Toxicogenomics of nanoparticulate delivery of etoposide: potential impact on nanotechnology in retinoblastoma therapy
© Springer-Verlag 2010
Received: 19 October 2010
Accepted: 28 November 2010
Published: 17 December 2010
To develop a suitable formulation with high entrapment efficiency, etoposide-loaded poly(lactide-co-glycolide) nanoparticles (NPs) were formulated by single emulsion-solvent evaporation method by changing different formulation parameters such as drug loading, choice of organic solvent and percentage of emulsifier polyvinyl alcohol. The NPs showed higher entrapment efficiency, ~86% (with 15% (w/w) drug loading). The physicochemical parameters revealed smooth topology with size range (240–320 nm), a negative zeta potential (~19 mV) and in vitro sustained-release activity (~60% drug release in 40 days). Greater anti-proliferative activity ~100 times was observed with NPs (IC50 = 0.002 μg/ml) than that of native etoposide (IC50 = 0.2 μg/ml) in retinoblastoma cell line (Y-79). These NPs demonstrated greater (G1/S) blocking and decreased mitochondrial membrane potential as measured by flow cytometry. There was upregulation of apoptotic gene activity in NPs than native etoposide, as revealed through microarray analysis. However, this is the first ever report demonstrating the intricate modulation of genetic network affected by NPs. Collectively, these results suggest that etoposide-loaded NPs could be potentially useful as a novel drug delivery system for retinoblastoma in the future.
KeywordsRetinoblastoma Ocular drug delivery PLGA nanoparticles Apoptosis Gene expression
Retinoblastoma is the most common intraocular malignancy found during infancy and childhood (Rodriguez-Galindo et al. 2008), and it represents the phenotypic expression of abnormal or absence of tumour suppressor gene known as retinoblastoma gene (RB1; Friend et al. 1987). The protein product of the RB1 gene (the retinoblastoma protein) regulates a cellular anti-proliferative Rb pathway. The deregulation of the RB1 gene results in a spectrum of malignancies (Van Quill et al. 2005). Treatment options for retinoblastoma include external radiotherapy, episcleral plaque radiotherapy and cryotherapy (Amendola et al. 2006). However, these treatments are associated with complications such as facial deformities, cataract and radiation retinopathy and with a substantial risk for secondary tumours (Abramson et al. 1998; Smith and Donaldson 1991). Therefore, systemic chemotherapy treatment is the only options left for the widely used treatment of retinoblastoma. However, their clinical use is limited with systemic toxicity, rapid blood clearance and drug resistance (Chan et al. 2005; Travis et al. 1999). The presence of the blood retinal barrier further limits the potential of various anticancer drugs. Therefore, ocular drug delivery is one of the challenging tasks faced by pharmaceutical scientists because of its critical and pharmacokinetically specific environment that exists in the eye (Sahoo et al. 2008).
As per the anatomical structure of the eye, the inner and outer blood retinal barriers separate the retina and vitreous from the systemic circulation to the vitreous body which reduces the movement of molecules, further limiting the potential of various anticancer drugs (Abramson et al. 2003). To increase the therapeutic index, nanotechnology is one of the potential approaches where cytotoxic drugs are encapsulated in nanoparticles to augment drug activity by maximizing drug availability, leading to the reduction of harmful effects of drug by minimizing drug exposure to healthy tissues. Harmia et al. (1986) encapsulated pilocarpin in poly(alkylcyanoacrylate) which are able to improve the intraocular penetration of drugs. Also, Calvo et al. (1996) formulated cyclosporine A polyester nanocapsules as a topical delivery system for improved ocular penetration of drugs. Similarly, Enríquez de Salamanca et al. (2006) developed chitosan-based nanocarriers as the potential vehicle for ocular delivery. However, all of the above studies demonstrated that these nanoparticles are well tolerated by the ocular surface tissues. These supportive facts further support the potential use of nanoparticles to deliver the drugs to the ocular surfaces.
