Thiolated chitosan-modified PLA-PCL-TPGS nanoparticles for oral chemotherapy of lung cancer
© Jiang et al.; licensee Springer. 2013
Received: 20 December 2012
Accepted: 19 January 2013
Published: 9 February 2013
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© Jiang et al.; licensee Springer. 2013
Received: 20 December 2012
Accepted: 19 January 2013
Published: 9 February 2013
Oral chemotherapy is a key step towards ‘chemotherapy at home’, a dream of cancer patients, which will radically change the clinical practice of chemotherapy and greatly improve the quality of life of the patients. In this research, three types of nanoparticle formulation from commercial PCL and self-synthesized d-α-tocopheryl polyethylene glycol 1000 succinate (PLA-PCL-TPGS) random copolymer were prepared in this research for oral delivery of antitumor agents, including thiolated chitosan-modified PCL nanoparticles, unmodified PLA-PCL-TPGS nanoparticles, and thiolated chitosan-modified PLA-PCL-TPGS nanoparticles. Firstly, the PLA-PCL-TPGS random copolymer was synthesized and characterized. Thiolated chitosan greatly increases its mucoadhesiveness and permeation properties, thus increasing the chances of nanoparticle uptake by the gastrointestinal mucosa and improving drug absorption. The PLA-PCL-TPGS nanoparticles were found by FESEM that they are of spherical shape and around 200 nm in diameter. The surface charge of PLA-PCL-TPGS nanoparticles was reversed from anionic to cationic after thiolated chitosan modification. The thiolated chitosan-modified PLA-PCL-TPGS nanoparticles have significantly higher level of the cell uptake than that of thiolated chitosan-modified PLGA nanoparticles and unmodified PLA-PCL-TPGS nanoparticles. In vitro cell viability studies showed advantages of the thiolated chitosan-modified PLA-PCL-TPGS nanoparticles over Taxol® in terms of cytotoxicity against A549 cells. It seems that the mucoadhesive nanoparticles can increase paclitaxel transport by opening tight junctions and bypassing the efflux pump of P-glycoprotein. In conclusion, PLA-PCL-TPGS nanoparticles modified by thiolated chitosan could enhance the cellular uptake and cytotoxicity, which revealed a potential application for oral chemotherapy of lung cancer.
Lung cancer continues to be one of the most common fatal cancers worldwide. Oral chemotherapy is quickly emerging as an appealing option for cancer patients because it is less stressful, being that the patient will have less hospital visits and can still maintain a close relationship with health care professionals . These features make oral delivery especially attractive for mass immunization and self-administration of medications. In addition, oral chemotherapy could maintain a sustained moderate concentration of the drug in the circulation to achieve a prolonged exposure of cancerous cells to the drug as well as to avoid high peak above maximum tolerable concentration. This will increase the therapeutic efficacy and decrease the side effects. However, most anticancer drugs especially those with excellent antitumor effects such as paclitaxel are poorly bioavailable. This is because oral administration of taxoids (paclitaxel and docetaxel) presents an extremely low bioavailability, with a less than 1% extent of oral absorption [2, 3]. The low systemic exposure of oral paclitaxel is, at least in part, due to their high affinity for P-glycoprotein (P-gp) multidrug efflux pump in the mucosa of the gastrointestinal (GI) tract [4, 5]. P-gp in the mucosa of the gastrointestinal tract may limit the absorption of the orally administered taxanes and mediate their direct excretion into the intestinal lumen . First-pass metabolism by cytochrome P450 isoenzymes in the gut wall and/or in the liver may also play a role in the low oral bioavailability of paclitaxel and docetaxel [6, 7]. Alternative pharmaceutical methods to improve oral bioavailability of taxoids and other antitumor agents are currently under intense investigation [2, 8–10]. The general medical approach is to make use of P-gp/P450 inhibitors such as cyclosporine A to suppress the elimination process [9, 10]. However, cyclosporine A may cause severe damage to the immune system of the body and, thus, create severe complications during cancer treatment. Polymeric nanoparticles are highly attractive from the pharmaceutical point of view due to their desirable properties such as biocompatibility, biodegradability, and controlled release. Furthermore, polymeric nanoparticles could avoid recognition by the P-gp efflux pump and, thus, have a strong potential to enhance the oral bioavailability of poorly absorbed drugs [11–13]. Their small size and their large specific surface area favor their absorption compared to larger drug carriers. In addition, polymeric nanoparticles can protect encapsulated drugs from luminal degradation as well as gut-wall metabolism . Moreover, they could reduce the multi-drug resistance (MDR) that characterizes many anticancer drugs by a mechanism of internalization of the drug, reducing its efflux from cells mediated by the P-gp. It seems to be commonly accepted that particle surface properties are utmostly important for their uptake by intestinal epithelial cells. Therefore, many methodologies and innovative techniques have been developed to enhance the intestinal absorption of particles, either by altering their surface properties or by conjugating a targeting molecule at their surface . In this research, our group proposed a new type of polymeric nanoparticles, i.e., biodegradable poly(lactide-co ε-caprolactone)-d-α-tocopheryl polyethylene glycol 1000 succinate (PLA-PCL-TPGS) nanoparticles modified with thiolated chitosan for oral chemotherapy using paclitaxel as a therapeutic agent due to its high therapeutic efficacy against a broad spectrum of tumors and its great commercial success as one of the best-selling antitumor therapeutic drugs.
