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He Hu: 0000-0002-5976-5273
Nicole F. Steinmetz: 0000-0002-0130-0481
The increasing prevalence of ultra-high-field magnetic resonance imaging (UHFMRI) in biomedical research and clinical settings will improve the resolution and diagnostic accuracy of MRI scans. However, better contrast agents are needed to achieve a satisfactory signal-to-noise ratio. Here, we report the synthesis of a bimodal contrast agent prepared by loading the internal cavity of tobacco mosaic virus (TMV) nanoparticles with a dysprosium (Dy3+) complex and the near-infrared fluorescence (NIRF) dye Cy7.5. The external surface of TMV was conjugated with an Asp-Gly-Glu-Ala (DGEA) peptide via a polyethylene glycol linker to target integrin α2β1. The resulting nanoparticle (Dy-Cy7.5-TMV-DGEA) was stable and achieved a high transverse relaxivity in ultra-high-strength magnetic fields (326 and 399 mM–1 s–1 at 7 and 9.4 T, respectively). The contrast agent was also biocompatible (low cytotoxicity) and targeted PC-3 prostate cancer cells and tumors in vitro and in vivo as confirmed by bimodal NIRF imaging and T2-mapping UHFMRI. Our results show that Dy-Cy7.5-TMV-DGEA is suitable for multiscale MRI scanning from the cellular level to the whole body, particularly in the context of UHFMRI applications.
Magnetic resonance imaging (MRI) is one of the most powerful and versatile noninvasive imaging techniques and is widely used for biomedical research and clinical diagnosis. The spatial and temporal resolution of MRI increases in stronger magnetic fields (≥3.0 T) resulting in higher signal-to-noise ratios.1–3 Preclinical MRI studies in small animal models often utilize ultrahigh field strengths (≥7.0 T).2,3 The relatively low signal-to-noise ratio of normal tissues is improved using contrast agents, which selectively reduce the T1 or T2 relaxation times in the region of interest to enhance the signal.3 Contrast agents are currently used in ~35% of clinical MRI scans, but this is expected to increase as the next generation of multifunctional MRI contrast agents become more widely available.4 The efficiency of a contrast agent is determined by its r1 (1/T1) or r2 (1/T2) relaxivity (the relaxation enhancement of solvent water protons caused by the presence of the relaxation enhancer at a concentration of 1 mM) as well as the r2/r1 ratio. As the r2/r1 ratio increases, the substance becomes a more efficient T2 contrast agent and a less efficient T1 contrast agent, and vice versa.3 Whereas gadolinium-(III) ion (Gd3+)-based T1 contrast agents are efficient in low- strength magnetic fields, the longitudinal relaxivity is rapidly lost at higher field strength,5,6 declining by as much as 30%.3,5,7 T2 contrast agents such as superparamagnetic iron oxide nanoparticles (SIONPs) have many advantages in both biomedical research and preclinical applications,8 but ultrahigh magnetic fields result in aggregation, movement, and saturated magnetization obstacles that limit the ability to distinguish genuine signals from background.3,9 As ultrahigh-field scanners become more widely available, new contrast agents are required to ensure a high signal-to-noise ratio can be achieved without the limitations described above.
