Efficient delivery of docetaxel for the treatment of brain tumors by cyclic RGD-tagged polymeric micelles
- Ai‑Jun Li
- Yue‑Hua Zheng
- Guo‑Dong Liu
- Wei‑Sheng Liu
- Pei‑Cheng Cao
- Zhen‑Fu Bu
- Published online on: November 28, 2014 https://doi.org/10.3892/mmr.2014.3017
- Pages: 3078-3086
Glioblastoma multiforme (GBM) is one of the most common and aggressive forms of brain tumor, accounting for 50–60% of all brain cancers in humans, and is associated with a low median survival rate (1). GBM is generally characterized by high lethality, invasiveness, excessive growth, and a poor prognosis (2,3). The current gold-standard treatment strategy for brain tumors is comprised of radiation therapy, surgical removal, and chemotherapy. However, difficulties in surgical excision, and the severe adverse effects associated with irradiation and chemotherapy, hinder these approaches (4,5). Furthermore, the advanced chemotherapy regimen has been reported as having limited or no impact on brain tumors due to the poor penetration profile of the drug through the highly variable, heterogeneous blood brain barrier (BBB) (6). In addition, a protective blood-brain tumor-barrier (BBTB) has been shown to form around tumor cells alongside the progression of GBM, which regulates the entry of small molecules (7). Therefore, any approach that can overcome the tight extracellular junctions of both the BBB and BBTB would be a promising treatment solution.
Nanotechnology may be a prospective method to overcome the BBB and BBTB. Polymeric nanoparticles (NP), or polymeric micelles, have drawn significant attention due to their ability to surpass the physiological barriers and improve the delivery of therapeutic agents into the brain (8,9). The enhanced permeability and retention effect is the main factor that allows the preferential accumulation of NP in the tumor fenestrations. However, limited penetrability, and non-uniform distribution into other body parts, impairs the performance of simple carrier-mediated delivery systems (10). Receptor-mediated active targeting moiety-tagged NPs may be a feasible approach in the translocation of the carriers. Cyclic Arginine-Glycine-Aspartic acid (cRGD) has been selected as a targeting moiety to promote the biological interactions between the delivery carrier and the overexpressed receptor in the tumor cells (11). Specifically, αvβ3 and αvβ5 integrins, which are over-expressed in tumor endothelial and GBM cells, have been shown to have a selective affinity to cRGD (12). Chen et al (13) successfully demonstrated the in vivo imaging of GBM, with the aid of an RGD-containing probe. Furthermore, an RGD-iron oxide NP conjugate has been developed, and shown to enhance the targeting efficiency in brain tumors (14).
Docetaxel (DTX) is an anti-mitotic taxane drug, considered to be one of the most effective drugs against brain tumors (15). The present study developed polylactic acid-polyethylene glycol (PLA-PEG)-based long circulating, DTX-loaded, cyclic RGD-attached polymeric micelles [DTX-PLA-PEG/c(RGDyK)]. These micelles could prolong the blood circulation time of the carriers, and specifically target the integrin receptors known to be over-expressed in brain tumors. The PEG provided an anti-fouling property and extended the circulation time of the carriers, whilst the cRGD specifically targeted the tumor cells. The aim of the present study was to develop a functional NP system which could be transported across the physiological barriers of the brain, and effectively deliver the therapeutic load. Pharmacokinetic and biodistribution studies were performed to quantify the amount of drug accumulated in the brain tissue. The antitumor efficacy of the system was determined using a U87MG bearing xenograft tumor model, by measuring the tumor volume and survival rate index. The study investigated whether cRGD-linked polymeric micelles can effectively penetrate the brain tumor and exhibit a potent antitumor effect.
Materials and methods
The materials used for the subsequent experiements were provided by the following suppliers. The methoxyl poly(ethylene glycol) (mPEG-OH, 2 kDa) and the maleimide-poly(ethylene glycol) (mal-PEG-OH, 3.5 kDa) were obtained from Sigma-Aldrich (Hong Kong, China). The benzotriazole-N,N,N,N′-tetramethyl-uronium-hexafluorophosphate was from American Bioanalytical Inc. (Natick, MA, USA). Benzotriazol-1-yl-oxytripyrrolidinophosphonium hexafluorophosphate was obtained from GL Biochem Ltd (Shanghai, China). Diisopropylethylamine and H-Gly-2-Chlorotrityl resin were both supplied by Fluka (Sigma-Aldrich). 3,3′-dithiodipronic acid and D,L-dithiotheriol (DTT) were purchased from Aladdin Reagents Co. (Shanghai, China). Cyclo[RGDfK(CX-)] (cRGD peptide, X=6-aminocaproic acid:-Acp) was purchased from Peptide Institute Inc. (Osaka, Japan). DTX was procured from Sigma-Aldrich (China).
