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Theranostic nanoparticles offer the potential for mixing and matching disparate diagnostic and therapeutic functionalities within a single nanoparticle for the personalized treatment of diseases. In this article, we present composite iron oxide-gadolinium-containing Prussian blue nanoparticles (Fe3O4@GdPB) as a novel theranostic agent for T1-weighted magnetic resonance imaging (MRI) and photothermal therapy (PTT) of tumors. These particles combine the well-described properties and safety profiles of the constituent Fe3O4 nanoparticles and gadolinium-containing Prussian blue nanoparticles. The Fe3O4@GdPB nanoparticles function both as effective MRI contrast agents and PTT agents as determined by characterizing studies performed in vitro and retain their properties in the presence of cells. Importantly, the Fe3O4@GdPB nanoparticles function as effective MRI contrast agents in vivo by increasing signal:noise ratios in T1-weighted scans of tumors and as effective PTT agents in vivo by decreasing tumor growth rates and increasing survival in an animal model of neuroblastoma. These findings demonstrate the potential of the Fe3O4@GdPB nanoparticles to function as effective theranostic agents.
Theranostics refers to the use of a diagnostic agent (Dx) in tandem with a therapeutic agent (Rx) for the personalized treatment of diseases.1 A well-known example of a commercialized theranostic is the use of HercepTest® (Agilent, Santa Clara, CA, USA) in combination with Herceptin® (Genentech, South San Francisco, CA, USA) for treating breast cancer.2 However, this approach requires the sequential administration of the paired Dx/Rx agents. A more desirable and potentially straightforward approach would be the simultaneous administration of the Dx/Rx agents to shorten procedure times while potentially improving patient comfort. Within this context, advances in the field of nanotechnology over the past few decades have facilitated the synthesis of nanoparticles with diverse and complementary diagnostic and therapeutic properties that can be incorporated within a single theranostic nanoparticle.3,4 These include iron oxide nanoparticles,5,6 carbon nanotubes,7,8 gold nanorods,9,10 dendrimers,11,12 and vesicles,13,14 of which multiple nanoparticles are already in the clinic.15,16 A key design criterion in the synthesis of theranostic nanoparticles, in addition to their complementary Dx/Rx properties, is that the component materials of the nanoparticles are biocompatible and/or safe for human use. Therefore, a compelling starting point would be to synthesize theranostic nanoparticles composed of materials with a known safety profile.
To this end, in this study, we describe the design, synthesis, and utilization of composite iron oxide-gadolinium-containing Prussian blue nanoparticles (Fe3O4@GdPB) as theranostic agents. Our Fe3O4@GdPB contain the following: Fe3O4, a US Food and Drug Administration (FDA)-approved material that has been used for T2-weighted (T2W) magnetic resonance imaging (MRI, in Combidex);16,17 Prussian blue, an FDA-approved material used in radiation poisoning treatment (as Radiogardase);18–20 and gadolinium, a key component of clinical MRI contrast agents including Magnevist and Gadovist.21,22 Earlier reports have described the synthesis of magnetic Prussian blue nanoparticles (without gadolinium) for T2W imaging combined with photothermal therapy (PTT) of tumors and gene transfection or chemotherapy combined with PTT of tumors.23–25
Building on these earlier findings, we utilize our Fe3O4@GdPB nanoparticles for magnetically guided, T1-weighted (T1W) imaging and PTT of tumors. Compared with T2W images, T1W images offer several advantages including enhanced visualization of vascular structures, key for the entry of Dx and Rx agents into tumors, and are less prone to artifacts such as those present in fluid-filled structures in particular.26 Under external magnetic guidance, T1W images offer the potential to visualize the entry of the composite Dx/Rx agents into a tumor through its vasculature in real-time, allowing for a more precise administration of PTT to targeted tumors. This approach can facilitate improved tumor treatment margins, which has implications not only for local tumor control but also in prevention of its recurrence.
