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INTRODUCTION
Breast cancer occurs when some breast cells begin to grow abnormally and divide more rapidly than healthy cells. These cells accumulate and form a lump or mass. Breast cancer cells can spread to the lymph nodes and other parts of the body. Therefore, the development of a drug with high efficacy in the treatment of breast cancer would play an important role in reducing the death rate of woman with this disease. Many drugs are currently used to treat breast cancer such as doxorubicin [1], gemcitabine [2], paclitaxel [3], docetaxel (DTX) [4], and leuprolide [5]. Among them, DTX is a second-generation taxane approved by the US Food and Drug Administration (FDA) to treat multiple types of cancers such as breast, non-small cell lung, hormone-refractory prostate cancers, and gastric adenocarcinoma and squamous cell carcinoma of the head and neck [6]. DTX is usually selected as a model drug for the treatment of breast cancer and it acts as a microtubule-stabilizing agent that blocks the cell cycle at the G2/M phase, which inhibits microtubule disassembly during cell-cycle progression, causing cell death. It is designated as biopharmaceutical classification system class IV agent that has poor aqueous solubility and permeability, which reduce its bioavailability, thereby limiting the treatment efficacy. Therefore, the commercial DTX product Taxotere (Sanofi Aventis, Bridgewater, NJ , USA) injection was developed to enhance drug solubility [7]. Taxotere is a clear yellow viscous solution, and each milliliter contains 20 mg DTX in 1 ml of polysorbate 80/dehydrated alcohol (50/50, v/v). It is packaged in single 1-, 4-, and 8-ml vials containing (20, 80, and 160 mg) of DTX, respectively. However, the Tween 80 component may cause various side effects such as accumulative fluid retention, acute hypersensitivity reactions, weight gain, pleural or pericardial effusion, and peripheral neuropathy [8,9]. Thus, the formulations of nanoparticles (NPs) have been developed to overcome these problems. Nanoformulations have various advantages such as enhanced solubility of hydrophobic drugs, controlled and sustained drug release, improvement of drug half-life in the circulation, and increased the efficacy of cancer therapy [10,11].
Poly(lactic-co-glycolic acid) (PLGA), a copolymer of polylactic acid (PLA) and polyglycolic acid (PGA), is a biocompatible, biodegradable, and nontoxic polymer. PLGA, which is one of the most widely used polymers in drug delivery systems, shows the potential to control sustained release [12-14]. It is approved by the FDA and used in various formulations for drug delivery [15-17] and has also demonstrated tumor targeting [18,19]. For NPs, the material used in the surface plays a crucial role in the controlled release, stability, and therapeutic efficacy. In clinical practice, many polymers have been used in the surface of NPs such as poly(ethylene glycol) (PEG) [20,21], methoxy poly(ethylene glycol) (MPEG) [22], 1,2-dilauroyl-sn-glycero-3-phosphocholine (DLPC) [23], and d-α-tocopherol polyethylene glycol 1000 succinate (TPGS [vitamin E TPGS]) [23]. TPGS was firstly introduced by Mu and Feng [24] as an emulsifier for NPs of paclitaxel. Recently, TPGS has been widely used to improve the aqueous solubility of hydrophobic drugs [25]. TPGS is formed by the esterification of vitamin E succinate with polyethylene glycol 1000, and its structure consists of a hydrophilic polar head and a lipophilic alkyl tail. Therefore, it can be used to solubilize both hydrophilic and hydrophobic drugs and is widely used to enhance the water solubility of poorly water-soluble drugs. Wang et al. [26] reported that by using TPGS in the surface of PLGA-NPs, the sustained release of drug from NPs can be controlled and thereby enhanced the encapsulation efficiency [27]. In addition, TPGS exhibited toxicity against cancer cells [28] and nontoxicity to normal cells and tissues [29,30], TPGS can enhance the cytotoxicity, cellular uptake [31-33], and the oral bioavailability [34] of the drug, thereby improving therapeutic efficacy of anticancer drugs in the formulation.