Synthesis of RGD-PLA-PEG polymer
The synthesis of PLA-PEG was performed as reported by previous methods (16). The PLA-PEG was conjugated with the thiolated c(RGDyK) to form c(RGDyK)-PLA-PEG as previously reported (17). Briefly, 3,3′-dithiodipronic acid was activated by dicyclohexylcarbodiimide (DCC) and N-hydroxysuccinimide (NHS) and the resulting active ester was reacted with c(RGDyK). The obtained product was reduced with DTT to obtain the thiolated cRGD peptide. To conjugate the peptide with PLA-PEG, mal-PLA-PEG was dissolved in acetonitrile (ACN) and a thin-film was formed by rotary evaporation. Phosphate-buffered saline (PBS-hydrated PLA-PEG was added to the c(RGDyK)-SH and stirred overnight. The resulting product was extracted and characterized by nuclear magnetic resonance. The polymers were characterized using 1H nuclear magnetic resonance (NMR; solvents, CDCl3, D2O and deuterated-dimethyl sulfoxide (DMSO); temperature, 25°C). The NMR spectra were recorded using a JEOL Alpha 500 spectrometer (500 MHz; Jeol, Ltd., Tokyo, Japan).
Preparation of DTX-loaded micelles
The DTX-loaded polymeric micelles were formed using a thin-film hydration technique. Briefly, 10 mg of PLA-PEG and 5 mg of DTX were dissolved in 5 ml of ACN. The mixture was rotary-evaporated and the thin-film was subsequently hydrated with PBS. For the c(RGDyK)-tagged micelles, 5% w/w c(RGDyK)-PLA-PEG was mixed with 95% DTX-PLA-PEG. The resulting micelles were evaluated for drug loading and dynamic light scattering (DLS) characteristics using a Malvern Zetasizer (Malvern Instruments Ltd., Malvern, UK).
Particle size distribution and zeta potential
The micellar solutions were suitably diluted, in order to analyze the particle size distribution and zeta potential, using the DLS method. A Malvern Zetasizer was used to determine the DLS characteristics. All measurements were performed at a fixed angle of 90° at 25°C. The results were expressed as the size ± standard deviation.
DTX loading efficiency
The loading efficiency of the carrier was calculated from the total amount of drug added, versus the amount of drug entrapped within the nanoparticles. Briefly, DTX-PLA-PEG (DPP), and RGD/DTX-PLA-PEG (RDPP) were filtered using an Amicon® centrifugal filter (Millipore, Billerica, MA, USA) at 550 × g for 10 min. The filtrate was then analyzed for unentrapped drugs by high performance liquid chromatography (HPLC). The mobile phase (acetonitrile : water, 60:40, pH 3.5) was set at 1 ml/min with an absorbance of 254 nm.
In vitro release study
The in vitro release of DTX from both PLA-PEG and RGD/PLA-PEG was evaluated by dialysis. A total of 1 ml of NP dispersions were placed in a dialysis bag (3000 MW cutoff; Spectra/Por®, Spectrum Laboratories, Inc., Rancho Dominguez, CA, USA) and both the borders were sealed with a dialysis clip. The dialysis bag was incubated in 30 ml release media (PBS, pH 7.4), containing 1% Tween® 80 as a solubilizer. The bag was placed in an automated shaker maintained at 2 × g and 37°C. At a specified time (1, 2, 4, 8, 12, 24, 48, 72, 96, 120, 144 and 168 h), the release media was collected and replaced with an equal amount of fresh media. The amount of released drug was quantified by HPLC.
U87MG human malignant glioma and 9L rat gliosarcoma cells (ATCC, Manassas, VA, USA) were cultured in normal RPMI-1640 media supplemented with 10% fetal bovine serum and 1% penicillin-streptomycin in a 5% CO2 and 95% humidified atmosphere. The viability of the cells was determined by MTT assay (Sigma-Aldrich). Briefly, the cells were seeded into a 96-well plate, at a seeding density of 1×104 cells, and incubated for 24 h. The following day, the media was refreshed and various concentrations of free DTX, DPP or RDPP were exposed to the cells followed by 24 and 48 h incubations. The cells were then washed and treated with MTT solution (5 mg/ml in serum-free media) and incubated for 3 h. The purple blue formazan crystals were extracted by the addition of DMSO and the absorbance was detected using a plate reader (Multiskan Ascent, Labsystems SA, Cergy-Pontoise, France) at 570 nm.
