Functionalized rare earth-doped nanoparticles for breast cancer nanodiagnostic using fluorescence and CT imaging
Breast cancer is the second leading cause of cancer death among women and represents 14% of death in women around the world. The standard diagnosis method for breast tumor is mammography, which is often related with false-negative results leading to therapeutic delays and contributing indirectly to the development of metastasis. Therefore, the development of new tools that can detect breast cancer is an urgent need to reduce mortality in women. Here, we have developed Gd2O3:Eu3+ nanoparticles functionalized with folic acid (FA), for breast cancer detection.
Gd2O3:Eu3+ nanoparticles were synthesized by sucrose assisted combustion synthesis and functionalized with FA using EDC-NHS coupling. The FA-conjugated Gd2O3:Eu3+ nanoparticles exhibit strong red emission at 613 nm with a quantum yield of ~ 35%. In vitro cytotoxicity studies demonstrated that the nanoparticles had a negligible cytotoxic effect on normal 293T and T-47D breast cancer cells. Cellular uptake analysis showed significantly higher internalization of FA-conjugated RE nanoparticles into T-47D cells (Folr hi ) compared to MDA-MB-231 breast cancer cells (Folr lo ). In vivo confocal and CT imaging studies indicated that FA-conjugated Gd2O3:Eu3+ nanoparticles accumulated more efficiently in T-47D tumor xenograft compared to the MDA-MB-231 tumor. Moreover, we found that FA-conjugated Gd2O3:Eu3+ nanoparticles were well tolerated at high doses (300 mg/kg) in CD1 mice after an intravenous injection. Thus, FA-conjugated Gd2O3:Eu3+ nanoparticles have great potential to detect breast cancer.
Our findings provide significant evidence that could permit the future clinical application of FA-conjugated Gd2O3:Eu3+ nanoparticles alone or in combination with the current detection methods to increase its sensitivity and precision.
KeywordsBreast cancer Cancer detection Luminescent nanoparticles Folate receptor
Nanoparticles have emerged as potential tools for the diagnosis and treatment of cancer due to their selective accumulation in cancer tissue via enhanced permeation and retention (EPR) effect . Due to the potential benefits of nanoparticles in cancer, various multimodality nanoparticle platforms have been developed for cancer imaging using computed tomography (CT), positron emission tomography (PET), and single-photon emission computed tomography (SPECT) [2, 3, 4]. However, due to the lack of spatial resolution and low sensitivity, most of these imaging techniques fail to detect cancer at an early stage [5, 6]. Therefore, a more sensitive dual imaging probe is needed for early cancer diagnosis that can complement clinically approved modality such as CT. On the other hand, fluorescent imaging is emerging as a powerful method to detect cancer at an early stage of the disease due to its high resolution (0.5–3 µm) and sensitivity [7, 8]. Besides fluorescence imaging is a versatile tool for biomedical imaging, therefore there is an increased demand for luminescent materials. Various luminescent nanoparticles have been developed for cancer imaging including quantum dots (QD) and inorganic nanoparticles functionalized with organic dyes [9, 10]. However, toxicity issues associated to QD and photobleaching of organic dyes limit their clinical applications [11, 12]. In contrast, rare-earth (RE) doped nanoparticles are of interest for in vivo imaging due to various advantages such as low cytotoxicity, high quantum yield, longer lifetime, narrow emission lines, large Stokes shifts, photo-stability and high chemical stability [13, 14]. Therefore, RE-doped luminescent nanoparticles have great potential as a biomarker tool for biomedical purposes.
Synthesis of various Eu3+:RE2O3 luminescent nanomaterials using Y, La or Gd as RE element has been reported [15, 16, 17]. Among them nanoparticles with Gd2O3 are of great interest due to its low phonon energy , proton relaxation  and scintillation  properties making it an excellent candidate for fluorescence imaging, MRI and X-ray CT, respectively. These Eu3+ doped Gd2O3 nanoparticles with different sizes and morphologies have been utilized in a variety of applications such as in optical displays, solar cells and in vivo imaging [21, 22, 23].
