- Nano Express
- Open Access
Smart Nanoparticles Based on Hyaluronic Acid for Redox-Responsive and CD44 Receptor-Mediated Targeting of Tumor
© Park et al. 2015
- Received: 16 March 2015
- Accepted: 14 June 2015
- Published: 11 July 2015
Since aggressive cancer cells highly express the CD44 receptor compared to normal cells, hyaluronic acid (HA) can be used for CD44 targeting molecule. Since glutathione (GSH) level is normally elevated in the intracellular compartment and in the tumor cell, the fact that disulfide bond can be cleaved by GSH is widely used for intracellular drug delivery.
HA was connected with poly(dl-lactide-co-glycolide) (PLGA) using disulfide linkage, and then a diblock copolymer (HAssLG) was prepared. Doxorubicin (DOX)-loaded HAssLG nanoparticles were prepared by dialysis procedures.
Results and Discussion
DOX-loaded HAssLG nanoparticles have spherical shapes with small particle size of less than 300 nm. In fluorescence measurement, DOX was dose-dependently liberated from nanoparticles by the addition of GSH. DOX release rate from HAssLG nanoparticles was increased by the addition of GSH. To confirm CD44 receptor-mediated endocytosis of nanoparticles, CD44-positive MDA-MB231 cells were employed and fluorescence intensity was strong when nanoparticles were treated to tumor cells. However, fluorescence intensity was significantly decreased through blocking of the CD44 receptor by pretreatment of cells with free HA. Fluorescence intensity of cells was increased again when GSH was added, indicating that HAssLG nanoparticles have CD44 receptor targetability and potential of redox-responsive drug delivery. For animal imaging study, CD44-positive MDA-MB231 cells and CD44-negative NIH3T3 cells were simultaneously implanted into the right flank and left flank of mice, respectively. Fluorescence intensity was significantly stronger at tumor mass of MDA-MB231 cells than solid mass of NIH3T3 cells, indicating that HAssLG nanoparticles were specifically delivered to tumor cells.
The results indicated that HAssLG nanoparticles have specificity against the CD44 receptor and can be used for anticancer drug targeting. We recommend HAssLG nanoparticles as a promising vehicle for cancer drug targeting.
- Hyaluronic acid
- CD44 receptor-mediated endocytosis
- Block copolymer
Nanomedicines based on nanotechnology have been extensively investigated for drug delivery issues, and they can be considered as appropriate vehicles for tumor targeting due to their small sizes [1–4]. Especially, nanosized vehicles such as nanoparticles or polymeric micelles have superior potentials for solid tumor targeting because the enhanced permeation and retention (EPR) effect against tumor blood vessels is regarded as a preferential advantage of nanovehicles for solid tumor targeting [5, 6]. Furthermore, nanoparticles can be decorated with various targeting moieties for specific targeting of cancer cells since they have a big surface area [7–10]. Due to these intrinsic properties, nanoparticles can concentrate cytotoxic anticancer drug to the solid tumor with minimal unwanted side effects for normal tissues/cells. From these points of view, nanoparticles decorated with targeting moieties have been also extensively investigated [7–10].
Aggressive tumor cells frequently overexpress the CD44 receptor in the cell membrane [11–18]. This is a specific receptor for hyaluronic acid (HA), and HA is known to stimulate spreading, migration, invasion, and metastasis of cancer cells [11–14, 17]. From these reasons, hyaluronic acid has been extensively used as a vehicle for specific targeting of the CD44 receptor of tumor cells [8, 18–22]. Especially, Prestwich’s group extensively investigated the potential of CD44 receptor delivery of HA-anticancer agent conjugates against cancer cells [19–22]. Furthermore, HA was also investigated for tissue engineering, gene delivery, and peptide delivery due to the biodegradability and biocompatibility [23–25].
Nanoparticles based on redox-responsive drug targeting for cancer cells also have been extensively investigated in the last decades [26–29]. Redox-responsive drug delivery is based on the fact that disulfide bond can be reduced by glutathione and intracellular glutathione (GSH) level is significantly higher than the extracellular fluid level . This peculiar property between GSH and disulfide bond stimulated the redox-responsive drug delivery concept. For example, Sun et al. synthesized a poly(ethylene glycol)/poly(ε-caprolactone) block copolymer using disulfide bond . They showed that drug release rate was increased by the addition of dithiothreitol (DTT) and enhanced tumor cell uptake of anticancer drugs was observed. Furthermore, redox-responsive delivery of DNA drugs using disulfide-linked polymer nanovehicles was also investigated by several authors [26–29]. In spite of successful development of the redox-responsive drug delivery system, GSH levels in normal tissues and low specificity of nanoparticles are still obstacles for efficient drug targeting. For example, GSH levels can be increased in the tissues of a tumor-bearing mice compared to a normal mice . Therefore, multiple targeting strategies are required to attain efficient targeting of tumors.
