Comparison of cyclic RGD peptides for αvβ3 integrin detection in a rat model of myocardial infarction
© Laitinen et al.; licensee Springer. 2013
Received: 8 March 2013
Accepted: 3 May 2013
Published: 11 May 2013
Expression of αvβ3 integrin is increased after myocardial infarction as part of the repair process. Increased expression of αvβ3 has been shown by molecular imaging with 18F-galacto-RGD in a rat model. The 68Ga-labelled RGD compounds 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 have high specificity and affinity, and may therefore serve as alternatives of 18F-galacto-RGD for integrin imaging.
Left coronary artery ligation was performed in rats. After 1 week, rats were imaged with [13N]NH3, followed by 18F-galacto-RGD, 68Ga-NODAGA-RGD or 68Ga-TRAP(RGD)3 using a dedicated animal PET/CT device. Rats were killed, and the activity in tissues was measured by gamma counting. The heart was sectioned for autoradiography and histology. Immunohistochemistry was performed on consecutive sections using CD31 for the endothelial cells and CD61 for β3 expression (as part of the αvβ3 receptor).
In vivo imaging showed focal RGD uptake in the hypoperfused area of infarcted myocardium as defined with [13N]NH3 scan. In autoradiography images, augmented uptake of all RGD tracers was observed within the infarct area as verified by the HE staining. The tracer uptake ratios (infarct vs. remote) were 4.7 ± 0.8 for 18F-galacto-RGD, 5.2 ± 0.8 for 68Ga-NODAGA-RGD, and 4.1 ± 0.7 for 68Ga-TRAP(RGD)3. The 68Ga-NODAGA-RGD ratio was higher compared to 68Ga-TRAP(RGD)3 (p = 0.04), but neither of the 68Ga tracers differed from 18F-galacto-RGD (p > 0.05). The area of augmented 68Ga-RGD uptake was associated with β3 integrin expression (CD61).
68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 uptake was equally increased in the infarct area at 1 week post infarction as 18F-galacto-RGD. These results show the potential of 68Ga-labelled RGD peptides to monitor integrin expression as a part of myocardial repair and angiogenesis after ischaemic injury in vivo.
Healing of myocardial infarct (MI) is a dynamic process, with stages of initial inflammation, angiogenesis, fibroblast proliferation and collagen deposition followed by scar formation in the maturation and remodelling phase . Inadequately healed MI results in infarct area expansion and dilatation of the heart by left ventricle (LV) remodelling, ultimately developing into chronic heart failure [2, 3]. Angiogenesis is a central part of infarct healing and is characterised by activation of angiogenic factors and expression of signalling molecules such as integrins. One particularly interesting member of this family is the integrin αvβ3. It is a cell-membrane glycoprotein receptor that is quiescent under normal conditions, but its expression and activation is up-regulated on the endothelial cells when angiogenesis takes place, such as in the infarct area after ischaemic myocardial injury . Radiolabelled antagonists containing the αvβ3-specific cyclic RGD peptide can be used for molecular imaging of αvβ3 integrin expression after MI [5–7]. Uptake is the highest at 1 week after infarct corresponding to the peak time of neovessel formation . Our recent study shows that the uptake of 18F-galacto-cyclo(RGDfK) (18F-galacto-RGD) in the infarct area at 1 week after MI predicts improved healing in the form of less LV remodelling seen 12 weeks after the injury . Taken together, imaging of αvβ3 integrin expression is an attractive tool to assay the post-MI angiogenesis and may be potentially used to predict outcome of infarct healing.
The production of 18F-galacto-RGD requires an on-site cyclotron and a multi-step synthesis, which is challenging to transfer to good manufacturing practice (GMP) conditions. Therefore, alternative RGD compounds have been sought after, such as a one-step-labelled positron-emission tomography (PET) tracer,18F-AIF-NOTA-PRGD2, which was also found to reflect ischaemia-induced angiogenesis in a rat model .68Ga-NODAGA-cyclo(RGDyK) and 68Ga-TRAP(cyclo(RGDfK))3 have been evaluated for αvβ3 imaging in tumour models, showing high target-to-background ratios [9–12]. 68Ga tracers have the advantage of easy and fast production with a generator-produced radionuclide. 68Ga-NODAGA-RGD and particularly 68Ga-TRAP(RGD)3 can be produced with high specific activity (approximately 200 to 600 GBq/μmol for 68Ga-NODAGA-RGD and over 5 TBq/μmol for 68Ga-TRAP(RGD)3 [9, 11]), which is essential when using 68Ga-labelled peptides, especially in case of small animal studies.
