Gefitinib loaded folate decorated bovine serum albumin conjugated carboxymethyl-beta-cyclodextrin nanoparticles enhance drug delivery and attenuate autophagy in folate receptor-positive cancer cells

Background Active targeting endocytosis mediated by the specific interaction between folic acid and its receptor has been a hotspot in biological therapy of many human cancers. Various studies have demonstrated that folate and its conjugates could facilitate the chemotherapeutic drug delivery into folate receptor (FR)-positive tumor cells in vitro and in vivo. In order to utilize FA-FR binding specificity to achieve targeted delivery of drugs into tumor cells, we prepared Gefitinib loaded folate decorated bovine serum albumin conjugated carboxymethyl-β-cyclodextrin nanoparticles for enhancing drug delivery in cancer cells. On this context, the aim of our study was to develop a novel nano-delivery system for promoting tumor-targeting drug delivery in folate receptor-positive Hela cells. Results We prepared folic acid (FA)-decorated bovine serum albumin (BSA) conjugated carboxymethyl-β-cyclodextrin (CM-β-CD) nanoparticles (FA-BSA-CM-β-CD NPs) capable of entrapping a hydrophobic Gefitinib. It was observed that nanoparticles are monodisperse and spherical nanospheres with an average diameter of 90.2 nm and negative surface charge of −18.6 mV. FA-BSA-CM-β-CD NPs could greatly facilitate Gefitinib uptake and enhance the toxicity to folate receptor-positive Hela cells. Under the reaction between FA and FR, Gefitinib loaded FA-BSA-CM-β-CD NPs induced apoptosis of Hela cells through elevating the expression of caspase-3 and inhibited autophagy through decreasing the expressing of LC3. It also confirmed that clathrin-mediated endocytosis and macropinocytosis exerted great influence on the internalization of both NPs. Conclusions These results demonstrated that FA may be an effective targeting molecule and FA-BSA-CM-β-CD NPs provided a new strategy for the treatment of human cancer cells which over-expressed folate receptors.


Background
Nanosized drug carriers functionalized with moieties specifically targeting tumor cells are promising tools in cancer therapy, due to their ability to circulate in the bloodstream for longer periods and their selectivity for tumor cells, enabling the sparing of healthy tissues [1][2][3][4][5]. Many synthetic biomimetic nanocrystalline apatites are used as nanocarriers to produce multifunctional nanoparticles, by coupling them with the chemotherapeutic drug, such as Gefitinib, Dox or membrane antibody DO-24 monoclonal antibody (mAb) directed against the c-Met/Hepatocyte Growth Factor Receptor (Met/HGFR), which is over-expressed on different kinds of carcinomas and thus represent a useful tumor target recently [6][7][8]. Gefitinib, a tyrosine kinase inhibitor of Epithelial Growth Factor Receptor (EGFR) usually expressed in solid tumors of epithelial origin, can prevent tumor growth, metastasis and angiogenesis, and promote apoptosis of tumor cells [9][10][11]. The main mechanism includes that it can block the signal transmission by competitive binding Mg-ATP situated on catalytic domain of EGFR-TK, then inhibit the activation of mitogen activated protein kinase, inducing the apoptosis of cancer cells [12]. However, Gefitinib is absorbed slowly and widely distributed in bodies following oral administration, resulting in the serious side effects and lower bioavailability. Moreover, the solubility of Gefitinib is decreased with the decline of pH in medium [13].
Cyclodextrins (CD), a family of carbohydrate polymers which are produced from starch by enzymatic conversion and commonly used in food, pharmaceutical, drug delivery, and chemical industries, as well as agriculture and environmental engineering, is cyclic oligosaccharide with cone barrel structure composed of seven glucopyranose units with cylindrical cavity [14][15][16]. The exterior of this cone is polar and hydrophilic, whereas the interior cavity is relatively nonpolar and hydrophobic. Small hydrophobic molecules as the guest molecules can be completely or partially embedded into CD cavity to form complexes, improving water solubility, stability and biological activity of the guest molecules [17][18][19][20][21]. Bovine serum albumin (BSA), a carrier protein, plays an important role in drug storage and transport, for its superior biocompatibility it has been widely used in biomedical research, such as Nano carrier, nanoparticle surface engineering and temples for preparation of nanoparticles [22][23][24][25].
To improve the solubility and stability of Gefitinib, we synthesize the amphiphilic BSA-CM-β-CD conjugates to prepare the assembled nanoparticles capable of entrapping hydrophobic Gefitinib into the cavity of CD through the host-guest interaction. Folate receptor (FR), as a transmembrane glycoprotein, promotes the transportation of folate (FA) or its conjugates into the cells by active targeting endocytosis mediated through FA-FR interaction [26][27][28]. FA is expressed at basal levels in normal adult organs such as brain, lung and liver, but it is over-expressed in many human cancers including ovarian cancer, breast cancer, endometrial cancer, lung cancer, kidney cancer, colon cancer and nasopharyngeal carcinoma cells [29][30][31].
Several lines of evidence have demonstrated that FA and its conjugates could significantly enhance the drug delivery efficiency into FR-positive tumor cells both in vitro and in vivo [32][33][34]. Herein, FA is adopted as the coupling molecule to improve FR-positive tumor-targeted drug delivery ( Figure 1). Properties of NPs such as size, morphology and surface potential were examined. Using Gefitinib as the model drug, we prepared drug-loaded nanoparticles. We found that FA-BSA-CM-β-CD NPs greatly facilitated Gefitinib uptake and enhanced the toxic effect in folate receptor-positive Hela cells. Our results demonstrated that FA-BSA-CM-β-CD NPs might be a higher efficiency drug delivery system than the conventional delivery system for the targeting therapy of FR positive human cancers.

