殼聚糖基聚合物碳點(diǎn)熒光材料合成及其自組裝載藥應(yīng)用

于淑娟，陳 寬，汪 豐，朱永飛

(廣西師范學(xué)院 化學(xué)與材料科學(xué)學(xué)院，廣西 南寧530001)

1 Introduction

Carbon dots(CDs) are a class of nanomaterials that have recently attracted attention due to their fascinating properties, including high photostability against photobleaching and blinking, good biocompatibility[1], low cytotoxicity[2], and excellent photoluminescence[3-4]. Compared with conventional fluorescent dyes, carbon-based fluorescent materials are advantageous since they are easily synthesized from a wide range of raw materials, such as citric acid(CA), glucose, milk, and oranges[5-7]. They have a wide range of applications in chemosensors, electroluminescent devices, catalysis, biological markers in the biomedical field and other areas[8-10]. Recent studies indicated that some non-conjugated polymers were inherently emissive[11-13]. Despite the absence of common fluorophores, these materials were still highly emissive in solution. Fluorescent polymeric carbon dots(PCDs) prepared from non-conjugated linear polymers have the advantages of being easily purified compared to CDs, and retaining functional groups on the polymer that are susceptible to molecular modification, giving them better water solubility than conjugated polymer fluorescent materials. In recent years, there has been increasing studies on the synthesis of PCDs using chitosan as the raw material and further expanding their application. For example, Yangetal.[14], used chitosan(CS) as a carbon source to synthesize chitosan-based carbon dots(CS-CDs) with hydrothermal method. The CS-CDs had a fluorescence quantum yield(QY) of 7.8% and were successfully applied to biological imaging of cancer cells in the human lung. Subsequently, Xiaoetal.[15], synthesized CS-CDs by microwave irradiation, and the QY was 6.4%. Wangetal.[16], also used CS as raw material to synthesize CS-based composite carbon dots and studied their applications as fluorescent films, fluorescent coatings and in cell imaging. Zuetal.[17], synthesized multicoloured fluorescent nanostructures for the imaging of small aquatic craniate animals with chitosan and starch as raw materials. These promising findings inspire further investigation of the application of CS-CDs. However, the QY of most of the CS-CDs were relatively low, so there were few active sites and the selectivity was poor in these studies[18]. These deficiencies will severely limit the widespread use of CS-CDs, so the preparation of polymer carbon dots with high QY, together with further exploration of their applications, is of great importance.

Over the years, fluorescent nanoparticles(NPs) have been much studied, especially those that are biocompatible. They are extremely useful for monitoring transport within cells and tissues, identifying disease sites and determining therapeutic response[19]. For instance, cellular internalization, intracellular trafficking andinvivobiodistribution of fluorescent NPs can be conveniently monitored using fluorescence microscopy[20-21]. Current methods of preparing fluorescent NPs include conjugating or encapsulating organic dyes or utilizing inorganic fluorescent NPs such as quantum dots(QDs) or other metal particles[22-23]. However, there are various limitations to these common approaches. For instance, the organic dyes conjugated onto or encapsulated into the NPs may dissociate from the NPs. Moreover, polymers used for encapsulation often lead to disappearance of the fluorescence of QDs[24]. Inorganic fluorescent NPs such as QDs can have high cytotoxicity, which limits their use as drug nanocarriers, and may also require complicated synthetic procedures.

Due to the above shortcomings, in this work we synthesized polyethylene glycol chitosan derivatives(CS-g-mPEG) using CS and PEG, molecules that have been widely used in drug-delivery, as raw materials[25]. Then, CA was grafted onto CS-g-mPEG under mild conditions. Finally, a chitosan-based polymer carbon dot(P(CS-g-mPEG- CA)CDs) fluorescent material with high fluorescence QY and long fluorescent lifetime was synthesized using a hydrothermal method after adding the nitrogen doping reagent N-(2-hydroxyethyl) ethylenediamine. The solution properties of the polymer carbon dots indicated that the P(CS-g-mPEG-CA)CDs could self-assemble into micelles. We prepared water-soluble drug-loaded nanoparticles, (P(CS-g-mPEG-CA)CDs/DOX), using doxorubicin(DOX) as the model drug, and studied drug loading and drug release performance. The toxicity and antitumor effect of P(CS-g-mPEG-CA)CDs were evaluated by MTT assay.