Physicochemical properties such as size and shape of the nanoparticles are very important for passive targeting of tumor vasculature through EPR effect. Studies elucidating the behavior of nanoparticle size, shape and surface charge on bio-distribution and biocompatibility in vivo are present in the literature [24, 25]. There are now various evidence that specificity and efficiency of passively targeted nanoparticle can be enhanced by surface modification with a specific targeting ligand [26, 27]. Therefore, for in vivo application introduction of surface modification is preferable for improving the dispersion properties and targeting potential .
Folate receptor alpha (FR) is highly expressed in some forms of cancers such as ovarian cancer and in up to 80% of breast cancer tumors . Therefore, the addition of folic acid molecule has been used to increase the specificity of nanoparticles or drugs for cancer cells. The strong affinity of FR for its ligand folate, permit the internalization via receptor-mediated endocytosis and specific uptake FA-functionalized nanoparticles [30, 31, 32]. Hence, folic acid represents an important ligand that could be used clinically for specific targeting of breast cancer. A variety of RE-doped nanoparticles has been proposed for targeted cancer cell imaging. For instance, Setua et al.  reported higher cellular uptake of FA conjugated fluorescent magnetic RE nanocrystals on FR positive human nasopharyngeal carcinoma cells (KB) compared to FR depressed KB and FR negative lung cancer cells A549 control cells. Stefanakis and Ghanotakis  demonstrated specific targeting of HeLa cells using Tb2(OH)5NO3-FA nanoparticles doped with Europium.
In this study, Gd2O3:Eu3+ nanoparticles were produced using sucrose combustion synthesis. Gd2O3:Eu3+ nanoparticles (N1-Bare) were then coated with amino-silane coupling agent APTMS to introduce amine groups (N2-APTMS). Finally, these amine groups were conjugated to the carboxyl groups of FA molecule using EDC-NHS coupling mechanism to produce FA-functionalized Gd2O3:Eu3+ nanoparticles (N3-FA). We examined the biocompatibility and potential of folic acid-functionalized Gd2O3:Eu3+ nanoparticles to target breast cancer cells in vitro and in vivo using a xenograft model by dual-modal fluorescence and CT imaging. The targeting ability and toxicity of these folic acid-functionalized Gd2O3:Eu3+ nanoparticles is compared with N1-Bare and/or N2-APTMS. Our findings suggest that folic acid-functionalized Gd2O3:Eu3+ nanoparticles are promising candidates for the detection of breast cancer.
Gadolinium nitrate (Gd (NO3)2·6H2O, 99.9%) and europium nitrate (Eu (NO3)2·6H2O, 99.9%) were purchased from Aldrich and Alfa Aesar, respectively. Sucrose (C12H22O11, 99.5%), 3-aminopropyltrimethoxysilane (APTMS, 97%), toluene (ACS grade, ≥ 99.5%), folic acid (≥ 97%), N-(2-dimethylaminopropyl)-N-ethylcarbodiimide hydrochloride (EDC), N-hydroxysuccinimide (NHS, 98%), dimethyl sulfoxide (DMSO, ≥ 99.5%), KBr (FTIR grade, 99%) were purchased from Sigma-Aldrich.
Synthesis of Gd2O3:Eu3+ nanoparticles (Gd/Eu = 0.95/0.05) (N1-Bare)
Gd2O3:Eu3+ nanoparticles were synthesized by sucrose combustion synthesis as previously reported . Stoichiometric amounts of the metal precursors and fuels were weighed and mixed with 30 ml of distilled water under magnetic stirring for 25 min at room temperature. The obtained transparent solution was transferred to a preheated muffle furnace maintained at 380 °C. The solution was kept inside the furnace for 25 min for the complete decomposition of fuel. The synthesis was completed with the ignition of the fuel. The obtained highly porous black powder was gently crushed with a pestle and mortar. Finally, the powder was annealed at 1000 °C for 3 h to obtain a white nanocrystalline Gd2O3:Eu3+ powder.