Results and discussion
The preparation and characteristics of various kinds of NPs Conjugation of CM-β-CD to BSA was obtained by carbodiimide coupling. Carboxylic group of CM-β-CD reacted with EDAC to form unstable reactive ester. With addition of NHS, semi-stable amine-reactive NHS-ester was synthesized and then mixed with BSA which containing amino group to obtain CM-β-CD conjugated BSA by stable amide bond [35,36].
The characterization of BSA-CM-β-CD conjugates was investigated by infrared spectroscopy (Figure 2). The result showed the FT-IR spectra of BSA, CM-β-CD, and BSA-CM-β-CD conjugates. The characteristic peak of BSA-CM-β-CD conjugates appeared at 1650 cm −1 and 1540 cm −1 should be ascribed to the newly formed amide bond between CM-β-CD molecules and BSA. These data supported that CM-β-CD has grafted to BSA, and they are correspond to the results of former literatures [37].
Spectrum of infrared absorption of Gefitinib loaded FA-BSA-CM-β-CD NPs was shown in Figure 3. It can be seen that when BSA-CM-β-CD NPs was bonded with FA, its spectrum demonstrated that the aromatic amine groups (νNH 2 , 3415 cm −1 and 3323 cm −1 ) from FA disappeared, suggesting that amine groups from FA reacted with carboxylic group of BSA. Furthermore, the characteristic peak of secondary amine group (νNH, 3398 cm −1 ) from Gefitinib disappeared because of the encapsulation of Gefitinib into the core of NPs.

Development and properties of Gefitinib-loaded FA-BSA-CM-β-CD NPs
Using transmission electronic microscope (TEM), we observed that Gefitinib-loaded FA-BSA-CM-β-CD NPs we prepared were monodisperse spheres, and further analysis revealed that the diameters of NPs ranged from 52.1 to 105.6 nm ( Figure 4). Table 1 summarized the average diameters measured by dynamic light scattering (DLS) and surface charge information of these prepared nanoparticles. It was remarkable that Gefitinib-loaded FA-BSA-CM-β-CD NPs showed smaller particle size, negative zeta potential. The average encapsulation efficiency of Gefitinib in FA-BSA-CM-β-CD NPs was 89.2% and about 70.1% of FA was conjugated on the surface of NPs.