In seeking to leverage these aforementioned advantages, we describe the synthesis and characterization of composite Fe3O4@GdPB nanoparticles. We determine the MRI and photothermal properties of the nanoparticles. Finally, as a proof-of-principle, we utilize the Fe3O4@GdPB nanoparticles for T1W MRI and PTT in an animal model of neuroblastoma,27,28 a prevalent solid tumor of childhood and a leading cause of cancer-related death in children.29,30 The findings of our study are crucial for further developing our composite theranostic nanoparticles for magnetically targeted, image-guided photothermal destruction of tumors.
Ultrapure water used in this study was obtained from a Milli-Q® system (MilliporeSigma; resistivity ≥17.8 MΩ cm). All chemicals were purchased from Sigma-Aldrich, and biological reagents were purchased from Thermo Fisher Scientific and used as supplied without further purification unless noted otherwise.
Fe3O4@GdPB nanoparticles were synthesized using a scheme modified from previously described studies.23–25 Briefly, coprecipitation was used to synthesize Fe3O4 nanoparticles where a 1:2 molar ratio of Fe2+:Fe3+ was added dropwise into a stirred solution of 1 M NaOH.31 The resultant black precipitate containing Fe3O4 nanoparticles was thoroughly rinsed and dispersed in ultrapure water by centrifugation (at least three times at 22,000× g for 10 minutes) and resuspension (using sonication to disperse the pellet, as needed). Next, Fe3O4 nanoparticles (diluted to 1 mg/mL) were added dropwise into a solution of K4[Fe(CN)6] (2 mM; pH =3) in a sonicator bath with continuous stirring maintained at 50°C. The above-mentioned solution was then added to a solution containing Gd(NO3)3 and FeCl3 (2 mM; pH =3) under the sonication, stirring, and heating conditions described earlier. Finally, the resultant solution containing Fe3O4@GdPb nanoparticles was rinsed and dispersed in ultrapure water as described earlier.
The size (hydrodynamic diameter) and charge (zeta potential) distributions of the Fe3O4@GdPB nanoparticles were compared with both Fe3O4 and GdPB nanoparticles (previously synthesized by us)32,33 using dynamic light scattering on a Zetasizer Nano ZS (Malvern Instruments, Malvern, UK). Multiday stability of the Fe3O4@GdPB nanoparticles in ultrapure water was assessed by measuring their hydrodynamic size distributions every 24 hours over 5 days using dynamic light scattering. The visible-near infrared (NIR) spectra of 1 mg/mL suspensions of the three different types of nanoparticles in ultrapure water were measured using a Genesys 10S Ultraviolet-Visible (UV-Vis) spectrophotometer (Thermo Fisher Scientific, Waltham, MA, USA). Transmission electron microscopy (TEM) images of the Fe3O4 and Fe3O4@GdPB nanoparticles were obtained by loading 5 µL of the nanoparticle suspensions separately onto copper grids (Electron Microscopy Sciences, Hatfield, PA, USA) using a JEOL JEM 2100 field-emission gun scanning transmission electron microscope (TEM; JEOL, Peabody, MA, USA). Analysis of the size distributions of the nanoparticles was performed using ImageJ (National Institutes of Health). Energy-dispersive X-ray spectroscopy (EDS) was performed using an INCA 250 analysis system (Oxford Instruments, Abingdon, UK) coupled to the TEM. A total of seven scans were performed on different parts of the grid and then averaged to obtain the relative percentages of Gd, Fe, and K.
The MR relaxivities of the Fe3O4@GdPB nanoparticles were measured using a clinical horizontal 3 T magnet (GE Healthcare, Chicago, IL, USA). Phantoms containing varying concentrations of the nanoparticles (Fe3O4, GdPB, and Fe3O4@GdPB) were prepared in 96-well plates in 0.5% agarose solutions. A constant temperature of 23°C was maintained for all the measurements. The phantoms were placed on a 2% solid block of agar and secured by tape at the center of an 8-channel high definition brain coil.32,34 T1 and T2 relaxation times were measured in the same coronal 0.5 mm thick slice. Inversion times (TI) were varied (from 50 to 4,000 ms) to obtain T1 measurements, while echo times (TE) were varied (from 12 to 245 ms) to obtain T2 measurements. Image processing software, OsiriX, was used to analyze the signal intensity within a region of interest (ROI) of the acquired images. To measure the T1 inversion, the signal intensity was plotted against the TI values, while signal intensity was plotted against TE values for the T2 decay curves. The data were then fitted using the following equations:
where SI is the signal intensity within the ROI, and A, B, and C are positive constants. The R1 and R2 relaxation rates were then obtained by calculating 1/T1 and 1/T2, respectively. The relaxation rates obtained were plotted against the concentrations of the corresponding contrast agent (Gd for T1W images and Fe for T2W images) and slopes of these plots yielded the relaxivities of the nanoparticles.