Synthesis of Gd2O3:Eu3+@ APTMS nanoparticles (N2-APTMS)
Freshly prepared Gd2O3:Eu3+ nanoparticles were dispersed in 80 ml of toluene with the help of probe sonication. After 30 min, APTMS was introduced in an equimolar ratio with Gd2O3:Eu3+ nanoparticles and placed under magnetic stirring, during 20 h, for efficient grafting of silane layer. The temperature of the reaction was then increased to 80 °C for 4 h for the formation of solid bonds between nanoparticle surface and silane groups. The nanoparticles were washed 4 times with ethanol and centrifuged at 6000 rpm for 15 min and dried at 65 °C overnight.
Synthesis of folic acid-functionalized Gd2O3:Eu3+ nanoparticles (N3-FA)
For the surface functionalization with FA, 0.05 M folic acid was prepared in DMSO under magnetic stirring. For the activation of carboxyl groups present in FA molecule, freshly prepared 1 ml EDC (75 mM) and 1 ml NHS (150 mM) in DMSO were added to 30 ml the mixture. The reaction was allowed to continue for 4 h under an N2 atmosphere in the dark. Then, APTMS coated Gd2O3:Eu3+ nanoparticles (N2-APTMS) dispersed in PBS (pH 7.4) were introduced into the activated folic acid solution. The reaction was stirred for another 24 h under similar condition. Lastly, the nanoparticles were washed several times with DI water and ethanol and centrifuged at 6000 rpm for 15 min and dried at 65 °C overnight.
The Crystal phase of Gd2O3:Eu3+ nanoparticles was characterized using a Philips X’pert X-ray diffractometer with a Cu Kα radiation (λ = 0.15406 nm), scanned over a 2θ range of 20–80°.
Size and morphology
Transmission electron microscopy (TEM) images were acquired using JEOL-JEM-2010 operated at 200 kV. The size of nanoparticles was defined by measuring the diameters of 240 different nanoparticles. The samples were prepared by dispersing the nanoparticles in an ultrasonic bath for 15 min and then placing a few drops of the sample on 400 mesh carbon-coated copper grids.
X-ray photoelectron spectroscopy (XPS) spectra of different Gd2O3:Eu3+ nanoparticle system (N1-bare, N2-APTMS, and N3-FA) was obtained by a SPECS system equipped with a PHOIBOS WAL analyzer using AlKα radiation (hυ = 1486.6 eV). The scale of the spectrometer was calibrated with the reference binding energy of Ag 3d5/2. Fourier transform infrared spectroscopy (FTIR) spectra were recorded using a Nicolet 6700, Thermo Scientific infrared spectroscope.
Thermogravimetry analysis (TGA) was carried out on a TA Q600, TA Instruments under Nitrogen atmosphere, with a heating rate of 10 °C/min.
Hydrodynamic diameter and zeta potential (ξ)
Particle size distribution and zeta potential measurements were carried out using Horiba Scientific, nanoparticle analyzer SZ-100. An aqueous suspension solution of the nanoparticles (0.25 mg/ml) was prepared in PBS (pH 7.4) by sonication in a water bath for 5 min. All the measurements were carried out at an equilibrium temperature of 25 °C and were repeated three times.
Photoluminescence spectroscopy, quantum yield and decay time
Human cancer cell lines MDA-MB-231, T-47D, 293T, and PC-3 cells were obtained from American Type Culture Collection (ATCC, USA). MDA-MB-231, MCF-7, and 293T cells were maintained in DMEM (Cellgro), and T-47D and PC-3 cells were cultivated in RPMI-1640, medium (Cellgro), all supplemented with 10% FBS (Biowest), penicillin, streptomycin and amphotericin B (Cellgro). Cells were maintained at 37 °C in an incubator with humidified atmosphere, containing 5% CO2.