In this study, DTX-NPs were prepared by nanoprecipitation method using PLGA as a polymer and TPGS as a surfactant. The optimal percentage of PLGA and TPGS was selected based on the particle size, polydispersity index (PDI) and zeta potential. The morphology was observed using transmission electron microscopy (TEM), whereas differential scanning calorimetry (DSC) and Fourier-transform infrared spectroscopy (FTIR) were used to evaluate the physicochemical interactions. The in vitro release of DTX from the DTX-NPs was analyzed in phosphate-buffered saline (PBS, pH 7.4) containing 0.5% (w/v) Tween 80. The in vitro therapeutic effects of DTX-NPs were evaluated based on anticancer effect and cellular uptake. The differential sensitivity of NPs between MDA-MB-231 and MCF-7 breast cancer cells was also investigated.
METHODS
Chemicals
DTX was obtained from Tokyo Chemical Industry Co., Ltd (Tokyo, Japan). TPGS and PLGA were purchased from Sigma-Aldrich (St. Louis, MO, USA). Acetone and acetonitrile were purchased from Samchun Chemicals (Pyeongtaek, Korea). Breast cancer MDA-MB-231 and MCF-7 cell lines were obtained from the Korean Cell Line Bank. Roswell Park Memorial Institute (RPMI) 1640 medium, fetal bovine serum (FBS), trypsin, and antibiotics were purchased from Hyclone (Logan, UT, USA). Dimethylsulfoxide (DMSO) and 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) were purchased from Sigma-Aldrich.
Preparation of DTX-NPs
DTX-NPs were prepared using the nanoprecipitation method [35] with modifications. Briefly, DTX and PLGA were dissolved in 2 ml acetone, sonicated for 10 min and then dropped into TPGS solution at a rate of 20 ml/h using a syringe pump. The solvent was removed by stirring at 500 rpm. DTX-NPs were collected by centrifugation at 12,000 rpm for 30 min and washed three times with distilled water (DW) to remove the residual excipients. The final solid was suspended in 2 ml DW. Coumarin-6-loaded NPs were prepared using same method.
Particle size and zeta potential
The particle size distribution and surface charge of the DTX-NPs were measured in triplicate using Zetasizer Nano-90 and Zetasizer Nano-Z (Malvern Instruments Ltd., Malvern, UK), respectively [15].
Drug encapsulation efficiency (EE) and drug loading (DL)
The percentage EE and DL of DTX were measured using high performance liquid chromatography (HPLC) with a Capcell Pak C18 column (150 × 4.6 mm, 5 µm particle size; Osaka Soda, Osaka, Japan) [15]. The mobile phase consisted of acetonitrile: water (70:30, v/v) and the flow rate was 1 ml/min. The quantity of DTX was determined by measuring the UV absorbance at a wavelength of 232 nm with injection volume of 20 µl.
Briefly, the NPs samples were dissolved in acetonitrile and the drug content was calculated using a calibration curve (coefficient of determination [R2] = 0.997). The samples were measured in triplicate and the percentage of EE and DL were calculated as the following equation:
Morphological observation
The micrograph of the DTX-NPs was evaluated using TEM (model TECNAI G2 F30 S-Twin; FEI, Hillsboro, OR, USA) at an accelerating voltage of 300 kV [15]. The DTX-NPs were placed onto the TEM grid and dried for 24 h. The NPs size was determined using ImageJ software (National Institutes of Health, Bethesda, MD, USA).
DSC and FTIR
The endothermic melting temperatures of DTX, PLGA, TPGS, and DTX-NPs were obtained using a TGA/DSC1 (Mettler-Toledo GmbH, Greifensee, Switzerland) [36]. The scan range of the samples was from 20 to 250°C at a rate of 10°C/min.
FTIR (Alpha-P; Brucker Optik, Ettligen, Germany) [36] was used to evaluate the chemical interactions of DTX, PLGA, TPGS, and DTX-NPs at a spectra ranging from 500 to 4,000 cm–1.