Considering these points, the development of a drug delivery system is becoming increasingly important in the treatment of vitreoretinal diseases by facilitating the drug efficacy and attenuating the adverse effects whilst assisting their interaction with ocular tissues (Wong et al. 1987). Nanoparticles are polymeric colloidal particles with size ranging from 10 to 1,000 nm, in which the therapeutic agents of interest can be encapsulated or conjugated or adsorbed to its surface (Sahoo et al. 2008; Misra et al. 2009). Moreover, polymeric nanoparticles have been evaluated as ocular drug delivery systems to enhance the absorption of therapeutic drugs, improve bioavailability, reduce systemic side effects, and to sustain intraocular drug levels (Hashizoe et al. 1997; Marchal-Heussler et al. 1993; Zimmer et al. 1995). In addition, polymeric nanoparticles have been shown to have potential in the treatment of inflammatory external eye diseases (Diepold et al. 1989). Poly(lactide-co-glycolide) (PLGA) is a copolymer of poly(d,l-lactide-co-glycolide) and is an ideal candidate of biodegradable polymers for formulation into nanoparticles due to its wide medical use, biocompatibility and safety (Yasukawaa et al. 2004).
Etoposide is an anticancer drug used in the treatment of a variety of malignancies including malignant lymphomas, acute myeloid leukemia, lung cancer, Hodgkin’s disease, non-Hodgkin’s lymphoma, AIDS-related Kaposi’s sarcoma, gastric cancer, breast cancer and ovarian cancer (Hande 1992; Smit et al. 1989). It acts by inhibiting topoisomerase-II and activating oxidation/reduction reactions to produce derivatives that bind directly to DNA and cause DNA damage (Ashley et al. 1996). Effective cancer therapy for tumours precisely depends on continuous exposure of the anticancer agents for a prolonged period of time, which is not possible due to the short biological half-life (190 min) of etoposide (Reddy et al. 2006). Etoposide, being a hydrophobic drug, possesses a dissolution-related absorption problem because of poor aqueous solubility and bioavailability (Shah et al. 1995). Snehalatha et al. (2008) have reported the high significance and advantage of PLGA and PCL nanoparticles as drug carriers for etoposide with enhanced bioavailability and reduced etoposide-associated toxicity in rabbits and mice. Similarly, Yadav and Krutika (2010) have developed a sustained-release formulation of etoposide for continuous intravenous administration replacing the conventional therapy. They have reported that nanoparticles (NPs) remained stable in terms of both size and drug content for a longer period of time. Therefore, it is of enormous interest to develop a formulation which can overcome the solubility and related bioavailability problems of etoposide as a therapeutic agent particularly for the treatment of retinoblastoma.
We propose here that the diverse side effects of etoposide can be significantly reduced by encapsulating the drug in the nanoparticulate system. In the present investigation, etoposide-loaded NPs were formulated to achieve a high entrapment efficiency of etoposide by varying different parameters like organic solvent, per cent of drug loading (w/w) and the amount of polyvinyl alcohol (w/v). We selected the best suitable formulation with optimum size range and higher encapsulation efficiency for further studies. The nanoparticles were characterized in terms of their particle size, zeta potential, surface morphology and entrapment efficiency by different techniques. We have studied the cytotoxicity, cellular uptake (qualitative and quantitative), induction of apoptosis and modulation of mitochondrial permeability by these nanoparticles using the Y-79 cell line, and these results were compared with native etoposide. Moreover, the NPs were further evaluated for the regulation of different apoptotic gene activities in the retinoblastoma cell line by microarray technique.
2 Materials and methods
Poly(d,l-lactide-co-glycolide) (copolymer ratio 50:50, viscosity 0.55–0.75) was purchased from Birmingham Polymers Inc. (Birmingham, USA); propidium iodide (PI) from MP, Biomedicals, Inc. (Germany); AnnexinV-FITC from Biosciences, Pharmigen; Pierce BCA Protein Assay Kit (Rockford, IL, USA); and uranyl acetate from Electron Microscopy Sciences (Hatfield, PA, USA). Polyvinyl alcohol (PVA, average Mw 31,000–50,000), etoposide, 6-coumarin, Tween 80 (polyoxyethylene sorbitan monooleate), Igepal CA-630, MTT (3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyl tetrasodium bromide) reagent and different salts were purchased from Sigma-Aldrich Co. (St. Louis, MO, USA). All other chemicals used in this study are of analytical grade from E Merck (India). Uranyl acetatae was from Electron Microscopy Services, Ft. (Washington, PA, USA) and carbon-coated copper TEM grid (150-mesh) from Ted Pella Inc. (Rrodding, CA, USA).
