (URP) incubated EAhy926 cells (the scale bar is 50 μm).

Acknowledgements

This work was supported by the National Key Research Program of China (2016YFA0100903), the National Funds for Distinguished Young Scientists of China (.81325009) and National Nature Science Foundation of China (81227901, 81530058, and 81570272) and Innovation Team Grant of Shaanxi Province (No.2014KCT-20).

Competing Interests

The authors have declared that no competing interest exists.

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Author contact

Corresponding author: Feng Cao, M.D., Ph.D. FACC, Department of Cardiology, Chinese PLA General Hospital, 28# Fuxing Road, Beijing 100853, China Tel: +86-10-55499138 E-mail: wind8828com or fengcaoedu.cn or fengcao8828com

Received 2017-4-27
Accepted 2017-9-16
Published 2017-10-17

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