In this study we sought to evaluate 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 for targeting αvβ3 integrin in comparison to 18F-galacto-RGD using a well-defined rat model of myocardial infarct [6, 8]. We investigated the uptake of all three tracers using in vivo and ex vivo techniques and validated the findings with immunohistochemistry.
Permanent ligation of the left anterior descending coronary artery was performed, as previously described  in 34 healthy male Lewis rats (Charles Rivers Laboratories, Sulzfeld, Germany) aged 8 to 10 weeks to induce MI. Briefly, the rats were anaesthetised with intramuscular administration of midazolam 5 mg/kg (Dormicum®, Roche; Grenzach-Wyhlen, Germany), medetomidin 0.5 mg/kg (Dormitor®, Pfizer, Karlsruhe, Germany) and fentanyl 0.05 mg/kg (Ratiopharm, Ulm, Germany) and connected to a rodent ventilator. The heart was exposed through a left lateral thoracotomy of the fourth intercostal space, and the left anterior descending (LAD) artery was ligated near to its origin (2 to 3 mm from the tip of the left atrium). Two rats underwent sham operation, which consisted of the same procedures except that the LAD artery suture was not tightened. The rats were treated with 0.05 mg/kg buprenorphin (Temgesic®, Essex, Germany) and 4 mg/kg carprofen (Rimadyl, Pfizer, Germany) for 72 h post surgery. The study protocols were approved by the regional governmental commission for animal protection (Regierung von Oberbayern, Munich, Germany).
The radiosynthesis and quality control of 18F-galacto-RGD (18F-galacto-cyclo(RGDfK)), 68Ga-NODAGA-RGD (68Ga-NODAGA-cyclo(RGDyK)) and 68Ga-TRAP(RGD)3 (68Ga-TRAP(cyclo(RGDfK))3) were performed as described previously [9–12].
Uptake of RGD in tissues
Rats were anesthetised using 1.5% isoflurane and were injected via tail vein catheter with 18F-galacto-RGD (37 MBq, n = 9), 68Ga-NODAGA-RGD (69 MBq, n = 10) or of 68Ga-TRAP(RGD)3 (54 MBq, n = 12). Rats were kept under anaesthesia in a warmed bed until euthanized after 90 min using intravenous injection of 150 mg/kg of pentobarbiturate (Narcoren®, Merial, Rohrdorf, Germany). The heart was excised and cut transaxially at the location of the infarct. The apical part, containing both infarct and non-affected remote myocardium, was processed for sectioning for autoradiography as described below.
Tissue samples (remote myocardium, apical part of myocardium, femoral muscle, operation wound and the connective tissue contralateral to the wound, spleen, liver, kidney, urine and blood) were dissected, and the weights of the tissue, urine, blood and serum samples were measured and their activity was detected using a gamma counter (1480 Wizard, PerkinElmer Wallac, Turku, Finland).
In order to determine the blood clearance, blood samples were drawn from a subset of animals (68Ga-NODAGA-RGD, n = 3; 68Ga-TRAP(RGD)3, n = 3) at 1, 5 and every 10 min after injection using a second tail vein catheter.
The excised hearts were frozen and embedded in Tissue Tek® mounting media (Sakura Finetek Europe B.V., Alphen aan den Rijn, the Netherlands). Serial LV short-axis cryosections of 20-μm thickness were obtained. Similar sections of muscle and spleen samples of the same rat were processed and used as negative and positive controls. After quick air drying, the sections were exposed to an imaging plate (Kodak Storage Phosphor screen GP, Eastman Kodak Company, Rochester, NY, USA). After an overnight exposure, the imaging plates were scanned with an image plate scanner (CR 35 BIO, Dürr Medical, Raytest Isotopenmeßgeräte GmbH, Germany; internal resolution of 25 μm), and the images were analysed for background-corrected count densities (PSL/mm2) with an image analysis programme (AIDA Image Analyser, Raytest Isotopenmeßgeräte, Germany). Later, the same sections were stained with hematoxylin-eosin (HE) for delineation of the affected area in the myocardium.