Unlike classic Gd3+ contrast agents, the paramagnetic dysprosium(III) ion (Dy3+) has the shortest electronic relaxation time (τe = 0.5 ps) and highest effective magnetic moment (μeff = 10.6 μB) among the lanthanide ions, affecting proton relaxivity via a Curie mechanism that primarily influences T2.10,11 The contribution of Curie relaxation increases substantially with the external magnetic field and is proportional to the square of the magnetic moment of the lanthanide ion, which results in highly efficient r2 relaxation in ultrahigh-field MRI (UHFMRI) applications. Although a small number of Dy3+ chelates (e.g., Dy3+-DTPA)12–14 and inorganic nanoparticles (e.g., Dy2O3 and NaDyF4)3,15,16 have been studied as potential T2 contrast agents, no further biological applications have been reported. Generally, nanoparticle contrast agents offer more advantages than small molecular chelates. Nanoparticles have uniform shapes and sizes and surfaces that can be functionalized to prolong circulation, target particular cells, and carry drugs or imaging agents.11 The advantages of both metal complexes and nanoparticles can be combined by optimizing the relaxivity of metal complexes confined within nanoparticles,9,10,17 such as dendrimers,18 polymers,19,20 silica,6,21 protein cages, viral nanoparticles (VNPs), or virus-like particles (VLPs).22,23
VNPs and VLPs, especially those based on plant viruses and bacteriophages, are remarkably versatile due to their high degree of symmetry, polyvalency, monodispersity, and genetic or chemical programmability.24 Using chemoselective bio-conjugation, VNPs and VLPs can be functionalized with imaging contrast agents, drugs, and/or targeting ligands such as peptides or antibodies.24 Rodlike plant viruses such as the virions of tobacco mosaic virus (TMV) are particularly versatile because the high aspect ratio shape confers superior properties. The TMV nanoparticles’ capsid comprises 2130 identical coat proteins that self-assemble into a 300 × 18 nm hollow tube with a solvent-accessible 4 nm interior channel with the viral ssRNA.25 The benefits of such rodlike particles include more effective evasion of the immune system, particularly the mononuclear phagocyte system, and more efficient margination toward the blood vessel wall to improve extravasation.26,27 TMV is biocompatible and biodegradable and does not cause infections in humans, allowing multiple nanomedical applications: for example, we have recently developed Gd(DOTA)-conjugated TMV nanoparticles for the imaging of atherosclerotic plaques22,23 and TMV carriers for the delivery of phenanthriplatin to cancer cells.28
Here, we aimed to determine whether the immobilization of Dy3+(DOTA) on the internal surface of the TMV nanotube offers an alternative strategy for the development of contrast agents with high transverse relaxivity for UHFMRI, using prostate cancer imaging as a case study. Prostate cancer is the sixth most common cancer in the world and the third most common in men, especially in Europe and North America.29–31 Among human prostate cancer cell lines, PC-3 is more aggressive and expresses higher levels of integrin α2β1 on the surface than cell lines CWR-22 and LnCap. The α2β1 integrin is a receptor for type I collagens, laminins, E-cadherin, matrix metalloproteinase 1, and several viruses,32 and its signaling activity is modulated during the initiation and progression of prostate cancer, making it an important diagnostic marker and therapeutic target. We have previously demonstrated that the peptide Asp-Gly-Glu-Ala (DGEA) can be used as a targeting ligand to visualize integrin α2β1 expression in vivo.33 Fluoromagnetic nanomaterials with multifunctional properties have recently attracted attention due to their special coupled behaviors.33 A single nanoparticle combining the high sensitivity of fluorescence and UHFMRI imaging would be suitable for multiscale scanning, from the cellular level to the whole body. Our bimodal design combines a near-infrared fluorescence (NIRF) dye and Dy3+(DOTA) loaded into the internal channel of TMV nanoparticles displaying external DGEA peptides for the targeting of prostate cancer cells. We tested the feasibility of this contrast agent for the imaging of prostate cancer cells in vitro and in vivo.
As shown in Scheme 1A, the TMV nanoparticle comprises 2130 identical coat protein subunits which self-assemble into an elongated nanotube (300 × 18 nm) with a 4 nm internal channel with the viral ssRNA. The high-resolution crystal structure of TMV highlights an internal glutamic acid residue (GLU97/106, blue) and an external tyrosine residue (TYR139, red) that can be functionalized using the well-established copper-catalyzed azide–alkyne cycloaddition (CuAAC) strategy, also known as click chemistry.23,34 The TMV nanoparticle is propagated in and isolated from Nicotiana benthamiana plants, which are inexpensive to grow and highly scalable. The internal surface is modified with alkyne handles then conjugated with the macrocyclic MRI contrast agent Dy-DOTA-azide (azido-monoamide-1,4,7,10-tetraazacyclodode-cane-N,N′,N″,N-tetraacetic acid, Figure S1) and the NIRF dye Cy7.5-azide (Scheme 1B). The external surface is modified with alkyne handles then conjugated with mPEG-azide to generate untargeted control particles (Dy-Cy7.5-TMV-mPEG) or the DGEA peptide (via a heterofunctional azide-PEG-maleimide linker) to generate targeted particles (Dy-Cy7.5-TMV-DGEA) that bind to integrin α2β1 on the surface of PC-3 prostate cancer cells (Scheme 1C).
