Novel tumor-targeting, self-assembling peptide nanofiber as a carrier for effective curcumin delivery
Authors Liu J, Liu J, Xu H, Zhang Y, Chu L, Liu Q, Song N, Yang C
Received 12 October 2013
Accepted for publication 28 November 2013
Published 24 December 2013 Volume 2014:9(1) Pages 197—207
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 4
Jianfeng Liu, Jinjian Liu, Hongyan Xu, Yumin Zhang, Liping Chu, Qingfen Liu, Naling Song, Cuihong Yang
Tianjin Key Laboratory of Molecular Nuclear Medicine, Institute of Radiation Medicine, Chinese Academy of Medical Science and Peking Union Medical College, People's Republic of China
Abstract: The poor aqueous solubility and low bioavailability of curcumin restrict its clinical application for cancer treatment. In this study, a novel tumor-targeting nanofiber carrier was developed to improve the solubility and tumor-targeting ability of curcumin using a self-assembled Nap-GFFYG-RGD peptide. The morphologies of the peptide nanofiber and the curcumin-encapsulated nanofiber were visualized by transmission electron microscopy. The tumor-targeting activity of the curcumin-encapsulated Nap-GFFYG-RGD peptide nanofiber (f-RGD-Cur) was studied in vitro and in vivo, using Nap-GFFYG-RGE peptide nanofiber (f-RGE-Cur) as the control. Curcumin was encapsulated into the peptide nanofiber, which had a diameter of approximately 10–20 nm. Curcumin showed sustained-release behavior from the nanofibers in vitro. f-RGD-Cur showed much higher cellular uptake in αvβ3 integrin-positive HepG2 liver carcinoma cells than did non-targeted f-RGE-Cur, thereby leading to significantly higher cytotoxicity. Ex vivo studies further demonstrated that curcumin could accumulate markedly in mouse tumors after administration of f-RGD-Cur via the tail vein. These results indicate that Nap-GFFYG-RGD peptide self-assembled nanofibers are a promising hydrophobic drug delivery system for targeted treatment of cancer.
Keywords: nanofiber, tumor-targeting, self-assembling, curcumin, drug delivery
Because almost all chemotherapeutic antitumor agents have no tumor-targeting activity and cause serious adverse effects, their clinical application is restricted. Many nanomaterials have been proposed as drug carriers to overcome this barrier to the use of chemotherapeutic drugs.1 The enhanced permeability and retention effect of nanomaterials can improve the accumulation of chemotherapeutic agents at tumor sites. For example, liposomes, carbon nanotubes, dendrimers, and micelles have been used as carriers for SN38, doxorubicin, paclitaxel, and cisplatin to improve drug concentrations in tumors and reduce adverse effects.2–5 Another advantage of using nanomaterials as drug carriers is the enhanced solubility of chemotherapeutic drugs. Many of these agents have poor aqueous solubility, leading to low bioavailability. For example, the aqueous solubility of paclitaxel is 30 μg/mL and for hydroxycamptothecin is only 3.9 μg/mL. The hydrophobic region of amphiphilic nanomaterials can solubilize drugs, and their hydrophilic region makes drugs soluble in an aqueous environment.6
Self-assembling peptide nanofibers have attracted considerable interest because of their good biocompatibility, easy modification, and design flexibility through a “bottom-up” approach. They have been widely used in three-dimensional cell culture,7 tissue engineering, and regenerative medicine research.8,9 Self-assembling peptide nanofibers have also been used as drug delivery systems to enhance solubility of a hydrophobic drug, improve accumulation at the tumor site, and reduce adverse effects.10 Hydrophobic antitumor drugs such as paclitaxel,11 camptothecin,12 and ellipticine13 encapsulated into peptide nanofibers have shown improved antitumor effects. Some studies have demonstrated that the two-dimensional structure of peptide nanofibers is superior to the three-dimensional structure of nanoparticles for drug carriers. For example, Law et al found that peptide-based nanofibers have better biocompatibility, better tumor targeting within a shorter time frame, and more rapid elimination compared with spherical nanomaterials (poly[lactic-co-glycolic acid], gold, polystyrene, cadmium and selenium quantum dots), and carbon rods.14
The conjugation of tumor-targeting agents to nanomaterials is another strategy for improving tumor accumulation and bioavailability of drugs. Peptides,15 proteins,16 aptamers,17 vitamins,18 and polysaccharides19 have been developed as tumor-targeting agents. Among these molecules, the tripeptide motif, arginine-glycine-aspartic acid (RGD), has attracted great attention. RGD is the binding motif of integrin ανβ3, which is overexpressed on the angiogenic endothelium in malignant tumors and is vital for the adhesion, signaling, migration, and survival of integrin ανβ3 over-expressed cancer cells.20,21 It has been widely used for tumor diagnosis and targeting therapy. Liposomes,22 micelles,23 dendrimers24 and silica nanoparticles25 have been conjugated with RGD to introduce tumor-targeting activity. RGD has also been used in positron emission tomography,26 single photon emission computed tomography,27 magnetic resonance imaging,28 and optical29 imaging for diagnosis of cancer.
