Letícia B. Silva1
Kelly A. D. F. Castro2
Caroline E. A. Botteon1
Cristiano L. P. Oliveira3
Roberto S. da Silva2
Priscyla D. Marcato1*- 1Department of Pharmaceutical Science, GNanoBio, School of Pharmaceutical Sciences of Ribeirão Preto, University of São Paulo, Ribeirão Preto, Brazil
- 2Department of Biomolecular Sciences, School of Pharmaceutical Sciences of Ribeirão Preto, University of São Paulo, Ribeirão Preto, Brazil
- 3Institute of Physics, University of São Paulo, São Paulo, Brazil
Photodynamic therapy (PDT) is a potential non-invasive approach for application in oncological diseases, based on the activation of a photosensitizer (PS) by light at a specific wavelength in the presence of molecular oxygen to produce reactive oxygen species (ROS) that trigger the death tumor cells. In this context, porphyrins are interesting PS because they are robust, have high chemical, photo, thermal, and oxidative stability, and can generate singlet oxygen (1O2). However, porphyrins exhibit low solubility and a strong tendency to aggregate in a biological environment which limits their clinical application. To overcome these challenges, we developed hybrid nanostructures to immobilize 5,10,15,20-tetrakis[(4-carboxyphenyl) thio-2,3,5,6-tetrafluorophenyl] (P), a new third-generation PS. The biological effect of this system was evaluated against bladder cancer (BC) cells with or without light exposition. The nanostructure composed of lipid carriers coated by porphyrin-chitosan (P-HNP), presented a size of ca. 130 nm and low polydispersity (ca. 0.25). The presence of the porphyrin-chitosan (P-chitosan) on lipid nanoparticle surfaces increased the nanoparticle size, changed the zeta potential to positive, decreased the recrystallization index, and increased the thermal stability of nanoparticles. Furthermore, P-chitosan incorporation on nanoparticles increased the stability and enhanced the self-organization of the system and the formation of spherical structures, as observed by small-angle X-ray scattering (SAXS) analysis. Furthermore, the immobilization process maintained the P photoactivity and improved the photophysical properties of PS, minimizing its aggregation in the cell culture medium. In the photoinduction assays, the P-HNP displayed high phototoxicity with IC50 3.2-folds lower than free porphyrin. This higher cytotoxic effect can be correlated to the high cellular uptake of porphyrin immobilized, as observed by confocal images. Moreover, the coated nanoparticles showed mucoadhesive properties interesting to its application in vivo. Therefore, the physical and chemical properties of nanoparticles may be relevant to improve the porphyrin photodynamic activity in BC cells.
Introduction
Photodynamic therapy (PDT) is a non-invasive approach to treat oncological and non-oncological diseases (Figueira et al., 2014; Kwiatkowski et al., 2018; Mesquita et al., 2018a,b; Gazzi et al., 2019; Negri et al., 2019; Castro et al., 2020; Gomes et al., 2020; Lee et al., 2020). PDT is a clinically approved treatment based on the activation of a photosensitizer (PS) by the light of a specific wavelength, in the presence of molecular oxygen to produce reactive oxygen species (ROS), resulting in neoplastic cell death (Agostinis et al., 2011; Bogoeva et al., 2016). When the PS is activated, its molecules absorb photons, transmitting energy to molecular oxygen and triggering the production of singlet oxygen (1O2) (type II), such as other ROS production by an electron transfer mechanism (type I) (Dougherty, 2002; Castano et al., 2004; Purushothaman et al., 2019). These ROS may activate a complex cascade of biochemical and physiological reactions able to induce tumor cell death by apoptosis, necrosis, or autophagy. The damage of microvessels suppresses the malignant tissue nutrition, oxygenation, and promotes adaptive antitumor immunity activation (Garg et al., 2010; Agostinis et al., 2011; Bacellar et al., 2015; Luiza Andreazza et al., 2016).
Bladder cancer (BC) is the tenth highest occurring malignant disease worldwide and the sixth with more incidence in men (Ferlay et al., 2019). In 2018, about 550,000 new cases were reported worldwide (Ferlay et al., 2019). Moreover, 75% of BC cases are diagnosed as non-muscle invasive bladder cancer (NMIBC) or superficial (Tse et al., 2019; Ramuta et al., 2020). Thus, due to the easy access to the bladder and the high exposition of malignant tissue on the bladder surface in cases of NMIBC, PDT has been suggested to enhance the effectiveness of BC therapy (Agostinis et al., 2011; Gomes et al., 2020).
Several porphyrins and their reduced derivatives (chlorins) have been developed and used in the clinic and clinical trials for cancer treatment (e.g., Photofrin or 5-ALA) (Dougherty, 2002; Master et al., 2013; Li et al., 2015; Zhang et al., 2016; Kou et al., 2017; dos Santos et al., 2019).
Porphyrins are aromatic heterocycle compounds formed by four pyrrole rings linked by four methyl bridges. These compounds are robust and have a high chemical, photo, thermal, and oxidative stability (Ptaszyńska et al., 2018). Porphyrins with varied structures and characteristics can be isolated from nature or synthesized. The ability of these derivatives to generate singlet oxygen enables its use as a photosensitizer in PDT (Plaetzer et al., 2003; Allison and Moghissi, 2013; Kou et al., 2017).
Although the use of porphyrin has been proposed as PS used in PDT, the disadvantages of this compound class have been observed, as it has clinical limitations due to its aggregation process (Nawalany et al., 2009; Liang et al., 2014). It is well established in literature that the photosensitizer must maintain a monomeric form to be photoactive (Ricchelli et al., 1998; Chen et al., 2005; Nawalany et al., 2009; Rabiee et al., 2020). Furthermore, several of these photosensitizers have shown low selectivity by cancer tissues (Purushothaman et al., 2019), resulting in the deactivation or reduction of the photosensitizer action. To overcome these challenges, several nanostructures have been developed as a photosensitizer delivery system to increase their selectivity (Zhou et al., 2016; Battogtokh and Ko, 2017; Ujiie et al., 2019).
Berndt-Paetz et al. (2019) reported the success of PDT using tetrahydroporphyrin-tetratosylat (THPTS) encapsulated into liposomes. This system was able to inhibit BC cell growth, trigger cells to apoptosis or necrosis, mainly due to their subcellular localization through the cytoplasm and in lysosomes (Berndt-Paetz et al., 2019). Similar results were reported by Gomes et al. (2020) using polyvinylpyrrolidone micelles containing a triazole-porphyrin derivative.
Mucoadhesive nanoparticles and lipid nanostructures have also been used as PS delivery systems to enhance PDT. The porphyrin 5,10,15,20-tetrakis(m-hydroxyphenyl) (mTHPP) was encapsulated in PLGA nanoparticles coated with poly(ethylene glycol) (PEG) or chitosan (Anderski et al., 2018; Mahlert et al., 2019). These systems showed an increase in the intracellular accumulation of mTHPP in HT-29-MTX and Caco-2 cells. Moreover, PEG-PLGA-mTHPP nanoparticles showed superior cytotoxicity to chitosan-PLGA-mTHPP nanoparticles. The PS chlorin e6 (Ce6) (Lee et al., 2011) and protoporphyrin IX (Lee et al., 2009) conjugated with chitosan nanoparticles and exhibited efficient accumulation in the tumor, exhibiting a superior therapeutic efficacy to free PS in tumor-bearing mice models. The encapsulation of verteporfin in nanostructured lipid carriers (NLCs-verteporfin) increased the uptake of this PS in 2D and 3D models of ovarian cancer cells and triggered a higher phototoxicity effect compared with free verteporfin (Michy et al., 2019). An enhancement of the phototoxic effect of meso-(tetra hydroxyphenyl) chlorin (mTHPC) in breast cancer cells was also obtained when this porphyrin was encapsulated in solid lipid nanoparticles (Navarro et al., 2014). Zhang et al. (2019) developed a NLC with a surface modified with folate to co-delivery Ce6 and paclitaxel. This nanostructured system enhanced the Ce6 and PTX internalization in cancer cells and showed, in an animal model, a significant decrease in the tumor volume compared with groups in dark conditions (Zhang et al., 2019).
Another strategy explored is the use of hybrid nanoparticles. Hybrid nanosystems can be obtained by the combination of different materials (organic–inorganic or organic–organic), combining the attributes of each material to obtain a nanostructure with unique properties (Bochicchio et al., 2018; Mukherjee et al., 2019; Ferreira Soares et al., 2020). Hybrid chitosan-coated gold nanoparticle conjugated with meso-tetrakis(4-sulphonatophenyl) porphyrin (TPPS) exhibited high photothermal conversion efficiency, enhancing the cellular uptake of TPPS in HepG2 cells, and showed superior cytotoxicity to free TPPS (Zeng et al., 2018). Thus, the association of PS with nanostructures can improve the photodynamic action, reduce its side effects in healthy tissue (Battogtokh and Ko, 2017; Kwiatkowski et al., 2018; Ujiie et al., 2019), improve its stability and tissue penetration, and enhance the PS uptake in cancer cells (Ujiie et al., 2019).
This study reports on the immobilization of the new 5,10,15,20-tetrakis[(4-carboxyphenyl) thio-2,3,5,6-tetrafluorophenyl] porphyrin (P) (Supplementary Figure S1) in a biodegradable hybrid nanoparticle of the NLCs coated with chitosan, aiming to minimize the aggregation process, enhance cellular uptake, and consequently improve the efficiency of this PS in PDT against BC cells.