In vitro cytotoxicity assay
Gene expression analysis: quantitative real-time PCR
Folr1 mRNA level was determined using a two-step quantitative reverse transcriptase- real-time PCR (RT-qPCR). MDA-MB-231, MCF-7, T-47D, 293 T and PC-3 cells were seeded in a 12-well plate at a density of 104 cells per well. Total RNA was extracted using the Gen-Elute total RNA extraction kit (Sigma-Aldrich) and reverse transcribed using SuperScript II Reverse Transcriptase (Thermo Scientific). Finally, the qPCR reactions were performed in triplicates using 10 ng of cDNA. The relative expression of Folr1 mRNA in different human cancer cell lines was quantified by comparing it with the standard curve obtained by qPCR of cDNA pool of different cells. Gene expression of the target gene was normalized using housekeeping gene ribosomal protein L32 (RPL32). The primers were purchased from T4Oligo and were designed using Primer3Plus. The primer sequence used were: Folr1 (forward, GCATTTCATCCAGGACACCT; reverse, GGTGTAGGAGGTGCGACAAT) and RPL 32 (forward, CAGGGTTCGTAGAAGATTCAAGGG; reverse, CTTGGAGGAAACATTGTGAGCGATC).
In-vitro fluorescence imaging and cellular uptake analysis
All animal experiments were performed in compliance with the local ethics committee. Male CD1 mice (8-week old) were obtained from Harlan-Envigo and female athymic mice (Crl: NU/NU-nuBR, 6–8 week old) were obtained from the Unidad de Producciòn y Experimentación de Animales Laboratorio de la Universidad Autónoma Metropolitana (Campus Xochimilco). Mice were maintained in an Optimice cage system (Animal care Systems), in a controlled environment room (temperature 24 °C and 12 h light/dark cycle). Mice received water and food (2018 Teklad Global 18% protein rodent diet) ad libitum. Mice were acclimated for at least a week before starting the experiments.
Acute toxicity of FA-conjugated Gd2O3:Eu3+ nanoparticles (N3-FA) in vivo
CD1 mice were divided into 6 groups (n = 5 per group) and received intravenous tail vein injection of PBS or a solution of N3-FA in PBS (35, 50, 100, 200, and 300 mg/kg). After N3-FA administration, body weight, food intake, water intake and behavior patterns were registered daily. Mice were euthanized 7 days after administration of N3-FA in a CO2 chamber, and cervical dislocation was used as a secondary method of euthanasia.
Luminescence of FA-conjugated Gd2O3:Eu3+ nanoparticle in blood
For the pharmacokinetics study, CD1 mice were divided into seven groups (n = 3 per group). Mice were administered with N3-FA nanoparticles at a dose of 200 mg/kg or with PBS. At different time interval up to 24 h, mice were anesthetized by intraperitoneal injection of 5-pentabarbitol and blood was collected using cardiac puncture. Later, the whole blood was diluted in PBS and the presence of FA-conjugated Gd2O3:Eu3+ nanoparticles was determined by monitoring the PL spectra using a Hitachi F-7000 fluorescent spectrophotometer.
Biodistribution analysis using confocal microscopy
To detect FA-conjugated Gd2O3:Eu3+ nanoparticles in vivo, selected organs of CD1 mice administered with N3-FA at 200 mg/kg were extracted immediately after the collection of blood samples (2 h post-injection). For biodistribution analysis, tissue sections of 6 μm were prepared using a cryostat and fixed with 4% paraformaldehyde for 10 min. Nuclei were stained using 4,6-diamidino-2-phenylindole (DAPI, 10 µg/ml) for 5 min. Later, the tissue sections were analyzed to determine the biodistribution of N3-FA using CLSM.