2 Materials and methods

2.1 Materials

Chitosan was provided by Zhejiang Aoxing Biochemical Technological Co. Ltd.(China) with a deacetylation degree of 97% and a viscosity average molecular weight of 25 kDa. Doxorubicin hydrochloride(DOX HCl, 98% purity), poly(ethylene glycol) methyl ether acrylate with molecular weight 2 000 g/mol(mPEGEA) and 3-(4,5-dimeth-ylthiazol-2-yl)-2,5-diphenylterazolium bromide(MTT) were purchased from Aladdin Chemical Reagent Co, Ltd.(Shanghai, China). The other reagents, including dichloromethane, triethylamine, citric acid(CA), ceric ammonium nitrate(CAN), acetone, 1-ethyl-3-(3-dimeth-ylaminopropyl) carbodiimide hydrochloride (EDC), N-hydroxysuccini-mide(NHS) and N-(2-hydroxyethyl)ethylenediamine(NHEA) were of analytical grade and were supplied by Sinopharm Chemical Reagent Co, Ltd, Shanghai, China. All commercially available solvents and reagents were used without further purification. CS-g-mPEG and CS-g-mPEG-CA were synthesized by reference [26] and [27] respectively.

2.2 Preparation of P(CS-g-mPEG-CA)CDs

Anhydrous CA(0.25 g), CS-g-mPEG-CA(0.25 g), NHEA(1 mL), and deionized water(8 mL) were added to a Teflon-lined stainless steel autoclave with a capacity of 25 mL. The autoclave was heated at 180 ℃ for 3 h and then cooled to room temperature. The resultant light yellow solution was separated by centrifugation at 10 000 rpm for 30 min. The supernatant was then loaded into dialysis bags(dialysis bag MWCO=8 000-14 000 Da) for dialysis against deionized water for 3 days, followed by freeze-drying to obtain pure P(CS-g-mPEG-CA)CDs.

The QY of P(CS-g-mPEG-CA)CDs was determined by using quinine sulfate(literature Ф=0.54 in 0.05 M H2SO4at 360 nm) as a standard[28].

2.3 Preparation of Drug-loaded Micelles

The incorporation of DOX·HCl into P(CS-g-mPEG-CA)CDs self-assembled micelles was achieved using an ultrasonic method[29]. Briefly, DOX·HCl(50, 150, 250, 450 or 650 μg) was dissolved in dichloromethane(DCM, 10 mL) and ultrasonicated for 2 h to obtain a DOX dispersion. The P(CS-g-mPEG-CA)CDs was dissolved in a 1% acetic acid solution. The DOX HCl dispersion in DCM(10 mL) was added to the P(CS-g-mPEG-CA)CDs acetic acid solution(1 mL). Drug-loaded micelles(P(CS-g-mPEG-CA)CDs/DOX) were obtained by sonication for 30 min and adjustment to pH 7. Blank micelles were also prepared in the same way, but without the addition of DOX. The resultant products were subjected to analysis and testing. All operations were carried out in a dark environment.

The synthesis of P(CS-g-mPEG-CA) CDs and its drug loading route to DOX are shown in Fig.1.

Fig.1 Illustration of the formation of P(CS-g-mPEG- CA)CDs from CS, mPEGEA and CA via a hydrothermal approach and the drug-loaded micelles

2.4 Characterization

Fourier transform infrared(FTIR) spectra were recorded on a FTIR spectrometer(Paragon 1000, Perkin Elmer, USA). The photoluminescence spectra of the samples were obtained using a spectrofluorometer(RF-5301PC, Shimadzu, JP). The morphologies of all samples were characterized by high resolution transmission electron microscopy(HRTEM, Tecnai G2 F30 S-TWIN, FEI, USA). UV-vis absorption spectra of the samples were obtained with a UV-vis spectrophotometer(Varian Cary 100 SCAN, Agilent Technologies Inc., Santa Clara, CA, USA). X-ray diffraction(XRD) patterns of CS, CS-g-mPEG-CA and P(CS-g-mPEG-CA)CDs powder were recorded on a diffractometer(D/max 2400, Rigaku Corporation, Tokyo, Japan) operating at 40 kV and 40 mA at 25 ℃. The scanning scope was from 10° to 40°(2θ) and the scanning rate was 4°/min. Luminescence lifetimes were measured using a fluorescence spectrometer(Fluorolog-3, Horiba Jobin Yvon Inc., France). X-ray photoelectron spectra(XPS) were collected using an X-ray photoelectron spectrometer(ESCALAB250, Thermo, UK).

