Resveratrol has been reported as a potential antitumor agent for several years. The possible application was greatly hampered by its poor solubility. The current study reported the construction of electrospun Resveratrol loaded nanofibers with methoxypolyethylene glycol-poly(caprolactone) (mPEG-PCL) block copolymers as drug carriers. Characterization studies showed the successful encapsulation of Rsv in the nanofibers with an in vitro sustained release pattern. In vitro XTT assay suggested the superior cytotoxicity of Rsv-NFs with more apoptosis induction on cancer cells. Cells that exposed to Rsv-NFs showed less clonogenic ability when compared to the equivalent dose of free Rsv. In addition, the migration and invasion ability of cells were also significantly lower when treated with Rsv-NFs. In the in vivo study, local implantation of Rsv-NFs greatly increased the growth inhibitory effect compared to free Rsv. Therefore, results from the current study demonstrated a promising way to improve the antitumor effect of Rsv by nanofiber delivery.

1. Introduction

Chinese herbal medicine, also known as Traditional Chinese Medicine, has attracted increasing interest in recent years. There are plenty of studies demonstrating the potential anti-inflammation, antitumor, antioxidant effects of herbal medicines such as Tetrandrine, Curcumin, Resveratrol, and Harmine[14]. Recently more and more researchers focus on the potential anticancer effect of herbal medicines as well as their possible mechanisms [57].

Among these herbal medicines, Resveratrol (Rsv) attracts intensive interest for its potential in cancer therapy. Previous studies have demonstrated the inhibitory effect of Rsv against a series of cancers, including glioma, colon cancer, and gastric cancer [8, 9]. It is reported that Rsv could induce apoptosis through regulating apoptosis-related proteins [10]. Moreover, Rsv could also block several pro-proliferative pathways, such as PI3k/Akt/mTOR and MAPK pathways [11, 12]. In addition, there are some reports stating that Rsv could enhance the antitumor effect of commonly used chemotherapeutics, which makes it a promising chemotherapy adjuvant [13, 14].

One hindrance for the application of Rsv is its poor solubility. However, the hydrophobicity of Rsv renders it a good model drug for nanodelivery systems. In previous studies, we prepared Rsv-loaded nanoparticles (Rsv-NPs) with amphiphilic polymers as drug carriers [2, 15, 16]. Characterization of Rsv-NPs showed good aqueous stability and loading efficiency and controlled release kinetics. In vitro studies indicated the superior cell inhibitory effect over free Rsv. In the in vivo study, Rsv-NPs showed better antitumor effect due to the EPR (Enhanced Permeability and Retention) effect. Nevertheless, there are still some disadvantages, such as lack of targeted ability and low loading efficiency.

To overcome these disadvantages, drug loaded nanofibers based on amphiphilic copolymers become an alternative to deliver the drugs. There are some studies focusing on the construction of drug loaded nanofibers with herbal medicine as model drugs [17, 18]. Drug loaded nanofibers have a large surface area-to-volume ratio, which enables an excellent drug loading efficiency. Moreover, previous studies focusing on the shape effect of nanostructures have demonstrated that nanofibers showed 10 times circulation times longer than spherical nanostructures, thereby exhibiting stronger tumor shrinkage [19].

In the current study, we prepared Rsv-loaded nanofibers (Rsv-NFs) with PCL-PEG as drug carriers by electrospinning. Rsv-NFs were characterized by DLS, Uvis, and FTIR. In vitro studies were performed including cellular uptake, cytotoxicity, migration, and invasion studies. Animal study was performed to evaluate the in vivo antitumor effect of Rsv-NFs.

2. Materials and Methods

2.1. Materials

Resveratrol and methoxypolyethylene glycol (mPEG) was purchased from Sigma Aldrich Co. (St. Louis, MO, USA). ε-Caprolactone (ε-CL, Sigma) was purified by drying over CaH2 at room temperature and distillation under reduced pressure. Coumarin-6 was purchased from Sigma (St. Louis, MO, USA). All other chemicals were of analytical grade. Human glioma cell line U87 was obtained from Shanghai Institute of Cell Biology (Shanghai, China).