Biodistribution analysis of nanoparticles in tumor-bearing mice
Breast cancer tumor xenografts were established by subcutaneous injection of either T-47D cells (5 × 106, n = 9) or MDA-MB-231 cells (2 × 106, n = 3) to each flank of female nude mice (female, 6–8 weeks old). All the mice were fed autoclaved food and water. For the mice receiving T-47D cells, in addition to normal food, they were fed with 2 g/kg of chocolate spread containing 5 µl of β-estradiol (10 nM) every day. Tumor growth was monitored using a vernier caliper, and their volume was calculated using the following formula: Volume = [length × (width)2]/2. Three and 7 weeks after the inoculation of MDA-MB-231 and T-47D cells, respectively, mice received an intravenous inoculation of PBS, APTMS coated (N2-APTMS, 200 mg/kg) and FA-conjugated (N3-FA, 200 mg/kg) Gd2O3:Eu3+ nanoparticles (n = 3 per group). Organ extraction was performed 2 h after i.v. of nanoparticles and were prepared for cryosectioning. Biodistribution was analyzed using CLSM as described before and by CT imaging.
µCT and image processing
The scanning of the tumors was done with a SkyScan 2211 nano-CT (Bruker micro-CT, Belgium). The samples were scanned using voltage of 40–50 kV, target current of 70 µA (0.1 μm Tungsten source), and exposure time of 300–350 ms, with resolution from 2.2 to 3.0 µm, depending on sample geometry, resulting in 1536 × 1920 pixels on a flat panel detector, rotation step of 0.200°, frame averaging of 4, and 360° scan to minimize artifacts produced by the combination of high-density Gd2O3:Eu3+ nanoparticles and low-density tissue. The reconstructed slices were obtained with NRecon v220.127.116.11 and each time histograms were forced to stay within − 750 to 5000 HU (Hounsfield Units). No staining was required. To obtain the ratio of the volume of nanoparticles/volume of the tumor, image-processing scripts were created and run with the native software of the nano-CT (CT Analyser v18.104.22.168; Bruker micro-CT, 2017). The processed volume for each tumor was fixed to ~ 0.99 mm3 (for comparison purpose) consisting of cylindrical sections with a diameter and height of 1.5 and 0.56 mm, respectively.
Statistical analyses were performed using GraphPad Prism v5.0 software (GraphPad Software, Inc). Comparisons of three or more groups were conducted with a 1-way ANOVA test, followed by a Bonferroni’s post-test. For responses that were affected by two variables, a 2-way ANOVA with a Bonferroni’s or Tukey post-test was used. Results are expressed as mean ± SEM and a P ≤ 0.05 was considered significant.
Synthesis and characterization of Gd2O3:Eu3+ nanoparticles
Figure 2b shows the TGA analysis of the different Gd2O3:Eu3+ nanoparticle systems. Weight loss in N2-APTMS and N3-FA at low temperature (≤ 200 °C) was due to the dehydration of water molecules attached to the surface of nanoparticles. The weight loss due to the presence of organic moieties (> 200 °C) was estimated to be 3.78 and 5.53% for N2-APTMS and N3-FA, respectively. The higher weight loss in N3-FA compared to N2-APTMS is due to the conjugation of folic acid molecules onto the surface of N2-APTMS.
Conjugation of FA to APTMS coated nanoparticles was further confirmed by XPS analysis. Preliminary confirmation of FA conjugation was obtained through the presence of an intense nitrogen peak in N3-FA compared to N2-APTMS, due to the presence of 7 nitrogen atoms in FA molecule (Additional file 1: Figure S1). Additionally, the high-resolution spectrum of C 1s of N2-APTMS and N3-FA are shown in Fig. 2c, d. Deconvolution of C 1s showed the existence of amide bond in N3-FA. The C 1s spectrum of N3-FA was well fitted into five peaks located at 282.8, 284.4, 285.2, 286.3 and 288.4 eV. The lowest binding energy (B.E.) component (282.8 eV) was associated with peaks that arise due to the presence of C–Si bonds in APTMS molecules. Higher B.E. components at 284.4, 285.2 and 286.3 eV has been assigned to C–C/C=C, C–O and C–NH3+/C–NH bonds , the presence of these peaks can be seen in both APTMS coated (Fig. 2c) and FA-functionalized Gd2O3:Eu3+ nanoparticles (Fig. 2d). In addition, another higher energy component at 288.4 eV (Fig. 2d) was obtained specifically in N3-FA, which corresponds to the backbone of amide bond (NH–C=O) . The presence of peak due to amide bonding confirms the successful conjugation of NH2 groups of Gd2O3:Eu3+ @ APTMS (N2-APTMS) with –COO− groups of FA.