Cellular uptake study
A cellular uptake study was performed to investigate the kinetics of drug internalization. A total of 1×106 U87MG and 9L cells were seeded in a 6-well plate and allowed to adhere for 24 h. The following formulations, free DTX, DPP or RDPP (DTX equivalent 20 μg/ml) were incubated with the cells for 1–4 h. Following the incubation, the media was removed and the cells were washed twice with PBS. An aliquot of lysis buffer was added to lyse the cells, followed by centrifugation at 500 × g for 10 min. The lysis buffer (Sigma-Aldrich) consisted of 50 mmol/l Tris, 150 mmol/l NaCl, 1% Triton X-100, 1% sodium deoxycholate, 0.1% sodium dodecyl sulfate, 1 mmol/l sodium orthovanadate, 1 mmol/l sodium fluoride, 1 mmol/l EDTA and 1 mmol/l phenylmethylsulfonyl fluoride. The supernatant was collected and analyzed by HPLC. The percentage of cellular uptake of DTX from the various formulations was estimated by normalizing to the initial DTX concentration administered.
Cell cycle analysis
U87MG and 9L cells were seeded in 6-well plates at a density of 3×105 cells/well with RPMI-1640 media for 24 h. The cells were then exposed to various doses of free DTX, DPP or RDPP and further incubated for 24 h. Following incubation the cells were washed and further incubated with propidium iodide (20 μg/ml) for 30 min The DNA content was measured for 10,000 events for each sample by flow cytometry using a BD FACS Atira II (BD Biosciences, Franklin Lakes, NJ, USA). The data were plotted using Cell Quest™ (BD Biosciences) software.
Analysis of glioma spheroids in vitro
The inhibitory effect of various formulations on the growth of glioma spheroids was investigated. U87MG tumor spheroids were incubated for a period of seven days, after which the media was refreshed, prior to the application of the formulations. The glioma cells, incubated in RPMI-1640 media, were exposed to free DTX, DPP, or RDPP. On days 0, 2, 4, 6, and 8, the tumor spheroids were observed under an inverted microscope. The inhibitory effects of the various formulations were calculated using the following formula: V=(π × dmax × dmin)/6, where dmax and dmin refer to major and minor diameters, respectively. The spheroid tumor volume at day 8 was calculated using the following formula: ratio %=(Vday8/Vday0) × 100. Vday0 is the spheroid volume t day 0. The sections were observed using a Zeiss Axioscope fluorescence microscope and photographed using a digital AxioCam mRM camera (Zeiss, Oberkochen, Germany).
Antitumor efficacy of c(RGDyK)-PLA-PEG-DTX
Nude mice were obtained from the Experimental Animal Center of Soochow University (Suzhou, China) and maintained under regular light and dark conditions with free access to food. The study was approved by the Institutional Animal Care Committee of Soochow University. U87MG tumor bearing xenograft nude mice were developed by subcutaneously injecting 1×106 cells into the right flank of the mice. The tumor growth was monitored until it reached ~100–150 mm3. Approximately two weeks after the tumor cell injection, the experiment was started. The mice were randomly divided into five groups (n=6/group). Groups I to IV were administered saline, free DTX, DPP or RDPP, and group V was identified as the untreated, control group. A total of 100 μl of each formulation (10 mg/kg body weight of DTX) was injected into the mice subcutaneously twice a week for two weeks. The tumor size was measured biweekly using a caliper, and the tumor volume (V) was calculated using the following formula V=1/2[L ×( W)2]; where L= length and W= width.
Pharmacokinetics and biodistribution
The pharmacokinetics study was performed in seven week old mice (~20 g). The mice were divided into three groups (n=5/group). Each group was administered with free DTX, DPP or RDPP (10 mg/kg DTX) via tail vein injection. The blood samples were collected at 0.25, 0.5, 1, 2, 4, 6, 8, 12, and 24 h. The samples were immediately centrifuged at 800 × g for 15 min and stored at −20°C until further analysis. To prepare the plasma samples, 100 μl of methanol containing 50 ng/ml of DTX was added to 50 μl of plasma. The mixture was vortexed for 30 min and subsequently centrifuged. The supernatant was collected and analyzed for DTX content by HPLC.