In vitro drug release
The micrograph of the DTX-NPs was evaluated using TEM (model TECNAI G2 F30 S-Twin; FEI, Hillsboro, OR, USA) at an accelerating voltage of 300 kV [15]. The DTX-NPs were placed onto the TEM grid and dried for 24 h. The NPs size was determined using ImageJ software (National Institutes of Health, Bethesda, MD, USA).
In vitro anticancer effect
MDA-MB-231 and MCF-7 cells were cultured in RPMI 1640 medium with 10% (v/v) FBS and 1% antibiotics at 37 ± 0.5°C in an atmosphere containing 5% CO2. The in vitro anticancer effect was evaluated by MTT assay. Briefly, MDA-MB-231 and MCF-7 cells were seeded in 96-well plates at a density of 1 × 104 cells per well and incubated overnight to allow the cells to adhere. After incubation, the growth medium was removed and cells were treated with DTX and DTX-NPs at 0.2, 0.5, 5, 10, and 20 μg/ml in the medium. After incubation for 24 h, the cells were washed with PBS, treated with MTT solution (0.5 mg/ml in medium) for 3 h, the MTT solution was removed, and then 100 μl DMSO was added to dissolve the purple formazan crystals. The absorbance was measured at 570 nm using a microplate reader (Infinite M200 PRO; Tecan Trading AG, Männedorf, Switzerland). The cell viability was calculated as following equation:
In vitro quantitative cellular uptake of NPs
In vitro quantitative cellular uptake of NPs was evaluated using microplate reader. Briefly, MDA-MB-231 and MCF-7 cells were seeded in 24-well plates at a density of 1 × 105 cells per well. After incubation for 24 h, the medium was replaced by coumarin- 6-loaded PLGA-NPs (10 μg/ml). Fluorescence-based quantitative technique was used to evaluate cellular uptake of NPs. Coumarin-6 has been used as a hydrophobic fluorescent dye in the in vitro and in vivo monitoring of NPs based delivery system. It is often used as a tracer marker of the PLGA NPs. In this study, coumarin-6 was selected as a fluorescent dye to mimic the characteristics of DTX to load in the NPs, both DTX and coumarin-6 are insoluble in water. After 0.5-, 1-, 2-, and 4-h incubation, the cells were washed three times with cool PBS and lysed with Trion X-100 (0.5%, w/v) solution. The fluorescence intensities were measured using a multimode microplate reader (Tecan Trading) at excitation wavelength of 440 nm and emission wavelength of 520 nm, respectively. Protein was quantified using bicinchoninic acid assay kit (Thermo Fisher Scientific, Waltham, MA, USA), and the fluorescence intensities were normalized to the total protein content.
RESULTS
Optimization of TPGS and PLGA composition
PLGA is a copolymer with high biodegradability and biocompatibility that is usually used as a drug delivery carrier in the preparation of formulations [12]. It is hydrolyzed to lactic acid and glycolic acid, which can be easily metabolized by the Krebs cycle in the body. To optimize the percentage of TPGS in the test formulations, a PLGA solution (1%, w/v) was prepared in 2 ml acetone, dropped into 35 ml TPGS solution (0.05, 0.1, 0.5, 1, 2, and 3%, w/v) using syringe pump at a rate of 20 ml/h while stirring at 500 rpm, and kept overnight for solvent evaporation.
The NPs were collected by centrifugation at 12,000 rpm for 30 min and washed three times with DW. The collected NPs were then dispersed in 2 ml DW. As shown in Table 1, the NPs formulation with 1% TPGS showed the smallest particle size (155.7 ± 1.7 nm) with PDI and zeta potential of 0.19 ± 0.01 and –27.3 ± 0.55 mV, respectively. Therefore, TPGS (1%) was selected from the results.