2.2. Methods
2.2.1. Synthesis of mPEG-PCL Block Copolymers

mPEG-PCL block copolymers were synthesized by a ring-opening copolymerization [20]. Certain amount of CL was mixed with mPEG with the presence of stannous octoate (0.1% wt/wt) in a tube connecting to a vacuum system and then incubated in an oil bath at 130 for 48 h. Dichloromethane (DCM) was utilized to dissolve the raw synthesized polymers and the obtained solution was precipitated into cold methanol to eliminate the excess monomer and oligomer. The precipitates were then purified by filtration before being thoroughly dried at lower pressure. The polymers were then characterized by 1H NMR and gel permeation chromatography (GPC).

2.2.2. Preparation of Rsv-Loaded Nanofibers

Rsv-NFs were prepared using an electrospinning device. mPEG-PCL was dissolved in ethanol and water at a ratio of 5 : 1 to generate a 10% transparent polymer solution. Then 5 wt%, 10 wt%, and 15 wt% Rsv with respect to mPEG-PCL were added and dissolved to the polymeric solution. The solution was then sonicated for 30 s and then loaded in a 5 mL syringe with a needle connected to a high voltage of DC supply. The distance between the top of the needle and the collector is 12 cm. The flow speed of the solution was set at 0.5 mL/h. The nanofiber was collected through an aluminum foil. Coumarin-6 loaded Rsv-NFs were prepared with the addition of coumarin-6 (1 wt%) together with Rsv.

2.2.3. SEM, FTIR, and Loading Efficiency

Scanning Electron Microscopy (SEM) (JEOL, Japan) was performed to observe the morphology of Rsv-NFs. Fourier transform infrared (FTIR) spectra were measured by a Perkin-Elmer Paragon 1000 Fourier transform spectrometer. Drug loading efficiency was determined by high performance liquid chromatography (HPLC, Shimadzu LC-10AD, Japan) system with a Shimadzu UV detector. Briefly, a predetermined amount of 10 mg Rsv-NFs was dissolved in mobile phase consisting of methanol (spectral grade, Merck, Germany)/double-distilled water/glacial acetic acid (48/52/0.05, v/v/v). The pump rate was 1 mL/min. The detected wavelength was 303 nm and the retention time was about 4.2 min. The encapsulation efficiency was calculated as the following equation: encapsulation efficiency (%) = weight of the drug in nanofibers/weight of the feeding drugs 100%.

2.2.4. In Vitro Release

For the in vitro release study, a small piece of 20 mg Rsv-NFs mat was immersed in a 50 mL glass tube with 30 mL PBS containing 5% ethanol and the tube was incubated at 37 in a thermostat shaker. At preset time points, the nanofiber mat was transferred to another tube with the same medium. The released Rsv in the previous medium buffer was extracted by the mobile phase and measured on a HPLC. The concentration of released Rsv was calculated and plotted at different time points.

2.2.5. Cellular Uptake

U87 cells were seeded in 6-well plates and allowed to grow for 24 h. Coumarin-6 loaded Rsv-NFs were incubated with cells in 6-well plate for 2 h. After cells were washed two times by PBS, cells were observed under a fluorescent microscopy.

For quantitative study, Res-NFs were incubated with cells for different time periods with different concentrations. Cells were then trypsinized, washed by PBS for 3 times, and centrifuged at 1500 rpm for 5 mins. The cell pellets were dissolved in 1 mL methanol and sonicated for 60 s, followed by a centrifugation of 10000 rpm for 5 mins. Supernatant was collected and run on a UV-spectrometer at a wavelength of 310 nm.

2.2.6. In Vitro Cytotoxicity

The in vitro cytotoxicity of Rsv-NFs with different Rsv loadings was evaluated by XTT assay. U87 was seeded in 96-well plates with a density of around /well. Cells were allowed to adhere for 24 h prior to the test and then exposed to free Rsv, blank copolymers, and Rsv-NFs for 24, 36, and 48 h, respectively. The concentration of Rsv was set to 2, 4, 8, 16, and 32 μM, while Rsv-NFs were administered at the equivalent dose of free Rsv. After the incubation, 50 μL XTT solution was added to each well of the plate and incubated for another 18 h at 37°C in the incubator. Then the plates were read at a wavelength of 490 nm with 670 nm as a reference.

2.2.7. Edu Staining and AO/EB Dual Staining

U87 cells were treated with Rsv and Rsv-NFs at an equivalent dose of μM for 36 h and then washed out with PBS. 300 μL 50 μM Edu solution was added to the wells for an incubation time of 2 h, followed by a staining of Hoechst 33342 for 5 min in the dark. After washing, air-drying, and fixing with 90% glycerol, cells were observed under a fluorescence microscope with an excitation wavelength of 350 nm and an emission wavelength of 550 nm. Cells stained with Edu were counted from five different fields.