In this study, we synthesized a HA-b-PLGA (HAssLG) copolymer having disulfide linkage between HA and PLGA for targeting of tumor cells through the CD44 receptor and redox-responsive process. Since PLGA is a biodegradable and lipophilic polymer, PLGA must form the core of the nanoparticles while HA would form the outer shell of the nanoparticles. We studied the potential of CD44 receptor-mediated and redox-responsive targeting of tumor cells by HAssLG nanoparticles using tumor cells and fibroblast cells in vitro and in vivo.
HA (molecular weight from the manufacturer’s data, 7460 g/mol) was purchased from Lifecore Biomedical (Chaska, MN, USA). Triethylamine (TEA), L-glutathione (GSH), sodium cyanoborohydride, N-(3-dimethylaminopropyl)-N′-ethylcarbodiimide hydrochloride, and cystamine hydrochloride were purchased from Sigma Chem. Co. (St. Louis, USA). N,N′-dicyclohexyl carbodiimide (DCC) and N-hydroxysuccimide (NHS) were purchased from Sigma-Aldrich Chemical Co, USA. The dialysis membranes (Spectra/Pro™ membranes) with molecular weight cutoffs (MWCO) of 2000 and 12,000 g/mol were purchased from Spectrum Labs. Doxorubicin (DOX) HCl was purchased from LC Labs Co. Ltd. (Woburn, MA, USA). Dichloromethane (DCM) and dimethyl sulfoxide (DMSO) were of HPLC grade or extra-pure grade. PLGA (PLGA-5005, MW = 5000 g/mol) was purchased from Wako Pure Chemicals Co. (Osaka, Japan). The molecular weight (MW) of PLGA was measured by GPC, as described previously . The weight average MW, number average MW, and polydispersity of PLGA were 4920, 4780, and 1.029, respectively.
Synthesis of HAssLG Block Copolymer
HA having disulfide linkage in the end of the chain was synthesized as described by Maruyama et al.  with brief modification. HA (400 mg) was dissolved in 10 ml of H2O/DMSO (3/7, v/v) solution, and then excess amount of sodium cyanoborohydride was added to this solution followed by magnetic stirring for 12 h at room temperature. After that, 10 equivalents of cystamine were added and the mixtures were further stirred for 24 h. The resulting solution was put into a dialysis membrane (MWCO, 2000 g/mol), and by-products were removed by dialysis procedure for 2 days followed by lyophilization for 3 days.
NHS-activated PLGA (PLGA-NHS) was separately prepared. Five hundred milligrams of PLGA was dissolved in DCM with 1.2 equivalents of DCC and NHS. This solution was stirred for 12 h, and then reactants were precipitated into the excess amount of methanol followed by filtration under reduced pressure. The white solid was washed with methanol three times followed by vacuum drying for a day.
The HAssLG block copolymer was synthesized as follows: 400 mg HA-cystamine conjugates and 250 mg of PLGA-NHS were simultaneously dissolved in dry DMSO and stirred in nitrogen atmosphere for 2 days. After that, this solution was then introduced into a dialysis membrane (MWCO, 12,000 g/mol) to remove the unreacted HA and organic solvent. During the dialysis procedure, water was exchanged at 3-h intervals for 2 days and then the resulting solution was lyophilized for 3 days. The lyophilized solid was precipitated into DCM to remove unreacted PLGA for three times, and then filtered precipitates were dried under a vacuum for 3 days. The yield of the final product was 81 % (w/w). Yield of product (%, w/w) = [(weight of final product)/(weight of aminated HA + PLGA-NHS)] × 100.
1H Nuclear Magnetic Resonance Spectroscopy
1H nuclear magnetic resonance (NMR) spectroscopy (500 MHz superconducting FT-NMR spectrometer, Unity-Inova 500, Varian Inc., Agilent Tech., CA, USA) was employed to confirm synthesis of polymers.