The morphology of the particles after each modification step was observed by transmission electron microscopy (TEM) as shown in Figure 1A–C. The native TMV nanoparticles show the typical elongated nanostructures (Figure 1A). After internal and external modification, the Dy-Cy7.5-TMV-mPEG (Figure 1B) and Dy-Cy7.5-TMV-DGEA (Figure 1C) particles remained structurally sound, showing the elongated nanotube shape. The order of chemical reactions was important to ensure particle integrity and stability. Specifically, we modified the interior first and then the exterior to ensure that all contrast agents were sequestered inside the particle and to avoid particle aggregation. Size-exclusion chromatography (SEC) showed that all particles eluted at ~7.4 mL, confirming that the modification did not cause particle degradation or aggregation (Figure 1D). Successful surface modification was confirmed by denaturing sodium dodecyl sulfate polyacrylamide gel electrophoresis (SDS-PAGE) and Western blotting, using antibodies against polyethylene glycol (PEG) (Figure 1E,F). The TMV coat protein (Mr = ~17 kDa) was present in all samples. After conjugation with Cy7.5 (Mr = 767.44 Da), Dy(DOTA) (Mr = 646.16 Da), and PEG (Mr = ~2000 Da), the Dy-Cy7.5-TMV-mPEG and Dy-Cy7.5-TMV-PEG-Mal particles were represented by an additional band of ~20 kDa corresponding to the anticipated increase in mass of the coat protein monomer. Following the further conjugation of Dy-Cy7.5-TMV-PEG-Mal with the DGEA peptide (Mr = 493.4 Da), the ~20 kDa band disappeared and was replaced with a ~38 kDa band, suggesting that the preferred conformation was a dimer, perhaps reflecting the intertwining of the PEG chains.35 Western blotting confirmed that PEG was present in both the ~20 and ~39 kDa bands. Further densitometric analysis of the particles indicated ~65% coverage with mPEG, ~50% coverage with the PEG-Mal linker, and ~20% coverage with the DGEA peptide.
The density of TMV coat protein labeling with Cy7.5 and Dy(DOTA) was quantified by UV/vis spectrophotometry (Figure S2) and inductively coupled plasma optical emission spectroscopy (ICP-OES), respectively. The loading efficiency depends on the carbodiimide coupling reaction, so we loaded a smaller quantity of dye than the fluorescence quench concentration (Figure S3) combined with maximum Dy-(DOTA) loading to achieve the strongest MRI signal. We found that TMV loaded with ~380 Cy7.5 molecules and ~980 chelated Dy3+ ions, covering ~18% and ~46% of the available internal surface, respectively, satisfied our requirements.
The transverse relaxivity (r2), longitudinal relaxivity (r1), and r2/r1 ratio of the Dy-Cy7.5-TMV-mPEG nanoparticles in different magnetic fields (1.5, 7, and 9.4 T) were measured as shown in Figure 2A–C. The r2 values of the nanoparticles were 62, 326, and 399 mM–1 s–1 at 1.5, 7, and 9.4 T, respectively, which is significantly higher than alternatives such as Dy2O3 nano-particles (190 mM–1 s–1 at 7.0 T) and NaDyF4 nanoparticles (101 mM–1 s–1 at 9.4 T).3,16 The r2 relaxivity of our nanoparticles was also much higher than that of Dy3+ chelates, e.g., ~33 times higher than complexes such as Dy3+-DOTA-(Gly)3 (~12 mM–1 s–1 at 9.4 T).36 The contrast in T2-weighted MRI depends on the r2 value, and the higher the r2/r1 ratio, the more efficient the T2 contrast agent. The r2/r1 ratios of our nanoparticles were 6.7, 155, and 160 at 1.5, 7, and 9.4 T, respectively, which is much higher than commercial Feridex (r2/r1 = 22 at 3 T),37 indicating that our nanoparticles are excellent candidate T2 contrast agents for UHFMRI applications.