In this study, we report the design, synthesis, and characterization of a novel peptide nanofiber, self-assembled from Nap-GFFYG-RGD, as a tumor-targeting drug carrier. In order to study the RGD tumor-targeting activity, nanofibers self-assembled from Nap-GFFYG-RGE were also synthesized as the control. Curcumin, a hydrophobic antitumor agent, was used as the model drug. The nanofibers were characterized with respect to their morphology, drug encapsulation efficiency, and in vitro drug release. In vitro cytotoxicity was analyzed in human hepatocellular liver carcinoma (HepG2) and mouse embryonic fibroblast (NIH3T3) cell lines. Cellular uptake was investigated in HepG2, human embryonic kidney (293T), and human breast cancer (MCF-7) cell lines. Ex vivo biodistribution on HepG2 xenografts in nude mice was also studied to confirm the tumor-targeting activity of the nanofibers.
Materials and methods
Curcumin (diferuloyl methane) and peptides were purchased from Sigma-Aldrich Corporation (Carlsbad, CA, USA). 2-chlorotrityl chloride resin and Fmoc-amino acids were obtained from GL Biochem (Shanghai, People’s Republic of China). 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyl tetrazolium bromide (MTT), dimethyl sulfoxide, and other chemical reagents and solvents were sourced from Alfa (Shenzhen, People’s Republic of China). A dialysis membrane (molecular weight cut-off 1,000 Da) was purchased from BBI Inc (Shanghai, People’s Republic of China). All cell culture media and supplies were purchased from Gibco Corporation (Grand Island, NY, USA).
NIH3T3, HepG2, 293T, and MCF-7cells were cultured in Roswell Park Memorial Institute 1640 medium supplemented with 10% fetal bovine serum, 100 U/mL penicillin, and 100 μg/mL streptomycin. The cells were maintained at 37°C with 5% CO2. Other reagents were commercially available and used as received.
1H nuclear magnetic resonance (NMR, Varian Unity Plus 400 mHz, Varian Instruments, Palo Alto, CA, USA) was used to characterize the peptides. Electrospray ionization tandem mass spectrometric analyses were performed on an LCQ AD system (Thermo Finnigan, Silicon Valley, CA, USA). Transmission electron microscopy was performed on a Tecnai G2 F20 system (FEI Co, Columbia, MD, USA) operating at 200 kV. The crude peptide was purified on a high-pressure liquid chromatography system (LumTech, Moorestown, Germany) using a C18 reversed phase column with MeOH (0.1% trifluoroacetic acid) and water (0.1% trifluoroacetic acid) as the eluents.