Preparation of HAssLG Nanoparticles
Characterization of HAssLG nanoparticles
Drug contents (%, w/w)
Analysis of Nanoparticles
Transmission electron microscopy (TEM, JEOL JEM-2000 FX II, Japan) was used to observe the morphology of nanoparticles. One drop of nanoparticle solution (0.1 mg/ml) was dropped onto a carbon film coated on a copper grid and then dried in room temperature. Three hours later, phosphotungstic acid (0.05 %, w/w) was then dropped onto nanoparticles for negative staining and dried in room temperature for more than 6 h. Observation of nanoparticles was performed at 80 kV.
Particle size was measured with dynamic laser scattering (DLS-7000, Otsuka Electronics Co., Japan) (nanoparticle concentration, 0.1~1 mg/ml).
Drug Release Study
DOX release from HAssLG nanoparticles was performed as follows: 10 mg of DOX-incorporated nanoparticles was dispersed in 5 ml of phosphate-buffered saline (PBS, 0.1 M, pH 7.4), and this solution was put into a dialysis membrane (MWCO, 12,000 g/mol). After that, the dialysis membrane was introduced into 95 ml PBS in a bottle. Drug release was performed in a shaking incubator with 100 rpm of stirring speed at 37 °C. Whole media were replaced with fresh media at specific time intervals. The released DOX was measured with a UV spectrophotometer (UV spectrophotometer 1601, Shimadzu Co., Japan) at 486 nm.
MDA-MB231 human breast carcinoma cells and NIH3T3 mouse fibroblast cells were obtained from Korea Cell Line Bank Co. (KCLB, Seoul, Korea). MDA-MB231 human breast carcinoma cells and NIH3T3 mouse fibroblast cells were maintained in RPMI1640 and DMEM supplemented with 10 % fetal bovine serum (5 % CO2 at 37 °C), respectively.
Cell viability test was performed as follows: MDA-MB231 (1 × 104 cell/well) cells were seeded into 96-well plates and then incubated overnight (5 % CO2 at 37 °C). DOX or nanoparticles were treated to these cells. The CD44 receptor of the cells was blocked with 10 equivalents of free HA 1 h before nanoparticle treatment, and then the cells were washed with PBS. After that, DOX or nanoparticles were added to the cells in the 96-well plates and incubated in a CO2 incubator (5 % CO2 at 37 °C) for 4 or 24 h. After that, media were discarded and then replaced with 100 μl of fresh media. To this solution, 30 μl of MTT (5 mg/ml) was added, and then the solution was further incubated in a CO2 incubator (5 % CO2 at 37 °C) for 4 h. Since the contents of the generated formazan were proportional to the number of viable cells, the generated formazan was solubilized with DMSO and determined with an automated computer-linked microplate reader (Molecular Device Co., USA) (560 nm test/630 nm reference).
Receptor-Mediated Delivery of Nanoparticles to Tumor Cells
Cellular uptake of DOX-loaded HAssLG nanoparticles was studied with fluorescence microscopy observation and flow cytometry analysis. MDA-MB231 cells were seeded onto a cover glass and incubated overnight in a CO2 incubator (5 % CO2 at 37 °C). Then, nanoparticles were treated to cells for 1 h in a CO2 incubator. One hour before the addition of nanoparticles, the CD44 receptor was blocked by pretreatment of free HA (10 equivalents of nanoparticle contents). Following this, cells were washed with PBS (pH 7.4, 0.1 M) and fixed with 4 % paraformaldehyde. This was fixed with immobilization solution (IMMU-MOUNT, Thermo Electron Corporation, Pittsburgh, PA, USA). Cells were then observed with a confocal laser scanning microscope (CLSM, TCS-SP2; Leica, Wetzlar, Germany).
For flow cytometry analysis of cells, 1 × 106 cells were seeded in each well of six-well plates. Nanoparticles were treated to the cells and incubated for 1 h in a CO2 incubator. One hour before the addition of nanoparticles, the CD44 receptor was blocked by pretreatment of free HA (10 equivalents of nanoparticle contents). Cells were washed with PBS (pH 7.4, 0.1 M) and trypsinized to harvest cells. The cells were analyzed with flow cytometery (FACScan) at an excitation wavelength of 488 nm and emission wavelength of 522 nm for DOX fluorescence intensity.