2.2 Preparation of etoposide-loaded nanoparticles
The NPs were prepared by single emulsion-solvent evaporation technique (Sahoo et al. 2004a). Briefly, 90 mg of PLGA was dissolved in 3 ml of chloroform or dichloromethane. To the above mixture, either 10% or 15% (w/w) etoposide was added and emulsified with 12 ml of either 2% or 5% (w/v) aqueous solution of PVA. The emulsification was carried out using a microtip probe sonicator (VC 505, Vibracell Sonics, Newton, USA) at 39 W of energy for 2 min in an ice bath and stirred with a magnetic stirrer overnight to evaporate the organic solvent. The NPs were recovered by ultracentrifugation at 40,000 rpm for 20 min at 4°C (Sorvall Ultraspeed Centrifuge, Kendro, USA), followed by washing twice with double distilled water. The obtained particles were resuspended in double distilled water and lyophilized (−80°C and <10-μm mercury pressure, LYPHLOCK 12, Labconco, Kansas City, MO, USA) for 48 h. Lyophilization is required for longer storage and stability of these nanoparticles which can be stored at 4°C for further experiments (Lemoine et al. 1996). To study the cellular uptake of NPs, 6-coumarin was used as a model fluorescent probe. To formulate 6-coumarin-loaded nanoparticles, 50 μl (1 mg/ml) of dye (dissolved in methanolic/chloroform, 12.5:87.5, v/v) was added to the polymer solution prior to emulsification instead of etoposide formulation.
2.3 Determination of encapsulation efficiency by RP-HPLC
To estimate the amount of drug entrapped inside the NPs drug content, 10 mg of etoposide nanoparticles was dissolved in 10 ml of methanol, sonicated in an ice bath for 1 min at 39 W (VC 505, Vibracell Sonics) and centrifuged at 13,800 rpm for 10 min at 25°C (Sigma1-15K, Germany). The supernatant was estimated by the reverse phase isocratic mode of HPLC with slight modification (Shirazi et al. 2001): Agilent 1100 (Agilent Technologies, Waldbronn Analytical Division, Germany), featured with C18 column (Zorbax Eclipse XDB-C18,150 × 4.6 mm, i.d), quaternary pump (model no. G1311A), thermostart (model no. G1316A) and a diode array detector (model G 1315A). Twenty microlitres of the sample was injected manually in the injection port and analysed with a flow rate 1 ml/min at 60°C with UV detection at 220 nm using the mobile phase of methanol/water (45:55, v/v). The standard curve of etoposide was prepared under identical condition. The encapsulation efficiency (%) was determined as the percentage of drug entrapped in nanoparticles with respect to the initial amount of drug added in the formulation (Sahoo et al. 2004a).
2.4 Physicochemical characterization of nanoparticles
Particle size, size distribution and zeta potential of the etoposide nanoparticles were determined by photon correlation spectroscopy and laser Doppler anemometry, respectively, using Zetasizer (Nano ZS, ZEN 3600, Malvern Instrument, UK) with a red laser of wave length λ0 = 633 nm (He–Ne, 4.0 Mw). For the above measurement, the lyophilized nanoparticles were suspended in double distilled water and sonicated to get a homogenous suspension. The acquired suspension was examined for mean diameter, size distribution, polydispersity and zeta potential. Scanning electron microscopy (Hitachi S-3400N, USA) was used to determine the shape and surface morphology of the nanoparticles. The powdered particles were gold-coated and vacuum-dried before scanning electron microscopy (SEM). For the transmission electron microscopy (TEM, Philips CM-10, FEI Inc., Hillsboro, OR, USA), a drop of diluted and sonicated solution of nanoparticle was negatively stained with 1% uranyl acetate for 10 min, placed in carbon-coated copper TEM grid and air-dried before TEM. Fourier transform infrared spectroscopy (Perkin Elmer model Spectrum1, USA) measurement was done to determine the possible chemical interaction between the drug and the polymer. The samples (native etoposide, void NPs and NPs) were crushed individually with KBr to get the pellets by applying a pressure of 300 kg/cm2, and the spectra scanned were obtained in the range between 4,000 and 500 cm−1 using IR solution software (version 1.10). Differential scanning calorimetry (DSC 821, Mettler Toledo, Switzerland) technique was implemented to determine the physical state of the encapsulated etoposide in nanoparticles. Each sample (native etoposide, void nanoparticles and etoposide nanoparticles) was sealed separately in a standard aluminium pan, purged with pure dry nitrogen with a flow rate of 10 ml/min, at 10°C/min, and heat flow recorded from 0°C to 350°C.