U87 cells were treated with Rsv and Rsv-NFs at an equivalent dose of μM for 36 h and then washed out with PBS. Cells were then stained by dual fluorescent staining solution (1 μL) containing 100 μg/mL AO and 100 μg/mL EB (AO/EB, Sigma, St. Louis, MO). Cells were immediately observed under a fluorescence microscope.

2.2.8. Clonogenic Assay

U87 cells were seeded in T 25 flasks and allowed to adhere to 80–90% confluent before drug treatment. After being treated with Rsv or Rsv-NFs at a series of equivalent doses (3, 6, and 12 μM) for 36 h, cells were trypsinized and seeded in 6-well plate at different density. After 10 days, cells were stained with 0.5% crystal violet for 2 mins, washed out, and air-dried in room temperature. The colonies at each well were counted. Plate efficiency (PE) and survival fraction (SF) were calculated with the following equations:

2.2.9. Wound Healing Assay

Cellular migration ability was evaluated through the wound healing assay. Briefly, U87 cells were seeded in 6-well plates and allowed to grow till confluent monolayers were observed. A vertical clear space “wound” was made by a sterile pipette tip. The time that the wound was made was designated as 0 h and the margins of the wound were photographed by microscopy. After cells were incubated with Rsv and Rsv-NFs at the equivalent doses for 36 h, the same fields of the wound margin were screened again. Adobe Photoshop was applied to superpose the pictures and wound area was measured by Scion Image Analysis Software (Scion Corporation, Frederick, MD, USA). Wound healing rate was calculated by the following equation: wound healing rate = (the average area of wound at 0 h − the average area of wound at 36 h)/the average area of wound at 0 h.

2.2.10. Transwell Assay

After growing to subconfluency, U87 cells were cultured in nonserum medium for 24 h. Cells were then trypsinized and resuspended in serum-free medium. After cells were seeded in the upper chamber, the equivalent doses of Rsv and Rsv-NFs were incubated with the cells for 36 h. The invaded cells on the lower membrane surface were then fixed with methanol and stained with 0.1% crystal violet. The cells were photographed and counted.

2.2.11. Protein Expression

Protein expression was examined by western blot as described in previous studies [21]. Whole cell lysates were fractionated by SDS-PAGE and then transferred into nitrocellulose membranes. After being blocked by 5% nonfat milk, the membranes were incubated overnight with primary antibodies including antiphospho-ERK, anti-ERK, anti-Bcl-1, anti-Bcl-xl, and anti-Bax. The blots were incubated with secondary antibodies according to the origin of primary antibodies, respectively, and then activated by an ECL kit (GE Healthcare, Piscataway, NJ).

2.2.12. In Vivo Study

Male nude mice were raised under specific pathogen-free circumstances. The experiments were in compliance with animal guidelines approved by the Animal Care Committee of Nanjing Medical University. 0.05 mL cell suspension containing 1 million U87 cells was injected into the left axillary space of the mice. After 7 to 10 days, the mice with tumor volume of around 50 mm3 were selected and this day was designated as Day 1. Mice were divided to four groups with each group containing 6 mice and treated with blank NFs, free Rsv, and Rsv-NFs, respectively. The dose of Rsv was at an equivalent dose of 10 mg/kg. Blank NFs and Rsv-NFs were implanted on the tumor nodule through a small surgery while free Rsv was injected intratumorally at the same dose. Mice were ear tagged and tumors were measured by an electronic caliber every other day. Tumor volume was calculated by the formula ()/2, where is the tumor measurement at the widest point and is the tumor dimension at the longest point.

2.2.13. Statistics

Data were presented as the mean ± SD of three independent experiments. Statistical analysis for the comparison of relative groups was based on Student’s -test or one-way ANOVA analysis with SPSS software. Significance was accepted at the 0.05 level of probability.

3. Results and Discussion

3.1. Synthesis and Characterization of mPEG-PCL Copolymers

The obtained mPEG-PCL copolymers were characterized by 1H NMR and GPC. The calculated molecular weight was listed in Table 1. The purity of the polymer was demonstrated by the only peak of mPEG-PCL copolymer in GPC curve (see Figure S1 of the Supplementary Material available online at http://dx.doi.org/10.1155/2016/5918462). The molecular weight and molecular weight distribution of mPEG-PCL from GPC were also listed in Table 1. As shown in Table 1, the molecular weight from NMR and GPC was consistent with the feeding ratios. In addition, the number of molecular weight from GPC was lower than that from NMR, which meant that GPC data were relative values based on polystyrene standards [22].