The diamagnetic contribution to the relaxivity is negligible for water protons, and the contact effect is transmitted through chemical bonds by scalar coupling between the unpaired electrons and the nuclear spins, which is much smaller than the dipolar and Curie contributions for the lanthanides (except Gd3+) and is thus negligible.3,10 The dipolar component is a spatial effect resulting from dipolar coupling between the spin of unpaired electrons of the lanthanide ion and nuclear spins, and is described by the Solomon–Bloembergen–Morgan (SBM) equations.38,39 The Curie component, or Curie spin relaxation, arises from the dipolar interaction of the nuclei with the thermal average of electron-spin polarization.40,41 Curie spin relaxation becomes an important contributor to water proton relaxivity when the electronic relaxation time (τ1e) of the paramagnetic ion is short enough to allow for spins to return to their thermal equilibrium before the molecule changes position, which is described as the rotational correlation time (τR). In the case of Dy3+, τ1e = ~ 0.5 ps. In other words, the lanthanide complex must be almost immobile during the interval τ1e, which can be achieved by conjugating the complex to nanoparticles.10 For example, τR = ~10–10 s in small lanthanide complexes such as Ln-DTPA, but this increases dramatically on the nanosecond scale following conjugation to nanoparticles.6 The dipolar and Curie components are therefore major contributors to the relaxivity enhancement achieved by Dy(DOTA)-modified TMV nano-particles. According to the well-established relaxivity theory, the transverse relaxivity of UHFMRI contrast agents should increase linearly with the square of the external magnetic field strength B and the static correlation time 1/Δω, where Δω is the difference between the Larmor frequency at the particle surface and at infinity.42 The transverse relaxivity is shown as a function of B2 and Δω is shown as a function of B in Figure S4A,B. The corresponding power functional relationship shows a sharp jump from intermediate (1.5 T) to ultrahigh (7 and 9.4 T) field strengths. These results confirm that the SBM effect contributes to the relaxivity of our nanoparticles in an intermediate-strength field, but the Curie component dominates the relaxivity in an ultrahigh-strength field, suggesting our nanoparticles would be ideal as UHFMRI contrast agents.
Finally, to demonstrate the feasibility of our nanoparticles for UHFMR imaging, concentration-dependent T2-mapping phantom images of the Dy-Cy7.5-TMV-mPEG water solutions were obtained at 7 and 9.4 T (Figure 2D,E). Both series of images show a clear concentration-dependent negative contrast gradient produced by the nanoparticles, confirming their suitability for UHFMRI applications.
The in vitro biocompatibility of the targeted particles (Dy-Cy7.5-TMV-DGEA) and untargeted control particles (Dy-Cy7.5-TMV-mPEG) was assessed using the methylthiazolyltetrazolium (MTT) assay in human prostate cancer cell line PC-3 (Figure 3). The viability of untreated cells was used as the blank. No significant reduction in cell viability (>95%) was observed when PC-3 cells were incubated at 37 °C with either of the nanoparticle preparations at concentrations of 0.1–0.4 mg/mL for 12 or 24 h. Notably, cell viability remained >92% even after 24 h incubation with 0.4 mg/mL of the nanoparticles, the highest concentration we tested. The low in vitro cytotoxicity of these nanoparticles suggests they are likely to be suitable for in vivo imaging.