2.5 In vitro release of etoposide from nanoparticles
The release of drugs from nanoparticles was carried out in phosphate-buffered saline (PBS, 0.01 M, pH 7.4, containing 0.1% (w/v) of Tween 80) in triplicates (Sahoo et al. 2004a). In brief, 10 mg of nanoparticles was dispersed in 3 ml of PBS, sonicated (30 s) and equally distributed into three tubes. Then, the tubes were placed in an orbital shaker bath (Wadegati Lab Equip, India) maintained at 37°C and with horizontal rotation at 150 rpm. At predetermined time intervals, the tubes were taken out of the shaker and centrifuged at 13,800 rpm for 10 min at 4°C (Sigma Microcentrifuge 1-15K, Germany). The entire supernatant was collected for further analysis. The residue pellet was resuspended with fresh PBS and placed back into the shaker to continue the release measurement. The collected supernatants were lyophilized for 48 h, dissolved in methanol for the dissolution of the drug and centrifuged at 13,800 rpm for 10 min. The obtained supernatant was subjected to RP-HPLC analysis to determine the amount of etoposide released as described above.
2.6 Quantitative cellular uptake of nanoparticles
Cellular uptake efficiency of cells was studied using 6-coumarin-loaded nanoparticles. For this, the cells were seeded at 5 × 104 per well density in 24-well plates (Corning, NY, USA) and left 24 h for attachment; thereafter, cells incubated for 2 h with 300 μg/ml of 6-coumarin-loaded nanoparticles and equivalent concentration of native 6-coumarin. After the incubation period, the cells were washed thrice with PBS (0.1 M, pH 7.4) and lysed by incubating them with 0.1 ml of 1× cell lysis reagent (Igepal CA-630, Sigma-Aldrich) for 30 min at 37°C. From which, 5 μl was taken out for the cell protein estimation using the Pierce BCA protein assay. The remaining cell lysate was lyophilized. The dye from the lyophilized nanoparticles was extracted by dissolving each sample with 1 ml of methanol/chloroform (12.7:87.5, v/v) solution and kept in a shaker at 37°C for 48 h at 150 rpm/min in an orbit shaking incubator (Wadegati Labequip, India) for the complete removal of the dye from the NPs. The samples were then centrifuged at 13,800 rpm for 10 min at 4°C and the supernatants collected. Fluorescence intensity of the supernatants was measured by a fluorescent spectrophotometer (Synergy HT, BioTek® Instruments, Inc., Winooski, VT, USA) at λex = 450 nm and λem = 490 nm. A standard plot of 6-coumarin nanoparticles (2–50 μg/ml) was constructed in a similar way to determine the amount of nanoparticles in the cell lysate. The uptake of nanoparticles by cells was calculated from the standard plot and expressed as the amount of nanoparticles (μg) taken per milligram cell protein.
2.7 Cytotoxicity assay
A comparison of the cytotoxic activity of NPs and native etoposide was performed using the MTT assay as described earlier (Sahoo et al. 2004b). Y-79 cells were plated in 96-well plates (Corning) at a density of 5,000 cells/well incubated for 24 h for cell adherence. A stock solution of etoposide was prepared in DMSO (1 mg/ml) and stored at −70°C. Different aliquots of the stock solution after suitable dilution were added to the culture medium to achieve the desired drug concentration. The concentration of DMSO in the medium was kept 0.1% so that it has no effect on the cell proliferation. Cells were incubated with different concentrations of etoposide either as solution or encapsulated in NPs. Medium and void nanoparticles (without drug) served as respective controls. The medium was changed on every alternate day and no further dose of the drug was added. The cell viability was determined at the fifth day following drug treatment using the MTT reagent. Ten microlitres of the MTT solution was added to each well and incubated at 37°C for 3 h in a cell culture incubator. The medium was removed and replaced with 100 μl of DMSO to dissolve formazan crystals; absorbance was read at 540 nm using a microplate reader (Synergy HT, BioTek® Instruments, Inc.). The anti-proliferative effects of different treatments were calculated as a percentage of cell growth with respect to the respective controls. IC50, the concentration of the drug at which 50% cell growth is inhibited, was calculated by the curve fitting of the cell viability data using Prism 4.0 (GraphPad, San Diego, CA, USA).