d,l-lactide (3,6-dimethyl-1,4-dioxane-2,5-dione, C6H8O4) and d-α-tocopheryl polyethylene glycol 1000 succinate (C33O5H54 (CH2CH2O)23) were purchased from Sigma-Aldrich (St. Louis, MO, USA). ε-caprolactone (CL) were obtained from Acros Organics (Geel, Belgium). Thiolated chitosan (Mw 33000 Da) was from NanoMed Biotech Co. Ltd (Shenzhen, China). Poly(ε-caprolactone) (PCL) (MW 42000 Da), and stannous octoate (Sn(OOCC7H15)2) were also purchased from Sigma (St. Louis, MO, USA). Paclitaxel powder of purity 99.9% was from BioOne Biotech Co. Ltd (Shenzhen, China). Fetal bovine serum was received from Gibco (Life Technologies, AG, Switzerland). Methanol and acetonitrile were obtained from EM Science (Mallinckrodt Baker, USA). Deionized (DI) water produced by Millipore Water Systems (Millipore Corporation, Billerica, USA) was utilized throughout all experiments.
PLA-PCL-TPGS random copolymers were synthesized from ε-caprolactone, lactide, and TPGS in the presence of stannous octoate as a catalyst via ring opening polymerization. In short, pre-weighted amounts of ε-caprolactone, lactide, TPGS, and one drop of stannous octoate were added in a flask. The mixture was heated to 145°C and allowed to react for approximately 16 h. Synthesis was carried out under an oxygen- and moisture-free environment. The product was dissolved in dichloromethane (DCM) and then precipitated in excess cold methanol to remove unreacted monomers and TPGS. The final product was collected by filtration and dried under vacuum. The TPGS content and number-averaged molecular weight of the copolymer was determined by 1H NMR in CDCl3 at 300 Hz (Bruker ACF300, Bruker AXS Pte Ltd., Singapore).
Nanoparticles were prepared by a modified solvent extraction/evaporation technique [29, 30]. In brief, 11 mg of paclitaxel powder and 100 mg of PLA-PCL-TPGS copolymer were weighed and dissolved in 6 ml DCM. The organic solution was immediately poured into 100 ml of 0.03% (w/v) TPGS solution under mild stirring. The mixture was then sonicated for 90 s at 30 W output to form water-in-oil emulsion. The emulsion was further evaporated under ambient conditions overnight to remove DCM. The nanoparticles were harvested by centrifugation at 80,000×g for 15 min and then washed three times to remove the emulsifiers and unentrapped drug. The resulting nanoparticles were finally resuspended in 5 ml of deionized water and lyophilized. The PLA-PCL-TPGS nanoparticles was further modified by thiolated chitosan using a method described previously . Preweighed thiolated chitosan was dissolved in deionized water at a concentration of 0.5 mg/ml. The nanoparticles were suspended in thiolated chitosan solution at a concentration of 9.5 mg/ml by sonication at 30 W power output for 30 s in an ice bath, and then were collected by centrifugation at 80,000×g for 15 min. The coumarin-6-loaded nanoparticles were prepared by encapsulation of 0.1% (w/v) coumarin-6 instead of paclitaxel. Thiolated chitosan-modified PCL nanoparticles were fabricated by the same procedure.
Particle size and size distribution of nanoparticles were measured using dynamic light scattering on a Malvern Zetasizer Nano-ZS90 (Malvern Instruments, Worcestershire, UK). The lyophilized nanoparticles were diluted with DI water before measurement. Surface charge of the nanoparticles was determined by laser Doppler anemometry using a Zetasizer Nano Series (Malvern Instruments). All measurements were done in triplicate.