Experimental Section
Materials
In general, the materials were purchased from Sigma-Aldrich without further purification. The Crodamol SS was obtained from CRODA and the N,N-Dimethylformamide (DMF) from Exodo.
Porphyrin Synthesis and Quantum Yields of Singlet Oxygen Determination
The porphyrin derivative was prepared according to the literature, following two steps: briefly. (1) The precursor 5,10,15,20-tetrakis(pentafluorophenyl)porphyrin [H2(TPFPP)] was synthesized by condensation of pyrrole with pentafluorobenzaldehyde in the presence of acetic acid and nitrobenzene under reflux conditions. (2) The tetra-substituted porphyrin 5,10,15,20-tetrakis[(4-carboxyphenyl) thio-2,3,5,6-tetrafluorophenyl] (simplified by P) was obtained by structural modification of [H2(TPFPP)] in the presence of the nucleophile 4-mercaptobenzoic acid and pyridine, using DMF as solvent at room temperature for 24 h (Castro et al., 2015). The compound P was characterized by 1H and 19F NMR (Bruker Avance 300 spectrometer at 300.13 and 282.38 MHz), UV-Vis (Agilent 8453 spectrophotometer), and fluorescence (F4500 – Hitachi spectrofluorometer) spectroscopies. In the fluorescent analysis, the widths of both excitation and emission slits were set at 3.0 nm. Additionally, the quantum yield of singlet oxygen (ϕΔ) was determined from the rate of decay of the 1O2 phosphorescence at 1270 nm using an Edinburgh F900 instrument consisting of a Rainbow OPO (Quantel Laser-France) 10 Hz, 2 mJ/pulse, which was pumped by a Brilliant NdYAG laser (Quantel Laser-France) and using 5,10,15,20-tetraphenylporphyrin (TPP) as standard in DMF (ϕΔ = 0.65) (Castro et al., 2020). The absorbance of the sample in DMF was adjusted to 0.1 at the excitation wavelength (420 nm).
Porphyrin Immobilized in Chitosan (P-Chitosan)
Chitosan solution in pH 5.2 at a concentration of 6.6 mg/mL was slowly dripped on a porphyrin solution in acetone (0.83 M) under magnetic stirring. The mixture was stirred (900 rpm) in dark conditions for 72 h at room temperature to acetone evaporation. Then, the homogeneous dispersion of the P-chitosan was incorporated into the aqueous phase of the nanoparticle’s preparation process (see below).
Hybrid Nanoparticle Preparation
The nanostrutured lipid carriers-NLCs (NP) coated with chitosan or P-chitosan (hybrid nanoparticles, HNP or P-HNP) were prepared in one step by the emulsification-ultrasonication method, a simple and scalable method (Pivetta et al., 2019). The lipid phase composed of 1.4% (m/v) of Crodamol SS and 0.4% (m/v) of oleic acid was melted at 70°C in a water bath. Thereafter, the aqueous solution of Tween® 80 (1.25% m/v) containing or not 0.24% (m/v) of chitosan, or P-chitosan at 70°C was added to the lipid phase. The hot emulsion was sonicated for 10 min (Sonics VCX 750, probe of 13 mm, 40% of amplitude) and then the dispersion was cooled at 25°C.
Particle Size and Zeta Potential
The diameter by intensity and polydispersity index (PdI) were measured by dynamic light scattering using NanoSize ZS (Malvern®) with a scattering angle of 90°. The zeta potential (ZP) was determined by electrophoretic light scattering (ELS) using NanoSize ZS (Malvern®). Samples (NP, HNP, and P-HNP) were diluted with deionized water (for size) and KCl solution (for ZP) and analyzed at 25°C.
Porphyrin Immobilization Efficiency (IE%)
The efficiency of porphyrin immobilization in the hybrid nanoparticles was calculated based on free porphyrin (P) amount in the dispersion, an indirect method (Equation 1). For this, 500 μL of the P-HNP dispersion was centrifugate at 5000 × g in an Amicon filter system from 10 kDa for 10 min. The filtrate containing the free P was diluted in DMSO and the absorbance was assessed using a UV-Vis (Agilent 8453 spectrophotometer). The concentration of non-immobilized P into nanoparticles dispersion was quantified using the molar extinction coefficient (ε) (127,902 M–1 cm–1) of P in DMSO, previously determined using calibration curves. In the equation below, the total amount of P added to the nanoparticle was considered 100%.
[P]total, total concentration of P; [P]free, free porphyrin concentration.
Atomic Force Microscopy
The morphology of the HNP was performed in a Shimadzu Scanning Probe Microscope (SPM-9600 model) operating in tapping mode. A probe of silicon (PPP-NCHR) was used with a length of 125 ± 10 μm, a resonance frequency of 204–497 kHz, and a constant force of 10–130 N/m. The HNP dispersion was dripped on mica, followed by evaporation for 24 h at room temperature before the analysis.
Cryogenic Transmission Electron Microscopy
The size and the morphology of coated nanoparticles were determined by cryogenic transmission electron microscopy (Cryo-TEM). The HNP and P-HNP dispersions were dripped in a grid. After 24 h, dry samples were frozen at −184°C and analyzed in a high-resolution transmission electron microscope FEI TECNAI G2 F20 (Thermo Fisher Scientific, United States), operating a beam voltage of 200 KeV. TEM images were analyzed in the ImageJ software (NIH, United States) to determine the size distribution of HNP and P-HNP.
Differential Scanning Calorimetry
The crystallinity of nanoparticles and their compounds were analyzed by differential scanning calorimetry (DSC) (Shimadzu DSC-50). The lyophilized samples were hermetically sealed in an aluminum pan and heated in the temperature range of 15–350°C. The heating rate was 10°C/min under nitrogen gas flow (3 kgf/cm2). The recrystallization index percentage (% IR) was calculated following Equation 2 (Shah and Pathak, 2010).
Thermogravimetric Analysis (TGA)
Thermogravimetric analysis (TGA) was carried out using Shimadzu DSC-50. The previously dried samples were hermetically sealed in an aluminum pan. Then, the samples were heated under an inert atmosphere with a rate of 10°C/min in a temperature range from 30 to 880°C.
Small-Angle X-Ray Scattering
The equipment was adjusted for a sample detector distance of 3.7 m to investigate sizes around 100 nm. The radiation used was Copper Kα (λ = 1.54 Å) and a measurement range of 0.038 < q < 1.03 (nm–1). Scattering data were collected using a two-dimensional Pilatus 300K detector. To guarantee the normalization of the data and the correct subtraction of medium contribution, capillary sample holders glued on steel liners were used. The azimuthal integration of the images was performed with the FIT2D program (Hammersley, 2016). Data processing was carried out according to standard procedures (Oliveira, 2011). The data were normalized to an absolute scale using water as a primary standard. Ten frames of 30 min were obtained for each sample. The treated data were compared to evaluate the stability of the sample and, later, experimental data were optimized. For the analysis, the Indirect Fourier Transformation method (Glatter, 1977) was used on a slightly different implementation (Oliveira et al., 2009). As a result, the theoretical fit of the scattering intensity and the corresponding pair distance distribution function [p(r)] are obtained. The overall shape of the p(r) curve provides indications of the particle shape in the system (Oliveira, 2011).
Evaluation of Porphyrin Photophysical Properties
Free porphyrin (P), P-chitosan, and P-HNP at 200 nM were evaluated regarding UV-Vis (Agilent 8453 spectrophotometer) and fluorescence (F4500 – Hitachi spectrofluorometer) spectroscopies. P-HNP and P-chitosan were prepared in deionized water, whereas free porphyrin (P) was prepared in DMSO 1% (v/v). The controls of chitosan, NP, and HNP were prepared in deionized water according to the same volume used for the P samples. All samples were excited at 420 nm. In the fluorescent analysis, the widths of both excitation and emission slits were set at 3.0 nm. The absorption and emission spectra were normalized.
Accelerated Stability
The accelerated stability of the nanoparticles was performed in a Dispersion Analyzer LUMiSizer 6120 centrifuges (L.U.M. GmbH, Berlin, Germany) using the SEPView v.6.4 software. This dispersion analyzer allows simultaneous recording of the intensity of transmitted light (808 nm) in dispersed systems as a function of time and the position of the sample in the cuvette using space and time resolved extinction profiles (STEP-technology) (Caddeo et al., 2013; Tan et al., 2016; Zielinska et al., 2019). NP, HNP, and P-HNP were added in 2 mm disposable polycarbonate sample cells. Measurements were performed at 25°C and the light transmission profile was acquired by the detector every 70 s for 250 min (200 profiles) at a rotation speed of 3801 rpm and light factor of 1. This analysis allows to detect signs of instability such as sedimentation, creaming, coalescence, flocculation, or phase separation (Caddeo et al., 2013; Tan et al., 2016; Zielinska et al., 2019). Instability indexes were calculated by SEPView v.6.4. The parameters used in this experiment mimic the stability or shelf life of 12 months (Caddeo et al., 2013; Tan et al., 2016; Zielinska et al., 2019).
Mucoadhesion Studies in vitro
To assess the mucoadhesive property of the coated nanoparticles in vitro, a mucin solution (1 mg/mL) was titrated under the nanoparticle dispersions diluted 50 times. This titration was performed in an MPT-2 accessory of the ZetaSizer Nano ZS. The concentration range analyzed was 0–0.05 mg mL–1. For each point of the titration, the ZP of HNP and P-HNP was determined.
T24 Bladder Cancer Cells Culture
The human BC cells T24 were obtained from the Rio de Janeiro Cells Bank (BCRJ). T24 cells were cultured in RPMI medium supplemented with 10% of fetal bovine serum and 1% of a streptomycin-penicillin mixture and kept at 5% of CO2 and 37°C (MCO-170AIC-PE, PHCbi, Canada).