Preparation and characterization of peptides
The peptides, ie, Nap-GFFYG-RGD (p-RGD) and Nap-GFFYG-RGE (p-RGE), were prepared by solid phase peptide synthesis using 2-chlorotrityl chloride resin. The first Fmoc-protected amino acid was loaded onto the resin at the C-terminal. The Fmoc group of the amino acid was deprotected with 20% piperidine in anhydrous N,N’-dimethylformamide. The next Fmoc-protected amino acid was activated by N,N-diisopropylethylamine and coupled to the free amino group using O-(benzotriazol-1-yl)-N,N,N′,N′-tetramethyluronium hexafluorophosphate as the coupling reagent. The growth of the peptide chain was allowed to proceed according to the standard Fmoc solid phase peptide synthesis protocol. After the last coupling step, the peptide derivatives were cleaved from the resin with a mixture of 1% trifluoroacetic acid and 99% dichloromethane for 10 minutes, then dried via rotary evaporation followed by diethylether precipitation. The crude products were purified by reverse phase high-pressure liquid chromatography. 1H NMR spectroscopy and high-resolution mass spectrometry were used to characterize the peptides.
Preparation of f-RGD-Cur and f-RGE-Cur
Fifty milligrams of curcumin were dissolved in 5 mL of anhydrous dimethyl sulfoxide and stirred at 40°C. p-RGD and p-RGE were dissolved in phosphate-buffered saline (pH 7.4) and the concentrations were adjusted to 3 mg/mL. Next, 500 μL of p-RGD and p-RGE solutions were heated to boiling point and cooled to 40°C, and 22 μL of curcumin solution at 40°C was then added to the p-RGD and p-RGE solutions. The reaction mixtures were incubated in a 40°C water bath for 2 hours. Curcumin-encapsulated Nap-GFFYG-RGD peptide nanofiber (f-RGD-Cur) and curcumin-encapsulated Nap-GFFYG-RGE peptide nanofiber (f-RGE-Cur) were then formed by incubation at room temperature for 2 hours. Unassembled curcumin was removed by centrifugation for 20 minutes at a speed of 1,500× g. The morphologies of the nanofibers were observed by transmission electron microscopy.
Transmission electron microscopy
Solutions of f-RGD, f-RGE, f-RGD-Cur, and f-RGE-Cur were prepared as described above. Next, 10 μL samples of each were placed on a carbon-coated copper grid and incubated for 30 seconds to allow the peptide nanostructures to adhere to the substrate, then rinsed twice with ultrapure water. The samples were then stained with a saturated uranyl acetate solution and placed in a desiccator overnight prior to analysis.
In vitro drug release
In vitro drug release was evaluated using the dialysis method. Dialysis bags (molecular weight cut-off 1,000 Da) containing 0.5 mL of f-RGD-Cur or f-RGE-Cur solution were immersed in a thermostatic gas bath containing 20 mL of release medium (0.5% Tween 80 in phosphate-buffered saline, pH 7.4) at 37°C. At predefined intervals, 1 mL aliquots of receiving buffer were withdrawn and replaced with the same volume of release medium. The drug-release behavior of the carriers was determined by ultraviolet spectrophotometry (Agilent 8453, Agilent Technologies, Santa Barbara, CA, USA) at 428 nm.
In vitro cellular uptake
Curcumin has an intrinsic fluorescence spectrum that is often used to monitor its localization. 293T, MCF-7, and HepG2 cells were seeded into 24-well plates at a density of 3 × 104 cells/well in 500 μL of Roswell Park Memorial Institute 1640 medium supplemented with 10% fetal bovine serum. After incubating for 24 hours, the culture medium in each well was replaced with 500 μL of fresh medium containing 10 μg/mL of free curcumin or equivalent curcumin-containing f-RGD-Cur or f-RGE-Cur. After incubating for 4 hours, the cells were rinsed three times with 500 μL of phosphate-buffered saline to remove the free curcumin, f-RGD-Cur, or f-RGE-Cur. Cellular uptake was visualized on an inverted fluorescence microscope (DMI6000B, Leica, Wetzlar, Germany).