In vitro drug release study
Gefitinib loaded FA-BSA-CM-β-CD NPs exhibited similar release profiles in the medium with different pH. The release curve in PBS could be divided into two phases: initial fast drug release stage and later stable release stage. Gefitinib was released rapidly in the initial fast release stage, and was released slowly in the later stable stage through diffusion because of the continuous degradation of the polymer ( Figure 5). The release speed of Gefitinib decreased with the increase of pH as polymer degraded faster in acid medium. Thus, it possibly suggested that the matrix of NPs tended to be eroded as a result of depolymerization of BSA at pH 5.0 which was closer to the isoelectric points of BSA (pH 4.9), and then drug could be more easily released from NPs. The release ratio during the first 48 h accounted for over 40% of the total drug and the remnants were released over longer time of incubation. It suggested that Gefitinibloaded FA-BSA-CM-β-CD NPs could be used as a longlasting and effective drug delivery system.

Cell viability assays
The cytotoxic effects of Gefitinib loaded FA-BSA-CM-β-CD NPs and BSA-CM-β-CD NPs were evaluated by MTT assay using Hela cell line. MTT analysis showed that in the absence of FA in culturing medium, treatment of Hela cells with Gefitinib loaded FA-BSA-CM-β-CD NPs caused a markedly increase in the cell cytotoxic activities as compared with free Gefitinib and Gefitinib loaded FA unconjugated NPs ( Figure 6B). The IC 50 values of Gefitinib loaded FA-BSA-CM-β-CD NPs treated Hela cells was 4.63 μg/mL, 7.85 μg/mL for free Gefitinib and 13.55 μg/mL for Gefitinib loaded BSA-CM-β-CD NPs. However, no obvious cytotoxic activities were observed when treating the cells with blank FA-BSA-CM-β-CD NPs in Hela cells ( Figure 6A). These data suggested that more drug loaded FA conjugated NPs could be internalized into Hela cells which expressed FA at higher level by the interaction between FA and FR, further leading to the significant cytotoxicity by the accumulation of drug in cells.
We next examined whether inhibition of FR, which expressed on the cell surface, affected the cytotoxic activities of Gefitinib loaded FA-BSA-CM-β-CD NPs. Hela cells were cultured in the medium containing FA at 5 μg/mL. MTT analysis ( Figure 6C) revealed that the presence of FA caused a significant decrease in the cytotoxic effect of Gefitinib loaded FA-BSA-CM-β-CD NPs compared with that without FA in Hela cells. However, pretreatment of FA had little effect on the cytotoxic activity of free Gefitinib and Gefitinib loaded BSA-CM-β-CD NPs. The IC 50 values of Gefitinib loaded FA-BSA-CM-β-CD NPs treated Hela cells was 13.02 μg/mL, 8.63 μg/mL for free Gefitinib and 14.76 μg/mL for Gefitinib loaded BSA-CM-β-CD NPs. These data further demonstrated that FA conjugation played critical roles in accumulating NPs inside FR-positive tumor cells and could be used as a targeting molecule in the treatment of human cancers which over-expressed FR on the cell surface.

In vitro uptake ability analysis
To visualize whether FA conjugation could enhance the uptake of BSA-CM-β-CD NPs, The NPs were labeled with Rodamine B and the uptake ability was evaluated in Hela cells. Using confocal laser scanning microscopy analysis, Hela cells showed increased number of red fluorescence patches in the cytoplasm when incubating Rhodamine B-labeled FA-BSA-CM-β-CD NPs in the  FA-free medium for 6 h compared with that of Rhodamine B-labeled BSA-CM-β-CD NPs. However, the uptake of FA-BSA-CM-β-CD NPs was significantly reduced by addition of FA in the medium (Figure 7). The free FA competition study suggested that free FA in medium competed to bind FR on the surface of Hela cells with FA conjugated NPs, leading to the lower uptake of NPs.