Cytotoxicity (Dark Condition)
The cytotoxicity of free porphyrin (P), HNP, and P-HNP was evaluated by the resazurin assay. T24 cells were seeded in 96-well plates at a density of 2 × 104 cells/well. After 24 h, the cells were treated with different concentrations of the samples (12.5–300 nM) prepared in RPMI phenol red free medium supplemented with 2% of fetal bovine serum and 1% of streptomycin-penicillin mixture (RPMI medium with 2% FBS). P stock solutions were prepared in DMSO (1 mM) and then diluted in RPMI medium [(DMSO) <0.5%]. After 6 or 24 h, the cells were washed with 200 μL PBS and then 200 μL of resazurin solution (25 μg/mL) in RPMI medium without phenol red and serum was added to each well. The cells were incubated at 37°C for 4 h. After this period, the fluorescence was then measured with excitation at 530 nm and emission at 590 nm in a microtiter plate reader spectrophotometer (SynergyTM HTX Multi-Mode Microplate Reader, BioTek). DMSO (20% v/v) was used as positive control and untreated cells (cells + RPMI medium) were used as negative control.
Photocytotoxicity
Photodynamic studies were carried out in T24 cells with free porphyrin (P), HNP, and P-HNP using the resazurin assay. Briefly, 2 × 104 cells/well were seeded and then incubated at 37°C for 24 h. After incubation, cells were treated with the samples at the same concentrations used in the cytotoxicity experiment. After 6 or 24 h of incubation, the cells were washed with PBS, and then fresh RPMI medium with 2% FBS was added in each well. Immediately, the cells were irradiated at room temperature using a set of LEDs with the emission band ranging between 385 and 425 nm at an irradiance of 24.5 mW cm–2 with a total light dose of 5 or 10 J/cm–2. The cells were incubated for 20 h at 37°C in a CO2 incubator. Then, the resazurin solution was added and the cells were incubated for 4 h. After incubation, fluorescence was evaluated under the same conditions described previously. In the assay with a treatment time of 6 h, the cells were irradiated with only the fluence of 10 J/cm2.
The phototoxicity was also evaluated in T24 cells using Cell-titer Glo 2.0 Cell Viability Assay Kit in the same condition described above. After incubation, cells were treated with the samples at the range concentrations (12.5–300 nM) and then incubated. After 6 h, the cells were washed with PBS, and then fresh RPMI medium with 2% FBS was added in each well. The cells were exposed to 10 J/cm2 at room temperature. Then, the cells were incubated at 37°C in a CO2 incubator for 20 h. After incubation, Cell-titer Glo 2.0 reagent was added to each well according to Promega Protocol, and cells were incubated at room temperature. After 10 min, samples were transferred to 96 wells opaque plates, and luminescence was measured in a microtiter plate reader spectrophotometer (Synergy TM HTX Multi-Mode Microplate Reader, BioTek). For those studies, the positive and negative controls were the same as those used for cytotoxicity assays. The IC50 values were calculated using Prism 5.01 (GraphPad Software Inc., San Diego, CA, United States) software.
Evaluation of Porphyrin Uptake by Laser Scanning Confocal Microscopy
For the laser scanning confocal microscopy studies, 80,000 cells were placed in each well of a glass-bottom plate (four divisions/wells, CELL view dish-Greiner Bio-One, Brazil). After 24 h, the cells were treated with P or P-HNP at 10 μM for 30 min. Then, the cells were washed twice with PBS and marked using Fluoroshield with DAPI (nucleus probe, Sigma-Aldrich). After 2 h of incubation, the cells were analyzed by a laser scanning confocal microscope (LEICA-TCS SP2) using a magnification of 64× a diode and HeNe laser with blue filter for DAPI and P (λexcitation = 405 nm). Untreated cells (cells + RPMI medium) market with DAPI were used as a negative control. The bandwidth established for emission detection ranged from 411 to 540 nm for DAPI and from 630 to 710 nm for P.
Statistical Analysis
The results of size, PdI, and ZP were analyzed by Prism 5 (GraphPad Software Inc., San Diego, CA, United States) software, using one-way analyses of variance (ANOVA) followed by Tukey. Phototoxicity results were analyzed using two-way analyses of variance followed by Bonferroni post-tests, with a significance level of 5% (0.05), 1% (0.001), and 0.1% (0.001). Data were expressed as mean ± standard deviation (SD).
Results and Discussion
Physicochemical Characterization of Nanostructures
This study explored 5,10,15,20-tetrakis[(4-carboxyphenyl) thio-2,3,5,6-tetrafluorophenyl] porphyrin (P) as a photosensitizer. It was chosen due to its interesting photophysical properties and encouraging results when immobilized in chitosan film, against Listeria monocytogenes biofilm after the light exposition (Castro et al., 2017). This porphyrin has never been applied as a photosensitizer against cancer cells.
Porphyrins have been immobilized or encapsulated in nanostructures as a strategy to avoid the potential problems intrinsic to these compounds, such as aggregation (Zhou et al., 2016). Furthermore, this strategy may increase the delivery of these compounds within the target cells, leading to an interesting intracellular localization to potentialize the effect of this PS on PDT (Lavado et al., 2015; Zhao et al., 2016; Kwiatkowski et al., 2018). Among the nanostructures, chitosan nanoparticles, and lipid nanoparticles have been explored as PS delivery systems (Anderski et al., 2018; Mahlert et al., 2019; Michy et al., 2019; Zhang et al., 2019). However, our group developed solid lipid–polymer hybrid nanoparticles to immobilize porphyrin on its surface, a new particle that has not to date been explored in the PDT area. Lipid–polymer hybrid nanoparticles are a powerful approach to mitigate disadvantages to lipid and polymeric nanoparticles, achieving a nanostructure with superior features (Wong et al., 2006; Wang et al., 2018; Khan et al., 2019).
The polymer chitosan is a non-toxic and biodegradable polysaccharide that plays a special role in porphyrin immobilization due to its ability to form stable complexes with negative charge compounds and substances (Knorr, 1984; Muzzarelli, 1996; Yang et al., 2009; Ferreira et al., 2016; Castro et al., 2017). In the pH of chitosan solution and the hybrid nanoparticles dispersions (pH ca. 5.2), the chitosan amino groups (–NH2) are protonated (–NH3+), with high positive density, and may interact with carboxylate meso-substituents groups from porphyrin (Knorr, 1984; Muzzarelli, 1996; Khunawattanakul et al., 2008; Yang et al., 2009; Mohammed et al., 2017). This interaction was promoted in two steps: (1) A solution of porphyrin in acetone was mixed with a homogeneous chitosan solution (pH = 5.2) under stirring to immobilize P on the chitosan surface by electrostatic interaction; (2) The homogeneous dispersion of P-chitosan acetone-free was mixed with an aqueous surfactant solution that then, after heating, was added to the melted lipid phase to obtain NLC coating with porphyrin-chitosan (P-HNP). The NP showed negative ZP while the hybrid nanoparticle (HNP and P-HNP) exhibited a positive value (Table 1). This result confirmed the success of the carrier’s coating process with the hypothesis of the chitosan adsorption in NP negative surface since this natural polymer is well known for its positive charge (Cheung et al., 2015; Liu et al., 2016a). Furthermore, values of ZP > ∣20 mV∣ could prevent aggregates formation by electrostatic repulsion forces (Feng and Huang, 2001).
Table 1. Values of size, polydispersity index (PdI), zeta potential (ZP), pH of the formulations NP, HNP, and percentage of immobilization efficiency (%IE) of P-HNP.
The nanoparticle surface modification with chitosan and P-chitosan significantly increased the hydrodynamic size and changed the ZP of HNP and P-HNP (p < 0.05, one-way ANOVA) (Table 1). Several studies have described the increase of lipid nanoparticles after the chitosan coating process (Liu et al., 2016a; Vieira et al., 2018; Malgarim Cordenonsi et al., 2019). However, the PdI was only significantly influenced by the incorporation of P-chitosan (p < 0.05, one-way ANOVA) (Table 1). Additionally, PdI values were below 0.3 for all nanoparticles, which is a characteristic of nanoparticles with low polydispersity and a narrow range of size distribution (Üner et al., 2004; Tomasina et al., 2013).
The percentage of immobilization efficiency (IE%) of porphyrin on HNP was measured through an indirect method and was high (ca. 96%).
The accelerated stability study showed that NP presented a low instability index of 0.065 and kept its transmittance profile practically unchanged over the 1-year, being considered stable in this period at a storage temperature of 25°C (Supplementary Figure S2). The hybrid nanoparticles HNP and P-HNP, over 1 year at 25°C, exhibited a tendency to instability phenomena, with signs of creaming (Supplementary Figure S2), exhibiting instability indexes of 0.818 and 0.700 (Pereira et al., 2018). However, over 31 days, the P-HPN was considered stable with instability indexes of 0.105, showing a stability time 1.6-fold higher than HNP. Thus, the porphyrin incorporation increased the HNP’s long-term stability.
Atomic Force Microscopy and Transmission Electron Cryo-Microscopy
The image of atomic force microscopy (AFM) in the phase mode shows a color variation on the particle, suggesting the structure core-shell of HNP due to the difference of materials in the surface (Figures 1A,B). The histograms from the Cryo-TEM analysis showed that both HNP and P-HNP exhibited a homogeneous distribution with well-defined nanoparticles size (Figures 1D,E). The HNP size ranged from 30 to 65 nm, whereas the size of P-HNP varied between 20 and 55 nm (Figures 1D,E).