Near-Infrared Absorption Dye Conjugation
A near-infrared (NIR) dye was conjugated with HAssLG for in vivo animal imaging studies. Fifty milligrams of HAssLG in 5 ml DMSO/water mixtures (4/1, v/v) was mixed with 3 mg of sulfo-cyanine7 amine (Lumiprobe Co., Florida, USA) with 1.2 equivalent moles of EDAC and NHS. This solution was then stirred for 24 h in room temperature. After that, the solution was dialyzed to remove unreacted dye with exchange of water at intervals of 2 h until the dye was not detected in the water. The detection of the dye and the contents in the polymer were measured with a UV spectrophotometer (UV-1601 UV-VIS spectrophotometer, Shimadzu, Kyoto, Japan) at 750 nm. The content of the NIR dye was 2.8 %, w/w. (Dye content (%, w/w) = (dye amount in the nanoparticles/total weight of the nanoparticles) × 100).
In Vivo Fluorescence Imaging
For fluorescence imaging of the biodistribution of nanoparticles, 1 × 106 MDA-MB231 cells and 1 × 106 NIH3T3 cells were implanted into the right flank and left flank of nude BALb/C mice (5 weeks, 20 g), respectively. After 20 days, NIR-dye-conjugated nanoparticles were administered intravenously (i.v.) into the tail vein of mice at a dose of 20 mg/kg (injection volume was 100 μl). Mice were observed with a Maestro™ 2 small-animal imaging instrument (Cambridge Research and Instruments, Inc., Woburn, MA, USA). Twenty-four hours later, mice were sacrificed to evaluate organ distribution of nanoparticles with the Maestro™ 2 small-animal imaging instrument. All animal studies were performed under the guidelines of the Committee of Care and Use of Laboratory Animals of Chonnam National University.
Characterization of HAssLG Block Copolymer
Characterization of Nanoparticles
CD44 Receptor-Mediated Targeting of HAssLG Nanoparticles
In Vivo Animal Imaging Study
HA is a linear polysaccharide composed of d-glucuronic acid/N-acetyl-d-glucosamine units and has a vital role in the physiological phenomenon of cells such as adhesion, growth, migration, cell motility, inflammation, and invasion [31–36]. Especially, specific receptors for HA such as CD44 and RHAMM are frequently overexpressed in cancer cells rather than normal cells [11–18]. In addition to these findings, the fact that HA has biocompatibility, biodegradability, and functional moiety such as carboxylic acid stimulates application of HA in the biomedical field and drug targeting research [8, 19–25]. Hyung et al. reported that HA-decorated nanoparticles on the surface effectively targeted the CD44 receptor of CD44-overexpressed cells rather than lower CD44-expressed cells, while pure PLGA nanoparticles did not show targeting differences in both cells . Since invasive cancer cells generally plentifully secreted hyaluronidase, anticancer agent release and delivery can be stimulated at invasive cancer cells and then specifically attack these cells through accelerated drug release by hyaluronidase .
Meanwhile, redox-responsive drug delivery has been also widely investigated for targeted drug delivery to tumor [26, 28, 29, 37]. Disulfide bond, which is abundant in the peptide and protein, can be cleaved by an intracellular reducing molecule, GSH, while it is stable at the extracellular environment . Furthermore, the GSH level in the intracellular compartment (~10 mM) is known to be elevated compared to that in the extracellular environment (~10 μM). Especially, GSH level is elevated in the tumor cells . These findings facilitated intracellular drug targeting strategy by the introduction of disulfide bond in the polymer chain [27, 37]. Sun et al. synthesized a diblock copolymer having a disulfide bond between dextran and poly(ε-caprolactone), and then drug release rate was increased through cleavage of disulfide bond by GSH . These phenomena enabled nanovehicles to target the intracellular compartment.
A HAssLG diblock copolymer was synthesized for application in the sequential targeting concept of nanoparticles by CD44 receptor-mediated and redox-responsive drug delivery. HAssLG nanoparticles have spherical shapes with nanosized diameter. DOX-loaded HAssLG nanoparticles were prepared by dialysis procedure. DOX release was facilitated by addition of GSH, indicating that the disulfide bond of HAssLG nanoparticles was cleaved and then DOX release rate was increased. In an in vitro cell culture study, DOX-loaded HAssLG nanoparticles were endocytosed by CD44 receptor-mediated pathway. An animal NIRF imaging study also proved that HAssLG nanoparticles were delivered to tumor tissues through a targeting mechanism. We suggest that HAssLG nanoparticles are a promising candidate for tumor targeting.
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