After careful co-registration of the autoradiographs and HE histological images, regional tracer uptake was analysed in the following two regions: (1) the infarcted myocardium containing the border zone as assessed after HE staining and (2) the remote, non-affected myocardium. The analysis was based on 12 to 15 sections from each heart. The results were expressed as a ratio of the mean value of activity in the infarct area divided by the mean value of activity in the remote area.
A subset of animals (n = 7) was imaged using a small-animal PET/CT scanner (Inveon, Siemens Medical Solutions, Knoxville, TN, USA). The rats were anaesthetised using 1.5% isoflurane. Breathing was monitored and temperature was maintained using a heating pad throughout the imaging procedures. The rats were injected with 37 MBq of [13N]NH3 via tail a vein catheter, and perfusion images were acquired for 15 min starting at the time of injection. A CT scan was performed for anatomical localisation. The animals were left anaesthetised in the scanner, and 60 min later, the animals were injected with either 68Ga-NODAGA-RGD (72 MBq, n = 4) or 68Ga-TRAP(RGD)3 (63 MBq, n = 3) via the tail vein. Dynamic PET data were acquired from the start of the injection for 90 min in a list mode. The rats were euthanized immediately after, and the tissues were processed as described above.
PET data were reconstructed using a 3D-filtered back-projection algorithm. The resulting matrix was 128 × 128 pixels with 159 transverse slices (voxel size of 0.78 × 0.78 × 0.80 mm3). Data were normalised and corrected for randoms, dead time and decay. No corrections were made for attenuation or scatter.
The CT acquisition consisted of 120 projections acquired with exposure time of 200 ms, X-ray voltage of 80 kVp and anode current of 500 μA for 220° rotation. CT images were reconstructed using a modified Feldkamp algorithm. The resulting matrix was 256 × 256 pixels with 631 transverse slices (reconstructed voxel size 0.21 × 0.21 × 0.21 mm3).
The 68Ga- and 13N-PET images were fused, and the uptake was visualised using the Inveon Research Workplace (Siemens, Knoxville, TN, USA). PET and CT images were co-registered for anatomical reference. Regions of interest (ROI) were manually drawn around the focal 68Ga-RGD uptake area in the myocardium on a transverse image, corresponding to 13N signal loss. This was repeated on four consecutive transverse images to cover the infarct area. The mean radioactivity concentration within the ROI was expressed as the percentage of injected dose per cubic centimetre (% ID/cc).
Five-micron LV short-axis sections were processed adjacent to the plane of sections for autoradiography. To visualise the endothelial cells, macrophages and β3 integrin expression in the myocardium, sections were stained with the following antibodies: CD31 (BD Pharmingen, Franklin Lakes, NJ, USA), F4/80 (Abcam, Cambridge, UK) and CD61 (BD Pharmingen, Franklin Lakes, NJ, USA). The sections were analysed for the extent of positive staining in remote, borderzone and infarct by light microscopy at ×400 magnification. After averaging the positive counts of ten fields, the vascular density and macrophage and β3 integrin expression were calculated per area (high-power field). For correlation with RGD uptake in the autoradiograms, the borderzone and infarct area results were pooled.
All data are expressed as mean ± standard deviation. The p values of <0.05 were considered as statistically significant. For comparison between two groups, Student's t test for unpaired data was used. ANOVA with Tukey-Kramer adjustment was used for comparisons of three different groups. For the correlation between two continuous variables, linear regression with Pearson's or Spearman's (for non-parametric) rank test was used.
Ligation of the LAD resulted in a myocardial infarction, which covered 15% to 25% of myocardial axial plain, as measured from autoradiography sections. Out of 34 operated rats, two died within 24 h after surgery and one during the imaging day, and one had 100% infarct in cross section and was therefore excluded. Average body weights were 310 ± 54 g and did not differ between the groups.
PET-CT in vivo imaging
Ex vivo biodistribution
Biodistribution of 68 Ga-NODAGA-RGD and 68 Ga-TRAP(RGD) 3 in tissues 90 min p.i
Mean ± SD
Mean ± SD
0.058 ± 0.02
0.101 ± 0.07
0.094 ± 0.05
0.166 ± 0.12
0.071 ± 0.03
0.154 ± 0.09
0.156 ± 0.06
0.353 ± 0.10
0.035 ± 0.01
0.066 ± 0.03
0.110 ± 0.05
0.190 ± 0.08
0.270 ± 0.24
0.256 ± 0.12
0.246 ± 0.16
0.415 ± 0.30
0.230 ± 0.17
0.524 ± 0.61
1.102 ± 0.70
1.447 ± 0.51
20.24 ± 6.40
35.10 ± 22.37
The apical part of the myocardium, containing both infarcted and remote myocardial tissue, was measured before processing into sections. The uptake was higher in the apical part as compared to the remote myocardium tissue sample (apical-to-remote ratio 2.4 (p > 0.01) for 68Ga-NODAGA-RGD and 2.1 (p > 0.01) for 68Ga-TRAP(RGD)3).