Figure 1. Atomic force microscopy image of HNP in phase mode (A); Cryo-TEM images of HNP (B) and P-HNP (D); size distribution histograms of HNP (C) and P-HNP (E).
Thermal Analysis: Differential Scanning Calorimetry and Thermogravimetry
The chitosan addition decreased the recrystallization index (RI) of nanoparticles from 27.4 to 25.3%, probably because of the enhancement of lattice defects in the lipid matrix of NP triggered by the interaction among chitosan, lipids, and surfactants (Table 2; Vieira et al., 2018; Malgarim Cordenonsi et al., 2019).
Table 2. Enthalpy, melting point, and recrystallization index (RI) of solid lipid (Crodamol SS), NP, HNP, and P-HNP.
Furthermore, the porphyrin incorporation increased the melting point (°C) of the nanoparticles from 46.1 to 48.6°C and the RI from 25.3 to 28.3% when compared with nanoparticles without porphyrin (Table 2).
Both chitosan and P-chitosan coating increased the thermal stability of nanoparticles as shown in TGA (Table 3). HNP and P-HNP showed a remaining weight percentage (RW %) of 37.5 and 40.5%, respectively, for the second maximum degradation temperature (Tdmax2), whereas NP had only 20.7% of remaining weight for a lower temperature of 415°C (Table 3). Furthermore, the HNP presented a lower weight percentage (ca. 4.4% less) than the values obtained for P-HNP at Tdmax3, which suggests that the incorporation of P improves the P-HNP heating resistance.
Table 3. Thermogravimetric data of the porphyrin (P), chitosan (Ch), nanostructured particles (NP), hybrid nanoparticles (HNP), and hybrid nanoparticles with porphyrin (P-HNP).
Small-Angle X-Ray Scattering
For a better understanding of the changes in the structure of nanoparticles after chitosan and P-chitosan incorporation, X-ray scattering analysis was carried out. The X-ray scattering intensity in the origin, I (0), and radius of gyration (Rg) of NP, HNP, and P-HNP are shown in Figure 2 and Table 4, respectively. Small-angle X-ray scattering (SAXS) intensity varies according to the concentration and size of nanoparticles (Li et al., 2016). Thus, the results suggested that the addition of coatings modulated the size and concentration of the nanoparticles. HNP and P-HNP exhibited well-defined size and higher concentrations of nanostructures when compared to nanoparticles without chitosan, which can be correlated with the increase in X-ray scattering (Figure 2A). Consequently, nanoparticles prepared with chitosan showed greater efficiency in the self-organization of components. Furthermore, the p(r) function for (HNP) or (P-HNP) with bell-shape suggests the interaction of the chitosan with other formulation components to form globular (spherical) nanostructures, while non-defined size and morphology were verified for NP (Figure 2B). These results agree with the AFM and Cryo-TEM images (Figure 1).
Figure 2. Experimental data from SAXS and Indirect Fourier Transform (IFT) modeling. (A) Experimental data (symbols) and theoretical model (solid lines). (B) Curves of distance distribution between pairs [p(r)] obtained for each sample.
Table 4. Values of X-ray scattering intensity in the origin [I(0)] and radius of gyration (Rg) of NP, HNP, and P-HNP.
Photophysical Properties
The absorption and emission spectra of the porphyrin are shown in Figure 3. The non-immobilized porphyrin (P) showed the typical Soret band at 421 nm attributed to the S0 → S2 transitions, and four weak Q-bands between 506 and 584 attributed to the S0 → S1 transitions (Gouterman, 1961). The value of singlet oxygen quantum yield (ϕΔ) found to P was 0.69 (Supplementary Figure S3). The UV-Vis spectra of the P-chitosan and P-HNP materials showed the typical porphyrin absorption profile. Additionally, the spectra of the nanoparticles (HNP) and raw chitosan did not present bands in the region of 400 nm (Figure 3A), confirming the successful immobilization.
Figure 3. Normalized absorption and emission spectra of free porphyrin (P), immobilized porphyrin (P-chitosan and P-HNP), and controls (NP, chitosan, and HNP). (A) Absorption spectra; (B) emission spectra, λexc = 420 nm.
Castro et al. (2017) and Ferreira et al. (2016) immobilized porphyrins in a chitosan film and observed the broadening and slightly red-shifted in the solid state. The same behavior was observed for P-chitosan in solution when compared to the P in an aqueous solution of DMSO (1%) at a concentration of 10 μM, red-shifted of Soret (ca. 4–5 nm) and Q-bands (ca. 4–5 nm). For P-HNP, the Soret and Q-bands are blue-shifted (ca. 5–11 nm). The emission spectra of P-chitosan and P-HNP also exhibited two emission peaks with the first fluorescence vibrational mode more remarkable than the second one, slightly red-shifted or blue-shifted effects were observed, respectively, compared to the non-immobilized porphyrin P according to the absorption spectra. These shifts are attributed to the small alterations in the porphyrin molecular environment to maximize the interaction with the support. Non-immobilized porphyrin (P) displayed two emission peaks at 663 and 711 nm, whereas P-HNP exhibited peaks at 655 and 710 nm, upon excitation at 420 nm (Figure 3B). Typical emission features of free or immobilized porphyrin allow cellular uptake studies and subcellular localization. As expected, both the nanoparticles and chitosan in absence of porphyrin P are non-luminescent. Furthermore, these results confirm that the process of nanoparticle preparation did not interfere with the photophysical properties of P to act as PS.
Mucoadhesion Evaluation in vitro
In general, when the drugs are administered in the bladder in an intravesical way, it shows a short residence time with easy elimination by the periodic emptying bladder, which decreases the therapeutic effect (Weintraub et al., 2014). A strong interaction of drugs or nanoparticles with the mucous bladder layer (the most superficial layer) may increase the residence time of the drug. Thus, the dose and number of administrations might be lower, and the biological effect improved (Weintraub et al., 2014). Chitosan can extend the residence time of nanoparticles in mucous membranes (Fonte et al., 2011; Liu et al., 2016b; Anderski et al., 2018). Additionally, this natural polymer was described as absorption-promoting due to its capacity of open tight junctions (Artursson et al., 1994; Sonaje et al., 2012). Hence, nanoparticles coated with chitosan are an interesting strategy to improve the permanence of nanoparticles in the bladder (Erdoğar et al., 2012).
The main expected mechanism accountable for the mucoadhesive property of nanocarriers is the electrostatic interaction (Yoncheva et al., 2011; Bhatta et al., 2012). The in vitro mucoadhesion studies employed by us explored the ionic interaction between the positive charge surface of hybrid nanoparticles and the negative sialic groups of mucin. This ionic interaction can be observed by the change in the ZP value of the nanoparticle as shown in Figure 4. A decrease in the positive charge of HNP and P-HNP by mucin concentration increase can be observed, indicating a mucoadhesive property of these particles (Figure 4). At 0.4 mg/mL of mucin, the HNP and P-HNP exhibited a negative ZP. Rençber et al. (2016) showed that polymeric nanoparticles coated with chitosan also displayed a reduction in the ZP after incubation with 0.1% of mucin.
Figure 4. Zeta potential values of HNP and P-HNP as function of mucin concentration in the mucoadhesion assays.
Cytotoxicity and Phototoxicity Assays
The study in the dark condition revealed that HNP, P-HNP, and free P were considered no cytotoxic for T24 cells once the results showed cell viability above 76% for all concentrations evaluated (Figure 5A; ISO, 2009). These data are relevant because the property of PS to be non-toxic under dark is crucial to its application in clinical trials (Nawalany et al., 2009).
Figure 5. Cell viability of T24 assessed by resazurin. (A) Cytotoxicity of hybrid nanoparticles (HNP), free porphyrin (P), and immobilized porphyrin on hybrid nanoparticles (P-HNP) after 24 h of treatment in the dark conditions. (B) Phototoxicity of free porphyrin (P) and porphyrin immobilized on hybrid nanoparticles (P-HNP) after 24 h of treatment followed by laser irradiation. a5 and b10 J/cm2 dose of light. Negative control (NC)-untreated cells (cells + RPMI medium). The results are presented as mean ± SD of three independent experiments performed in triplicate. Significant differences relative to P and P-HNP, in each photoinduction dose, are indicated with an asterisk. Statistical significance: ***p < 0.001, **p < 0.01, *p < 0.05. Data obtained by two-way ANOVA analysis followed by Bonferroni post-test.
The experiments of PDT using 24 h of treatment showed that P-HNP and P displayed a light dose-dependency phototoxicity (Figure 5B), while HNP did not show phototoxicity against T24 cells for both fluences assessed (Supplementary Figure S4). P, as well as P-HNP, were phototoxic to T24 cells for concentrations above 50 nM. In the concentration of 300 nM, P reduced the cell viability to 32.5%, whereas P-HNP was reduced to 16.3%. The IC50 for P-HNP was 2.2-fold smaller for cells exposed to 10 J/cm2 (IC50 = 66.5 nM) than for the cells exposed to 5 J/cm2 (IC50 = 149.5). Comparing the fluences of 5 and 10 J/cm2, the IC50 of P-HNP were, respectively, 3.2- and 2.5-fold lower than free P (IC50 = 483.7 and 165.8 nM). Thus, P-HNP exhibited superior phototoxicity than P.