Hydrodynamic diameter (d), zeta potential (ζ) and polydispersity index of different Gd2O3:Eu3+ nanoparticles
PBS (pH 7.4)
+ 9.9 ± 3.22
+ 16.2 ± 1.05
+ 23.2 ± 1.84
Photoluminescence (PL) properties
Average decay time and absolute quantum yield values of different Gd2O3:Eu3+ nanoparticle system measured in aqueous colloidal form
Average decay time (ms)
1.076 ± 0.003
39.6 ± 2.43
1.114 ± 0.002
41.4 ± 3.03
1.061 ± 0.006
35.3 ± 1.79
The photoluminescence excitation and emission spectra of the nanoparticle systems, measured in PBS is shown in Fig. 3c. The excitation spectra of Gd2O3:Eu3+ (Eu3+ doping concentration = 5%) nanoparticles consisted of three main excitation bands with peaks located at 254, 275 and at 394 nm. The characteristic peak at 254 nm corresponds to the charge transfer band which arise due to the transfer of an electron to 4f orbital of europium from 2p orbital of oxygen. Other peaks observed at ~ 275 and 394 nm are associated with 4f-4f electronic transitions of Gd3+ and Eu3+, respectively. The emission spectra was observed after excitation with 254 nm, which produced the highest PL intensity. The observed emission bands are the result of the transition from 5D0 excited state level of Eu3+ to 7FJ (J = 0, 1, 2, 3) ground state level. A group of peaks around ~ 580 nm was attributed to the transition from 5D0 → 7F0 and another peak located at 593 nm to magnetic dipole allowed by 5D0 → 7F1 level. The observed red emission of Gd2O3:Eu3+ nanoparticle was due to the emission peak at 613.4 nm, which is due to an electric dipole associated with 5D0 → 7F2 transition of Eu3+. We observed variations in the PL emission intensity of N1-Bare, N2-APTMS and N3-FA systems. The PL emission intensity of Gd2O3:Eu3+ nanoparticles was increased after APTMS coating, which could be attributed to the removal of hydroxyl groups (Fig. 2a, peak 2), well known for quenching radiative process from nanophosphor materials. Additionally, the decrease in reflectivity of UV light from the surface of the nanoparticles due to the presence of silane layer could be another reason for the increased PL intensity. Finally, the PL intensity of N3-FA nanoparticles was decreased, which is probably due to the introduction of folic acid that contains a large number of organic groups. The high energetic vibration of organic groups near the surface of a nanophosphor has also been shown to reduce PL intensity by increasing non-radiative recombination process .
In vitro cytotoxicity
Folate receptor expression and cellular uptake
In vivo acute toxicity and pharmacokinetics of folic acid conjugated-Gd2O3:Eu3+ nanoparticles (N3-FA)
Next, we question for how long we can find the nanoparticles in the blood circulation. Taking into account the optimal QY of N3-FA, their presence in blood samples of CD1 mice after i.v. injection was analyzed by monitoring their emission spectra. Figure 6b shows that the nanoparticles were detected in whole blood up to 2 h after inoculation, which could be attributed to rapid clearance of N3-FA from blood circulation. Further, in vivo biodistribution of N3-FA nanoparticles was analyzed in different organs of CD1 mice, 2 h after intravenous injection. N3-FA was detected in kidneys, liver, lungs, and spleen (Fig. 6c, d). Highest levels of N3-FA were detected in kidneys, while liver and lungs showed a lower, but similar accumulation. Spleen presented very weak fluorescence signal, suggesting poor uptake of N3-FA by spleen cells. The significantly higher accumulation of N3-FA in kidney compared to other organs suggests their rapid metabolism and clearance from the body (Fig. 6d). The presence of nanoparticles in liver, lungs, and spleen has been attributed to the distribution of mononuclear phagocytes .