To evaluate the feasibility of the particles for cancer cell detection by NIRF and MRI, PC-3 cells were incubated for 3 h at 37 °C with different concentrations of Dy-Cy7.5-TMV-mPEG or Dy-Cy7.5-TMV-DGEA (0.1, 0.2, 0.3, and 0.4 mg/mL) and then immobilized in agarose. A concentration-dependent NIRF signal was observed in cells treated with either the control or the targeted nanoparticles, but the signal generated by the targeted particles was higher at all concentrations, and as much as 1.5-fold higher at the maximum concentration of 0.4 mg/mL (Figure 4A,B). Similarly, a T2-mapping MRI scan revealed that the nanoparticles reduced the normalized T2 value in a concentration-dependent manner, with the targeted nanoparticles achieving a 7-fold greater effect at a concentration of 0.1 mg/mL (~20% vs ~3% reduction) and a 2-fold greater effect at a concentration of 0.4 mg/mL (~27% vs ~11% reduction) (Figure 4C,D). The amount of Dy3+ taken up by PC-3 cells per milligram of protein was quantified by ICP-OES and the Bradford protein assay, revealing a concentration-dependent range of 120–230 pmol Dy3+/mg protein for the targeted nanoparticles compared to 44–100 pmol Dy3+/mg protein for the control nanoparticles (Figure 4E). Based on the Dy3+ loading ratio of 46%, the efficiency of particle uptake was 32–57% for the targeted particles and 11–25% for the control particles. The observed 2–3-fold difference in uptake efficiency matched well with the faster T2 relaxivity, and the greater difference at lower particle concentrations emphasized the advantage of targeting ligands. Even so, the control particles still achieved relatively efficient passive uptake into cancer cells, consistent with earlier reports that elongated nanoparticles pass through cell membranes more effectively than spherical nanoparticles due to their high degree of curvature.23,26,27
We determined the binding affinity of the Dy-Cy7.5-TMV-DGEA to PC-3 cells and found that the specific binding affinity constant (Kd) of Dy-Cy7.5-TMV-DGEA to PC-3 cells lies at 71.5 nM, which is at the same rank order of that of antiprostate specific membrane antigen (PSMA) monoclonal antibody (35.6–46.5 nM) (Figure S5).43 Therefore, our Dy-Cy7.5-TMV-DGEA nanoparticles appear to bind α2β1 integrin efficiently in vitro.
Having confirmed the ability of Dy-Cy7.5-TMV-DGEA nanoparticles to target α2β1 integrin on the surface of human PC-3 prostate cancer cells in vitro, we proceeded to test their ability to target PC-3 tumors in vivo in mouse models by bimodal NIRF imaging and T2-mapping MRI. Accordingly, athymic nude mice (n = 3) with xenografted human prostate tumors were scanned before particles injection and at 1, 6, and 24 h after injection.
Quantitative NIRF imaging was carried out by measuring fluorescence intensities, defined as photons per second per centimeter squared per steradian (p/s/cm2/sr), and normalizing them to the same scale bar in the whole-body image as a function of time (Figure 5A). Maximum uptake into tumor tissue was observed 6 h postinjection, followed by gradual washing out. In contrast, rapid uptake into other tissues (such as liver and spleen) was observed after 1 h postinjection. We also detected a signal in the lymph nodes 6 h postinjection which had declined slightly by 24 h postinjection, indicating that the nanoparticles remained in circulation for a significant length of time. The enhancement of the signal in the tumor was quantified in complete tumor cross sections, using preinjection mice as background controls normalized to 100%. The signal intensity in the PC-3 tumor region had increased by ~2.5-fold (p < 0.05) 6 h postinjection (Figure 5B) and declined slightly thereafter, but remained ~2-fold (p < 0.05) higher than the control 24 h postinjection (Figure 5B). The ex vivo NIRF images (Figure 5C) clearly show the changes in fluorescence intensity between the dissected tumor and other tissues. Compared to the blank control and nontargeted nanoparticles, the targeted nanoparticles achieved a significant increase in fluorescence. The semiquantitative biodistribution data agreed with the ex vivo and in vivo NIRF images (Figure 5D).