3.2. Preparation and Characterization of Rsv-NFs

As shown in Figure S2, SEM was performed to observe Rsv-NFs with a uniformed size of about a hundred nanometer (Figure S2). FTIR spectrum in Figure S3 showed three characteristic peaks of pure Rsv, which corresponded to the three typical strong bands at 1383.85 (C–O stretching), 1586.53 (C–C olefinic stretching), and 1606.21 cm−1 (C–C aromatic double-bond stretching) [23]. As reported in previous study, PCL was characterized by the two bands corresponding to amorphous (1735 cm−1) and crystalline (1725 cm−1) absorption [24, 25]. In the FTIR spectrum of mPEG-PCL, there was a strong absorption at 1728 cm−1, indicating the high PCL crystallinity inside the mPEG-PCL nanofibers. As reported earlier, PCL crystallinity was one of the main factors that affect the drug loading efficiency. There was a blue shift of the C=O vibration from 1728 cm−1 to 1730 cm−1 in the spectrum of Rsv-NFs. Possible explanations may be some form of interaction between Rsv and the C=O group of mPEG-PCL. Moreover, the characteristic peaks of Rsv and mPEG-PCL in the spectrum of Rsv-NFs demonstrated the successful loading of Rsv into Rsv-NFs.

3.3. In Vitro Release Study

Figure S4 showed the in vitro release pattern of two kinds of Rsv-NFs. For the lower loading nanofibers (5 wt%), there was an initial burst of more than 20% drugs in the first several hours, followed by a relatively controlled release in the rest of hours. At the end of the experiment (128 h), nearly 60% of the loading drug was released from the nanofibers. In contrast, a much faster release pattern was observed in higher loading Rsv-NFs at 15 wt%. The different release kinetics suggested that drug loading efficiency had a great impact on the release pattern of the nanofibers. According to the structure of the drug loaded nanofibers, the hydrophobic PCL of the nanofiber functioned as the main part to encapsulate poor soluble Rsv. As the drug loading content increased without the corresponding augment of the amount of PCL, the interaction of the hydrophobic PCL and Rsv weakened to some extent, which led to the faster release of Rsv-NFs. Moreover, during the preparation process, some of the drug was finally entrapped inside the nanofibers and some drug was absorbed to the surface of the nanofibers. Therefore, high drug loading might cause the relatively high drug absorption to the surface, thereby leading to the faster burst release of the drug loaded nanofibers. Similar results were also reported by a previous study about Curcumin loaded nanofibers [26].

3.4. Cellular Uptake of Rsv-NFs

As reported previously, the uptake efficiency of loaded drugs was primarily influenced by the physicochemical characteristics of nanocarriers instead of the drug since the drug is mostly encapsulated inside the nanocarriers [21]. In the current study, coumarin-6 was utilized as fluorescent marker to trace the nanofibers. Two-hour incubation with the cells was enough for the fluorescent Rsv-NFs to enter the cells (Figure 1). From the fluorescent photos, Rsv-NFs were mainly located in the cytoplasm instead of being in the nucleus. The cellular uptake efficiency of nanofibers was closely related to the drug loading content.

As shown in Figures 1(b) and 1(c), higher loading efficiency of coumarin-6 led to brighter fluorescence in cells, which means higher uptake efficiency. As reported in previous studies, cellular uptake of nanofiber was mainly through the absorption mediated endocytosis [1]. However, the internalization of free coumarin-6 was dependent on diffusion with most of the coumarin-6 trapped in cell membrane. Therefore, Rsv-NFs could transport the lipophilic drug into the cells through efficient endocytosis.

3.5. In Vitro Cytotoxicity and Apoptotic Induction of Rsv-NFs

As shown in Figures 2(a) and 2(b), both Rsv and Rsv-NFs had a time- and dose-dependent cytotoxicity against U87 cells. When cells were incubated with both drugs for 24 h, free Rsv showed a stronger cell growth inhibitory effect than Rsv-NFs did at the equivalent dose. As the incubation time increased to 36 h, both Rsv-NFs and Rsv led to similar toxicity to cells at the equivalent concentration. Moreover, further extension of incubation time to 48 h resulted in a faster increase in the cytotoxicity of Rsv-NFs than that of free Rsv. For example, about 85% cells survived after 24 h incubation with 4 μM Rsv while only 73% cells were alive when incubated with the same dose of Rsv-NFs. However, after 72 h incubation, there were only 51% cells alive in Rsv-NFs treated group while the viability was more than 56% in the groups of Rsv treatment. In addition, Table 1 indicated that the IC50 value of Rsv-NFs for 24 h was higher and decreased faster than that of Rsv as incubated time extended.