In vitro cytotoxicity
The cytotoxicity of free curcumin, f-RGD-Cur, and f-RGE-Cur was evaluated using the MTT assay with NIH3T3 and HepG2 cells. The cells were seeded into 96-well plates at a density of 1 × 104 cells/well in 100 μL of culture medium and incubated for 24 hours. Next, 100 μL of culture medium containing different concentrations of free curcumin, f-RGD-Cur, or f-RGE-Cur were added to 96-well plates for 24 hours. Each treatment was repeated in eight wells. After incubation for the specified time at 37°C in a humidified incubator, 20 μL of MTT solution (5 mg/mL in phosphate-buffered saline) were added to each well. Four hours later, the medium containing MTT was removed and 150 μL of dimethyl sulfoxide were added to dissolve the formazan crystals. The optical density of the solution was measured at 570 nm on a microplate reader (Varioskan Flash, Thermo Fisher Scientific, South Logan, UT, USA). The effect of each agent on growth inhibition was determined as a percentage of the viability of cells treated with nanofiber without curcumin, for which the viability was taken as 100%. The cell viability was calculated from the equation:
Ex vivo distribution
BALB/c mice (male, aged 4–6 weeks, weight 18–22 g) were purchased from the Laboratory Animal Center of The Academy of Military Medical Sciences (Beijing, People’s Republic of China). All animal procedures were performed according to the guidelines of the Regulations for the Administration of Affairs Concerning Experimental Animals (Tianjin, People’s Republic of China, revised in June 2004) and adhered to the Guiding Principles in the Care and Use of Animals of the American Physiological Society. HepG2 cells (1 × 107) suspended in phosphate-buffered saline were subcutaneously injected into the right flank to produce liver cancer xenografts. About 2 weeks after inoculation, when the tumors had reached a volume of approximately 300 mm3, the mice were randomized into three groups (n=5 each), and 200 μL (10 μg/mL) of free curcumin or equivalent curcumin-containing f-RGD-Cur or f-RGE-Cur were injected via the tail vein. Four hours following injection, the mice were sacrificed, and the heart, liver, spleen, lung, kidneys, and tumor were isolated under white light and immediately scanned using a Kodak IS in vivo FX imaging system (Kodak, New Haven, CT, USA). The fluorescence images were acquired using a 464 nm excitation filter and 535 nm emission filter. The relative fluorescence intensity per unit area was calculated using Kodak 5.1 software.
All statistical analysis was performed using Statistical Package for the Social Sciences version 16 software (SPSS Inc, Chicago, IL, USA). The statistical significance of differences was determined by one-way analysis of variance. All statistical tests were two-sided, and P-values less than 0.05 were considered to be statistically significant. The results are shown as mean ± standard deviation.
Results and discussion
Preparation and characterization of f-RGD-Cur and f-RGE-Cur
Recent studies have indicated that the shape of nanostructures may greatly affect their in vivo biodistribution, and some flexible filament nanostructures have shown longer blood circulation and better antitumor effects than spherical nanostructures.14,30,31 The p-RGD and p-RGE peptides were synthesized (Figures 1A and S1–S4) and used to form nanofiber skeletons by self-assembly via electrostatic and hydrophobic interactions. The peptides formed single-layer nanofibers (approximately 10–20 nm in width) that could be visualized by transmission electron microscopy (Figure 2A and B). Curcumin was encapsulated into the nanofibers without any obvious effects on the shape of the nanofibers (Figure 2C and D). This result is consistent with the report of Zhang et al.11 Figure 1B shows the Nap-GFFYG-RGD peptide self-assembling into nanofibers and drug encapsulation.
Figure 1 (A) Molecular structures of Nap-GFFYG-RGD and Nap-GFFYG-RGE. (B) Schematic illustration for formation of Nap-GFFYG-RGD peptide nanofibers and encapsulation of curcumin.