A phototoxicity assay using reduced treatment time (6 h) at a fluence of 10 J/cm2 was also performed. This study suggested that 6 h of treatment is enough for P-HNP delivery of P into cells and improves their phototoxicity. For the concentrations of 300, 200, and 100 nM, P-HNP significantly reduced the cell viability when compared to free P (Figure 6). The P-HNP IC50 was 130.6 nM, whereas the IC50 of free P could not be estimated because it was non-toxic for cells.
Figure 6. Phototoxicity of free porphyrin (P) and porphyrin immobilized on hybrid nanoparticles (P-HNP) in T24 cells evaluated by resazurin after 6 h of treatment followed by photoinduction with a dose of 10 J/cm2. Negative control (NC)-untreated cells (cells + RPMI medium). The results are presented as mean ± SD of three independent experiments performed in triplicate. Significant differences relative to P and P-HNP, in each photoinduction dose, are indicated with an asterisk. Statistical significance: ***p < 0.001, *p < 0.05. Data obtained by two-way ANOVA analysis followed by Bonferroni post-test.
Furthermore, a bioluminescence ATP assay was carried out to evaluate the free P and P-HNP phototoxicity against T24 BC cells. This assay was chosen because it is considered more sensitive, robust, and precise than colorimetric and fluorescence assays. It also has a high correlation between ATP detection and cell viability values, since ATP production is immediately interrupted during cell death (Maehara et al., 1987; Zumpe et al., 2010).
The same phototoxicity profile observed in resazurin assay for P and P-HNP were also verified in the ATP experiment, confirming the significant phototoxic effect of P-HNP (Figure 7). As result, P-HNP exhibited significantly higher phototoxic effects when compared with free P for all concentrations except to 12.5 nM. The IC50 of P-HNP was 86.12 nM, while the free P was non-toxic for cells in the concentration range evaluated.
Figure 7. Phototoxicity of free porphyrin (P) and porphyrin immobilized on hybrid nanoparticles (P-HNP) in T24 cells using ATP bioluminescent assay after treatment of 6 h followed by PDT with 10 J/cm2 of fluence. Negative control (NC)-untreated cells (cells + RPMI medium). The results are presented as mean ± SD (n = 3). Significant differences relative to free P and P-HNP are indicated with an asterisk. Statistical significance: ***p < 0.001, **p < 0.01. Data obtained by two-way ANOVA analysis with post-tests of Bonferroni.
The superior activity of P-HNP compared to free P can be attributed to the favorable physical and chemical properties of hybrid nanoparticles, which promoted a quick and efficient P delivery into cells, avoiding P aggregation. In this context, we evaluated the photophysical properties of PS in the cell culture medium under dark conditions. The free porphyrin (P) exhibited a broad Soret band when compared to free P in DMSO 1% (Supplementary Figure S5A). P self-aggregation changed drastically its absorption spectral profile, once the bands enlarged and decreased the absorption intensity as shown in Supplementary Figure S4. Consequently, the emission intensity decreased, and new bands appeared. Such changes may be due to the mixture of monomeric and aggregates species of porphyrin that trigger fluorescence quenching (Supplementary Figure S5B). However, when assessed in cell culture medium, P immobilized in nanoparticles (P-HNP) was stable, and its aggregation was minimized since the absorption and emission spectra of the PS were similar to those shown in Figure 3.
Evaluation of Porphyrin Uptake by Laser Scanning Confocal Microscopy
Figure 8A showed the high uptake of immobilized P (P-HNP) into T24 cells for only 30 min of incubation (red fluorescence). This high and fast porphyrin internalization explains the enhancement of the phototoxicity of P-HNP previously described (see Figures 5–7). The use of nanoparticles as a PS delivery system increased the accumulation of P at strategic points in the cancer cell. In contrast, the free P, in the same conditions of incubation, exhibited a weaker fluorescence when compared with P-HNP that may be due to the free aggregation phenomena in cell culture medium (Figure 8B). According to Nawalany et al. (2009) and Brezaniova et al. (2016), the high internalization and accumulation of PS are responsible for the great phototoxic effect of porphyrin.
Figure 8. Subcellular localization of porphyrin (P) in bladder cancer cells T24 determined by confocal laser scanning microscopy. (A) P-HNP uptake. (B) Free P uptake. a: DAPI (blue fluorescence), b: porphyrin (red fluorescence), c: merged, d: control (untreated cells + DAPI, emission 630–710 nm). T24 cells were incubated sequentially with P or P-HNP for 30 min and marked with DAPI (nucleus probe).
Photosensitizer is supposed to be in specific organelles from cells to trigger the mechanism involved in cellular death by the production of ROS including singlet oxygen (Nawalany et al., 2009; Bacellar et al., 2015; Gazzi et al., 2019). The merged fluorescence images showed that P-HNP is distributed throughout the cell, including the nucleus (Figures 8A,B). Nevertheless, free P was localized only in the nucleus. Some studies describe that the DNA can also be oxidized in PDT treatments (Bacellar et al., 2015). This is a strategy explored in cancer treatment (Zhu et al., 2017; Kadhim et al., 2019). Porphyrin and metalloporphyrins can break DNA single-strand by photoinduction mechanisms with singlet oxygen action or by cleavage of the sugar moieties from nucleic acids (Defedericis et al., 2006). Anti-tumor drugs into nuclei can inhibit the replication and transcription of DNA, wrecking genetic material and inducing cells to apoptosis (Wang et al., 2011). Therefore, targeting-nuclei drugs are considered interesting and efficient to kill cancer cells (Zhu et al., 2017). However, nucleus and organelle dual-targeting drugs have been applied successfully in cancer therapy once the drugs can act trigger two different mechanisms, increasing drug efficiency on tumors as reported by Zhu et al. (2017). Thus, those results suggest that the dual-targeting and the reduced aggregation showed by the immobilized P (P-HNP) can explain the higher phototoxic effect of this PS compared to free P in BC cells.
Conclusion
The unique properties of the hybrid nanoparticles developed in this study increased the stability, improved the photophysical properties of the porphyrin in the cell culture medium, and quickly and efficiently delivered it within T24 cells. The application of P-HNP triggered a potent phototoxic effect (low IC50 = 66.5 nM) in PDT against T24 BC cells. Thus, this study represents an advance to the development of macrocycle incorporation in biodegradable hybrid nanoparticles as a possibility to potentialize their PDT action. Furthermore, the hybrid nanoparticles presented mucoadhesive properties in studies in vitro. This property is interesting for BC treatment since it might improve the permanence time of nanoparticles in the bladder after its intravesical administration. When these results are together, the porphyrin delivery system developed in this study has the potential to be applied in other cancer models and should be explored in animal models with the aim of enhancing PDT.
Data Availability Statement
The original contributions presented in the study are included in the article/Supplementary Material, further inquiries can be directed to the corresponding author.
Author Contributions
LS: porphyrin synthesis, development of nanoparticles, materials preparation, and biological studies, and writing—original draft. KC: porphyrin synthesis and characterization, and writing—review and editing. CB: biological studies, review, and editing. RS: writing—review and editing and supervision. CO: writing, review, and editing. PM: validation, writing—review and editing, and supervision. All authors contributed to worte the manuscript and approved the final version of the manuscript.
Funding
Coordination for the Improvement of Higher Education Personnel (CAPES) (Finance Code 001). São Paulo Research Foundation (FAPESP) (Grant Numbers: 2018/13465-5, 2016/12707-0, and 2019/19448-8). This study is part of the National Institute of Science and Technology in Pharmaceutical Nanotechnology: a transdisciplinary approach INCT-NANOFARMA (FAPESP Grant #2014/50928-2, and CNPq Grant #465687/2014-8).
Conflict of Interest
The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
Publisher’s Note
All claims expressed in this article are solely those of the authors and do not necessarily represent those of their affiliated organizations, or those of the publisher, the editors and the reviewers. Any product that may be evaluated in this article, or claim that may be made by its manufacturer, is not guaranteed or endorsed by the publisher.
Acknowledgments
We would like to acknowledge to São Paulo Research Foundation (FAPESP), National Council for Scientific and Technological Development (CNPq), and Coordination for the Improvement of Higher Education Personnel (CAPES). We would like to acknowledge Maurício da Silva Baptista (Cepid Redoxoma #2013/07937-8) and Helena Couto Junqueira from the Institute of Chemistry, University of São Paulo, for all assistance with the quantum yields of singlet oxygen determination. We would like to thank Márcia C. A. Fantini and Igino G. V. Martins for their contributions to SAXS analysis. We would like to thank Gilberto Úbida Leite Braga for all assistance with LED 405 nm. We would like to acknowledge Antonio Claudio Tedesco and Henrique Luís Piva for assistance with the studies of accelerated stability.
Supplementary Material
The Supplementary Material for this article can be found online at: https://www.frontiersin.org/articles/10.3389/fbioe.2021.679128/full#supplementary-material
References
Agostinis, P., Berg, K., Cengel, K. A., Foster, T. H., Girotti, A. W., Gollnick, S. O., et al. (2011). Photodynamic therapy of cancer: an update. CA Cancer J. Clin. 61, 250–281.
Allison, R. R., and Moghissi, K. (2013). Photodynamic therapy (PDT): PDT mechanisms. Clin. Endosc. 46, 24–29. doi: 10.5946/ce.2013.46.1.24
Anderski, J., Mahlert, L., Mulac, D., and Langer, K. (2018). Mucus-penetrating nanoparticles: promising drug delivery systems for the photodynamic therapy of intestinal cancer. Eur. J. Pharm. Biopharm. 129, 1–9. doi: 10.1016/j.ejpb.2018.05.018
Artursson, P., Lindmark, T., Davis, S. S., and Illum, L. (1994). Effect of chitosan on the permeability of monolayers of intestinal epithelial cells (Caco-2). Pharm. Res. 11, 1358–1361.