MRI imaging was performed to determine the impact of the targeted and untargeted nanoparticles on the T2 relaxation times of local tissues. As the T2 relaxation time declines, the color of the T2 MR images changes from red to blue, as shown in the scale bar (Figure 6A), reflecting the accumulation of contrast agents. The quantitative analysis of T2 relaxation times (Figure 6B) revealed only a slight signal enhancement 1 h postinjection compared with the preinjection background, probably because only a limited number of Dy3+(DOTA)-conjugated TMV nanoparticles enter the tumor site within this short time while most remain in circulation, unlike small molecular contrast agents which usually achieve maximum signal enhancement within 1 h.9,11 Accordingly, much stronger signal enhancement was achieved by the targeted particles 6 h postinjection (~40%) compared with the control particles (~14%) and both treatment groups showed a recovery of T2 relaxation times 24 h postinjection, reflecting the biodegradation and clearance of nanoparticles from the mice. The rapid clearance of contrast agents after MRI is a desirable property, and the biodegradable, proteinaceous TMV-based particles may be advantageous in this context over synthetic and metallic contrast agents, which can persist in the body for long periods of time.44,45
Prostate cancer is typically seen as an island of low signal intensity (indicative of a shorter T2 relaxation time constant for tumor) enclosed by high signal intensity (longer T2) from surrounding benign peripheral tissue.46 However, MRI typically requires a long spin-echo time (TE) to obtain sufficient tumor-to-normal prostate contrast because of a limited relaxation time constant differential between benign and neoplastic tissue. To date, there is only a limited number of reports on quantitative MRI in vivo. In one example, the prostate-specific membrane antigen (PSMA) peptides conjugated Gd-DOTA complex was used for targeting MR imaging of prostate cancer with PC-3 tumor model.47 The results showed average 36% enhancement in R1 values in the first 40 to 60 min postinjection using targeted formulations. However, the highest contrast enhancement in the control group was approximately 24% at 20 min post injection, followed by a rapid decay in contrast enhancement. In the case of iron oxide based T2 MRI contrast agents, here using Gd-DTPA modified ultrasmall magnetic iron oxide nanoparticles for liver imaging, the results demonstrated that the signal from T1-weighted MRI was positively enhanced by 26% based on the Gd-DTPA moiety, and negatively decreased by 20% from the iron oxide nanoparticles, respectively.48 In a different study, folate-targeted super-paramagnetic iron oxide nanoparticles enabled cervical tumor imaging in a mouse model with T2-weighted MR signals decreased by 20–25%.49 In comparison, in this work, we showed that 6 h post administration of the TMV-based contrast agent, the tumor T2 value dropped by 40% using the DGEA-targeted particles, compared with only 14% decrease in the nontargeted control group. Therefore, compared to previous literature examples, our results stand out and highlight the potential of TMV as a contrast agent for UHFMRI.
The dose of our contrast agent in terms of Dy3+ ions was 5 μmol/kg, which is 200 times lower than typical T1 contrast agents (0.1 mmol/kg for Prohance, which is the most similar formulation), and 20 times lower than commercial T2 contrast agents (0.01 mmol/kg for Feridex, which is based on Fe3+ ions).50 Even so, we achieved significant contrast enhancement at these low doses, reflecting two key properties of our nanoparticles: the high r2 relaxivity (326.0 mM–1 s–1) and r2/r1 ratio (155) in ultrahigh-strength magnetic fields (7 T), and the ability of the DGEA peptide ligands to target specific cells.
To confirm the biodistribution of our nanoparticles in normal organs and tumors, the Dy3+ content was determined by ICP-OES (Figure 6C). In agreement with the in vivo MRI data, more Dy3+ accumulated in the tumors of mice treated with the targeted nanoparticles (86 ng) than those treated with the control particles (49 ng). Relatively large numbers of particles also accumulated in the liver in both treatment groups, which is expected given that nanoparticles are taken up from the circulation by the mononuclear phagocytic system. Some particles also accumulated in the lung, perhaps due to particle agglomeration caused by the adsorption of plasma proteins,21,51 but also probably due to the targeting of α2β1 integrin which is expressed in healthy lung tissue.52–54 The kidneys accumulated similar levels of Dy3+ to the tumor tissue, consistent with their role as an excretory pathway for nanoparticles. Collectively, our in vivo results confirmed that Dy-Cy7.5-TMV-DGEA particles can be used as efficient NIRF/T2-UHFMRI bimodal contrast agents for in vivo applications.