Encapsulation efficiency and in vitro release of curcumin
As a natural medicine used in Asia, curcumin extracted from different plants has been shown to have potential antitumor activity. It can suppress the expression of epidermal growth factor receptor and estrogen receptors, which are cancer-associated growth factor receptors.32 Curcumin has been widely used in antitumor research, but its poor solubility in water results in poor bioavailability and restricts its clinical application.33,34 Amphiphilic nanomaterials have been used to improve the solubility of curcumin.35,36 Zhang et al found that the hydrophobic drug, paclitaxel, could be encapsulated into the hydrophobic core formed by self-assembled peptide nanofibers.11 Pochan et al also reported that curcumin could interact with hydrophobic peptide moieties and encapsulate into self-assembled peptide hydrogels.37 Figure 3A shows the encapsulation efficiency of curcumin with RGD and RGE peptide nanofibers. The amount of curcumin solubilized in the nanofibers increased with the peptide concentration from 0.5 mg/mL to 5 mg/mL. When the concentration of curcumin was 0.5 mM and the peptide concentration was 5 mg/mL, the efficiency of encapsulation of curcumin into the nanofibers reached about 32%.
Controlled and sustained drug release is a desirable feature of drug carriers. In order to verify the sustained drug release characteristics of curcumin-loaded peptide nanofibers, the in vitro release of f-RGD-Cur and f-RGE-Cur was studied using a dialysis method. The drug release profile was performed under simulated physiologic conditions (pH 7.4). As shown in Figure 3B, both f-RGD-Cur and f-RGE-Cur showed a sustained drug release profile, with total curcumin release from the nanofibers being about 51.6% and 60.9%, respectively, while treatment with free curcumin led to release of more than 95% of the drug.
In vitro cellular uptake
One of the advantages of curcumin is its intrinsic fluorescence, which can be detected directly to quantify its cellular uptake and intracellular trafficking. We used fluorescence microscopy to compare the fluorescence intensity of free curcumin, f-RGD-Cur, and f-RGE-Cur in normal human 293T cells, human MCF-7 cancer cells with low expression of ανβ3, and human HepG2 cancer cells with high expression of ανβ3. To better compare their internalization, parameters such as laser power, offset, sensitivity, and gain constant were harmonized during the cell imaging procedure. As shown in Figure 4, very similar and low fluorescence intensity was observed in normal human 293T cells incubated with free curcumin, f-RGD-Cur, or f-RGE-Cur (Figure 4A–C). For MCF-7 cells, the fluorescence intensity was slightly higher when they were incubated with f-RGD-Cur rather than with free curcumin or f-RGE-Cur (Figure 4D–F). In HepG2 cells, the fluorescence intensity following incubation with f-RGD-Cur was much higher than following incubation with free curcumin and f-RGE-Cur (Figure 4G–I). The cells incubated with free curcumin showed the lowest fluorescence intensity, and the fluorescence intensity was HepG2 > MCF-7 > 293T cells when incubated with f-RGD-Cur (Figure 4B, E, and H). These results indicate that cellular uptake of f-RGD-Cur was higher in cancer cells overexpressing integrin ανβ3 than in ανβ3-negtive cancer cells and normal cells and that the RGD-containing peptide self-assembled nanofibers possessed in vitro cancer cell-targeting activity.
In vitro cytotoxicity
The cytotoxicity of free curcumin, p-RGD, p-RGE, f-RGD-Cur, and f-RGE-Cur was evaluated by MTT assay in the HepG2 cell line overexpressing integrin ανβ3, using the normal NIH3T3 cell line with low expression of integrin ανβ3 as the control. The peptide nanofibers showed good biocompatibility, and the viability of both normal cells and tumor cells was greater than 80% when the peptide concentration was less than 180 μg/mL (Figure 5A and C). f-RGD-Cur showed lower cytotoxicity than f-RGE-Cur in normal NIH3T3 cells (Figure 5B), but higher cytotoxicity in HepG2 tumor cells (Figure 5D). This may be caused by the active targeting ability of RGD, which could enable f-RGD-Cur to kill tumor cells more efficiently and thus protect normal tissues. Free curcumin showed higher cytotoxicity than f-RGD-Cur and f-RGE-Cur. The phenomenon of free drug showing higher cytotoxicity in normal cells than in cancer cells and lower cell viability than nanoparticle-encapsulated drugs has also been reported by Xu et al38 and Su et al,39 and may be caused by the controlled and sustained release of active drug from f-RGD-Cur and f-RGE-Cur. From the in vitro release results, we found that free curcumin had higher drug release than f-RGD-Cur and f-RGE-Cur, and this may the reason for the higher cytotoxicity of free curcumin.