The morphology of nanoparticles was characterized by field emission scanning electron microscopy (FESEM; ZEISS 77 SUPRA 40VP, Carl Zeiss, Co., Ltd., Shanghai, China) at 5.0 kV electron high tension. To prepare samples for the FESEM observations, a drop of the particle suspension was placed on a grid or a stud, and the supernatant liquid was removed with a capillary after the particles were allowed to settle. The particles were then coated with platinum layer for 30 s.
The encapsulation efficiency (EE) and the actual drug loading of the nanoparticles were measured by high-performance liquid chromatography (LC 1100, Agilent Technologies, Santa Clara, USA) as described before [31, 32]. In short, dried nanoparticles (5 mg) were dissolved in 1 ml of methylene chloride under vigorous vortex. The organic solution was transferred to 5 ml of mobile phase consisting of acetonitrile and deionized water (50:50, v/v). Methylene chloride was evaporated under a nitrogen stream until a clear solution obtained. The samples were then used for high-performance liquid chromatography (HPLC) analysis. The column effluent was monitored at 227 nm with a UV–vis detector. The standard size HPLC column (4.6 × 250 mm) is run at a flow rate of 1 mL/min. The drug encapsulation efficiency was defined as the percentage of the drug loaded in the final product. All these experiments were done in triplicates.
Accurately weighted aliquots of drug-loaded nanoparticles (15 mg) were suspended in 5 ml release medium (PBS pH 7.4 containing 0.1% w/v Tween 80). The use of Tween 80 in the release media was able to increase the solubility of drug in the PBS and avoided the binding of drug to the tube wall. The nanoparticle suspension was transferred into a dialysis tubing membrane which is sealed at one end with a clamp. The sealed dialysis bag was placed into a centrifuge tube and immersed in 15-ml release medium. The centrifuge tube was placed in an orbital water bath shaking at 130 rpm at 37.0°C. A 10 ml aliquots of samples was periodically removed for HPLC analysis and replaced with fresh medium. The samples were extracted with 2 ml methylene chloride and reconstituted in 5 ml mobile phase. Methylene chloride was evaporated under a nitrogen stream until a clear solution was obtained. The analysis procedure was the same as for the determination of drug EE.
Caco-2 cells which were obtained from the American Type Culture Collection (Manassas, USA) were used in this research to simulate the gastrointestinal barrier for oral chemotherapy. The cells were grown in tissue culture flasks maintained at 37°C in a humidified, 5% CO2 atmosphere. The medium, Dubelco's modified essential medium (DMEM) supplemented with 100 μg/ml streptomycin and 20% fetal bovine serum, was freshened once every 3 days. After reaching 70% to 90% confluence, the cells were harvested with 0.25% of trypsin-EDTA solution (Invitrogen, Corporation, Grand Island, USA) and cultured in 96-well black plate (Corning Inc., Corning, USA) at the density of 1.3 × 104 cells per well; when the cells reached confluence, the cells were equilibrated with HBSS buffer at 37°C for 60 min and then incubated with coumarin-6-loaded nanoparticle suspension medium. The nanoparticles were well-dispersed in the culture medium at concentrations of 100, 250, and 500 μg/ml. Nanoparticle dispersions were incubated at 37°C in a 5% CO2 atmosphere for 2 h. After incubation with the corresponding nanoparticles, the suspension was removed from the wells, and the cell monolayers were rinsed three times with 50 μl cold PBS (pH 7.4) to remove any traces of nanoparticles left in the wells. After that, the cells were lysed with 50 μl of 0.5% (w/v) Triton-X 100 in 0.2 N NaOH solution (Sigma-Aldrich, MO, USA). The fluorescence intensity presented in each well was then measured on a GENios Lueifcrase microplate reader (Tecan Group Ltd., Männedorf, Switzerland) with excitation wavelength at 430 nm and emission wavelength at 485 nm. Cellular uptake efficiency was expressed as the percentage of cell-associated fluorescence vs. that present in the positive control. Culture of human lung cancer cell lines A549 cells and their uptake of the coumarin-6-loaded nanoparticles were performed using the same procedure.