Bacellar, I. O., Tsubone, T. M., Pavani, C., and Baptista, M. S. (2015). Photodynamic efficiency: from molecular photochemistry to cell death. Int. J. Mol. Sci. 16, 20523–20559. doi: 10.3390/ijms160920523
Battogtokh, G., and Ko, Y. T. (2017). Mitochondrial-targeted photosensitizer-loaded folate-albumin nanoparticle for photodynamic therapy of cancer. Nanomedicine 13, 733–743. doi: 10.1016/j.nano.2016.10.014
Berndt-Paetz, M., Schulze, P., Stenglein, P. C., Weimann, A., Wang, Q., Horn, L. C., et al. (2019). Reduction of muscle-invasive tumors by photodynamic therapy with tetrahydroporphyrin-tetratosylat in an orthotopic rat bladder cancer model. Mol. Cancer Ther. 18, 743–750. doi: 10.1158/1535-7163.mct-18-1194
Bhatta, R. S., Chandasana, H., Chhonker, Y. S., Rathi, C., Kumar, D., Mitra, K., et al. (2012). Mucoadhesive nanoparticles for prolonged ocular delivery of natamycin: in vitro and pharmacokinetics studies. Int. J. Pharm. 432, 105–112. doi: 10.1016/j.ijpharm.2012.04.060
Bochicchio, S., Dalmoro, A., Bertoncin, P., Lamberti, G., Moustafine, R. I., and Barba, A. A. (2018). Design and production of hybrid nanoparticles with polymeric-lipid shell–core structures: conventional and next-generation approaches. RSC Adv. 8, 34614–34624. doi: 10.1039/c8ra07069e
Bogoeva, V., Siksjø, M., Sæterbø, K. G., Melø, T. B., Bjørkøy, A., Lindgren, M., et al. (2016). Ruthenium porphyrin-induced photodamage in bladder cancer cells. Photodiagn. Photodyn. 14, 9–17. doi: 10.1016/j.pdpdt.2016.01.012
Brezaniova, I., Hruby, M., Kralova, J., Kral, V., Cernochova, Z., Cernoch, P., et al. (2016). Temoporfin-loaded 1-tetradecanol-based thermoresponsive solid lipid nanoparticles for photodynamic therapy. J. Control. Release 241, 34–44. doi: 10.1016/j.jconrel.2016.09.009
Caddeo, C., Manconi, M., Fadda, A. M., Lai, F., Lampis, S., Diez-Sales, O., et al. (2013). Nanocarriers for antioxidant resveratrol: formulation approach, vesicle self-assembly and stability evaluation. Colloids Surf. B 111, 327–332. doi: 10.1016/j.colsurfb.2013.06.016
Castano, A. P., Demidova, T. N., and Hamblin, M. R. (2004). Mechanisms in photodynamic therapy: part one-photosensitizers, photochemistry and cellular localization. Photodiagn. Photodyn. 1, 279–293. doi: 10.1016/s1572-1000(05)00007-4
Castro, K. A. D. F., Brancini, G. T. P., Costa, L. D., Biazzoto, J., Faustino, M. A., Tomé, A., et al. (2020). Efficient photodynamic inactivation of Candida albicans by a porphyrin and potassium iodide co-encapsulated in micelles. Photochem. Photobiol. Sci. 19, 1063–1071. doi: 10.1039/d0pp00085j
Castro, K. A. D. F., Moura, N. M. M., Fernandes, A., Faustino, M. A. F., Simões, M. M. Q., Cavaleiro, J. A. S., et al. (2017). Control of Listeria innocua biofilms by biocompatible photodynamic antifouling chitosan based materials. Dyes Pigments 137, 265–276. doi: 10.1016/j.dyepig.2016.10.020
Castro, K. A. D. F., Simões, M. M. Q., Neves, M. G. P. M. S., Cavaleiro, J. A. S., Ribeiro, R. R., Wypych, F., et al. (2015). Synthesis of new metalloporphyrin derivatives from [5,10,15,20-tetrakis (pentafluorophenyl)porphyrin] and 4-mercaptobenzoic acid for homogeneous and heterogeneous catalysis. Appl. Catal. A Gen. 503, 9–19. doi: 10.1016/j.apcata.2014.12.048
Chen, B., Pogue, B. W., and Hasan, T. (2005). Liposomal delivery of photosensitising agents. Expert Opin. Drug Del. 2, 477–487. doi: 10.1517/17425247.2.3.477
Cheung, R. C., Ng, T. B., Wong, J. H., and Chan, W. Y. (2015). Chitosan: an update on potential biomedical and pharmaceutical applications. Mar. Drugs 13, 5156–5186. doi: 10.3390/md13085156
Defedericis, H. C., Patrzyc, H. B., Rajecki, M. J., Budzinski, E. E., Iijima, H., Dawidzik, J. B., et al. (2006). Singlet oxygen-induced DNA damage. Radiat. Res. 165, 445–451.
dos Santos, A. F., De Almeida, D. R. Q., Terra, L. F., Baptista, M. S., and Labriola, L. (2019). Photodynamic therapy in cancer treatment - an update review. J. Cancer Metastatis Treat. 5:25.
Dougherty, T. J. (2002). An update on photodynamic therapy applications. J. Clin. Laser Med. Surg. 20, 3–7.
Erdoğar, N., Iskit, A. B., Mungan, N. A., and Bilensoy, E. (2012). Prolonged retention and in vivo evaluation of cationic nanoparticles loaded with Mitomycin C designed for intravesical chemotherapy of bladder tumours. J. Microencapsul. 29, 576–582. doi: 10.3109/02652048.2012.668957
Feng, S., and Huang, G. (2001). Effects of emulsifiers on the controlled release of paclitaxel (Taxol) from nanospheres of biodegradable polymers. J. Control. Release 71, 53–69. doi: 10.1016/s0168-3659(00)00364-3
Ferlay, J., Colombet, M., Soerjomataram, I., Mathers, C., Parkin, D. M., Piñeros, M., et al. (2019). Estimating the global cancer incidence and mortality in 2018: GLOBOCAN sources and methods. Int. J. Cancer. 144, 1941–1953. doi: 10.1002/ijc.31937
Ferreira, D. P., Conceição, D. S., Calhelha, R. C., Sousa, T., Socoteanu, R., Ferreira, I., et al. (2016). Porphyrin dye into biopolymeric chitosan films for localized photodynamic therapy of cancer. Carbohydr. Polym. 151, 160–171. doi: 10.1016/j.carbpol.2016.05.060
Ferreira Soares, D. C., Domingues, S. C., Viana, D. B., and Tebaldi, M. L. (2020). Polymer-hybrid nanoparticles: current advances in biomedical applications. Biomed. Pharmacother. 131:110695. doi: 10.1016/j.biopha.2020.110695
Figueira, F., Pereira, P. M. R., Silva, S., Cavaleiro, J.a.S, and Tomé, J. P. C. (2014). Porphyrins and phthalocyanines decorated with dendrimers: synthesis and biomedical applications. Curr. Org. Synth 11, 110–126. doi: 10.2174/15701794113106660089
Fonte, P., Nogueira, T., Gehm, C., Ferreira, D., and Sarmento, B. (2011). Chitosan-coated solid lipid nanoparticles enhance the oral absorption of insulin. Drug Deliv. Transl. Res. 1, 299–308. doi: 10.1007/s13346-011-0023-5
Garg, A. D., Nowis, D., Golab, J., and Agostinis, P. (2010). Photodynamic therapy: illuminating the road from cell death towards anti-tumour immunity. Apoptosis 15, 1050–1071. doi: 10.1007/s10495-010-0479-7
Gazzi, A., Fusco, L., Khan, A., Bedognetti, D., Zavan, B., Vitale, F., et al. (2019). Photodynamic therapy based on graphene and MXene in cancer theranostics. Front. Bioeng. Biotechnol. 7:295. doi: 10.3389/fbioe.2019.00295
Glatter, O. (1977). A new method for the evaluation of small-angle scattering data. J. Appl. Crystallogr. 10, 415–421. doi: 10.1107/s0021889877013879
Gomes, A. T. P. C., Fernandes, R., Ribeiro, C. F., Tomé, J. P. C., Neves, M. G. P. M. S., Silva, F. C. D., et al. (2020). Synthesis, characterization and photodynamic activity against bladder cancer cells of novel triazole-porphyrin derivatives. Molecules 25:1607. doi: 10.3390/molecules25071607
Hammersley, A. (2016). FIT2D: a multi-purpose data reduction, analysis and visualization program. J. Appl. Crystallogr. 49, 646–652. doi: 10.1107/s1600576716000455
ISO (2009). ISO 10993-5:2009 Biological Evaluation of Medical Devices — Part 5: Tests for in vitro Cytotoxicity [Online]. Available online at: https://www.iso.org/standard/36406.html: ISO - International Organization for Standardization. (accessed 2021)
Kadhim, A., Mckenzie, L. K., Bryant, H. E., and Twyman, L. J. (2019). Synthesis and aggregation of a porphyrin-cored hyperbranched polyglycidol and its application as a macromolecular photosensitizer for photodynamic therapy. Mol. Pharm. 16, 1132–1139. doi: 10.1021/acs.molpharmaceut.8b01119
Khan, M. M., Madni, A., Torchilin, V., Filipczak, N., Pan, J., Tahir, N., et al. (2019). Lipid-chitosan hybrid nanoparticles for controlled delivery of cisplatin. Drug Deliv. 26, 765–772. doi: 10.1080/10717544.2019.1642420
Khunawattanakul, W., Puttipipatkhachorn, S., Rades, T., and Pongjanyakul, T. (2008). Chitosan-magnesium aluminum silicate composite dispersions: characterization of rheology, flocculate size and zeta potential. Int. J. Pharm. 351, 227–235. doi: 10.1016/j.ijpharm.2007.09.038
Knorr, D. (1984). Use of chitinous polymers in food—a challenge for food research and development. Food Technol. 38, 85–97.