2.8 Cell cycle analysis
The distribution of DNA in the cell cycle was studied by flow cytometry. Cell cycle analysis of native etoposide and etoposide-loaded nanoparticles was done with slight modification (Noh et al. 2004). Briefly, 5 × 105 cells/5 ml were seeded in T-25 flask (Corning) and incubated overnight for better attachment. The cells were exposed to a particular concentration (0.0005 μg/ml) of drug in solution, drug-loaded nanoparticles in RPMI medium, and incubated for 48 and 120 h. Void nanoparticle-treated cells and untreated cells were used as respective controls. The cells were collected and washed with PBS (0.1 M, pH 7.4) twice and resuspended in hypotonic propidium iodide solution (10 μg of propidium iodide, 10 μg of RNase A and 0.5% ”Tween 20 in 1 ml of PBS) for 1 h at room temperature and kept in the dark at 4°C before analysis. Cell cycle distribution was determined by analysing 10,000 cells using FACScan flow cytometer and Cell Quest software Caliber (Becton-Dickinson, San Jose, CA, USA). All experiments were performed in triplicate.
2.9 Mitochondrial membrane permeability study
Mitochondrial membrane depolarization study was done using flow cytometry (Raffaella et al. 2005). Briefly, 5 × 105 cells per well were seeded and incubated overnight. The cells were exposed to a particular concentration (0.0005 μg/ml) of native etoposide and etoposide-loaded nanoparticles for 5 days. The medium was changed in every alternate day. Cells were stained with the cationic dye 5,5,6,6 tetrachloro-1,1,3,3-tetraethylbenzimidazol-carbocyanine iodide (JC-1, 3 μg/ml) for 10 min at 37°C, which exhibits potential-dependent accumulation in mitochondria. The cells were washed with PBS (0.1 M, pH 7.4) twice and analysed using FACScan flow cytometer and Cell Quest software Caliber (Becton-Dickinson). All experiments were performed in triplicate.
2.10 Assessment of apoptosis
Annexin V-FITC staining was used for the assessment of apoptosis. This assay is based on the observation that soon after the initiation of apoptosis, phosphotidylserine (PS) translocates from the inner face of the plasma membrane to the cell surface. The translocated PS can thus be easily detected by staining with a FITC conjugate of Annexin V, a protein that has a strong natural affinity for PS (Martin et al. 1995). In our experiments, 1 × 106 cells/well were cultured on six-well plates (Corning) in 3 ml medium; 24 h post-seeding, they were treated with two different concentrations (0.0005 and 0.005 μg/ml) of the native drug and etoposide-loaded nanoparticles, and 5 days after treatment, the cells were collected from the wells, centrifuged, washed thrice with PBS (0.01 M, pH 7.4) and incubated for 15 min in the dark in 100 μl of binding buffer containing 2 μg/ml Annexin V-FITC (BD Biosciences Pharmingen) and 10 μg/ml of the vital dye, propidium iodide (MP Biomedicals, Inc., Germany). Thereafter, the cell suspension was placed on a glass slide, covered with a glass coverslip and photographed using a fluorescence microscope (Nikon Fluorescence, Nikon, Japan) equipped with blue, red and green filter attachment. The apoptotic index was obtained by dividing the number of apoptotic cells by the total number of cells, multiplied by 100 (Rödel et al. 2003). A minimum of 1,000 cells were counted using an image analyzer.
2.11 DNA fragmentation studies by gel electrophoresis
DNA fragmentation into oligonucleosomal ladder is a characteristic of apoptosis. To study this, 1 × 106 cells per well were seeded in six-well plate (Corning) and after 24 h were then treated with two different concentrations (0.0005 and 0.005 μg/ml) of the drug either as a solution or encapsulated in nanoparticles. Medium and void nanoparticles served as respective controls. After 5 days of post-treatment, cells were collected, washed and centrifuged at 2,500 rpm for 5 min. The cell pellet was lysed with 0.1 ml of 1× cell lysis buffer (Igepal CA-630, Sigma-Aldrich) and incubated for 30 min at 37°C; after, 2 μl of 10 μg/ml RNase was added and incubated for a further 1 h. The obtained cell lysate samples of 20 μl/well were subsequently run at 120 V on a 1% (w/v) agarose gel containing 0.1 mg/ml ethidium bromide. Gels were examined on an ultraviolet light source and photographed.
2.12 Statistical analysis
Statistical analyses were performed using a Student’s t test of the software, and the differences were considered significant for p values of <0.05* and <0.005**.