3 Results and discussion

3.1 FTIR Spectroscopy

Fig.2 FT-IR spectra of CS-g-mPEG(a), CS-g-mPEG-CA(b) and P(CS-g-mPEG-CA) CDs(c)

The FTIR spectra of CS-g-mPEG(a), CS-g-mPEG- CA(b), and P(CS-g-mPEG-CA)CDs(c) are shown in Fig.2. A very strong broad peak at around 3 432 cm-1in the spectrum of CS-g-mPEG can be attributed to the stretching vibrations of CS-NH2and -OH groups. The peak at 2 884 cm-1is attributed to the mPEG C-H stretching vibration. The peaks at 1 718 and 1 641 cm-1can be assigned to the CS-g-mPEG C=O stretching and CS-NH2scissoring vibrations, respectively. The band observed at 1 112 cm-1is due to the C-O-C stretching vibration of CS glycosidic linkages and mPEG. The broadened peak at around 3 405 cm-1in the spectrum of CS-g-mPEG-CA could be due to the stretching vibration of CA O-H, and the extension vibration of CS N-H, and intermolecular hydrogen bonds of CS and CA. The amide I band appearing at 1 641 cm-1is associated with the C=O stretching vibrations and the amide II band at 1 532 cm-1is associated with the C-N stretching and N-H vibration. These results indicated that the CS-g-mPEG-CA was successfully prepared. It is apparent that the FTIR spectrum of P(CS-g-mPEG-CA)CDs contains characteristic absorption bands of CS and mPEG, but not of CA. This indicates that the CS and mPEG fragments are preserved during hydrothermal treatment while most of the CA is carbonized.

3.2 XRD Analysis

Fig.3 XRD patterns of P(CS-g-mPEG-CA)CDs(a), CS-g-mPEG-CA(b) and CS(c)

As shown in Fig.3, the XRD pattern of CS showed characteristic peaks at 20.2°, indicating a high degree of crystallinity. Modification of CS with mPEG and CA produced two narrow peaks at 19.18° and 23.40° in the XRD pattern of CS-g-mPEG-CA, which coincided with the diffraction peaks of mPEG crystals and thereby demonstrated the presence of crystalline phases of mPEG in the copolymers. Furthermore, these peaks were clearly different from the crystalline peaks of CS, suggesting that the crystal structure of the grafted compound was disrupted. This probably results from disruption of intermolecular hydrogen bonds between CS units by PEG as previously reported[30]. Compared to CS-g-mPEG-CA, the crystallization peak of P(CS-g-mPEG-CA)CDs was relatively unchanged, but the intensity of the peak increased slightly, indicating that the structure of the main chain was not further damaged after pyrolysis of CS-g-mPEG-CA. In addition, the presence of crystalline peaks of PEG showed that the molecular chains of PEG were not broken down, which also provides favorable conditions for the application of the P(CS-g-mPEG-CA)CDs.

3.3 XPS Study

The surface composition and chemical environments of the as-synthesized P(CS-g-mPEG-CA)CDs were determined using XPS. In the XPS survey spectrum of P(CS-g-mPEG-CA)CDs, the peaks at 287.42, 400.42, and 535.42 eV correspond to C1s, N1s, and O1s, respectively, as shown in Fig.4a. This result indicated that the P(CS-g-mPEG-CA)CDs was composed of carbon, nitrogen, and oxygen at atomic percentages of 64.49%, 2.87%, and 32.64%, respectively. From the high resolution spectrum of the C1s region(Fig.4b) three surface components could be assigned, corresponding to C-C at a binding energy of 286.2 eV, together with C-O and C-N at 286.8 eV. In the N1s spectrum, the peaks at 400.1 and 401.7 eV were attributed to nitrogen doped by the NH2of the chitosan molecular chain, corresponding to C-N and N-H, respectively(Fig.4c). The O1s spectrum also contained two peaks, at 532.8 and 533.4 eV, assigned to C-OH/C-O-C and C=O, respectively(Fig.4d).