For proliferation detection, cells were dually stained by Edu and Hoechst 33342 (Figure 3). Red staining from Edu stood for proliferative cells with blue staining by Hoechst 33342 indicating cell nucleus. From Figure 3, when cells were incubated with the equivalent dose of Rsv and Rsv-NFs, there was less red fluorescence in Rsv-NFs treated group than in the group of Rsv, which demonstrated the stronger cytotoxicity of Rsv-NFs.

Moreover, AO/EB dual staining was applied to visualize the apoptosis and necrosis of cells. AO can penetrate the intact membrane of living cells and early apoptotic cells and stain them green while EB can only enter late apoptotic cells and dead cells with broken membrane and stain them red. As shown in the lower panel of Figure 3(a), cells underwent obvious apoptosis and necrosis when treated with either Rsv or Rsv-NFs. Most importantly, Rsv-NFs led to more early apoptosis and late apoptosis (necrosis) of U87 cells than the equivalent dose of Rsv did.

Previous studies have reported the preparation of drug loaded nanofibers made by electrospinning [17, 18, 27]. Most of them focused on the characterization of nanofibers [18]. Few of them evaluate the antitumor effect systematically. For example, Zupančič et al. successfully constructed Rsv-loaded nanofibers with PCL as drug carriers. They characterized the nanofiber by FTIR, DSC, and so forth with no further evaluation on the anticancer effect [28]. Here we studied the in vitro antitumor effect of Rsv-NFs through XTT assay, proliferation and apoptosis staining, and clonogenic assay. XTT assay and cell staining indicated that Rsv-NFs were more cytotoxic than free Rsv against cells within certain range of concentrations, which was in accordance with the results from Edu staining that less proliferation was observed in the Rsv-NFs treated group.

3.6. Clonogenic Assay

As indicated in previous studies, there are two ways to evaluate the cell drug sensitivity. One way is to measure the cytotoxicity, which assesses the cellular ability of proliferation after drug treatment. The other way is to study the cell survival by clonogenic assay to evaluate the ability of individual cells to form colonies [29]. Cells that are able to go through mitosis but cannot divide and reproduce a big number of progeny are considered as dead due to the loss of reproductive integrity. Only cells that possess the ability to proliferate and reproduce a large colony are regarded as “clonogenic” [30]. Therefore, cell survival cure generated from clonogenic assay describes a relationship between cytotoxic drug and the percent of cells that survive.

In the current study, clonogenic assay was performed to evaluate the ability of proliferation and clonogenesis of glioma cells. Figure 2(c) showed that the survival curve of cells exposed to either Rsv or Rsv-NFs. At the three dose levels, cells treated with Rsv-NFs exhibited less clonogenic abilities than cells exposed to the equivalent dose of Rsv. The numbers of cell colonies in the Rsv-NFs treated groups were significantly lower than those in corresponding Rsv-treated groups, which means that the clonogenic ability of cells treated with Rsv-NFs was substantially abrogated compared to free Rsv-treated cells.

3.7. Inhibition on the Migration and Invasion of Cells by Rsv-NFs

There are several important steps during the process of tumor metastasis including the ECM degradation, vascular penetration, and adhesion elsewhere [31]. During the whole process, the ability of cells to migrate and invade is the main factor that contributes to the tumor metastasis [32].

Here we employed a highly invasive cell line to evaluate the migration and invasion of cells when exposed to Rsv and Rsv-NFs by wound healing and transwell assay. As shown in Figure 4, both Rsv-NFs and Rsv inhibited the migration of cells in a dose-dependent manner. Moreover, Rsv-NFs delayed the migration of cells more efficiently than free Rsv did at the equivalent concentration. Similar trends could be observed from the results of transwell assay (Figure 5). The number of successful invading cells in the Rsv-NFs treated group was significantly lower than that in Rsv treated group, which demonstrated an enhanced inhibitory effect of Rsv-NFs.