3 Results and discussion
3.1 Physicochemical characterization of nanoparticles
Comparative analysis of encapsulation efficiency, size and zeta potential of etoposide-loaded nanoparticles
Drug loading (%, w/w)
Encapsulation efficiency (%)a
Mean diameter (nm)b
Zeta potential (mV)c
316 ± 1.5
−14 ± 0.9
322 ± 1.1
−14 ± 0.9
299 ± 1.1
−17 ± 1.1
305 ± 0.9
−19 ± 1.2
267 ± 1.2
−20 ± 1.3
270 ± 1.0
−19 ± 1.6
247 ± 1.2
−24 ± 1.8
251 ± 1.1
−22 ± 1.2
Physical properties of the solvents
Boiling point (°C)
Melting point (°C)
Solubility in water at 25°C
Interfacial tension (dyne/cm)
1 in 50
1 in 200
Apart from the smaller size, the successful implementation of nanoparticles as drug delivery vehicles requires a higher drug loading efficiency. Therefore, we have used 10% or 15% (w/w) drug loading corresponding to the polymer weight (Table 1). We achieved higher encapsulation efficiency in the case of 15% (w/w) drug loading irrespective of the organic solvent and concentration of emulsifier. An increased encapsulation efficiency up to ~86% was achieved using chloroform as organic solvent, whereas using dichloromethane, the encapsulation efficiency reached up to ~72%. The slightly hydrophilic nature of dichloromethane leads to a slightly lower entrapment efficiency with smaller particle size, whereas the less hydrophilic nature of chloroform leads to higher entrapment efficiency with a slightly bigger particle size. This could happen probably due to more accommodation of drug molecule in the polymeric surface due to drug–polymer interaction (Panyam and Labhasetwar 2004). Besides, the polarity behaviour of the organic solvent (Table 2) also might have affected the entrapment efficiency during the nanoparticle formulation. Therefore, in our formulation, we established chloroform to be a more suitable solvent than dichloromethane for the encapsulation of the hydrophobic drug etoposide (Table 1).
3.2 FT-IR analysis
Fourier transform infrared spectroscopy (FT-IR) spectral analysis was exercised to determine any possible chemical interaction (formation of chemical bonds) that occurred in the polymer due to the addition of drug during the synthesis process (Misra et al. 2009; Vandana 2009). Figure 2 depicted the FT-IR spectra of void nanoparticles, native etoposide and NPs. The spectra of NPs showed the presence of bands similar to void NPs along with some extra bands due to the drug. The vibrational spectral analysis of native etoposide illustrated characteristic bands due to different functional groups such as 3,450, 2,892, 1,769, 1,615,1,459, 1,390 and 1,161 cm−1, corresponding to OH, –CH2 stretching, lactone group, aromatic groups, –OH, –C–O from –OCH3 and AROH functional groups, respectively. Similar types of bands were also observed earlier (Jasti et al. 1995). However, the vibrational spectral peaks of drugs at 3,450, 2,892 and 1,769 cm−1 are slightly displaced to 3,434, 2,998 and 1,761 cm−1 in NPs due to some minor chemical interaction between etoposide and the PLGA matrix. Moreover, the band appearing at 1,769 cm−1 in native etoposide also appeared in NPs with increased intensity, indicating the presence of negligible chemical interaction with the polymer. However, such chemical interaction has no significant effect on the in vitro release profile of drug. Similar chemical integrity and chemical stability of doxycycline drug inside the nanoparticles were also studied through FT-IR analysis (Misra et al. 2009).
3.3 DSC studies
3.4 In vitro release profile of nanoparticles
3.5 Cellular uptake of native 6-coumarin and 6-coumarin-loaded nanoparticles
We have studied the intracellular uptake of nanoparticles by confocal microscopy. The cells exposed to nanoparticles demonstrated increased fluorescence activity. Maximum fluorescence activity was observed in cells exposed to 6-coumarin-loaded nanoparticles, which indicated that nanoparticles were internalized more by the cells than native 6-coumarin (Fig. 5b). The fluorescence intensity of native 6-coumarin decreased with increased incubation time, i.e. 2, 24, 48 and 120 h. But in the case of 6-coumarin-loaded nanoparticles, the fluorescence intensity increased with increased time of incubation, signifying that the nanoparticulate formulation might act as an intracellular depository to maintain a sustained release of the dye from nanoparticles.