The PLGA was prepared at 1%, 2%, 3%, 5%, and 7% (w/v) for screening and optimizing the percentage using the same method used for TPGS, which was used at 1% (w/v). As shown in Table 2, 1% PLGA, which produced the smallest particle size (as above), was considered as the optimal concentration and, thus, was selected for NPs preparation.
EE and DL
DTX-NPs were prepared as described in the methods, and DTX was used at 3, 6, and 9 mg to optimize the amount. As shown in Table 3, the zeta potential was not significantly different among the formulations, ranging from –26.7 ± 0.46 to –29.9 ± 1.50 mV. The smallest size (160.5 ± 3.0 nm) was obtained with 3 mg DTX, whereas the largest size (205.9 ± 8.2 nm) was obtained with 9 mg DTX. The EE (%) decreased from 81.3 ± 1.85% to 50.2 ± 2.54% when the amount of DTX increased from 3 to 9 mg, respectively. Similarly, the DL (%) decreased from 10.6 ± 0.24 to 5.19 ± 0.26% when the amount of DTX increased from 3 to 9 mg, respectively. Based on these results, the formulation with 3 mg DTX was selected as the final NPs preparation.
TEM, DSC, and FTIR
The morphology of the DTX-NPs was analyzed using TEM, and shown in Fig. 1, the NPs morphology was spherical. The TEM images shows the size of NPs is about 100 nm differed from that of DLS results. It could be explained by the difference in sample preparation for each instrument. Dried samples (dehydrated) were used for TEM, while suspension samples (hydrated) were used for Zetasizer. Thus, the particle sizes of the samples in TEM would be smaller than those in Zetasizer [15].
Fig. 2A shows the DSC thermograms of DTX, PLGA, TPGS, and the DTX-NPs, which were important for evaluating the interactions between DTX and polymers. The melting temperatures of DTX, PLGA, and TPGS were 164.05, 53.07, and 37.92°C, respectively. Furthermore, the DTX peak did not appear in the DTX-NPs formulation; the reason may be because DTX was interacted with the polymer in the formulation or due to a small amount of DTX in the formulation. This will be clarified in the FTIR results.
To evaluate the interactions between DTX and polymers, FTIR was scanned from 500 to 4,000 cm–1. The interactions were indicated by the shifting of peaks from their position in the formulation. The FTIR spectra of DTX, PLGA, TPGS, and DTX-NPs are presented in Fig. 2B. From Fig. 2B, the major peaks of pure DTX appeared at 3,464.8 cm–1 for O–H stretch, 1,703.2 cm–1 for C=O stretch, 1,492.6 cm–1 for benzene ring, 1,370.1 cm–1 for C–H stretch, and 1,123.7 cm–1 for C–O stretch. This result was similar to the results of Li and Zuo [37] and Kulhari et al. [38]. In the study by Li and Zuo [37], FTIR spectra were obtained at 3,462 cm–1 (O–H stretch), 1,465 cm–1 (benzene ring), and 1,344 cm–1 (C–H stretch). In the study by Kulhari et al. [38], the FTIR spectra were obtained at 3,480 cm–1 (O–H stretch), 1,741 cm–1 (C=O stretch), and 1,109 cm–1 (C–O stretch). The main peaks of PLGA appeared at 1,752.6 cm–1 in relation to the stretching vibration of C=O ester bond, 1,168.3 for C–O stretch, and 1,089.1 cm–1 in relation to the stretching vibration of C–O–C. This result was similar to that of a previous study (1,758, 1,747 cm–1 for C=O ester bond, 1,182 for C–O stretch, and 1,082 and 1,088 cm–1 for C-O-C) [39-41]. The major peaks of vitamin E TPGS appeared at 2,884.1 cm–1 for O–H stretch, 1,737.3 cm–1 for C=O stretch, 1,463.9 cm–1 for benzene ring, 1,342.1 cm–1 for C–H stretch, and 1,103.6 for C–O stretch. The main peaks of DTX-NPs appeared at 2,880.3 cm–1 for C–H stretch, 1,762.9 cm–1 for C=O stretch, 1,468.1 cm–1 for benzene ring, 1,341.8 cm–1 for O–H stretch, and 1,097.8 cm–1 for C–O stretch.