The photothermal properties of the Fe3O4@GdPB nanoparticles were measured using aqueous dispersions of the nanoparticles irradiated using an 808 nm NIR laser (Laserglow Technologies, Toronto, Canada), as previously described.35 The PTT capabilities of the Fe3O4@GdPB nanoparticles were measured as a function of concentration by varying the concentration of the nanoparticles from 0.01 to 0.2 mg/mL at a fixed laser fluence (power density) of 1.875 W/cm2 for 10 minutes. The PTT capabilities were measured as a function of varying laser fluence (0.625–3.125 W/cm2) by irradiating 0.1 mg/mL Fe3O4@GdPB for 10 minutes. The stability of the nanoparticles as a photothermal agent was assessed by a cyclic heating/cooling study where 1 mg/mL Fe3O4@GdPB was irradiated by the NIR laser (laser on/off times =10 minutes each). The photothermal conversion efficiency of the Fe3O4@GdPB nanoparticles was measured by first heating 0.1 mg/mL of the nanoparticles with the NIR laser at a fluence of 1.875 W/cm2 for 10 minutes. The laser was then turned off, and the cooling kinetics of the nanoparticles was measured as a function of time. The photothermal conversion efficiency was calculated using the following equation described by Roper et al.36
Where h is the heat transfer coefficient, A is the surface area of heat transfer of the system, Tmax is the maximum system temperature, Tamb is the ambient temperature, Q0 is the rate of heat input due to absorption of light energy by water, I is the incident laser power, and Aλ is the absorbance of the Fe3O4@GdPB at 808 nm.
The intrinsic and PTT-induced cytotoxicity of the Fe3O4@GdPB nanoparticles in vitro was measured using the murine neuroblastoma cell line Neuro2a (ATCC). Briefly, Neuro2a was seeded in 96-well plates and incubated with either vehicle or varying concentrations of the Fe3O4@GdPB nanoparticles (0.01–0.5 mg/mL) with or without laser irradiation using the NIR laser (1.5 W/cm2; 10 minutes). Twenty-four hours after the treatment, cell viability was assessed using the CellTiter-Glo luminescent cell viability assay (Promega Corporation, Madison, WI, USA). Each treatment was conducted with at least three replicates.
All animal studies were conducted in accordance with protocols approved by the Institutional Animal Care and Use Committee (IACUC) at Children’s National Health System and were conducted to ensure humane care of the animals as per the IACUC’s guidelines. For the animal studies, 4–6-week old female A/J mice were purchased from Jackson Laboratory, and the animals were acclimated for 3–4 days prior to commencing the studies.
To establish the murine neuroblastoma model, one million Neuro2a cells suspended in phosphate-buffered saline were injected subcutaneously into the shaved backs of 4–6-week old female A/J mice. Tumor growth was monitored by routine caliper measurements, as previously described.35,37 All treatments commenced only after the Neuro2a tumors reached a diameter of at least 5 mm (~60 mm3). Tumor-bearing mice were divided into three groups (n≥9 mice/group): 1) untreated group: receiving no further treatment, 2) Fe3O4@GdPB group: receiving 100 µL of 1 mg/mL Fe3O4@GdPB by tail vein injection, and 3) Fe3O4@GdPB + magnet group: receiving 100 µL of 1 mg/mL Fe3O4@GdPB by tail vein injection followed by application of an external magnetic field for 10 minutes; by externally affixing a 3,000 Gauss magnet (0.25″×0.25″×0.25″ Nickel-plated neodymium; K&J Magnetics Inc, Pipersville, PA, USA) to the surface of the tumors for mice in this group. After this step, the mice in each group were divided into two cohorts (n≥4 mice/cohort). Mice in cohort 1 were used for MRI. These mice were immediately euthanized after the aforementioned procedures and their tumors extracted. Tumor phantoms were prepared using 5% agarose solutions and T1W images of these tumors were acquired and analyzed as described earlier. Mice in cohort 2 were used for PTT. These mice were irradiated after completing application of the external magnet with the NIR laser (1.5 W/cm2; 15 minutes). The tumor surface temperature achieved during the laser treatment step was measured using an i7 thermal camera (FLIR, Wilsonville, OR, USA). Post-PTT, tumor growth, and animal survival were monitored.