Fig.4 XPS survey spectrum of P(CS-g-mPEG-CA)CDs(a); High resolution XPS spectrum of C1s region(b); High resolution XPS spectrum of N1s region(c); High resolution XPS spectrum of O1s region(d)

3.4 Analysis of UV-vis and Fluorescence Spectra of P(CS-g-mPEG-CA)CDs

The UV-vis absorption spectrum(Fig.5A) showed strong peaks at 231 and 357 nm, attributed to the π-π*transition of C=C and the n-π*transition of C=O or C-OH bonds, respectively[31-32]. In the PL spectrum(Fig.5A), the P(CS-g-mPEG-CA)CDs in aqueous solution exhibited excitation and emission wavelengths at 375 and 462 nm, respectively. The solution was a light yellow color under ambient light(Fig.5A-a), which became bright blue under a hand-held UV lamp(Fig.5A-b). The aqueous solution of P(CS-g-mPEG-CA)CDs exhibited excitation- independent PL behavior(Fig.5B). When the excitation wavelength was changed from 280 to 420 nm, the corresponding PL emission peaks for P(CS-g-mPEG-CA)CDs were not significantly shifted. This behavior is a consequence of the surface/molecular state and particle size distribution of the carbon dots[30]. The fluorescence lifetimes of P(CS-g-mPEG-CA)CDs with different degrees of substitution are shown in Fig.5C. It can be seen that the fluorescence lifetimes of P(CS-g-mPEG-CA)CDs I, II and III were 14.399, 14.936, and 15.247 ns, respectively. Higher fluorescence lifetimes are attributed to the contribution of nitrogen atoms from doping reagents and chitosan NH2. The induction of longer average lifetimes by nitrogen atoms may be due to suppression of non-radiative energy transitions in P(CS-g-mPEG-CA)CDs[33]. The relative fluorescence QY values of P(CS-g-mPEG-CA)CDs were measured by the linear slope method(using quinine sulfate as a reference). As shown in Fig. 5D, the QY values of P(CS-g-mPEG-CA)CDs I, II and III were 26.93%, 31.53% and 66.81%, respectively. The QY increased as the degree of mPEG grafting increased, which may be because the polyethylene glycol molecule has a certain passivation effect on the polymer carbon dots[36]. These values are much higher than for chitosan-based carbon dots[15-16].This enhancement is due to co-passivation of the PCD by CS, PEG molecular chains and nitrogen dopants, which increases the surface defects. In addition, CS and PEG can also be used as carbon sources[15,34], so P(CS-g-mPEG-CA)CDs exhibits higher QY. It is worth mentioning that P(CS-g-mPEG-CA)CDs is a solid powder with excellent storage stability, and its QY was unchanged a year later. The good stability of the P(CS-g-mPEG-CA)CDs, high QY and long fluorescent lifetime provide a broader scope for its application. Further, we also investigated the influence of the solution pH on the fluorescence intensity of P(CS-g-mPEG-CA)CDs. It was found that the fluorescence intensity of the carbon dots first increased and then decreased as the pH value increased, and the fluorescence intensity was highest when pH=7(Fig.5E). It can be seen that changes in the fluorescence intensity were small at pH values from 3 to 11, which indicates that P(CS-g-mPEG-CA)CDs has high fluorescence stability in this range. Good fluorescence stability also provides a basis for application in the pH= 4-10 physiological range. This is critically important for practical fluorescent drug carrier applications.

Fig.5 UV-Vis spectrum and the maximum PL excitation and emission spectra of P CS-g-mPEG-CA) CDs in water and their digital photographs(a) under daylight and UV light(b)(A); PL emission spectra of P(CS-g-mPEG-CA)CDs under different wavelength excitations(B); Fluorescence lifetime(C) and fluorescence quantum yield(QY)(D) of the P(CS-g-mPEG-CA)CDs I, II, and III; Effect of the pH on the P(CS-g-mPEG-CA) CDs fluorescence, (all of the experiments were excited at 360nm)(E)

3.5 TEM of P(CS-g-mPEG-CA)CDs Before and After Drug Loading

Fig.6a shows a representative TEM image of P(CS-g-mPEG-CA)CDs dispersed in water. It can be seen that the formed P(CS-g-mPEG-CA)CDs was mostly present as uniformly dispersed spherical dots, with a particle size of about 3-4 nm without apparent aggregation. The morphology of the micelles after drug loading was still spherical, with a particle size of about 60 70 nm which was significantly higher than that of the P(CS-g-mPEG-CA)CDs. as shown in Fig.6b. This was attributed to the successful loaded of DOX. In addition, the carboxyl groups, Amino groups and hydroxyl groups tended to self-assemble in aqueous solution to form larger size nanoparticles[35].