We investigated the properties of Dy3+(DOTA)/Cy7.5-conjugated TMV bimodal contrast agents and confirmed their high transverse relaxivity in ultrahigh-strength magnetic fields, which is mainly dependent on the Curie mechanism. Our systematic in vitro and in vivo studies demonstrated that the targeted Dy-Cy7.5-TMV-DGEA nanoparticles are suitable for both NIRF imaging and T2-mapping MRI in the context of prostate cancer cells, and could therefore serve as a bimodal contrast agent for both fluorescence imaging and UHFMRI. Importantly, our proof-of-principle approach confirmed that the robust molecular structure of TMV offers a versatile platform for future theranostic applications.
Wild-type TMV nanoparticles were propagated in N. benthamiana plants and isolated from plant extracts by chloroform: butanol extraction and ultracentrifugation as previously described.24 The virus concentration in plant extracts was determined by UV/vis spectrophotometry (ε260 nm = ~3.0 mLmg–1cm–1). The Dy-Cy7.5-TMV-mPEG and Dy-Cy7.5-TMV-DGEA nanoparticles were synthesized using a combination of carbodiimide coupling (targeting internal glutamic acid residues) and diazonium coupling (targeting external tyrosine side chains) to introduce alkyne ligation handles, followed by the introduction of Cy7.5 and Dy-DOTA as contrast agents and the Asp-Gly-Glu-Ala (DGEA) peptide using copper-catalyzed azide–alkyne cycloaddition (CuAAC) and thiol–maleimide Michael addition reaction chemistry (see the Supporting Information).
Particle integrity was confirmed by TEM and SEC. Bioconjugation was confirmed by SDS-PAGE and Western blotting (see the Supporting Information). The concentration of nanoparticles was determined using a standard Bradford assay followed by measuring the absorbance on a NanoDrop 2000 spectrophotometer (Thermo Fisher Scientific, Waltham, MA). The ionic relaxivity of the particles was tested at 37 °C using a Brukman Minispec mq60 relaxometer (60 MHz) and a BioSpec 70/30USR preclinical 7.0 T (300 MHz) and 9.4 T (400 MHz) MRI (Bruker Inc., Billerica, MA). The concentration of Dy3+ ions was determined by 730-ES ICP-OES (Agilent Technologies, Santa Clara, CA).
The human prostate cancer cell line PC-3 was maintained at 37 °C in a humidified 5% CO2 atmosphere. The cells were grown in RPMI-1640 medium (Corning Life Sciences, New York, NY) with 10% fetal bovine serum (Atlanta Biologicals, Flowery Branch, GA) and 1% penicillin–streptomycin (Thermo Fisher Scientific). The in vitro cytotoxicity of the nanoparticles was evaluated using the MTT cell proliferation assay (ATCC 30-1010K). We seeded 5 × 104 cells/well into a 96-well cell culture plate and incubated it as described above for 24 h. We then added different concentrations of the nanoparticles (0, 0.1, 0.2, 0.3, and 0.4 mg/mL) and incubated it for a further 12 or 24 h as above. We then added 10 μL of MTT to each well, and the plate was incubated for an additional 2–4 h until a purple precipitate became visible. We then added 100 μL/well of Detergent Reagent and incubated the contents at room temperature in the dark for 2 h before reading the OD570 absorbance on a Infinite 200 microplate reader (Tecan, Männedorf, Switzerland). The following formula was used to calculate the inhibition of cell growth:
Approximately 2 × 105 PC-3 cells were seeded per well into 24-well plates and incubated as above overnight. We then added different concentrations of the nanoparticles (0, 0.1, 0.2, 0.3, and 0.4 mg/mL, equivalent to 0, 1 × 106, 2 × 106, 3 × 106, and 4 × 106 particles/cell, diluted in PBS) and incubated for 3 h as above. The cells were then washed three times with PBS, detached with trypsin/EDTA, transferred to Falcon tubes and fixed with 25% agarose. In vivo NIRF imaging was carried out using an IVIS 200 small-animal imaging system (Xenogen, Alameda, CA). A Cy7.5 filter set was used to acquire the Cy7.5 signal. Identical illumination settings (lamp voltage, filters, f/stop, field of views, binning) were used to acquire all images, and fluorescence emission was normalized to photons per second per centimeter squared per steradian (p/s/cm2/sr). Images were acquired and analyzed using Living Image v2.5 software (Xenogen).