Kou, J., Dou, D., and Yang, L. (2017). Porphyrin photosensitizers in photodynamic therapy and its applications. Oncotarget 8, 81591–81603. doi: 10.18632/oncotarget.20189
Kwiatkowski, S., Knap, B., Przystupski, D., Saczko, J., Kȩdzierska, E., Knap-Czop, K., et al. (2018). Photodynamic therapy - mechanisms, photosensitizers and combinations. Biomed. Pharmacother. 106, 1098–1107. doi: 10.1016/j.biopha.2018.07.049
Lavado, A. S., Chauhan, V. M., Alhaj Zen, A., Giuntini, F., Jones, D. R. E., Boyle, R. W., et al. (2015). Controlled intracellular generation of reactive oxygen species in human mesenchymal stem cells using porphyrin conjugated nanoparticles. Nanoscale 7, 14525–14531. doi: 10.1039/c5nr00795j
Lee, S. J., Koo, H., Jeong, H., Huh, M. S., Choi, Y., Jeong, S. Y., et al. (2011). Comparative study of photosensitizer loaded and conjugated glycol chitosan nanoparticles for cancer therapy. J. Control. Release 152, 21–29. doi: 10.1016/j.jconrel.2011.03.027
Lee, S. J., Park, K., Oh, Y. K., Kwon, S. H., Her, S., Kim, I. S., et al. (2009). Tumor specificity and therapeutic efficacy of photosensitizer-encapsulated glycol chitosan-based nanoparticles in tumor-bearing mice. Biomaterials 30, 2929–2939. doi: 10.1016/j.biomaterials.2009.01.058
Lee, S. Y., Lee, R., Kim, E., Lee, S., and Park, Y. I. (2020). Near-Infrared light-triggered photodynamic therapy and apoptosis using upconversion nanoparticles with dual photosensitizers. Front. Bioeng. Biotechnol. 8:275. doi: 10.3389/fbioe.2020.00275
Li, J. W., Wu, Z. M., Magetic, D., Zhang, L. J., and Chen, Z. L. (2015). Antitumor effects evaluation of a novel porphyrin derivative in photodynamic therapy. Tumour Biol. 36, 9685–9692. doi: 10.1007/s13277-015-3745-z
Li, T., Senesi, A. J., and Lee, B. (2016). Small angle X-ray scattering for nanoparticle research. Chem. Rev. 116, 11128–11180.
Liang, X., Li, X., Jing, L., Yue, X., and Dai, Z. (2014). Theranostic porphyrin dyad nanoparticles for magnetic resonance imaging guided photodynamic therapy. Biomaterials 35, 6379–6388. doi: 10.1016/j.biomaterials.2014.04.094
Liu, D., Li, J., Pan, H., He, F., Liu, Z., Wu, Q., et al. (2016a). Potential advantages of a novel chitosan-N-acetylcysteine surface modified nanostructured lipid carrier on the performance of ophthalmic delivery of curcumin. Sci. Rep. 6, 28796–28796.
Liu, M., Zhang, J., Zhu, X., Shan, W., Li, L., Zhong, J., et al. (2016b). Efficient mucus permeation and tight junction opening by dissociable “mucus-inert” agent coated trimethyl chitosan nanoparticles for oral insulin delivery. J. Control. Release 222, 67–77. doi: 10.1016/j.jconrel.2015.12.008
Luiza Andreazza, N., Vevert-Bizet, C., Bourg-Heckly, G., Sureau, F., José Salvador, M., and Bonneau, S. (2016). Berberine as a photosensitizing agent for antitumoral photodynamic therapy: insights into its association to low density lipoproteins. Int. J. Pharm. 510, 240–249. doi: 10.1016/j.ijpharm.2016.06.009
Maehara, Y., Anai, H., Tamada, R., and Sugimachi, K. (1987). The ATP assay is more sensitive than the succinate dehydrogenase inhibition test for predicting cell viability. Eur. J. Cancer Clin. Oncol. 23, 273–276. doi: 10.1016/0277-5379(87)90070-8
Mahlert, L., Anderski, J., Mulac, D., and Langer, K. (2019). The impact of gastrointestinal mucus on nanoparticle penetration – in vitro evaluation of mucus-penetrating nanoparticles for photodynamic therapy. Eur. J. Pharm. Sci. 133, 28–39. doi: 10.1016/j.ejps.2019.03.010
Malgarim Cordenonsi, L., Faccendini, A., Catanzaro, M., Bonferoni, M. C., Rossi, S., Malavasi, L., et al. (2019). The role of chitosan as coating material for nanostructured lipid carriers for skin delivery of fucoxanthin. Int. J. Pharm. 567:118487. doi: 10.1016/j.ijpharm.2019.118487
Master, A., Livingston, M., and Sen Gupta, A. (2013). Photodynamic nanomedicine in the treatment of solid tumors: perspectives and challenges. J. Control. Release 168, 88–102. doi: 10.1016/j.jconrel.2013.02.020
Mesquita, M. Q., Dias, C. J., Gamelas, S., Fardilha, M., Neves, M. G. P. M. S., and Faustino, M.a.F (2018a). An insight on the role of photosensitizer nanocarriers for Photodynamic Therapy. An. Acad. Bras. Cienc. 90, 1101–1130. doi: 10.1590/0001-3765201720170800
Mesquita, M. Q., Dias, C. J., Neves, M. G. P. M. S., Almeida, A., and Faustino, M.a.F (2018b). Revisiting current photoactive materials for antimicrobial photodynamic therapy. Molecules 23, 1–47.
Michy, T., Massias, T., Bernard, C., Vanwonterghem, L., Henry, M., Guidetti, M., et al. (2019). Verteporfin-Loaded lipid nanoparticles improve ovarian cancer photodynamic therapy In Vitro and In Vivo. Cancers (Basel). 11:1760. doi: 10.3390/cancers11111760
Mohammed, M. A., Syeda, J. T. M., Wasan, K. M., and Wasan, E. K. (2017). An overview of chitosan nanoparticles and its application in non-parenteral drug delivery. Pharmaceutics 9:53. doi: 10.3390/pharmaceutics9040053
Mukherjee, A., Waters, A. K., Kalyan, P., Achrol, A. S., Kesari, S., and Yenugonda, V. M. (2019). Lipid-polymer hybrid nanoparticles as a next-generation drug delivery platform: state of the art, emerging technologies, and perspectives. Int. J. Nanomed. 14, 1937–1952. doi: 10.2147/ijn.s198353
Muzzarelli, R.a.A (1996). Chitosan-based dietary foods. Carbohydr. Polym. 29, 309–316. doi: 10.1016/s0144-8617(96)00033-1
Navarro, F. P., Creusat, G., Frochot, C., Moussaron, A., Verhille, M., Vanderesse, R., et al. (2014). Preparation and characterization of mTHPC-loaded solid lipid nanoparticles for photodynamic therapy. J. Photochem. Photobiol. B 130, 161–169. doi: 10.1016/j.jphotobiol.2013.11.007
Nawalany, K., Rusin, A., Kepczyński, M., Mikhailov, A., Kramer-Marek, G., Snietura, M., et al. (2009). Comparison of photodynamic efficacy of tetraarylporphyrin pegylated or encapsulated in liposomes: in vitro studies. J. Photochem. Photobiol. B 97, 8–17. doi: 10.1016/j.jphotobiol.2009.07.005
Negri, L. B., Martins, T. J., Da Silva, R. S., and Hamblin, M. R. (2019). Photobiomodulation combined with photodynamic therapy using ruthenium phthalocyanine complexes in A375 melanoma cells: effects of nitric oxide generation and ATP production. J. Photochem. Photobiol. B 198:111564. doi: 10.1016/j.jphotobiol.2019.111564
Oliveira, C. L., Behrens, M. A., Pedersen, J. S., Erlacher, K., Otzen, D., and Pedersen, J. S. (2009). A SAXS study of glucagon fibrillation. J. Mol. Biol. 387, 147–161. doi: 10.1016/j.jmb.2009.01.020
Oliveira, C. L. P. (2011). Investigating macromolecular complexes in solution by small angle X-Ray scattering. Curr. Trends X-Ray Crystallogr. 367–392.
Pereira, I., Zielińska, A., Ferreira, N. R., Silva, A. M., and Souto, E. B. (2018). Optimization of linalool-loaded solid lipid nanoparticles using experimental factorial design and long-term stability studies with a new centrifugal sedimentation method. Int. J. Pharm. 549, 261–270. doi: 10.1016/j.ijpharm.2018.07.068
Pivetta, T. P., Silva, L. B., Kawakami, C. M., Araújo, M. M., Del Lama, M. P. F. M., Naal, R. M. Z. G., et al. (2019). Topical formulation of quercetin encapsulated in natural lipid nanocarriers: evaluation of biological properties and phototoxic effect. J. Drug Deliv. Sci. Technol. 53:101148. doi: 10.1016/j.jddst.2019.101148
Plaetzer, K., Kiesslich, T., Verwanger, T., and Krammer, B. (2003). The modes of cell death induced by PDT: an overview. Med. Laser Appl. 18, 7–19. doi: 10.1078/1615-1615-00082
Ptaszyńska, A. A., Trytek, M., Borsuk, G., Buczek, K., Rybicka-Jasińska, K., and Gryko, D. (2018). Porphyrins inactivate Nosema spp. microsporidia. Sci. Rep. 8:5523.