Statistically significant differences between groups were determined by using a Student’s t-test. The log-rank test was used to determine statistically significant differences in survival, analyzed by generating Kaplan–Meier plots. A P-value of <0.05 was considered statistically significant in all studies (denoted by *).
The Fe3O4@GdPB nanoparticles were synthesized by growing a “shell” of gadolinium-containing Prussian blue on an iron oxide nanoparticle “core” by modifying previously published schemes for synthesizing magnetic Prussian blue nanoparticles (without gadolinium).23–25 This synthesis relies on the attachment of Fe(CN6)4− onto the surface of iron oxide nanoparticles at an acidic pH (refer “Materials and methods” section for details), and the subsequent growth of a GdPB shell by the reaction of Fe(CN6)4−, Fe3+, and Gd3+ on the surface of the iron oxide nanoparticles. To determine the properties of the Fe3O4@GdPB nanoparticles synthesized using the presented two-step scheme (Figure 1A), we first measured the size distributions and charges of the nanoparticles using dynamic light scattering. The synthesis yielded monodisperse Fe3O4@GdPB nanoparticles (polydispersity index ~0.2) with a mean hydrodynamic diameter of 164.2 nm, which was higher than the mean hydrodynamic diameters of the constituent Fe3O4 (68 nm) and GdPB (91 nm) nanoparticles (Figure 1B). Zeta potential measurements revealed that the Fe3O4@GdPB nanoparticles exhibited charges (−16.5 mV) intermediate to those of the constituent Fe3O4 (−13.3 mV) and GdPB (−24.8 mV) nanoparticles (Figure 1C). Multiday stability studies using dynamic light scattering demonstrated that aqueous suspensions of the Fe3O4@GdPB nanoparticles retained nearly constant size distributions over 5 days (Figure 1D). Visible-NIR spectroscopy of equal concentrations (1 mg/mL each) of Fe3O4, GdPB, and Fe3O4@GdPB nanoparticles demonstrated that Fe3O4@GdPB retained the characteristic absorption band of Prussian blue-based nanoparticles (GdPB) in the 600–900 nm range and, as expected, demonstrated an attenuated absorption band relative to GdPB (Figure 1E). TEM images illustrated individual Fe3O4@GdPB nanoparticles (Figure 2A) with a size range of 28.2±8.3 nm, representing an increase in size from the Fe3O4 core nanoparticles (without GdPB) that had a size range of 8.0±2.2 nm (Figure S1). EDS scans conducted on seven different areas of the TEM grid revealed that the analyzed nanoparticles comprised both Fe and Gd (Figure 2B). Taken together, these findings demonstrate that our synthesis scheme results in stable Fe3O4@GdPB nanoparticles with properties that are a composite of the constituent Fe3O4 and GdPB nanoparticles.