For the biodistribution study, brain tumor-bearing mice were developed as previously described in the above methods. Three weeks after the tumor implantation, the mice were divided into three groups (n=14/group). The groups were administered free DTX, DPP or RDPP (10 mg/kg DTX) via tail vein injection. At a specified time point, two mice were sacrificed and their organs were surgically removed and preserved on ice. At 0.5, 1, 2, 4, 6, 12 and 24 h, mice were sacrificed by carbon dioxide inhalation in a closed tube, according to the ethical guidelines. The organs were macerated using a high pressure homogenizer (10,000 × g; Ultra-Turrax T25 Homogenizer; IKA®-Werke GmbH & Co. KG, Staufen, Germany) and the drug levels present in the homogenate of each organ were analyzed by HPLC.
Statistical significance was determined using one-way analysis of variance, followed by Tukey’s post hoc test. Statistical significance was evaluated using SPSS version 5 (SPSS, Inc., Chicago, IL, USA). All values are expressed as the mean ± standard deviation. P<0.05 was considered to indicate a statistically significant difference.
Results and Discussion
Characterization of DPP and RDPP micelles
Brain tumors are one of the most aggressive and difficult tumors to treat, partly due to the complexity of the anatomical location. Furthermore, both the BBB and BBTB hamper any therapeutic strategy made to increase the drug accumulation in the brain. An attractive prospect of brain chemotherapy is the use of targeted drug delivery, which target cellular receptors in the brain. Such cellular responsive brain targeting systems are expected to increase the drug concentration in brain tumors. In the present study RGD, which has a high affinity for the αvβ3 and αvβ5 integrins in GBM cells, was conjugated with PLA-PEG by a DCC/NHS reaction. DTX was encapsulated within PLA-PEG and RGD/PLA-PEG, resulting in the formation of DPP and RDPP micelles respectively. The mean particle size of DPP was ~90 nm with a uniform size distribution (polydispersity index ~0.150) (Table 1). RGD-linking to the PLA-PEG slightly increased the size of micelles, however the size remained small (~120 nm) with a narrow distribution of particles (Fig. 1A). The RGD linking was evident as the overall zeta potential of micelles decreased from ~-28 to ~-22 mV (Fig. 1B). Both of the micelles showed high entrapment efficiency of >90% and a markedly high loading capacity of ~30%. RGD substitution did not decrease the drug loading capacity of the micelles and presented self-assembled mono-dispersed spherical shaped particles.
Physicochemical characterization of docetaxel polylactic acid-polyethylene glycoL/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles. (A) Particle size distribution, determined by Zetasizer. (B) Zeta potential analysis. (C) Release kinetics of DTX from DTX-PLA-PEG/c(RGDyK) micelles, DTX-PLA-PEG micelles, or free DTX suspension in phosphate buffered saline (pH 7.4) at 37°C. The data represents the means ± standard deviation (n=3). DTX, docetaxel.
In vitro drug release
The cumulative DTX release from both the DPP and RDPP micelles are presented in Fig. 1C. Free DTX exhibited a burst release profile with 60% of drug released within 24 h. The drug-loaded micelles however, significantly controlled the release rate without any burst-release phenomenon (P<0.05). As expected, DPP and RDPP micelles showed similar release profiles throughout the study period. During a 24 h incubation <20% of DTX was released, whilst ~60% of the drug had been released by the end of seven days. Such a sustained release profile would be of significant importance for systemic delivery, or brain tumor targeting, where a substantial amount of drug is expected to locate in the intracellular environment. To investigate the release kinetics, the data were fitted to various mathematical models including zero order, first order and Higuchi. It was found that the micellar formulations were best fitted to the Higuchi model. These results indicated that diffusion was the governing mechanism of release. In addition, the Korsemeyer-Peppas equation indicated the presence of more than one mechanism of release (18).