Caco-2 cells were reseeded in the Lab-Tek chambered cover glass system (Nalge Nunc International, Rochester, USA). After the cells were incubated with 250 μg/ml coumarin-6-loaded thiolated chitosan-modified PLA-PCL-TPGS particle suspension at 37°C for 2 h, the cells were rinsed with cold PBS buffer for three times and then fixed with 70% ethanol solution for 20 min. The cells were further rinsed twice with PBS and then counter-stained with 4′,6-diamidino-2-phenylindole dihydrochloride (DAPI; Fluka, Buche, Switzerland) for the visualization of the cell nuclei. The cell monolayer was rinsed twice with PBS solution and mounted using the Dako fluorescent mounting medium (Dako, Carpinteria, USA) to be observed by confocal laser scanning microscope (CLSM; Olympus Fluoview FV-1000, Olympus Optical. Co., Ltd., Tokyo, Japan). The images of the cells were determined with differential interference contrast channel, and the images of coumarin-6-loaded nanoparticles and the nuclei of the cells stained by DAPI were recorded with the following channels: blue channel (DAPI) with excitation at 340 nm and green channel (coumarin-6) with excitation at 488 nm.
A549 cells were counted and seeded in 96-well plates at a density of 0.5 × 104 cells per well and incubated overnight to allow cell attachment. The cells were incubated with drug-loaded PLA-PCL-TPGS nanoparticle suspension, thiolated chitosan-modified PLA-PCL-TPGS nanoparticles, and Taxol® (Bristol-Myers Squibb, New York, USA) at 0.25, 2.5, 12.5, and 25 μg/ml equivalent paclitaxel concentrations and blank thiolated chitosan-modified PLA-PCL-TPGS nanoparticles with the same amount of nanoparticles for 24, 48, and 72 h, respectively. At the determined time, the formulations were replaced with fresh DMEM containing MTT (5 mg/ml), and the cells were then incubated for additional 4 h. MTT-containing medium was aspirated off, and 150 ml of DMSO was added to dissolve the formazan crystal formed by living cells. The absorbance at 570 nm was measured by a microplate reader (Model 680, Bio-Rad Laboratories, Hertfordshire, UK). Untreated cells were taken as a control with 100% viability, and cells without the addition of MTT were used as blank to calibrate the spectrophotometer to zero absorbance. IC50 values (concentration required to reduce cells viability by 50% as compared to the control cells) for each sample was calculated by curve fitting of the cell viability data. The results are expressed as mean ± SD of one representative experiment performed in triplicate, and the experiments were performed three times.
The everted sac method was chosen for the measurement of transportation of paclitaxel across the intestine barrier. It was carried out according to the slightly modified method that was described previously , as follows.
First, a section of about 5 cm of the jejunum was removed from a male rat under ketamine (50 mg/kg) and chlorpromazine (10 mg/kg) anesthesia and washed with Krebs-Ringer bicarbonate solution of pH = 7.4. This section was then gently inverted with a glass rod, and a tube was inserted in one side of the section and tied securely with tape. The other side of the intestine was tied, and 1 mL Krebs-Ringer bicarbonate solution was poured through the hypodermic needle in the tube. The gut sac was placed in a medium saturated with 95% O2, 5% CO2, and contained the test sample in Krebs-Ringer bicarbonate solution at 37°C. The test samples used include: (1) paclitaxel (1 mg) as Taxol®, and (2) thiolated chitosan-modified PLA-PCL-TPGS nanoparticles (equivalent to 1 mg of paclitaxel). In absorption studies, an O2 and CO2 mixture was bubbled into the intestinal mucosa to obtain intestinal peristaltic movement. At certain periods of time, 0.5-mL samples were drawn from inside the intestine and replaced with the same volume of fresh medium. The amount of transported paclitaxel in the samples was measured by the HPLC method.
Data were presented as the mean ± SD. Student's t test was used to assess the differences between means. A P value <0.05 was considered to indicate a significant difference.
Synthesis and characterization of PLA-PCL-TPGS random copolymer.
The structure of the synthesized PLA-PCL-TPGS copolymer was detected by 1H NMR in CDCl3. Figure 1 shows the chemical structure of PLA-PCL-TPGS random copolymer and 1H NMR spectroscopy of the PLA-PCL-TPGS copolymer. The signals at 5.2 and 1.69 ppm (peaks a and e) were assigned to the CH protons and methyl protons -CH3 of PLA segment, respectively. The peak at 3.65 ppm (peak c) was assigned to the -CH2 protons of PEO part of TPGS. The lower peaks in the aliphatic region belong to various moieties of vitamin E tails. The peaks at 4.06 (peak b), 2.31 (peak d), 1.60 to 1.70 (peak e), and 1.35 to 1.43 (peak f) were assigned to -OCH2, -COCH2, -CH2 (4 H), and -CH2 (2 H) segments of PCL, respectively . The molecular weight of the PLA-PCL-TPGS was calculated using the ratio between the peak areas at 4.06 (peak area 9.64), 5.2 (peak area 1.23), and 3.65 (peak area 3.00). The number-averaged molecular weight of the PLA-PCL-TPGS random copolymer was determined to be 33,229. The feeding ratios of ε-caprolactone, lactide, and TPGS molecular mass were 75%, 15%, and 10%, respectively. However, the ratios of ε-caprolactone, lactide, and TPGS molecular mass which were integrated into the PLA-PCL-TPGS copolymers were 87.18%, 8.17%, and 4.64%.