To determine if the Fe3O4@GdPB nanoparticles function as effective MRI contrast agents, we conducted scans of phantoms containing serial dilutions of Fe3O4@GdPB and the constituent Fe3O4 and GdPB nanoparticles in a clinical 3 T MRI magnet. T1W scans demonstrated that the Fe3O4@GdPB nanoparticles generated increased contrast in a concentration-dependent manner (Figure 3A), ie, increased brightening at increased concentrations, similar to GdPB nanoparticles (previously characterized by us and others).32,38,39 Similarly, T2W scans demonstrated that the Fe3O4@GdPB nanoparticles generated increased contrast in a concentration-dependent manner (Figure 3B), ie, increased darkening with increasing concentrations, similar to Fe3O4 nanoparticles, which have been well-described in the literature.5,6 Based on image processing of multiple T1W and T2W scans, we generated relaxation time plots as a function of the contrast agent, namely Gd3+ ions for GdPB (Figure 3C) and Fe3O4@GdPB (Figure 3D), and Fe for Fe3O4 (Figure 3E) and Fe3O4@GdPB (Figure 3F). These studies yielded the r1 and r2 relaxivities (Figure 3G) of the Fe3O4@GdPB nanoparticles: r1 =5.5 mM−1 s−1 and r2 = 126 mM−1 s−1. Although the r1 value of Fe3O4@GdPB is lower than that of GdPB (38.4 mM−1 s−1), it is in a range similar to most clinically approved, gadolinium-based T1 contrast agents at a field strength of 3 T, including Magnevist (3.1 mM−1 s−1), ProHance (2.8 mM−1 s−1), and Omniscan (3.2 mM−1 s−1).22 Additionally, a unique feature to our Fe3O4@GdPB is that they can be guided to a particular anatomical location by an external magnetic field, which cannot be achieved using GdPB nanoparticles that have to rely on vasculature for anatomical targeting. If improved contrast in T1W images is desired, the synthesis of Fe3O4@GdPB can be appropriately modified to incorporate a larger shell of GdPB with increased loading of Gd3+ ions during synthesis over a smaller core of Fe3O4. These results suggest that Fe3O4@GdPB can function as an effective MRI contrast agent in T1W scans. In parallel with these studies, we analyzed the T2 relaxivities of Fe3O4@GdPB nanoparticles and obtained an r2 value of 126 mM−1 s−1 at a 3 T field strength. Although we do not explicitly utilize the T2 contrast of our Fe3O4@GdPB nanoparticles in this study, since the proposed use of our nanoparticles is for PTT of tumors and we have previously discussed the limitations of using T2W images especially for fluid-filled structures, our results demonstrate that there may be future potential of these agents as contrast agents in T2W imaging applications.
To quantify the photothermal heating properties of Fe3O4@GdPB nanoparticles, we measured their heating as a function of concentration, laser fluence, and multiple cycles of heating and cooling. At a constant laser fluence of 1.875 W/cm2, the nanoparticles were observed to heat to significantly higher temperatures over the background (water; Figure 4A) with changes in temperature approaching 20°C at a nanoparticle concentration of 0.01 mg/mL and ~35°C at nanoparticle concentrations ≥0.05 mg/mL. At a constant nanoparticle concentration of 1 mg/mL, Fe3O4@GdPB was observed to heat to higher temperatures in a laser fluence-dependent manner (Figure 4B). Additionally, the nanoparticles retained their photothermal heating properties over four cycles of heating and cooling (Figure 4C) indicating their stability as photothermal agents over multiple heating cycles. Finally, studies conducted to calculate the photothermal conversion efficiency (Figure 4D) demonstrated that the nanoparticles had a photothermal conversion efficiency of 16.1%, which is consistent with the previously determined photothermal conversion efficiency of Prussian blue nanoparticles (around 20%)35 despite the fact that Fe3O4@GdPB nanoparticles are a composite of both Fe3O4 and GdPB. These results demonstrate that Fe3O4@GdPB nanoparticles are stable and effective PTT agents.