Ex vivo autoradiography of RGD tracer uptake in the myocardium
The tracer distribution in the myocardium of the sham-operated rats was uniform and comparable to the remote area of the operated rats (Figure 5). Pre-injection of high-dose cilengitide [12–15] reduced the uptake in the myocardium and also in the spleen, demonstrating specific binding (Figure 5). Infarct-to-remote ratio was 1.7 for both tracers when blocked with cilengitide (n = 3).
Studies in the rat model of myocardial infarct have shown that monitoring the expression of αvβ3 integrin by molecular imaging provides valuable prognostic information about myocardial repair after infarct [5–8]. First studies with animal models and humans using 18F-galacto-RGD have been promising, but further studies using this tracer are limited due to the difficulties of producing 18F-galacto-RGD in compliance with the GMP. Therefore, we sought to study new 68Ga-labelled RGD tracers for the use for MI imaging. Using in vivo imaging and ex vivo autoradiography analysis, we show that 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 accumulate in the myocardial infarct area in a similar manner as 18F-galacto-RGD. Autoradiography analysis revealed 4.1 to 5.2 times higher uptake in the infarct area as compared to the remote myocardium. Both in vivo and ex vivo gamma counting results supported this finding, although attenuation, partial volume and signal spillage diminished the acquired infarct-to-remote ratios obtained using these methods. In comparison to 18F-galacto-RGD, neither of the 68Ga-labelled tracers was superior, but when compared between each other, 68Ga-NODAGA-RGD had slightly higher infarct-to-remote myocardium ratio in the autoradiograms. This was not affected by the infarct size, vascular density or macrophage count. Moreover, we found that the RGD uptake correlated with β3 integrin expression in the myocardium.
Integrins have been shown to be essential in maintaining the homeostasis of the myocardium after pathologic stressors, such as myocardial infarct injury . Adverse healing of infarct leads to maladaptive hypertrophic growth of the left ventricle and, therefore, biomarkers for early detection are sought after. In addition to the role in the formation of neovessels during the granulation phase of infarct healing, the αvβ3 integrin participates in signalling events for further processes. β3 integrin together with β1 integrin play a role in hypertrophic growth via the activation of survival mechanisms by attenuating myocyte apoptosis [16–19]. Therefore, molecular imaging of integrin expression may offer an attractive way to improve risk assessment of post-MI patient and may serve as a biomarker for targeted therapy.
Cyclic RGDfK pentapeptides have been extensively studied for αvβ3 integrin imaging [20, 21]. Cyclic RGDfK and RGDyK compounds have a high affinity in the nanomolar range to αvβ3 and αvβ5 and have selectivity over other integrin subtypes [22, 23]. Several RGD compounds for PET and SPECT have been introduced for integrin imaging in malignant tumours and angiogenesis . The potential of αvβ3 targeting RGD peptides for imaging of myocardial infarct healing has also been demonstrated recently using 18F-galacto-RGD [6, 8], 99mTc-RAFT-RGD  and 18F-AlF-NOTA-PRGD2 .
68Ga-NODAGA-RGD is a cyclic RGD pentapeptide conjugated with a NODAGA chelator without affecting the binding affinity. 68Ga-TRAP(RGD)3  is a trimer based on a TRAP chelator for gallium(III) binding [11, 26, 27]. The specificity of 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 has been demonstrated in cell culture and mouse models [10–12], as well as for 18F-galacto-RGD in the same animal model as used in this study [6, 8]. We also show that pre-injection of a blocking dose of cilengitide, a cyclic RGD peptide with high affinity for αvβ3 and αvβ5 integrins [14, 15], diminished the 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 signal in the infarcted area of the myocardium and in the other measured tissues such as spleen and muscle, showing that the signal in these tissues is specific to integrin expression.