Effects of thiolated chitosan modification on size, encapsulation efficiency, and zeta potential
Zeta potential (mV)
Drug content (%)
Thiolated chitosan modification
203.56 ± 4.35
−19.63 ± 4.10
198.46 ± 2.49
−18.29 ± 3.25
206.15 ± 3.66
24.66 ± 4.19
219.33 ± 4.25
26.18 ± 5.02
Regarding the drug EE, it can be seen from Table 1 that the 5% thiolated chitosan-modified PLA-PCL-TPGS nanoparticles achieved much higher EE than the 5% thiolated chitosan-modified PCL nanoparticles. This might be contributed to the self-emulsification effect of TPGS segment in the PLA-PCL-TPGS copolymer [2, 8].
It can be obtained from Figure 4A that there is an increasing trend in the Caco-2 cellular uptake: TNP > CNP > UNP. The TNP resulted in 1.45-, 1.61-, and 1.67-fold higher cellular uptakes than those of CNP, and 1.48-, 1.72-, and 1.72-fold higher cellular uptakes than those of UNP at the incubated particle concentration of 100, 250, and 500 μg/ml, respectively. Figure 4A also shows that the cellular uptake was particle concentration-dependent.
Figure 4B shows that the cellular uptake efficiency of the coumarin-6-loaded TNP by A549 cells is higher than that of CNP and UNP, which is also found to be dose-dependent. The TNP resulted in 1.49-, 1.68-, and 1.93-fold higher cellular uptakes than those of CNP, and 1.31-, 1.36-, and 1.65-fold higher cellular uptakes than those of UNP at the incubated particle concentration of 100, 250, and 500 μg/ml, respectively. The positive surface charge of thiolated chitosan provided the incentive to aid drug delivery, since it is expected to ensure better interaction with the negatively charged cell membrane [31, 41, 42]. This resulted in increased retention time at the cell surface, thus increasing the chances of particle uptake and improving oral drug bioavailability .
IC50 of A549 cells after 24-, 48-, 72-h incubation with paclitaxel formulated in the Taxol®, CNP, UNP, and TNP
Incubation time (h)
Three types of nanoparticles were developed from biodegradable self-synthesized PLA-PCL-TPGS random copolymer and commercial PCL for oral delivery of antitumor agents with paclitaxel employed as a model drug, including CNP, UNP, and TNP. The design of the nanoparticle matrix material was made to take full advantages of TPGS in nanoparticle fabrication process such as high emulsification effects and high encapsulation efficiency, as well as improvement of therapeutic effects such as the reduction of P-gp-mediated MDR and superior antitumor efficacy. Thiolated chitosan could greatly increase its mucoadhesiveness and permeation properties, thus increasing the chances of nanoparticle uptake by the gastrointestinal mucosa and improving drug absorption. The data showed that the thiolated chitsoan-modified PLA-PCL-TPGS nanoparticles have significantly higher level of the cell uptake than that of thiolated chitosan-modified PCL nanoparticles and unmodified PLA-PCL-TPGS nanoparticles. In vitro cell viability studies showed advantages of the thiolated chitosan-modified PLA-PCL-TPGS nanoparticles over commercial Taxol® in terms of cytotoxicity against A549 cells. It seems that the mucoadhesive nanoparticles can increase paclitaxel transport by opening tight junctions and bypassing the efflux pump of P-gp. In short, oral chemotherapy by thiolated chitosan-modified PLA-PCL-TPGS nanoparticle formulation is an attractive alternative approach to the treatment of lung cancer.
LJ, XL, LL, QZ are Ph.D., assistant professor, associate professor, and professor, respectively. All authors are from Tianjin Key Laboratory of Biomaterial Research, Institute of Biomedical Engineering, Peking Union Medical College & Chinese Academy of Medical Sciences.
This work is supported by the Natural Science Foundation of Tianjin.
This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/2.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.