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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptHHS Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
J Am Chem Soc. Author manuscript; available in PMC 2013 July 4.
Published in final edited form as:
PMCID: PMC3397236
NIHMSID: NIHMS387491

Discrete Bimodal Probes for Thrombus Imaging

Abstract

Here we report a generalizable solid/solution phase strategy for the synthesis of discrete bimodal fibrin-targeted imaging probes. A fibrin-specific peptide was conjugated with two distinct imaging reporters at the C- and N-terminus. In vitro studies demonstrated retention of fibrin affinity and specificity. Imaging studies showed that these probes could detect fibrin over a wide range of probe concentrations by optical, magnetic resonance, and positron emission tomography imaging.

Keywords: fibrin, gadolinium, copper, positron emission tomography, magnetic resonance imaging, fluorescence

Thrombosis, the formation of a blood clot within an artery or vein, is implicated in many of the leading causes of death worldwide: heart attack, stroke, pulmonary embolism, and deep vein thrombosis.1 The in vivo detection and characterization of thrombus is essential for disease diagnosis, for guiding therapy and for monitoring treatment. Several imaging modalities can be used for noninvasive identification of thrombus in a clinical or preclinical setting, and these include, positron emission tomography (PET), magnetic resonance (MR) imaging, and optical imaging (OI). Each modality has its own strengths and weaknesses; therefore combinations of modalities are increasingly used to provide synergies.25 Concurrently, multimodal imaging probes are being developed to exploit the gains in hybrid imaging systems for the improved detection of disease.69 We present here thrombus-targeted imaging probes employing positron-emitters, MR relaxation agents and fluorophores.

For molecular imaging of thrombus-related biomarkers, fibrin offers the potential for high disease specificity and sensitivity. This is because fibrin is present in all thrombi but is only found in clot and not in circulating blood. Discrete peptide-based probes,1017 antibodies,18 and nanoparticles1924 have been used to image fibrin. For imaging solid thrombi, peptide-based probes may be more advantageous than antibodies or nanoparticles because their small size offers higher potential to penetrate the clot. However, unlike nanoparticles which are insensitive to the incorporation of multiple imaging reporters, it is a challenge to modify a short peptide with two imaging reporters and still maintain target affinity and specificity.9 For instance, the incorporation of hydrophobic fluorescent dyes may induce non-specific protein binding.25 We reasoned that conjugation of a hydrophilic metal complex might offset the hydrophobicity introduced by the organic dye. In order to minimize the impact of the imaging reporters on fibrin binding, we positioned each reporter at the N- and C-terminus of the peptide. To this end, we describe fluorescent/MR and fluorescent/PET labeled peptides that maintain fibrin affinity and specificity after derivatization.

In our previous work, we noted that derivatizing both the C- and N-terminus of fibrin-specific peptides with Gd chelates not only increased detection sensitivity, but also protected those probes from exopeptidase degradation.26 Peptide substitutions at the C- and N-termini were relatively insensitive to fibrin affinity, presumably because of the conformational rigidity imparted by the cyclic peptide core. To introduce different imaging reporters, we reasoned that a mixed solid/solution phase synthetic approach could be used to incorporate a fluorophore (OI) at one terminus and a chelator for Gd (MRI) or 64Cu (PET) at the other terminus. Probe synthesis is outlined in Scheme 1 where the peptide and N-terminal modification are synthesized on resin. After resin cleavage, deprotection, and cyclization, the C-terminus is modified in solution. Complexation with Gd3+ or 64Cu2+ is the final synthetic step.

Scheme 1
Multimodal Probe Synthesis

In our probe design we employed the established fibrin-specific cyclic peptide used in the MR thrombus agent EP-2104R, and maintained the modification with p-xylenediamine to introduce a primary amine at the C-terminus.14 The isothio-cyanate of fluorescein (FITC) was used to incorporate a fluorescent reporter at the C-terminus. For attachment of FITC at the N-terminus it was necessary to introduce a linker, since direct thiourea bond formation at the N-terminus is not stable under the peptide deprotection conditions. The tris(t-butyl) ester of DOTA was used to couple the chelate as a monoamide to either the C- or N-terminus. After removal of the t-butyl protecting groups, either gadolinium(III) or copper(II) was introduced. The probes are denoted Fl-NPep-Gd, etc where Fl is fluorescein, Gd is GdDOTA-monoamide, Cu is CuDOTA-monoamide, and NPep refers to the peptide; in the example Fl-NPep-Gd, the fluorescein is conjugated to the N-terminus. Full synthetic details are described in the supporting information.