The cytotoxicity profiles of free DTX, DPP and RDPP when exposed to U87MG and 9L brain cancer cell lines for 24 and 48 h are shown in Fig. 2. All of the formulations showed time and concentration-dependent cytotoxicity on both of the cell lines. Marked differences were observed in the RDPP group, which exhibited significantly greater cytotoxicity as compared with the free drug and DPP groups (P<0.05). It was hypothesized that the pronounced cytotoxicity of RDPP may result from the enhanced internalization of the particles. The potent cytotoxic action of RGD-linked particles may increase the chances of brain cancer recovery. Conversely, free DTX showed higher cytotoxicity as compared with DPP, which is consistent with a previously published report which stated that free drugs diffuse easily into the cell nucleus, whereas micellar drugs have to be detached from the NP prior to exhibiting any therapeutic action (19). The 9L cells were relatively more sensitive to all of the formulations, as compared with the U87MG cells. The difference in the cytotoxic effects on both of the cell lines may be attributed to the difference in genetic origin and indigenous biological behavior (20). In order to precisely quantify the effects of the individual therapeutic systems, the half maximal inhibitory concentration (IC50) was evaluated. The IC50 values of free DTX, DPP and RDPP in U87MG were 8.56, 9.89, and 3.26 μg/ml, respectively following 24 h incubation, while these values decreased to 2.18, 2.38, and 1.05 μg/ml following 48 h incubation. The respective values in 9L cells were 6.85, 7.92, and 2.54 μg/ml for the 24 h incubation and 1.68, 1.74, and 0.76 μg/ml for the 48 h incubation periods. These results suggest that the specific interactions of the targeting ligand and the enhanced cellular uptake of carriers during a longer incubation period may greatly increase the drug cytotoxicity. Therefore, actively targeted RDPP may be preferentially taken up by the cells through receptor-mediated endocytosis resulting in increased cytotoxicity, whereas non-targeted micelles may enter by normal passive uptake mechanisms only (21).
In vitro cytotoxic analysis of different concentrations of docetaxel (DTX) on (A and B) U87MG and (C and D) 9L glioblastoma cancer cell lines. The cell viability was determined by MTT assay. The cells were seeded at a density of 10,000 cells per/well and incubated for 24 h prior to the exposure of free DTX, docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles for 24 h and 48 h at 37°C.
The majority of delivery systems exert their therapeutic action following internalization into the cells. Therefore, the present study investigated the cellular uptake efficiency of U87MG and 9L cancer cells, that can augment the accumulation of drugs. The cellular uptake of both the free drug and the NPs increased in a time-dependent manner up to 4 h (Fig. 3a,b). Maximum internalization was completed by 1 h, followed by a relatively slower uptake until the end of 4 h. As expected, the RDPP group exhibited a significantly higher uptake, as compared with that of either the free drug or DPP groups (P<0.05). This may be due to the presence of the RGD moiety on the surface, which has a selective affinity towards the overexpressed αvβ3 and αvβ5 integrins on the cancer cell surface (22). It has previously been demonstrated that RGD-based complexes are internalized by a combination of various mechanisms; including clathrin and caveolae-mediated endocytosis, clathrin and caveolae-independent endocytosis and macropinocytosis (23,24). The free DTX was continuously internalized in both of the cell lines, through passive diffusion. Specifically, 9L GBM cells showed relatively higher cellular uptake as compared with the U87MG cells. These data suggest that the RGD delivery system may be preferentially recognized by the integrin receptors present on the GBM cell surface, and may be internalized by various receptor and energy-dependent processes. Consequently, the active targeting moiety may be used to target the cancer cells upon intravenous injection and the higher uptake efficiency can rapidly remove the drug from the circulation.
Cellular uptake efficiency of free docetaxel (DTX), docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles in (A) U87MG and (B) 9L gliobastoma cancer cell lines. The cells were incubated with 25 μg/ml (DTX equivalent) for between 1–4 h and analyzed by high-throughput liquid chromatography. (C) U87MG and (D) 9L cells were treated with different formulations and cell cycle analysis was then performed using flow cytometry. *P<0.05, vs. free DTX.
Cell cycle analysis
The polymerization and depolymerization of microtubules has an important role in biological processes. DTX tightly binds microtubules, and promotes their stabilization, resulting in the mitotic arrest of cancer cells (25). It is well known that DTX induces cell cycle arrest through the impairment of mitosis and chromosomal damage, thereby inducing typical G2/M phase arrest (26). The cell cycle analyses of the cells treated with the different formulations are presented in Fig. 3C and D. The data shows the presence of the cell populations in the different phases upon treatment with the drug formulations. In the control group ~50% cells were in the G1 phase, whereas only ~7% cells were in the G2/M phase. In the RDPP group ~45% cells were shown to be in G2/M phase, as compared with ~30 and ~20% for the DPP and free DTX groups in U87MG cells, respectively. A similar trend was observed in 9L cells, however the proportion of cells in G2/M phase was relatively higher as compared with U87MG cells. The superior cell arresting effects of the RDK-linked formulations was consistent with the higher cellular uptake and cytotoxic potential, demonstrated in both of the cancer cell lines. It was hypothesized that RDPP may promote the stabilization of microtubules and differentiation of cancer cells. This may result in the downregulation of tubulin, leading to the impairment of mitotic spindle formation and eventually cell cycle arrest.