The O–H stretching peak did not appear in DTX-NPs. The peak of C=O stretching shifted from 1,703.2 cm–1 (DTX) to 1,762.9 cm–1 (DTX-NPs). The peak of the benzene ring stretching shifted from 1,492.6 cm–1 (DTX) to 1,468.1 cm–1 (DTX-NPs). The peak of C–H stretching shifted from 1,370.1 cm–1 (DTX) to 1,341.8 cm–1 (DTX-NPs). The peak of C–O stretching shifted from 1,123.7 cm–1 (DTX) to 1,097.8 cm–1 (DTX-NPs). These shifts in the peaks indicate the interactions between DTX and the polymer in NPs formulations.
In vitro drug release
The in vitro drug release was studied for 24 h using the dialysis method. Because of the poor solubility of DTX in the buffer solution, 0.5% (w/v) Tween 80 was used to simulate sink conditions. The amount of DTX released from the NPs was measured using HPLC, and the in vitro release profiles are shown in Fig. 3. Pure DTX was quickly released and reached a cumulative release of 92.1 ± 0.88% after 12 h, whereas DTX showed a slower release profile from DTX-NPs (32.9 ± 4.96%) after 12 h, which was approximately 2.8 times slower than that of the pure DTX [15].
In vitro anticancer effect and cellular uptake of NPs
The anticancer effect of DTX-NPs at concentrations of 0.2, 0.5, 5, 10, and 20 µg/ml was evaluated in MDA-MB-231 and MCF-7 breast cancer cells by determining the percentage of cell viability using the MTT assay. The results are shown in Fig. 4, the percentage of viable cells was reduced with increasing concentrations of DTX, and the DTX-NPs exhibited a higher anticancer effect at all concentrations than that of the pure DTX for both MDA-MB-231 and MCF-7 cells (Fig. 4A, B, respectively). The enhanced anticancer effect of DTX-NPs may be due to sustained release of DTX from NPs. The viability of the DTX-treated MDA-MB-231 cells decreased from 89.8 ± 0.62% to 50.5 ± 3.24%, whereas that of cells treated with DTX-NPs decreased from 72.2 ± 3.96% to 37.5 ± 0.50% by increasing the concentrations of DTX from 0.2 to 20 µg/ml, respectively. For the pure DTX-treated MCF-7 cells, the viability decreased from 91.5 ± 10.4% to 48.1 ± 0.17%, whereas the DTX-NPs-treated cells showed a decrease in viability from 71.2 ± 0.57% to 30.3 ± 1.13% with an increase in DTX concentration from 0.2 to 20 µg/ml, respectively. The anticancer effect of DTX-NPs in MDA-MB-231 and MCF-7 cells was 1.26- and 1.34-fold higher, respectively, than that of pure DTX at 20 µg/ml. Although the change in the percentage of cell viability after 24 h is similar between MDA-MB-231 cells and MCF-7 cells, the sensitivity of DTX-NPs was different in MDA-MD-231 cells and MCF-7 cells. As the results, the anticancer effect of DTX-NPs in MCF-7 cells was 1.12-fold higher than that in MDA-MB-231 cells at 20 µg/ml. In this study, the different sensitivity of DTX-NPs to MCF-7 and MDA-MB-231 cells was more clarified in the result of half-maximal inhibitory concentration (IC50), as below.