Biodistribution and tumor-targeting ability of folic acid-conjugated Gd2O3:Eu3+ nanoparticles in breast cancer xenograft models analyzed using CLSM
Tumor accumulation of Gd2O3:Eu3+ nanoparticles analyzed using CT imaging
Breast cancer is the most common cause of cancer-related death among women, and it is estimated that more than 40,000 women in the USA alone will die because of it in 2017 . To increase the chances of successful treatment or survival, it is critical to detect breast cancer as early as possible. Despite the progress in screening with mammography, there is still a significant amount of false-negative results (10–25%) that will lead to therapeutic delay, thus increasing the risk of developing metastasis by the time of detection . Therefore, the development of new diagnostic tools for breast cancer detection is of vital importance. We reported here the development and characterization of folic acid-functionalized luminescent Gd2O3:Eu3+ nanoparticles as a new diagnostic tool for breast cancer detection alone or in combination with CT imaging.
Gd2O3:Eu3+ nanocrystals were produced using sucrose combustion synthesis, and nanoparticles exhibited good crystallinity, narrow size distribution, and optimal quantum yield. Compared to other conventional synthesis methods of Gd2O3:Eu3+ nanoparticles such as sol–gel, hydrothermal and spray pyrolysis, combustion synthesis is a low cost and rapid synthesis procedure to produce nanoparticles with improved photoluminescence properties [43, 44]. The QY of the synthesized nanoparticles strongly depended upon the doping concentration of the activator ion (Eu3+). We found 5% Eu3+ was optimum to obtain highest QY (~ 41%) and an average decay time of ~ 1 ms. Surface functionalization with folic acid reduced the QY of Gd2O3:Eu3+ nanoparticles to ~ 35% due to increased non-radiative recombination process. Nevertheless, the obtained values indicate that FA-conjugated Gd2O3:Eu3+ nanoparticles (N3-FA) are a good candidate for in vivo bioimaging.
Most of the nanoparticles used for drug delivery or cancer imaging application are 50–150 nm in diameter in order to take advantage of the passive targeting of tumor vasculature via EPR effect . The specificity and efficiency of nanoparticles can be improved by surface modification with a specific targeting ligand. In view of that, the surface of Gd2O3:Eu3+ was functionalized with folic acid to target Folr1, which is frequently over-expressed in breast cancers. The average size of the FA-conjugated nanoparticles (N3-FA) was 55 ± 6 nm, which lies in the size range for passive targeting via EPR effect. The produced nanoparticles can then use both passive and active targeting to reach the cancer cells. Surface charge is important to avoid agglomeration of the particles that are electrostatically stabilized in suspensions. Zeta potential measurements showed that N1-Bare have poor colloidal stability in PBS with a value of + 9.9 ± 3.22 mV, which could be attributed to the lack of surface reactive groups, such as –OH. However, colloidal stability was improved after surface functionalization with APTMS and FA, reaching a zeta potential of + 23.2 ± 1.84 mV for N3-FA, indicating a decreased risk of aggregation. Overall, N3-FA nanoparticles combine a good size for passive targeting to tumors in vivo as well as a limited risk of aggregation, which is an important characteristic for systemic delivery in patients.