Purushothaman, B., Choi, J., Park, S., Lee, J., Samson, A.a.S, Hong, S., et al. (2019). Biotin-conjugated PEGylated porphyrin self-assembled nanoparticles co-targeting mitochondria and lysosomes for advanced chemo-photodynamic combination therapy. J. Mater. Chem. B 7, 65–79. doi: 10.1039/c8tb01923a
Rabiee, N., Yaraki, M. T., Garakani, S. M., Garakani, S. M., Ahmadi, S., Lajevardi, A., et al. (2020). Recent advances in porphyrin-based nanocomposites for effective targeted imaging and therapy. Biomaterials 232:119707. doi: 10.1016/j.biomaterials.2019.119707
Ramuta, T. Ž, Jerman, U. D., Tratnjek, L., Janev, A., Magatti, M., Vertua, E., et al. (2020). The cells and extracellular matrix of human amniotic membrane hinder the growth and invasive potential of bladder urothelial cancer cells. Front. Bioeng. Biotechnol. 8:554530. doi: 10.3389/fbioe.2020.554530
Rençber, S., Karavana, S. Y., Yılmaz, F. F., Eraç, B., Nenni, M., Özbal, S., et al. (2016). Development, characterization, and in vivo assessment of mucoadhesive nanoparticles containing fluconazole for the local treatment of oral candidiasis. Int. J. Nanomed. 11, 2641–2653. doi: 10.2147/ijn.s103762
Ricchelli, F., Gobbo, S., Moreno, G., Salet, C., Brancaleon, L., and Mazzini, A. (1998). Photophysical properties of porphyrin planar aggregates in liposomes. Eur. J. Biochem. 253, 760–765. doi: 10.1046/j.1432-1327.1998.2530760.x
Shah, M., and Pathak, K. (2010). Development and statistical optimization of solid lipid nanoparticles of simvastatin by using 2(3) full-factorial design. AAPS PharmSciTech 11, 489–496. doi: 10.1208/s12249-010-9414-z
Sonaje, K., Chuang, E. Y., Lin, K. J., Yen, T. C., Su, F. Y., Tseng, M. T., et al. (2012). Opening of epithelial tight junctions and enhancement of paracellular permeation by chitosan: microscopic, ultrastructural, and computed-tomographic observations. Mol. Pharm. 9, 1271–1279. doi: 10.1021/mp200572t
Tan, C., Feng, B., Zhang, X., Xia, W., and Xia, S. (2016). Biopolymer-coated liposomes by electrostatic adsorption of chitosan (chitosomes) as novel delivery systems for carotenoids. Food Hydrocoll. 52, 774–784. doi: 10.1016/j.foodhyd.2015.08.016
Tomasina, J., Poulain, L., Abeilard, E., Giffard, F., Brotin, E., Carduner, L., et al. (2013). Rapid and soft formulation of folate-functionalized nanoparticles for the targeted delivery of tripentone in ovarian carcinoma. Int. J. Pharm. 458, 197–207. doi: 10.1016/j.ijpharm.2013.09.025
Tse, J., Singla, N., Ghandour, R., Lotan, Y., and Margulis, V. (2019). Current advances in BCG-unresponsive non-muscle invasive bladder cancer. Expert Opin. Investig. Drugs 28, 757–770. doi: 10.1080/13543784.2019.1655730
Ujiie, H., Ding, L., Fan, R., Kato, T., Lee, D., Fujino, K., et al. (2019). Porphyrin-high-density lipoprotein: a novel photosensitizing nanoparticle for lung cancer therapy. Ann. Thorac. Surg. 107, 369–377. doi: 10.1016/j.athoracsur.2018.08.053
Üner, M., Wissing, S. A., Yener, G., and Müller, R. H. (2004). Influence of surfactants on the physical stability of solid lipid nanoparticle (SLN) formulations. Pharmazie 59, 331–332.
Vieira, A. C. C., Chaves, L. L., Pinheiro, S., Pinto, S., Pinheiro, M., Lima, S. C., et al. (2018). Mucoadhesive chitosan-coated solid lipid nanoparticles for better management of tuberculosis. Int. J. Pharm. 536, 478–485. doi: 10.1016/j.ijpharm.2017.11.071
Wang, Y., Chen, J., and Irudayaraj, J. (2011). Nuclear targeting dynamics of gold nanoclusters for enhanced therapy of HER2+ Breast cancer. ACS Nano 5, 9718–9725. doi: 10.1021/nn2032177
Wang, T., Hu, Q., Lee, J. Y., and Luo, Y. (2018). Solid lipid-polymer hybrid nanoparticles by in situ conjugation for oral delivery of astaxanthin. J. Agric. Food Chem. v. 66, 9473–9480. doi: 10.1021/acs.jafc.8b02827
Weintraub, M. D., Li, Q. Q., and Agarwal, P. K. (2014). Advances in intravesical therapy for the treatment of non-muscle invasive bladder cancer (Review). Mol. Clin. Oncol. 2, 656–660. doi: 10.3892/mco.2014.314
Wong, H. L., Rauth, A. M., Bendayan, R., Manias, J. L., Ramaswamy, M., Liu, Z., et al. (2006). A new polymer-lipid hybrid nanoparticle system increases cytotoxicity of doxorubicin against multidrug-resistant human breast cancer cells. Pharm. Res. 23, 1574–1585. doi: 10.1007/s11095-006-0282-x
Yang, R., Shim, W. S., Cui, F. D., Cheng, G., Han, X., Jin, Q. R., et al. (2009). Enhanced electrostatic interaction between chitosan-modified PLGA nanoparticle and tumor. Int. J. Pharm. 371, 142–147. doi: 10.1016/j.ijpharm.2008.12.007
Yoncheva, K., Vandervoort, J., and Ludwig, A. (2011). Development of mucoadhesive poly(lactide-co-glycolide) nanoparticles for ocular application. Pharm. Dev. Technol. 16, 29–35. doi: 10.3109/10837450903479954
Zeng, J., Yang, W., Shi, D., Li, X., Zhang, H., and Chen, M. (2018). Porphyrin derivative conjugated with gold nanoparticles for dual-modality photodynamic and photothermal therapies In Vitro. ACS Biomater. Sci. Eng. 4, 963–972. doi: 10.1021/acsbiomaterials.7b00886
Zhang, L. J., Zhang, X. H., Liao, P. Y., Sun, J. J., Wang, L., Yan, Y. J., et al. (2016). Antitumor activity evaluation of meso-tetra (pyrrolidine substituted) pentylporphin-mediated photodynamic therapy in vitro and in vivo. J. Photochem. Photobiol. B 163, 224–231. doi: 10.1016/j.jphotobiol.2016.08.044
Zhang, Q., Zhao, J., Hu, H., Yan, Y., Hu, X., Zhou, K., et al. (2019). Construction and in vitro and in vivo evaluation of folic acid-modified nanostructured lipid carriers loaded with paclitaxel and chlorin e6. Int. J. Pharm. 569:118595. doi: 10.1016/j.ijpharm.2019.118595
Zhao, L., Kim, T. H., Kim, H. W., Ahn, J. C., and Kim, S. Y. (2016). Enhanced cellular uptake and phototoxicity of Verteporfin-conjugated gold nanoparticles as theranostic nanocarriers for targeted photodynamic therapy and imaging of cancers. Mater. Sci. Eng. C 67, 611–622. doi: 10.1016/j.msec.2016.05.047
Zhou, Y., Liang, X., and Dai, Z. (2016). Porphyrin-loaded nanoparticles for cancer theranostics. Nanoscale 8, 12394–12405. doi: 10.1039/c5nr07849k
Zhu, S., Yao, S., Wu, F., Jiang, L., Wong, K.-L., Zhou, J., et al. (2017). Platinated porphyrin as a new organelle and nucleus dual-targeted photosensitizer for photodynamic therapy. Org. Biomol. Chem. 15, 5764–5771. doi: 10.1039/c7ob01003f
Zielinska, A., Ferreira, N. R., Durazzo, A., Lucarini, M., Cicero, N., Mamouni, S. E., et al. (2019). Development and optimization of alpha-pinene-loaded solid lipid nanoparticles (SLN) using experimental factorial design and dispersion analysis. Molecules 24:2683. doi: 10.3390/molecules24152683
Keywords: hybrid nanoparticles, chitosan, porphyrin, PDT-photodynamic therapy, bladder cancer cells
Citation: Silva LB, Castro KADF, Botteon CEA, Oliveira CLP, da Silva RS and Marcato PD (2021) Hybrid Nanoparticles as an Efficient Porphyrin Delivery System for Cancer Cells to Enhance Photodynamic Therapy. Front. Bioeng. Biotechnol. 9:679128. doi: 10.3389/fbioe.2021.679128
Received: 11 March 2021; Accepted: 28 June 2021;
Published: 17 September 2021.
Edited by:
Christiane Pienna Soares, Sao Paulo State University, BrazilReviewed by:
Juan Chen, University Health Network (UHN), CanadaRun Zhang, The University of Queensland, Australia
Copyright © 2021 Silva, Castro, Botteon, Oliveira, da Silva and Marcato. This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.
*Correspondence: Priscyla D. Marcato, cG1hcmNhdG9AZmNmcnAudXNwLmJy