Binding of the probes to human fibrin was assessed in a plate-based assay as previously described.10,14 In this assay, a fibrinogen solution is aliquoted into a 96-well plate and then polymerized to fibrin by addition of CaCl2 and thrombin. The fibrin gel is then dried onto the base of the plate by evaporation at 37 °C. Rehydration with an equivalent volume of liquid results in a known concentration of polymeric fibrin based on fibrinogen monomer. Solutions of Gd-NPep-Fl, Cu-NPep-Fl and Fl-NPep-Gd ranging from 0.1 to 50 μM in either tris buffered saline (TBS) or citrated rat plasma were added to each of the wells of a dried fibrin (7 μM) microtiter plate. After 2 h incubation, the concentration of free probe, [free], was assayed by ICP-MS or by fluorescence-HPLC. The concentration of fibrin-bound species, [bound], in the clot was determined by subtraction ([bound] = [total] – [free]). The binding data were fit to a stoichiometric binding model with stepwise association constants K1, K2 and K3 (Figure S1). The affinities of Gd-NPep-Fl and Fl-NPep-Gd for human fibrin (Table 1) were similar and comparable to EP-2104R. Not surprisingly, replacement of Gd(III) with Cu(II) did not significantly change the fibrin affinity of the probe.

Table 1
Fibrin Association Constants

One concern with using organic fluorophores for in vivo applications is the potential for non-specific binding of the hydrophobic fluorophore. Non-specific protein binding would adversely impact the distribution of the probe and its specificity for fibrin in vivo. In our previous work with this type of peptide, we found that peptide derivatives bind to two equivalent binding sites on fibrin.10,14 When fluorescein is incorporated into the molecule, there is a third, weaker fibrin binding event that we attribute to a non-specific interaction. We were concerned that non-specific binding to other proteins could lower the effective affinity of the probe for fibrin, and so we measured fibrin affinity in the presence of blood plasma proteins. However the apparent fibrin affinity of Gd-NPep-Fl measured in rat plasma was only 2–3 fold lower than when measured in buffer (Table 1), indicating that this probe maintains high specificity for fibrin.

Relaxivities of the Gd-containing probes as well as the commercial contrast agent [Gd(HP-DO3A)(H2O)] (Pro-Hance®, gadoteridol) were measured at 1.4T, 37 °C in either pH 7.4 TBS, 30 μM fibrinogen solution in TBS, or 30 μM fibrin gel in TBS (Table 2). The relaxivities in TBS are much higher than for small Gd(III) complexes such as [Gd(HP-DO3A)(H2O)], and this relaxivity increase is due to the increased molecular weight resulting in slower rotational diffusion. Protein binding further decreases the correlation time and results in increased relaxivity.27 This is reflected by the 50% higher relaxivity of Fl-NPep-Gd in fibrin gel compared to buffer alone. On the other hand there is little to no increase in relaxivity observed in fibrinogen solution implying that these probes do not bind fibrinogen as was seen previously with this peptide sequence. The lack of fibrinogen binding is important since there is ~7 μM fibrinogen in circulating blood plasma. The specificity of the probes for fibrin over the structurally similar fibrinogen precursor may be expected to enhance target:background in vivo. In addition, there was no change in the relaxivity of [Gd(HP-DO3A)(H2O)] when measured in TBS, fgn, or fibrin gel suggesting no protein binding, and indicating that the mechanical properties of the gel do not affect relaxivity. We note that the relaxivities for the probes in the presence of fibrin are quite high (21.2 mM−1s−1 for Gd-NPep-Fl and 18.8 Fl-NPep-Gd) at this clinically relevant field strength and comparable to other high relaxivity compounds such as fibrin-bound EP-2104R and albumin-bound MS-325 at 1.4T.14,28 Relaxivity will decrease with increasing field strength but based on the field dependence of the related molecules,29 we expect higher relaxivity than simple Gd(III) chelates at fields up to 9.4T.