We further showed that FA-functionalized Gd2O3:Eu3+ nanoparticles had low cytotoxic effect in vitro at concentrations up to 50 µg/ml. A slight decrease in cell viability was induced quickly after addition of the nanoparticles, even at low concentration (6.25 µg/ml) and kept increasing over time. Since this decrease was quickly induced, it seems likely that the nanoparticles could partly stop cell cycle and proliferation. Additional experiments would be require to study this matter and, at the moment, we cannot discard the possibility of inducing apoptosis if the treatment was prolonged. However, since the primary goal with this nanoparticle is diagnostic, a single injection would be given to patients. The distribution of the signal would then be measured and the nanoparticles would be cleared out of the body hence reducing the risks of continuous exposure and the induction of serious side effects. This is conforted by the fact that in vivo, N3-FA nanoparticles were well tolerated in mice, with doses up to 300 mg/kg, as there was no mortality or change in body weight during the course of the study. In rats, a single injection of gold nanoparticles, eventually led to side effects almost a month after the inoculation, due to their coating . Additional experiments in a different model, with longer time of study would be needed to clear out this possibility. In the meantime, these results suggested a good biocompatibility of N3-FA, encouraging further research for an application as tumor detection markers.
To assess the targeting potential of these nanoparticles Folrhi cancer cells, we used a combination of in vitro and in vivo characterization using fluorescence and CT imaging. In vitro, N3-FA nanoparticles had a faster and significantly higher uptake in Folrhi cancer cells like T-47D compared to Folrlo cancer cells such as MDA-MB-231. Similarly in tumor-bearing mice, systemically delivered N3-FA nanoparticles accumulated preferentially in T-47D tumors when compared to MDA-MB-231 tumors. This distribution was due to the expression of Folr1 on cancer cells and the presence of FA on the nanoparticles since there was significantly less uptake in T-47D tumors when N2-APTMS were injected. Accumulation of N3-FA and N2-APTMS nanoparticles in MDA-MB-231 and T-47D tumors, respectively, is likely due to passive EPR effect. In addition, the presence of fluorescence in the tumors 2 h after the inoculation indicated that there was retention of the nanoparticles since, at this time, it was not possible to detect nanoparticles in blood circulation. The absence of nanoparticles in the blood after 2 h, also indicated a fast clearance of the nanoparticles, which minimizes the risk of toxic response . In normal tissues, fluorescence was detected in the kidneys, probably due to renal clearance of the nanoparticles. However, there were few, or no N3-FA detected in lungs, liver or spleen in tumor-bearing mice, indicating reduced uptake in non-cancerous tissues, which is required for a cancer probe. CT imaging analysis demonstrated that the combination of CT imaging with N3-FA nanoparticles significantly enhanced tumor detection.
In summary, we have described the development of folic acid-conjugated Gd2O3:Eu3+ nanoparticles with low toxicity that can be used as a fluorescent probe for the detection of Folr1 breast cancer in vivo. Our work provides major evidence that justify future research focused towards the clinical application of FA-conjugated Gd2O3:Eu3+ for detection of breast cancer using optical imaging. In combination with CT scans, it would be possible to achieve high-resolution imaging and detection of deeply located tumors.
AJ performed all the experiments. AJ, PF, GH, and PJ conceived the idea and designed the experiments. FG assisted to RNA preparation and qRT-PCR experiments. VL, EI, TK assisted in acquiring and analyzing CT imaging data. PS assisted to the in vivo cytotoxicity experiments. AJ, PF, GH, PJ analyzed and interpreted the obtained data. AJ, PF, GH, and PJ wrote, reviewed the manuscript. All authors read and approved the final manuscript.
AJ and PS are grateful to CONACyT for Ph.D. scholarship. The authors would like to thank Eloisa Aparicio Ceja, Francisco Ruiz Medina, David Dominguez, Olga Alicia Callejas-Negrete and Deyanira Rodarte Venegas for their invaluable technical support.
The authors declare that they have no competing interests.
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Data sharing not applicable to this article as no datasets were generated or analyzed during the current study.
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Ethics approval and consent to participate
All animal experiments were performed in compliance with the local ethics committee (CICESE).
The authors acknowledge financial support from CONACyT Grant No. 247892 and CICESE Grant No. 985-105 to P.J.; DGAPA-UNAM Grant No. IN111017 and CONACyT Grant No. 232608 to G.H.
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