Analysis of in vitro spheroid inhibition
The inhibitory effects of free DTX, DPP and RDPP on the growth of U87MG and 9L spheroids are presented in Fig. 4. Spheroids in the untreated group grew rapidly and attained a maximum volume of ~125 and ~110% for U87MG and 9L cells, respectively. In contrast, the free and micellar drugs significantly inhibited the growth of the spheroids (P<0.05). The spheroids appeared distorted, disintegrated, shrunken and had lost their typical three dimensional structures. RDPP treatment resulted in a >80% reduction in spheroidal volume, indicating its superior inhibitory effects. Free DTX could directly kill the cells on the surface, however transport across the spheroid proved difficult. In contrast, hydrophobic core-containing micelles exhibited a preferential uptake. RGD-mediated cellular uptake may further increase the drug concentration within the spheroids. The inhibitory effect was in the order of RDPP > DPP > DTX. The stronger inhibitory effects of RDPP may be due to its better permeability within the cells, resulting in superior in vitro therapeutic effects (27).
Change in glioma spheroid volume upon exposure to the different formulations: Free docetaxel, docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles, at a dose of 1 μg/ml, on U87MG and 9L gliobastoma cancer cell lines. *P<0.05, vs. free DTX; **P<0.01, vs. control.
Evaluation of pharmacokinetics
The plasma concentration-time profiles of DTX, following a single dose intravenous administration of free DTX, DPP or RDPP, are presented in Fig. 5. Free DTX was immediately removed from the blood circulation and reached the detection limit within 6 h of the study period. In contrast, the micellar formulations significantly enhanced the circulatory performance of DTX (P<0.05). Substitution of PEG with the RGD block did not hamper the long circulation profile of RDPP, and a substantial concentration of DTX was detected throughout the study period (24 h). RDPP showed a 3–4 fold higher area under curve (36.85±4.52 h μg/ml) as compared with the free DTX (7.96±2.62 h μg/ml). Consequently, RDPP showed a significantly higher terminal half-life of 4.57 h, as compared with 0.91 h of the free drug. The longer circulation profile of RDPP may promote the likelihood of BBB permeation and higher tumor targeting ability.
Plasma concentration-time profile of docetaxel (DTX) following a single dose intravenous administration of free docetaxel, docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles. The formulations were administered via a tail vein injection, at a dose of 10 mg/kg. **P<0.01, vs. free DTX.
The concentration of DTX present in the mouse organs, including the brain, heart, spleen, liver, kidney, and lungs were investigated at different time points. The study was performed following a single dose intravenous injection of each formulation via the tail vein. The results clearly showed that RDPP was able to deliver the DTX into the brain at a significantly higher level as compared with the non-targeted DPP micelles and the free drug (P<0.05; Fig. 6A). RDPP exhibited ~1 μg DTX/g tissue after 30 min; this level gradually decreased up to 6 h, after which no drug was detected. Conversely, DPP showed ~0.5 μg DTX/g tissue at 30 min, which immediately decreased to the lowest level at 1 h, after which no drug was detected. No drug was detected in the free DTX group. The significantly higher concentration (P<0.05) observed in the RDPP group was consistent with its ability to interact with the cancer cells via receptor mediated endocytosis, whereas DPP could not influence the cellular uptake beyond a certain limit. Furthermore, the BBB is randomly disrupted in brain tumors, along with the components of the tumor blood vessels including the basement membrane, pericytes and the endothelial cells which provide entry for the nanosized particles (28). This further proves that passive targeting is inefficient in maintaining adequate concentrations of drugs in brain cancer cells. RGD-linking, however, along with an increased circulative ability, markedly enhanced the drug concentration levels. In the heart, liver and spleen, RDPP accumulated at relatively low levels, suggesting that drug-related systemic cytotoxicity may be effectively avoided (Fig. 6B–F). The reduced presence of the drug in the lung, in response to treatment with either of the micellar formulations, may be due to its nanosize, which may avoid enhanced uptake by the lung tissue.