Ex vivo distribution
Because of the high proteolytic activity and low pH in the gastrointestinal tract, oral delivery of intact peptide nanofibers to the target site is difficult. The low permeability of peptides at the intestinal barrier is another factor adding to their low bioavailability.40,41 Gastrointestinal delivery of peptide nanofibers is not feasible. Upon intravenous administration, nanostructures will undergo adsorption or opsonization by serum proteins, which results in a change in the physicochemical properties of the nanostructures.42 This may affect their half-life in blood and their biodistribution. Therefore, some agents show good targeting ability in vitro but no effect in vivo. Ex vivo optical imaging may have some diagnostic value because it is not subject to interference from overlying tissues, eg, skin and blood vessels, and thus closely resembles intraoperative procedures in surgical oncology as opposed to whole-body imaging.13 To determine whether curcumin accumulates efficiently at tumor sites after injection of f-RGD-Cur, ex vivo imaging of all major organs was performed 4 hours post-injection using a tumor xenograft assay. Representative color-coded fluorescence images of the excised tumors and tissues (heart, liver, spleen, lung, and kidney) obtained 4 hours post-treatment are shown in Figure 6A. These images show that the tumor group treated with f-RGD-Cur had the strongest curcumin fluorescence intensity, followed by tumors in the f-RGE-Cur group. Minimal curcumin fluorescence intensity was observed for tumors in the free curcumin group. The total fluorescence intensity in the free curcumin group was lower than in the f-RGD-Cur and f-RGE-Cur groups. As shown in Figure 6B, the fluorescence intensity in the f-RGD-Cur group was about 4-fold higher than that in the free curcumin group (P<0.01). In addition, the fluorescence intensity in the f-RGD-Cur group was also significantly higher than in the f-RGE-Cur group (P<0.05). Our results indicate that these peptide nanofibers can deliver curcumin into tumors, perhaps as a result of the enhanced permeability and retention effect. The RGD motif may enable RGD-containing peptide nanofibers to accumulate more effectively in tumors by active tumor-targeting. Further in vivo studies should be performed to determine the antitumor effects and toxicity of these nanofibers in targeted tumor therapy.
In this study, we have identified a new tumor-targeting peptide nanofiber, f-RGD-Cur, formed by the Nap-GFFYG peptide together with an RGD peptide as the tumor-targeting agent. This nanofiber efficiently encapsulated the hydrophobic drug, curcumin, and showed sustained drug release. Compared with free curcumin and non-targeting f-RGE-Cur nanofibers, f-RGD-Cur showed highly selective targeting of tumor cells and xenografts overexpressing integrin ανβ3. f-RGD-Cur also demonstrated higher cytotoxicity than f-RGE-Cur to tumor cells and lower cytotoxicity to normal cells. These results suggest that RGD-containing peptide nanofibers may provide a useful platform for developing hydrophobic drug delivery carriers with tumor-targeting activity.
We thank the Science Foundation of China (81171371, 51203189), Tianjin Natural Science Foundation (13JCZDJC28100), PUMC Youth Fund and the Fundamental Research Funds for the Central Universities (3332013045), and the Development Foundation of the Institute of Radiation Medicine, Chinese Academy of Medical Sciences and Peking Union Medical College (SF1209, SZ1334) for financial support.
The authors report no conflicts of interest in this work.
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Figure S3 1H NMR spectrum of Nap-GFFYG-RGE.
Figure S4 HR-MS of Nap-FFG.
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