3.6 Cytotoxicity studies of native drug and nanoparticles
3.7 Cell cycle analysis of native drug and nanoparticles
3.8 Assessment of apoptosis by mitochondrial permeability/Annexin V-FITC and DNA fragmentation method
Apoptosis was also further confirmed by DNA fragmentation, as DNA fragmentation into the oligonucleosomal ladder is the characteristic of apoptosis, and the percentage of DNA fragmentation in cultured cells exhibited a direct correlation with the percentage of apoptotic DNA (Ioannou and Chen 1996). The results demonstrated that the Y-79 cells treated with different concentrations of NPs (0.0005 and 0.005 μg/ml) underwent more DNA fragmentation as compared with native etoposide (Fig. 9b). As our formulation showed higher cytotoxic effect than native etoposide, this could be one of the reasons of showing relatively greater apoptosis in the case of cells treated with NPs.
3.9 cDNA microarray screening for potential gene expression changes induced by etoposide loaded in nanoparticles in cells
We have shown our interest to discover the potential gene expression changes in Y-79 cells after treatment with NPs mainly for two reasons. One reason is that the Y-79 cells form tumours in the murine models that closely resemble the naturally occurring tumuor in anatomic sites without disrupting the choroids and sclera or involving the anterior chamber (Chévez-Barrios et al. 2000). The second reason is that RB tumours found in Indian RB patients are mostly advanced tumours, presenting with choroidal and optic nerve invasion (Moutushy et al. 2010). Therefore, the Y-79 cell line is appropriate for in vitro studies and the data can be translated to actual tumour state. In order to screen and compare the potential gene expressional changes occurring in the Y-79 cells treated with (0.0005 μg/ml) of NPs and with native etoposide, RNA was extracted from Y-79 cells to perform cDNA microarray analysis.
3.10 Identification of genetic networks through upregulation and downregulation of various genes
The microarray analysis demonstrated that NP treatment primarily upregulated the expression of three groups of potential genes related to cell cycle and cell differentiation, cell migration, apoptosis and few anti-apoptosis-related genes. Amongst them, seven genes are upregulated more than onefold in apoptosis, such as Homo sapiens (BCL2-antagonist of cell death (BAD), caspase 8, apoptosis-related cysteine peptidase (CASP8; Polzien et al. 2009), growth arrest and DNA damage-inducible, alpha (GADD45A), PERP, TP53 apoptosis effector (PERP), tumour necrosis factor TNF receptor-associated factor 1 (TRAF1; Kim et al. 2010), caspase recruitment domain family, member 14 (CARD14) and members of the tumour necrosis factor receptor superfamily (TNFRSF17, TNFRSF1B, TNFRSF10B, TNFRSF19; Coffer et al. 1998). Two cell cycle and cell differentiation genes, i.e. nuclear factor of kappa light polypeptide gene enhancer in B cells inhibitor, alpha (NFKBIA, platelet-derived growth factor alpha polypeptide (PDGFA), and two anti-apoptosis, i.e., baculoviral IAP repeat-containing 3 (BIRC3), transcript variant 1, BCL2-related protein A1 (BCL2A1), mRNA were upregulated. Similarly, angiogenesis factor genes, i.e. E74-like factor 3 (ets domain transcription factor, epithelial-specific; ELF3) and Kruppel-like factor 2 (lung; KLF2), were also upregulated. Moreover, one gene for cell proliferation, i.e. v-fos FBJ murine osteosarcoma viral oncogene homolog (FOS), and anti-proliferation, i.e. dual specificity phosphatase 1 (DUSP1), were upregulated too (details in ESM Tables S1 and S2). On the other hand, NP action also resulted in the significant downregulation of genes (less than onefold) related to cell cycle cell differentiation, cell invasion, various oncogenes, migrations, proliferations, angiogenesis and DNA repair, as depicted in ESM Tables S1 and S2.
3.11 Functional grouping of differentially expressed genes
All the distinct gene identifications were examined for their known biologic function according to gene ontology convention and grouped in their respective functional category. The proportion of each functional category in the total number of selected identified genes (taken as 100%) was shown in Fig. 10b. Amongst the upregulated genes, the majority of genes belonged to the apoptosis functional category (60%, i in Fig. 10b). Therefore, it became interesting to speculate that drug delivery through nanoparticulate formulation may promote apoptosis in Y-79 cells. However, other identified genes belonged to proliferation, anti-proliferation, angiogenesis, anti-angiogenesis and anti-apoptotic genes. Amongst the downregulated genes, one third of the total genes belonged to the oncogenic functional category (47%) and other cell cycle and differentiation groups (16%, ii in Fig. 10b). However, other downregulated genes belonged to cellular invasion, anti-apoptosis, proliferation, and angiogenic genes.