Biodistribution of free docetaxel (DTX), docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles in U87MG tumor-bearing nude xenograft mice in different organs following intravenous administration of the different formulations. (A) Brain, (B) heart, (C) liver, (D) spleen, (E) lung, (F) kidney. The mice were sacrificed at 0.5, 1, 2, 4, 6, 12, and 24 h post-injection.
A U87MG-bearing tumor model was developed and treated with the various formulations. As shown in Fig. 7, RDPP significantly inhibited the growth of glioblastoma tumors, as compared with that of the control and free drug treated groups of mice (P<0.05). The tumor volume remained the same until day four, however after that, significant differences were observed between the different groups. Tumors in the saline and control groups grew rapidly and attained maximum size. The marked antitumor efficacy of the RGD-linked micelles was attributed to the specific binding with the highly angiogenic neovasculature of subcutaneously grown GBM cells. Consistent with the long circulation profile and the drug accumulation in the specific tumors, enhanced tumor regression may be anticipated. Similar results have been reported by previous studies which demonstrated the improved antitumor effects for RGD-linked delivery systems (29,30).
In vivo antitumor efficacy upon treatment with free docetaxel (DTX), docetaxel polylactic acid-polyethylene glycol (DTX-PLA-PEG) or DTX-PLA-PEG/cyclic (Arginine-Glycine-Aspartic acid-D-Tyrosine-Lysine) [DTX-PLA-PEG/c(RGDyK)] micelles in U87MG tumor-bearing nude xenograft mice. (A) The change in tumor volume and (B) the variation in body weight as a function of time. The formulations were administered at a dose of 5 mg/kg by tail vein injection four times over an interval of three days. ***P<0.01, vs. control.
The body weight fluctuations of the mice were assessed in terms of in vivo systemic toxicity of the drug and delivery system. Body weight of the individual mice was noted throughout the study period alongside the tumor volume measurement. The mice administered with saline and the control group experienced a gain in body weight, attributed to an increased tumor volume. In the DPP and RDPP administered groups, no loss of body weight was observed, indicating a lack of any serious drug-related toxicity.
Thus far, glioblastoma, which represents one of the deadliest forms of cancer, is unresponsive to chemotherapy mainly due to the poor penetrability of therapeutics across the BBB and BBTB. Therefore, the aim of the present study was to design a delivery system, appended to a targeting ligand, that could overcome these physiological barriers and deliver the anticancer drugs into the glioma cells. GBM is generally characterized by angiogenesis and over-expression of the integrin αvβ3 receptor on the surface of the tumor neovasculature. In the present study c(RGDyK) peptide was selected as a specific targeting agent to the integrin receptors. The results clearly showed that RDPP could effectively bind the αvβ3 receptor, facilitating the cellular uptake and inreasing the cytotoxicity of the drug. Overexpression of the αvβ3 receptor resulted in an enhanced accumulation of RDPP in the brain tumor cells in vivo, whilst non-targeted micelles had limited access. RGD-linked micelles showed pronounced tumor regression with an excellent safety profile. Therefore, the results clearly revealed the superior antitumor efficacy of c(RGDyK)/DTX-PLA-PEG in an experimental brain tumor model.
In conclusion, DPP and RDPP were successfully prepared and subjected to various in vitro and in vivo characterizations. RDPP showed enhanced accumulation in U87MG and 9L glioblastoma cell lines, through various endocytic pathways, and displayed pronounced cytotoxic effects in the cell lines with markedly lower IC50 values. Furthermore, RDPP showed a typical G2/M phase arrest and stronger microtubule stabilizing effects. Consequently, high accumulation and distribution of RDPP resulted in tremendous growth inhibition of glioma spheroids, as compared with the non-targeted DPP and free drug. The ability of RDPP to bind the αvβ3 integrin receptor resulted in a high accumulation of DTX in the brain glioblastoma cells, which in turn may be due to the specific interaction of micelles, small particle size and an extended blood circulation profile. The enhanced tumor regression in the U87MG tumor-bearing mice further confirmed the superior anti-glioblastoma efficacy of RDPP. The findings of the present study suggest that c(RGDyK) linked to delivery carriers may be a potential strategy for the treatment of advanced brain cancer.
The authors would like to thank Dr. Shiam for proof reading the manuscript.
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