Table 2
Relaxivity of Gd-containing Probes

The relaxivity results were corroborated by imaging studies on a clinical 1.5T MRI scanner. Here we compare the commercial contrast agent [Gd(HP-DO3A)(H2O)] with equimolar Gd-NPep-Fl. Figure 1 shows T1-weighted MR images of 6 tubes containing water, fibrinogen solution, or fibrinogen solution that has been polymerized to fibrin gel and then separated by mechanical agitation. Tubes A and B contain no gadolinium and represent the baseline signal intensity. Tubes C and D contain 25 μM [Gd(HP-DO3A)(H2O)] in fibrinogen or fibrin gel, respectively. There is a slight enhancement in signal (16.5%) compared to tube B due to the dilute, low relaxivity contrast agent. However the enhancement is uniform in both C and D, indicating that [Gd(HP-DO3A)(H2O)] cannot distinguish the fibrin clot on the wall of tube D from the unclotted solution. Tube E shows equimolar Gd-NPep-Fl in fibrinogen solution and the signal enhancement (59% compared to tube B) is much greater than [Gd(HP-DO3A)(H2O)] due to the higher relaxivity of Gd-NPep-Fl. Tube F shows that when a fibrin clot is prepared and separated, that Gd-NPep-Fl localizes in the clot and generates high clot signal intensity (156% increased compared to tube B) and strong contrast between the clot and the supernatant with a very high contrast to noise ratio of 39.

Figure 1
MR Imaging of Fibrinogen (fgn) and Fibrin Clots

We performed a similar experiment using a IVIS fluorescence spectrum imager. Figure 2 compares 50 nM Gd-NPep-Fl to equimolar fluorescein in either fibrinogen solution or in a separated fibrin clot. In this study, fibrinogen was clotted (Tubes B and C) and the tubes were centrifuged to separate the clot from the supernatant as apparent from the photograph of the tubes (Figure 2, top). The fluorescence image overlayed on the photograph clearly shows that Gd-NPep-Fl localizes in the clot and is depleted from the supernatant whereas untargeted fluorescein is evenly distributed between the clot and the supernatant. In Figure 2E we show a fluorescence confocal microscopy image of a fibrin gel in the presence of Gd-NPep-Fl. The probe highlights the web-like fibrin mesh at the microscopic level.

Figure 2
Fluorescence Images of Fibrinogen (fgn) and Fibrin Clots

Finally we compared the Cu-64 versions of both probes to 64CuDOTA in a similar experimental paradigm, using PET imaging on a clinical PET scanner. The images in Figure 3 demonstrate that the dual probes can visualize fibrin with PET imaging. For the fibrinogen solutions (Figure 3A, 3C, 3E), the 64Cu is distributed equally throughout the samples giving rise to uniform signal intensity. When the fibrinogen is clotted and the tube spun down (tube B), there was no difference in the PET image between tubes A and B indicating that untargeted 64CuDOTA cannot be used to detect fibrin. The 64CuDOTA is distributed equally in the clot, at the bottom of tube B, and in the liquid above the clot. The 64CuDOTA experiment also demonstrates that clot formation does not physically trap the molecule. On the other hand, the fibrin-targeted dual probes both demonstrate an ability to detect fibrin. Tubes D and F indicate that radioactivity is centered in the bottom of each tube, i.e. in the clot, and very little activity remains in the liquid above the clot.

Figure 3
PET Imaging of Fibrin Clots

In conclusion, we have described four new fibrin-targeting probes that can be modified to be detectable in multiple modalities and still maintain fibrin affinity and specificity. These bimodal probes offer the opportunity for fibrin imaging over a range of spatial resolutions (OI > MRI > PET) and detection sensitivities (PET > OI > MRI). This proof-of-concept study utilized inexpensive reagents; however our mixed solid/solution phase synthesis is generalizable and amenable to incorporating any bifunctional chelator or fluorophore using standard amine bioconjugation techniques. Combinations of labels may have important applications where high sensitivity, low resolution PET imaging can detect the presence of thrombus throughout the body and then be used to guide where high resolution MR or catheter-based optical imaging should be performed. For instance, one such clinical application could be to detect the presence of coronary artery thrombus and guide stent placement.

Supplementary Material

1_si_001

Acknowledgments

Thomas Benner and Zdravka Medarova are thanked for assistance in the MR and fluorescence imaging studies. This work was supported in part by awards R01HL109448, R01EB009062, T32CA009502, and P41RR14075 from the National Institutes of Health. P.C. has equity in Factor 1A, LLC, the company which holds the patent rights to the peptides used in these probes.

Footnotes

Supporting Information Available: Experimental procedures, probe synthesis and characterization, details of fibrin binding, relaxivity, and imaging measurements are provided in supporting information. This material is available free of charge via the internet at http://pubs.acs.org.

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