The in vitro MRI studies were carried out using a horizontal Biospec 7 and 9.4 T scanners equipped with a 3 cm birdcage 1H coil (Bruker, Erlangen, Germany). First, a multislice, T2 weighted imaging sequence (RARE) was used to provide location information on the cells or tumor with the following parameters:55 TE/TR = 24/3000 ms, RARE factor = 8, NAV = 1, 15 axial slices with 1.5 mm thickness, matrix size = 128 × 128, 30 × 30 mm field of view (FOV). Total acquisition time was 48 s. Next, a single slice, T2-mapping Carr–Purcell–Meiboom–Gill sequence was optimized to detect the boundary of the lesions at the xenograft site with the following parameters:56 TE = 8, 16, 24...512 ms (64 echoes), TR = 1000 ms, NAV = 2, 1.5 mm thickness, matrix size = 128 × 128, 30 × 30 mm FOV. Total acquisition time was 4 min 16 s. After imaging, the cell samples were collected and sonicated at 30% power for 30 s in ice, and the total protein content was measured using the Quick Start Bradford Protein Assay with bovine serum albumin as standard (Biorad, Hercules, CA). Next, the reset cell samples were digested with concentrated hot HNO3 and the Dy content was determined by ICP-OES as described above.
Animal experiments were performed according to IACUC-approved procedures at Case Western Reserve University. Male athymic nude mice (NCR nu/nu), obtained from Case Western Reserve University Athymic Core at 4–6 weeks of age (25–30 g), were injected subcutaneously in the right shoulder with 1 × 106 PC-3 human prostate cancer cells suspended in 100 μL RPMI medium and Matrigel (Corning Life Sciences) at a 1:1 ratio. Once established, tumors were monitored daily. The mice were analyzed when the tumors reached 80–100 mm3 (14–21 days postinjection).
Mice were anesthetized for all procedures (isoflurane 2.5%; O2 2.0 L/min), and their respiration, body temperature, and heart rate were monitored in real time. They were scanned before and 1, 6, and 24 h after the injection of 200 μL of nanoparticles in PBS through the tail vein (n = 3 for each time point, dose = 20 mg/kg).
At each time point, mice were first visualized by in vivo NIRF imaging (as described above for the in vitro experiments) and then by in vivo MRI using a 7 T system for T2-mapping studies. The parameters used for in vivo MRI are as the same as the in vitro scan. During MR imaging, mice were anesthetized by isoflurane, and their respiration rate was maintained at 70–80/min. Images were acquired before and after injection. T2 maps were statistically analyzed using in-house developed Matlab software (Natick, MA).
The tumor and major organs (brain, lung, heart, liver, spleen, and kidneys) were removed, and ex vivo fluorescence images were obtained as above. The tissues were weighed and digested in concentrated nitric acid overnight and heated to 90 °C for a further 6 h before the Dy content was determined by ICP-OES. Values are presented as means plus standard deviations for n = 3 mice per group.
This work was funded by a grant from the National Institutes of Health (R01-CA202814) to NFS. We acknowledge Dr. Andrzej S. Pitek for help with the preparation of TMV nanoparticles and Dr. Duc H. T. Le for help with western blot analysis.
The Supporting Information is available free of charge on the ACS Publications website at DOI: 10.1021/acsnano.7b04472.
Mass spectrometry, absorption and NIRF emission spectrum, Job curve of the fluorescence intensity of Cy7.5 vs concentration, binding affinity (Kd), comparison of r1,2 relaxivity of Dy3+-based nanoparticles, relationship of r2 as a function of the square of magnetic field (B2) (PDF)
The authors declare no competing financial interest.