Intracellular ATP level assay
After cells were treated with free Gefitinib, Gefitinib loaded BSA-CM-β-CD NPs, Gefitinib loaded FA-BSA-CM-β-CD NPs, the changing rates of intracellular ATP level were presented in Figure 8. It can be seen that compared with ATP level of untreated Hela cells as the control group, The changing rates of intracellular ATP level for free Gefitinib, Gefitinib loaded BSA-CM-β-CD NPs and Gefitinib loaded FA-BSA-CM-β-CD NPs were decreased to 70.5%, 75.4% and 50.1%, respectively. The results showed that Gefitinib and Gefitinib loaded NPs were internalized to induce the apoptosis of cells by lowering ATP level rates. It also confirmed that with the interaction between FA conjugated on the surface of NPs and FR situated at Hela cells, more drug loaded FA conjugated NPs were transported into the interior of cells to inhibit energy generation and accelerate the apoptosis of cells by accumulation of drugs in cells.

Cell apoptosis analysis
To identify the effect of Gefitinib and Gefitinib loaded NPs on cell apoptosis and autophagy, we detected the expression of caspase-3, Bax, and LC3 by western blot (Figure 9). Compared with free Gefitinib and Gefitinib loaded NPs, Gefitinib loaded FA-BSA-CM-β-CD NPs induced the highest caspase-3 protein expression. It also illustrated that with the mediation of FA, a large amount of drug loaded FA conjugated NPs were accumulated in Hela cells and caspase-3 as the main apoptosis relevant protein was increased, corresponding with the results of MTT experiments. However, there was no obvious difference on the Bax protein expression in the treated groups and the control group, confirming that Bax was not involved in Gefitinib induced cell apoptosis ( Figure 9A). LC3 (microtubule-associated protein light chain 3) is a specific autophagic marker in mammalian cells during autophagy. So, to identify whether Gefitinib affects autophagy, expression of LC3 was detected in Hela cells, and found that free Gefitinib did not influence the expression of LC3, but with the addition of NPs, the expression of LC3 has been inhibited, also, with the mediation of FA, the inhibition rate increased obviously ( Figure 9B). So, the results suggested that through autophagy, Hela cells may be survival and resist free Gefitinib, and FA-NPs mediated accumulation of Gefitinib in cells inhibits LC3 expression. Taken together, through inhibition of autophagy, Gefitinib loaded FA-BSA-CM-β-CD NPs induced cells apoptosis.

Inhibition of various endocytosis assay
To get more insight to know which uptake mechanisms were implied in NPs uptake, Hela cells were pretreated with various endocytic inhibitors specific for a particular endocytic pathway. Figure 10 showed that when genistein as an inhibitor to block caveolae-mediated endocytosis (CvME) was added into cells, there was no significant difference in both NPs internalization suggesting a minor role of CvME. When cells were treated with cytochalasin D (30 μM, macropinocytosis), the uptake ability of both NPs were significantly decreased to 55.4% and 60.2%. It was also observed that internalization of both NPs in cells with chlorpromazine treatment (clathrin-mediated endocytosis) was significant lower than that in untreated cells. Moreover, 40.1% reduction in FA-BSA-CM-β-CD NPs was observed in comparison with 32.1% reduction of intracellular uptake of BSA-CM-β-CD NPs. Some previous study have    reported that different conjugation with targeting ligands, such as iRGD, siRNA and disaccharide, could enhance uptake or change the endocytosis pathway of NPs resulting in improving cytotoxicity to cancer cells [38][39][40][41]. The results demonstrated that both NPs were internalized into cells mainly depending on clathrinmediated endocytosis and macropinocytosis being proved by the significant uptake reduction of both NPs in treated cells with chlorpromazine and cytochalasin D. In contrast, the regulation of caveolae-mediated endocytosis on NPs internalization was not significantly different from untreated group.