To assess the intrinsic cytotoxicity of our Fe3O4@GdPB nanoparticles as well as test whether they can function as effective PTT agents in the presence of cells, we added varying concentrations (0.01–0.5 mg/mL) of the nanoparticles to Neuro2a cells (which will be used in our animal studies) in vitro, with and without laser irradiation (Figure 5). Our studies demonstrated that Fe3O4@GdPB nanoparticles exhibit marginal intrinsic toxicity (in the absence of NIR laser irradiation) to Neuro2a cells at concentrations ≥0.1 mg/mL. Neuro2a cell viability was slightly decreased to ~80% of the vehicle-treated controls at these concentrations, suggesting that the nanoparticles can be safely used for PTT of cells without intrinsic cytotoxicity at concentrations lower than 0.1 mg/mL. Upon irradiation with the NIR laser, the Fe3O4@GdPB nanoparticles generated significantly increased cytotoxicity to Neuro2a cells with cell viability decreasing to <60% of controls at nanoparticle concentrations ≥0.1 mg/mL (under the experimental conditions). At a Fe3O4@GdPB concentration of 0.5 mg/mL, cell viability was observed to decrease 3.5-fold to around 25% upon irradiation compared to 80% viability in the absence of the laser. Together, these results establish the concentrations at which Fe3O4@GdPB nanoparticles do not exhibit intrinsic cytotoxicity as well as demonstrate that the nanoparticles retain their PTT properties in the presence of targeted cells.
As a step toward evaluating the efficacy of the Fe3O4@GdPB nanoparticles as effective theranostic agents in vivo, we tested the ability of the nanoparticles to function as MRI contrast agents in an animal model of neuroblastoma. Specifically, mice bearing palpable subcutaneous Neuro2a tumors (average tumor size ≥5 mm) were divided into three groups (n=5/group): 1) untreated: receiving no further treatment, 2) Fe3O4@GdPB-treated: tumor-bearing mice were tail-vein injected with the nanoparticles, and 3) Fe3O4@GdPB + magnet-treated: tumor-bearing mice were tail-vein injected with the nanoparticles and an external magnetic field was applied over the tumor for 10 minutes to direct the circulating nanoparticles into the tumor. T1W scans (Figure 6) of extracted tumor phantoms demonstrated that tumors extracted from the Fe3O4@GdPB + magnet-treated group exhibited increased contrast, ie, increased signal:noise ratios relative to tumors extracted from the untreated group and Fe3O4@GdPB-treated groups (Figure 6A). Tumors (Figure 6B) from the Fe3O4@GdPB + magnet-treated group exhibited an average signal:noise ratio of around 3.2, which was significantly higher (P<0.05) than tumors from the untreated group (~1.84) and Fe3O4@GdPB-treated (~2) groups. Although further T1W imaging studies in a live tumor-bearing animal are needed, these ex vivo studies demonstrate that Fe3O4@GdPB nanoparticles can function as effective contrast agents for T1W imaging of tumors in the presence of external magnetic guidance. Our studies represent an important first step toward achieving this important end goal of T1W resolution of tumors.
Complementary to the T1W imaging studies, we conducted studies assessing the PTT properties of the Fe3O4@GdPB nanoparticles in the Neuro2a mouse model of neuroblastoma. Neuro2a tumor-bearing mice (average tumor size ≥5 mm) were divided into three groups (n=5/group): 1) untreated: receiving no further treatment, 2) Fe3O4@GdPB-treated: where tumor-bearing mice were tail-vein injected with the nanoparticles, and 3) Fe3O4@GdPB + magnet-treated: where tumor-bearing mice were tail-vein injected with the nanoparticles, and an external magnetic field was applied over the tumor for 10 minutes to direct the circulating nanoparticles into the tumor. Shortly after application of the external magnet, tumors of mice in the Fe3O4@GdPB-treated group and Fe3O4@GdPB + magnet-treated group were irradiated with the NIR laser (Figure 7). Tumor surface temperatures as measured by infrared thermometry demonstrated that mice in the Fe3O4@GdPB + magnet-treated group achieved an average tumor surface temperature of 52°C after 10 minutes of irradiation, which was marginally higher than the tumor surface temperature of 50°C achieved in the Fe3O4@GdPB-treated group (Figure 7A). Furthermore, both groups achieved tumor surface temperatures that were on average >20°C above the initial tumor surface temperatures (~25°C). Our observations of significantly elevated temperatures over basal temperatures even in the Fe3O4@GdPB-treated group are not unexpected given that our previous studies in the same Neuro2a model have demonstrated that NIR irradiation of tumors even in the absence of PTT agents can elevate tumor surface temperatures by 5°C–10°C.35 Additionally, when using nanoparticle-based PTT agents particularly at short time intervals after tail-vein injection (ie, <1 h), further heating is caused by nanoparticles circulating through tumor vasculature that are irradiated by the laser (intravascular heating). The addition of magnet concentrates a larger amount of nanoparticles within the tumors, which accounts for the heating observed in the Fe3O4@GdPB + magnet-treated group above the Fe3O4@GdPB-treated. Strategies that can be employed to increase the temperature elevation achieved in the Fe3O4@GdPB + magnet-treated group over the Fe3O4@GdPB-treated group are to apply the external magnet for longer periods of time, or wait until the majority of the nanoparticles are cleared from circulation (typically 1–2 hours, unless the nanoparticles are specifically designed for longer circulation times).