3.8. Protein Expression

Protein expressions were evaluated by western blot to elucidate the possible mechanism of antitumor effects of Res-NFs. As a member of the mitogen-activated protein kinase (MAPK) family, extracellular signal-regulated kinase (ERK) is constitutively expressed and contributes to cell proliferation and survival in a series of cancer cells [33]. The close relationship between ERK and apoptotic proteins has also been established in previous studies. The activity of ERK pathway has been proved with the upregulation of proapoptotic members of the Bcl-2 family, such as Bax and Bak, as well as the downregulation of antiapoptotic members, such as Bcl-2 and Bcl-xl [34, 35].

It is shown in Figure 6 that both Res and Res-NFs inhibited the expression of p-ERK when compared to control. Most importantly, the expression of p-ERK in cells treated with Res-NFs was significantly lower than that treated with the equivalent dose of Res. Moreover, Res-NFs were more efficient to induce proapoptotic protein Bax and decrease the antiapoptotic proteins Bcl-2 and Bcl-xl (Figure 6). Therefore, it is demonstrated that Res-NFs induced the apoptosis of U87 cells through the inhibition of ERK activity and the regulation of apoptotic pathway.

3.9. In Vivo Study of Rsv-NFs

Figure 7 shows the curve of tumor volume of tumor bearing mice in different groups. It is noted that both Rsv and Rsv-NFs dose-dependently delayed the growth of tumors with no antitumor effect observed in either control group or blank nanofiber treated group. From Day 9 to the end of observation, the difference between the groups of Rsv and control was significant (), as was the difference between the groups of Rsv-NFs and control (). Most importantly, the antitumor efficiency of Rsv-NFs was much more stronger than that of free Rsv as the mean tumor volume of mice treated by Rsv-NFs was significantly smaller than that of mice with the treatment of the equivalent dose of Rsv from Day 11 to the end of experiment (). For instance, mice in the group of Rsv reached the standard of euthanization ( cm3) while the mice in Rsv-NFs treated group was only a bit larger than half the size ( cm3) of euthanization standard.

Here Rsv-NFs mats were implanted to cover the tumor nodule through a small surgery instead of injection through tail vein. Three advantages could be achieved due to the characteristic pharmacokinetics profile of Rsv-NFs through local implantation of the drug loaded nanofibers. First, a sustained release of Rsv around the tumor through local implantation of nanofiber means a continuous exposure of tumor nodule to the drug. Second, controlled release of Rsv around the tumor will increase the penetration of drug into the tumor since the density of neovessels on the surface of tumor mass is much more higher than that inside the tumor. This will lead to an effective long-term high drug concentration in the tumor site, thereby generating stronger antitumor effect. Third, the efficient cellular uptake of Rsv-NFs through endocytosis also contributes to the increase of intracellular drug concentration. Two previous reports which studied the in vivo efficiency of drug loaded nanofibers also supported the idea that local implantation increases the antitumor effect of drug loaded nanofibers [36, 37].

4. Conclusion

In the current study, we prepared Rsv-loaded nanofibers by electrospinning with mEPG-PCL as drug carriers. Characterization studies showed the successful encapsulation of Rsv in the nanofibers with an in vitro sustained release pattern. In vitro XTT assay suggested the superior cytotoxicity of Rsv-NFs with more apoptosis induction. Cells that exposed to Rsv-NFs showed less clonogenic ability when compared to the equivalent dose of free Rsv. In addition, the migration and invasion ability of cells were also significantly lower when treated with Rsv-NFs. In the in vivo study, local implantation of Rsv-NFs greatly increased the growth inhibitory effect compared to free Rsv. Therefore, results from the current study demonstrated a promising way to improve the antitumor effect of Rsv by nanofiber delivery.

Competing Interests

The author reports no conflict of interests in this work.

Authors’ Contributions

Hui Zhou, Xiaoxing Liu, and Fenglei Wu contributed equally to the study.


This work was supported by the National Natural Science Foundation of China (no. 81401968) and Natural Science Foundation of Jiangsu Province (BK20151157 and BK20141245).

Supplementary Materials

mPEG-PCL copolymers were characterized by GPC. The purity of the polymer was demonstrated by the only peak of mPEG-PCL copolymer in GPC curve. The characteristic peaks of Rsv and mPEG-PCL in the spectrum of Rsv-NFs from FTIR demonstrated the successful loading of Rsv into Rsv-NFs. In vitro release study indicated that Rsv was released from Rsv-NFs in a sustained manner.

  1. Supplementary Material