Conclusions
In summary, CM-β-CD was conjugated with BSA by carbodiimide coupling. FA as a small targeting molecule, was bond to the surface of NPs. Gefitinib loaded FA-BSA-CMβ-CD NPs showed good monodispersity, negative charge and homogenous particle size. The encapsulating efficiency of Gefitinib and the release pattern were investigated in vitro. MTT results showed that no obvious cytotoxity was observed when incubating naked FA-BSA-CM-β-CD NPs with Hela cells. The free folic acid competition study showed that the cell inhibition of FA conjugated NPs in FR positive cells was significantly enhanced

Characterization of Gefitinib loaded FA-BSA-CM-β-CD NPs
The characterization of Gefitinib loaded FA-BSA-CM-β-CD NPs was investigated by using AFFINITY-1 IR spectroscopy (Shimadzu, Kyoto, Japan). Its morphology was observed by using transmission electron microscope (TEM) (JEM-1200EX, Tokyo, Japan) and the mean diameter and zeta potential were determined by Zetasizer (Nano ZS90, Malvern, UK). The encapsulation efficiency (EE) of Gefitinib in FA-BSA-CM-β-CD NPs was calculated using the equation listed below.

Assessment of drug release
The drug releases were carried out in PBS containing 10% serum with different pH at 37.0 ± 0.5°C under gentle agitation. 10 mL PBS (pH 7.4) in which accurate weighed 10 mg dried Gefitinib-loaded FA-BSA-CM-β-CD NPs were suspended was put into a dialysis bag with 1000 molecular weight cutoff and the dialysis bag was immersed into 100 mL phosphate buffer solution containing 10% serum maintained at pH 7.4 or 5.0 at 37.0 ± 0.5°C. At predetermined intervals, 5 mL of release medium was withdrawn and the same volume of fresh buffer solution was added. Samples were filtered through 0.45 μm filter and the concentrations of Gefitinib released were analyzed by spectrophotometry at 338 nm.

Cell viability assays
A 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) assay was used to investigate cell viability. Hela cells were chosen and used as a model folate receptor-positive cell line in angiogenesis targeting delivery and treatment for their high FR expression [42,43]. Hela cells were seeded into the 96-well plate at a density of 5 × 10 4 /mL and attached for 24 h at 37°C in both folate-free medium and the medium containing folate at 5 μg/mL under 5% CO 2 . Then, the cells were treated with free Gefitinib and Gefitinib-loaded NPs for 48 h, followed by addition of 20 μL MTT (5 mg/mL) and incubated for 4 h at 37°C. Then, the supernatant was carefully removed and 150 μL DMSO was added to each well and stirred for 30 min. The absorbance was measured using microplate reader at 490 nm.

Tracking of uptake pathways using various endocytic inhibitors
In order to analyze the potential mechanism on uptake pathways of nanoparticles, three types of endocytic inhibitors including cytochalasin D (30 μM, macropinocytosis), genistein (1 μg/mL, caveolae mediated endocytosis) and chlorpromazine (10 μg/mL, clathrin mediated endocytosis) were preincubated with Hela cells in 96-well plate for 30 min, respectively. Then both FITC labeled BSA-CM-β-CD NPs and FA-BSA-CM-β-CD NPs were treated with cells to track the uptake pathways. The effects of various inhibitors on the uptake pathway of the NPs were evaluated by comparing the intracellular fluorescent intensity between treatment of adding inhibitors and non-inhibitors.

Western blot assay
After treated with free Gefitinib, Gefitinib loaded BSA-CM-β-CD NPs, Gefitinib loaded FA-BSA-CM-β-CD NPs, cells were harvested, washed twice with ice cold PBS, then lysed in RIPA buffer (150 mM NaCl, 1% NP-40, 1% SDS, 1 mM PMSF, 10 μg/mL leupeptin, 1 mM aprotinin, 50 mM Tris-Cl, pH 7.4). The cell lysate was cleared by centrifugation at 12,000 × g for 25 min. Cell lysate containing 50 μg protein in 20 μL was separated by 10% SDS-PAGE and the protein was transferred onto polyvinylidene fluoride (PVDF) membrane. After blocking with 1% BSA, the PVDF membrane was incubated with the primary antibodies (caspase-3, Bax, tubulin, LC3) at 4°C overnight. Subsequently, incubated with appropriate EE % ð Þ ¼ Weight of initially added drug-Weight of free drug in supernatant Weight of initially added drug Â 100 secondary antibody for 1 h and stained with ECL. The level of the targeted proteins were photographed and analyzed by UVP gel analysis system.