Kaplan–Meier survival plots demonstrated that mice in both the Fe3O4@GdPB-treated group and Fe3O4@GdPB + magnet-treated group exhibited significantly higher survival than the mice in the untreated group as determined by a log-rank test (P<0.05; Figure 7B). Mice in the Fe3O4@GdPB + magnet-treated group exhibited marginally increased survival as compared to mice in the Fe3O4@GdPB-treated group although this was not statistically significant. Further optimization studies with increased power, ie, increased number of mice per group, are required to completely characterize the observed PTT effects and their implications for animal survival. Finally, tumor growth curves demonstrate that PTT applied in both the Fe3O4@GdPB-treated and Fe3O4@GdPB + magnet-treated groups causes slower tumor progression as evidenced by the lower tumor growth curve slopes relative to mice in the untreated group. Once again, tumor growth in the Fe3O4@GdPB + magnet-treated group appeared to be marginally slower than in mice in the Fe3O4@GdPB-treated group but this was not observed to be statistically significant. Taken together, our findings suggest that Fe3O4@GdPB nanoparticles function as effective PTT agents resulting in slower tumor growth rates and increased survival relative to untreated mice although further studies are needed to identify the optimal modes for applying the external magnet and NIR laser.
We have presented Fe3O4@GdPB nanoparticles as effective theranostic agents, particularly for T1W imaging and PTT of tumors. Our facile synthesis scheme resulted in stable Fe3O4@GdPB nanoparticles that exhibited composite properties of both the Fe3O4 and GdPB (Figures 1 and and2).2). The nanoparticles possessed the ability to function as effective contrast agents in both T1W and T2W scans (Figure 3) as well as effective PTT agents (Figure 4). The Fe3O4@GdPB nanoparticles generated cytotoxicity of targeted Neuro2a cells upon laser irradiation in vitro (Figure 5). Ex vivo imaging studies demonstrated that the nanoparticles increased signal:noise ratios in T1W scans of tumor phantoms relative to controls (Figure 6). Finally, the nanoparticles functioned as effective PTT agents in vivo by decreasing tumor growth rate and increasing survival relative to untreated controls (Figure 7). Our findings demonstrate the theranostic utility of our Fe3O4@GdPB nanoparticles and represent an important prelude to their eventual preclinical to clinical translation in treating cancer.
Representative TEM images of (A) Fe3O4 and (B) Fe3O4@GdPB nanoparticles as synthesized.
Note: The nanoparticles size analysis was performed using ImageJ by manually measuring the size of the individual nanoparticles from the TEM images, which yielded a mean particle diameter of 8.0±2.2 nm for Fe3O4 and 28.2±8.3 nm for Fe3O4@GdPB.
Abbreviations: Fe3O4@GdPB, composite iron oxide-gadolinium-containing Prussian blue; TEM, transmission electron microscopy.
This work was supported by a Research Advisory Council award from the Sheikh Zayed Institute for Pediatric Surgical Innovation and a Pilot Studies Award from the Joseph E Robert Jr. Endowment Awards at Children’s National Health System, and funding was provided by MedImmune.
All authors contributed toward data analysis, drafting and critically revising the paper and agree to be accountable for all aspects of the work.
The authors report no conflicts of interest in this work.