The different sensitivity of DTX-NPs to MDA-MB-231 and MCF-7 cells became more evident in the results of IC50. IC50 was measured using GraphPad Prism 5 software (San Diego, CA, USA) and the result was shown in Table 4. For MDA-MB-231 cells, the IC50 values were 14.7 ± 1.14 and 3.75 ± 1.03 µg/ml for DTX and DTX-NPs, respectively. The IC50 values of DTX-NPs was 3.92-fold lower than that of DTX. For MCF-7 cells, the IC50 values were 11.0 ± 1.08 and 1.63 ± 1.03 µg/ml for DTX and DTX-NPs, respectively. The IC50 values of DTX-NPs was 6.75-fold lower than that of DTX. These results showed that the DTX-NPs formulation improved the anticancer effect of DTX. In addition, the IC50 of DTX-NPs in MCF-7 cells was 2.3-fold lower than that in MBA-MB-231 cells, indicating that the DTX-NPs formulation was more sensitive in MCF-7 cells than MDA-MB-231 cells.
The cellular uptake results of coumarin-6-loaded PLGA-NPs in MDA-MB-231 and MCF-7 cells are shown in Fig. 5. The results show that cellular uptake increased as the incubation time increased. The cellular uptake in MDA-MB-231 cells was 221.3 ± 19.7, 239.3 ± 54.7, 539.9 ± 33.5, and 763.7 ± 42.5 (fluorescent intensity/µg protein) at 0.5, 1, 2, and 4 h, respectively, whereas corresponding values in MCF-7 cells were 253.3 ± 72.5, 273.7 ± 175.9, 695.5 ± 78.3, and 898.7 ± 204.1 (fluorescent intensity/µg protein), respectively. The cellular uptake of the NPs in MCF-7 cells was higher than that in MDA-MB-231 cells at all-time points. At 0.5, 1, 2, and 4 h, the cellular uptake of NPs in MCF-7 cells was 1.1-, 1.1-, 1.3-, and 1.2-fold higher than that in MDA-MB-231 cells. In addition, the cellular uptake of coumarin-6-loaded PLGA-NPs in MCF-7 cells was significantly higher (p < 0.05) than that in MDA-MB-231 cells at 2 and 4 h. These results indicate that the cellular uptake of the NPs in MDA-MB-231 and MCF-7 breast cancer cells increased with time and was significantly (p < 0.05) higher in MCF-7 cells than in MDA-MB-231 cells after 2 and 4 h.
Stability
The stability of a formulation played an important role in clinical therapy of anticancer drugs [42]. In this study, the stability of the DTX-NPs sample was analyzed after storage at 4°C by measuring the particle size, PDI, and zeta potential every 2 weeks for 3 months, and the results are shown in Fig. 6. The results are expressed as means ± SD. The results illustrated in Fig. 6 show that all three factors of the DTX-NPs were stable with a very small change over 3 months. The initial particle size of the DTX-NPs was 160 ± 3.0 nm, and it remained stable at 166.9 ± 3.8 nm after 3 months. The zeta potential changed slightly after the first 2 weeks (from –26.7 ± 0.46 mV to –22.8 ± 0.46 mV) and then remained stable during the storage time (–21.6 ± 1.3 mV after 3 months) [43]. This indicates the good stability of the sample.
DISCUSSION
In this study, the NPs were prepared with 1% of PLGA and 1% of TPGS. Based on the Table 3, the particle size of the NPs increased with increasing amount of DTX; the increase in particle size may have been due to the increase of drug amount in the nanoformulation [44]. In a previous study, the particle size increased with an increase in the drug amount from 0.25% to 1% (w/v), whereas the EE decreased along the same drug amount range [45]. In fact, only a fixed amount of drug can be incorporated with a fixed amount of polymer in the formulation. Increasing the amount of drug resulted in a more viscous dispersed phase, which increased the particle size. The EE (%) and DL (%) decreased with the increase of DTX amount. The EE decreased with increasing drug content, which may be due to the increased drug diffusion to the external phase caused by a greater flux at the higher drug content during the NPs formation process [45,46]. Therefore, the final DTX-NPs were prepared with 3 mg of DTX, 1% PLGA, and 1% TPGS.