The affinity of trimeric 68Ga-TRAP(RGD)3 to αvβ3 integrin is more than seven times higher than that of the monomers 68Ga-NODAGA-RGD and 18F-galacto-RGD (IC50 of 44 nM vs. 336 nM and 319 nM, respectively, determined in a competitive displacement assay on M21 human melanoma cells [9, 10]). Multimerisation of the RGD molecule has been shown to increase affinity [20, 28, 29], but not necessarily the tumour-to-background ratio. This can be due to the specific (blockable) uptake of the ‘background’ tissue, which may express small amounts of the integrin. Another explanation can be the relatively low local concentration of the integrins in the target area and hence lack of bivalency binding of a multimeric molecule [10, 30, 31]. We also found a similar effect: the infarct-to-remote ratio in myocardium was not increased in the case of 68Ga-TRAP(RGD)3. In this case, the increased affinity of 68Ga-TRAP(RGD)3 to the small amount of integrin present in remote myocardium  results in a higher overall uptake, as was seen in vivo and ex vivo when compared to 68Ga-NODAGA-RGD (Table 1).
The selective and specific binding of cyclic RGD molecules to αvβ3 and αvβ5 integrins has been established with in vitro methods as well as in vivo experiments (reviewed in [20, 32]). The αvβ3 integrin expression is upregulated in several cancer cell lines  and in sprouting and activated vessels during wound healing of the skin, muscle and myocardium [4, 34, 35]. In supporting the earlier data of integrin location , the recent study by Gao and co-workers used dual immunofluorescence staining to demonstrate dominant co-localisation of CD61 (β3) signal with CD31-positive endothelial cells at 1 week after experimental ischaemia-reperfusion-induced infarct . We also show that RGD signal correlates with the number of CD61-positive cells in permanent ligation-induced MI. Previously, we have shown that 18F-galacto-RGD uptake does correlate to the vascular density in the infarct area, but does not correlate to the amount of macrophages at 1 week after injury . At 3 days after myocardial ischaemia reperfusion injury, Gao and colleagues did not find a strong co-localisation of CD61 and CD31 , which could indicate that the other cells might be responsible for RGD signal at this earlier time point. Myofibroblasts also express αvβ3 integrins and can be targeted with a pro-collagen-targeting Cy5.5-RGD imaging peptide . In addition to neovessels and myofibroblasts, macrophages have also been shown to express αvβ3 integrin . However, the relative amounts of integrin in these cell types have not been compared over time in MI. The temporal changes of the expression of αvβ3 and other integrins and, therefore, the cellular localization of the signal of labelled cRGD compounds in the case of myocardial infarct still warrant further studies.
Taken together, we as well as several other groups have established the use of integrin imaging in monitoring of myocardial infarct healing and the feasibility of cyclic RGD compounds for that purpose. The current requirements for the production of radiopharmaceuticals in GMP compliance have made the clinical use of 18F-galacto-RGD difficult. There is an increasing number of different RGD imaging compounds available, but which candidate should be selected further for clinical use is an open question. Although high specificity and selectivity to integrins and high affinity are necessary qualities, the selection for a clinically usable tracer needs to take into account the practical issues such as the ease and safety of the production. 68Ga tracers appeal to sites with no cyclotron close by, but for instance, the FASTlab production cassette for 18F-fluciclatide is also already available , which will facilitate the clinical use of this RGD-containing tracer using F-18 and a distribution network. Ultimately, the resulting imaging quality is a factor that cannot be compromised.
Prominent in vivo and ex vivo signal of 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 was found in the myocardium of rats at 1 week post infarct, localising to the area of hypoperfusion and β3 integrin expression. Both 68Ga-NODAGA-RGD and 68Ga-TRAP(RGD)3 showed similar binding behaviour in the myocardium after infarct as 18F-galacto-RGD. These results show the potential of 68Ga-labelled cyclic RGD peptides to monitor angiogenesis after myocardial injury in vivo.
We thank the personnel of the Laboratory of Molecular Imaging (Sybille Reder, Markus Mittelhäuser, Marco Lehmann, Marcus Bode and Annette Frank) for assistance on performing the animal imaging, Johanna Silvola for statistical analysis, as well as Michael Herz and Petra Watzlowik for the production of 18F-galacto-RGD. The financial support from the Deutsche Forschungsgemeinschaft (SFB 824, project Z1) and the BMBF (MOBITUM) is gratefully acknowledged.
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