In particular, genes involved in oncogenic signalling and apoptotic events were discussed below. Genes related to apoptosis such as CARD14, associated with induction of apoptosis via NFKB activation (Shammas et al. 2006); TNFRSF10B, a member of the TNF-receptor superfamily (Kim et al. 2010); p53 apoptosis effector related to PMP-22 (PERP), a transcriptional target gene of p53 tumour suppressor (Davies et al. 2009); Gadd45a, a p53 effector and stress-inducible gene, like p53 (Hildesheim et al. 2002); and BAD, a pro-apoptotic member of the Bcl-2 protein family (Polzien et al. 2009), have been significantly upregulated in cells treated with etoposide. These changes were coupled with the downregulation of important oncogenes such as KIF14, FGR, AKT3, MYB and MET. The mitotic kinesin gene KIF14 has been predicted to be one of the possible oncogenes in the 1q region which was found to overexpress by more than two orders of magnitude in RB (Corson et al. 2005). Another proto-oncogene, FGR, is expressed in elevated level in invasive breast cancer and seems to have a negative impact on disease-specific survival (Mayer and Krop 2010). AKT3 serine/threonine protein kinase that has been implicated in mediating a variety of biological responses, which include inhibition of apoptosis and stimulation of cellular growth (Coffer et al. 1998), is the predominantly active family member of AKT. The increased AKT3 gene copy number and/or loss of a negative regulatory phosphatase called PTEN leads to AKT3 activation, which reduces melanoma cell apoptosis mediated through caspase-3 to promote melanoma development (Stahl et al. 2004). MYB overexpressed in colon cancer upregulates Bcl-xL and increases tumorigenesis of colon carcinoma cells by inhibiting the apoptotic process (Biroccio et al. 2001). MET hepatocyte growth factor contributes to oncogenesis and tumour progression in several human cancers and promotes aggressive cellular invasiveness that is strongly linked to tumour metastasis (Giubellino et al. 2009). Few genes leads to tumour proliferation, such as BCL2, BCL11A; cell migration MMP8, CD44 and drug resistance ABCA1, ABCC4, ABCC1, ABCA5 were also found to be significantly downregulated in response to treatment. BCL11A defines a superfamily of C2HC zinc-finger transcription factors involved in hematopoietic malignancies (Liu et al. 2006). Bcl-2 is the prominent member of a family of proteins that are responsible for dysregulation of apoptosis and prevention of death in cancer cells (Gross et al. 1999). The ABC transporters investigated might act as drug transporters and resistance (ABCA1, ABCA5, ABCC1 and ABCC4; Gillet et al. 2004).
Our functional study showed induced apoptotic event and reduced cell proliferation, and microarray analysis revealed a wide network of etoposide responsive genes which are involved in initiating apoptosis and reducing tumour oncogenesis. This might be due to the more uptake of etoposide into cells through endocytosis via nanoparticles. Thus, NPs can persuade more apoptosis due to the accumulation of more drug as compared to the native etoposide inside the cell.
We report for the first time that drug-loaded nanoparticles affect effectively the genetic network of cancer cells, leading to enhanced apoptosis. In the current study, we have successfully prepared etoposide-loaded nanoparticles with higher entrapment efficiency, ~86% with an optimum size range. These etoposide-loaded nanoparticles displayed greater cellular drug uptake, sustained drug retention and an enhanced anti-proliferative effect of the encapsulated anti-neoplastic agent in Y-79 cancer cells. Furthermore, microarray analysis exemplifies that these drug-loaded nanoparticles could rapidly induce cell cycle disturbance by inhibiting the expression of multiple cell cycle regulatory genes and upregulating apoptotic-related genes. Thus, at present, these drug-loaded nanoparticles could focus their therapeutic strategy towards toxicity to tumour cells, but not to healthy normal cells, in a dose-limiting manner. Hence, this nanoparticulate formulation could be a more effective promising approach for expanding tumour-targeted cancer therapy.
SKS would like to thank the Department of Biotechnology, Government of India, for providing the grants no. BT/04(SBIRI)/48/2006-PID and BT/PR7968/MED/14/1206/2006. SKS and SK acknowledges ICMR for providing grant no. 58/12/2005-BMS.
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