The release profile of pure DTX was very fast, whereas DTX showed sustained release from the NPs formulations. The sustained release behavior may be due to the slow degradation of the PLGA polymer and strong interaction between the drug and polymer [47,48]. Therefore, the DTX-NPs showed sustained release, which could be clinically beneficial. Generally, a high or repeat dose is required to obtain the desired effect in the treatment of cancer, resulting in many side effects because of the toxicity of anticancer drugs. Therefore, the dose and frequency of drug administration could be reduced by preparing DTX-NPs with sustained release. Moreover, the maintenance of drugs in the body after administration of DTX-NPs could improve the drug pharmacokinetics following both oral and parenteral administration.
The in vitro anticancer effect results indicated that the anticancer effect of DTX-NPs in MDA-MB-231 and MCF-7 breast cancer cells was higher than that of pure DTX. Moreover, the anticancer effect of DTX-NPs was higher in MCF-7 cells than in MDA-MB-231 cells, suggesting the sensitivity of DTX-NPs was higher in MCF-7 cells than MDA-MB-231 cells. The different sensitivity of NPs to MCF-7 and MDA-MB-231 cells may due to the differences in the expression of breast cancer-related proteins. In practice, MCF-7 and MDA-MB-231 are the most common cell lines used in breast cancer research. They belong to subtypes of metastatic lobular carcinoma and originated from pleural effusions. However, there are difference between two cell lines. MCF-7 is a hormone receptor (estrogen, ER; progesterone, PR) positive breast cancer cell. It is widely studied model for hormone-dependent human breast cancer. MDA-MB-231 is a triple-negative breast cancer cell (lack of ER and PR). MDA-MB-231 cell line provides a model for human breast cancer, which exhibits an estrogen-independent state and does not express estrogen receptor. The lack of ER and PR in MDA-MB-231 is the key for the different sensitivity between MCF-7 and MDA-MB-231. Besides, another difference between MCF-7 and MDA-MB-231 is MCF-7 represents for luminal epithelial phenotype while MDA-MB-231 represents for mesenchymal phenotype. In addition, the different sensitivity of these two cell lines MCF-7 and MDA-MB-231 depends on the drug used.
The cellular uptake of the NPs was evaluated by loading coumarin-6 into the PLGA-NPs, which were then incubated with MCF-7 and MDA-MB-231 breast cancer cells. The ratio of the fluorescence intensities to total protein content was calculated. The cellular uptake of NPs was confirmed by coumarin-6-loaded NPs and it is believed that of DTX-loaded NPs was also increased because we already confirmed the in vitro anticancer effect of DTX-loaded NPs. The enhanced cellular uptake of DTX-NPs in breast cancer cells improved intracellular accumulation of DTX and increased cytotoxic effect of DTX. DTX-NPs showed more cytotoxic and higher cellular uptake than DTX alone. Furthermore, the sensitivity of DTX-NPs to MDA-MB-231 cells and MCF-7 cells was different. The sensitivity of DTX-NPs in MCF-7 cells was higher than that of MDA-MB-231 cells.
In conclusion, DTX-NPs were successfully formulated using PLGA as the polymer and TPGS as the surfactant with high encapsulation, low PDI, and negative zeta potential. The TEM results revealed that the NPs had a spherical morphology. The in vitro release analyses showed the sustained release of DTX from the DTX-NPs, which also exhibited a higher anticancer effect on breast cancer cells than that of the pure DTX. As a result of visual experiments, the quantitative cellular uptake of coumarin-6-loaded PLGA-NPs was higher than DTX alone. The anticancer effect and cellular uptake results showed the different sensitivity of DTX-NPs between MDA-MB-231 cells and MCF-7 cells. The sensitivity of DTX-NPs on MCF-7 cells was significantly higher than on MDA-MB-231 cells. Moreover, the DTX-NPs showed stability of particle size, PDI, and zeta potential after 3 months. In conclusion, our study indicates that the DTX-NPs formulation is a potential candidate for breast cancer therapy with different sensitivity between MDA-MB-231 cells and MCF-7 cells. To confirm these findings, further studies are needed in various cancer cell lines and in vivo.
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