Fig.6 TEM of P(CS-g-mPEG-CA)CDs(a) and HRTEM of the P(CS-g-mPEG-CA)CDs/DOX(b)

3.6 Drug Release Properties of Drug-Loaded Micelles (P(CS-g-mPEG-CA)CDs/DOX)

DOX was successfully loaded into P(CS-g-mPEG-CA)CDs to give P(CS-g-mPEG-CA)CDs/DOX. Drug loading(DL), entrapment efficiencies(EE) and CMC values are shown in Tab.1. It can be seen that the DL and EE increased as the mPEG substitution degree increased, due to the decreased intramolecular hydrogen bonding of chitosan at higher mPEG substitution, which is beneficial for the drug DOX/chitosan combination. The in vitro cumulative release of DOX from self-assembled micelles was carried out in PBS(pH 7.4) at 37.8 ℃ and the results are shown in Fig.7. P(CS-g-mPEG-CA)CDs/DOX displayed an initial fast release followed by a slow phase that was similar to a two-phase pattern[36]. In the early stage of drug release, drug-loaded micelles of P(CS-g-mPEG-CA) at different PEG grafting ratios showed rapid release of drug. After 24 h, drug release was slow, and the total drug released reached only 28.7%(III), 27.6%(II) and 22.9%(I) within 400 h. The rate of release from the drug carrier increased at higher PEG grafting ratio. This is a consequence of the higher proportion of PEG molecules, resulting in increased hydrophilicity and degradation rate of the micelles, thereby increasing the drug release rate. It can be seen that the rate of drug release can be controlled by the degree of grafting of mPEG.

Tab.1 Elemental analysis data, critical micelle concentration, DL and EE for different micelles

aDS:degree of substitution.

Fig.7 In vitro release of DOX from P(CS-g-mPEG-CA)CDs micelles in the PBS(pH 7.4)

3.7 In Vitro Cytotoxicity Analysis

For the cell viability test, human nasopharyngeal carcinoma cells(CNE-2) were treated with P(CS-g-mPEG-CA)CDs micelles at varying concentrations(0, 5, 10, 20, 25 and 50 μg/mL) for 72 h and the results are summarized in Fig.8. It can be seen that the cell viability was 85.9% in the presence of blank micelles, indicating that P(CS-g-mPEG-CA)CDs was essentially nontoxic. The P(CS-g-mPEG-CA)CDs/DOX micelles exhibited dose- dependent cytotoxicity, and cell viability declined at higher drug concentrations. The results showed that all three self-assembled P(CS-g-mPEG-CA)CDs preparations had low cytotoxicity toward CNE-2 cells, indicating excellent biocompatibility. The results suggest that these drug-loaded micelles may have potential in cancer therapy.

Fig.8 Cell viability of the CNE-2 cells after incubation with the P(CS-g-mPEG-CA)CDs/DOX micelles for 72 h(n=3)

4 Conclusions

In this study, P(CS-g-mPEG-CA)CDs polymer carbon dots were successfully synthesized using a hydrothermal process as a new carrier material for drug delivery. The results of TEM and CMC analysis indicated that the synthesized P(CS-g-mPEG-CA)CDs could self-assemble into stable micelles with controlled size. A drug-loading study showed that the maximum entrapment efficiency of DOX was 40.8%, with maximum drug loading of 51.3%. Drug release was sustained over 400 h, with a maximum release of 28.7%. An MTT assay showed that drug-loaded polymer carbon dot micelles were cytotoxic toward CNE-2 cells. The P(CS-g-mPEG-CA)CDs can not only be loaded with a drug but also has fluorescent tracing properties, making it a good tracer drug carrier material. In addition, the P(CS-g-mPEG-CA)CDs has good application prospects in biomedical imaging, can support diagnosis and treatment of disease, and the surface molecules of P(CS-g-mPEG-CA)CDs can easily be modified to prepare multi-functional medical nano-particles to further expand its application.

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