# Green Strategy to Develop Novel Drug-Containing Poly (ε-Caprolactone)-Chitosan-Silica Xerogel Hybrid Fibers for Biomedical Applications

Authors: Hua-Jian Zhou; Shu-Hua Teng; Yi-Bo Zhou; Hai-Sheng Qian
Journal: Journal of Nanomaterials
 (2020)

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## Abstract

A facile and green method was explored to prepare the tetracycline hydrochloride- (TCH-) loaded poly (ε-caprolactone)-chitosan-silica xerogel (PCL-CS-SiO2) hybrid fibers by using 90% acetic acid as a suitable solvent. The SEM results showed that those fibers exhibited a continuous, bead-free morphology, an average diameter of about 430 nm, and super-hydrophilicity (θwater≈0°). The presence of SiO2 was found to enhance the thermal stability of the hybrid fibers, and the actual content of SiO2 was obtained by the TG measurement. Moreover, SiO2 xerogel as an important bioceramic endowed the hybrid fibers with good drug release behavior and in vitro bioactivity, suggesting their potential use as novel drug carriers for bone tissue engineering. The present work is expected to offer a green strategy to develop novel, multifunctional hybrid materials.


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## Body

## 1. Introduction

Micro- and nanofibers produced by electrospinning have been extensively used in tissue engineering, drug delivery, and some other biomedical fields due to their small size, good uniformity, high porosity, and large specific surface area [1–4]. Among the various electrospun biopolymers, poly (ε-caprolactone) (PCL) has attracted particular attention in terms of its good electrospinnability, mechanical strength, and biocompatibility [5–7]. Romos et al. prepared porous PCL microfibers at high relative humidity (65%) and explored the drug release behavior of the PCL fibers with different surface porosities [8]. However, when used as tissue engineering materials, the PCL fibers possess a poor hydrophilicity and lack bioactivity, which is unfavorable to the cell adhesion and tissue regeneration. To overcome those drawbacks, different kinds of PCL-based composite fibers have been developed by blending PCL with some other biocompatible inorganic or organic materials [9–12].Chitosan (CS) as a natural polysaccharide exhibits excellent hydrophilicity and biological properties [13–15], but poor electrospinnability and weak mechanical strength. Silica (SiO2) xerogel is an important inorganic biomaterial having high mechanical properties, good bioactivity, and controlled drug release behavior [16, 17]. Therefore, it is desirable that the combination of PCL, CS, and SiO2 would avoid their above-mentioned drawbacks and produce novel hybrid fibers with good morphology and multiple biofunctions. Ma et al. prepared the core-shell PCL/CS composite fibers through an emulsion electrospinning process [18]. Lee et al. formulated the PCL/SiO2 hybrid sol into fibrous membranes by electrospinning for guided bone regeneration [19]. However, in order to obtain the bead-free PCL-based nanofibers, the researchers generally used some organic solvents (chloroform, dichloromethane, 1,1,1,3,3,3-hexafluoro-2-propanol, etc.) with more or less toxicity to the environment and human health. Moreover, there has been no relevant research on fabricating the tricomponent hybrid fibers of PCL-CS-SiO2 for biomedical applications so far. Thus, green synthesis of the novel PCL-CS-SiO2 fibers with improved hydrophilicity and biological performance is of great significance and urgency for the multiple bioapplications.In this study, 90% acetic acid was used for the first time as a suitable green solvent to one-pot prepare the drug-containing PCL-CS-SiO2 hybrid fibers. The composition, morphology, and wettability of the hybrid fibers were characterized, and their drug release behavior was investigated to evaluate the feasibility as a novel drug carrier. In addition, their ability to form bone apatite in vitro was also assessed. The combination with SiO2 xerogel would effectively improve the hydrophilicity and biological properties of the PCL-CS fibers while maintaining their good electrospinnability, thus generating PCL-CS-SiO2 hybrid fibers with superior performance for multiple biomedical applications. Moreover, the present study would offer an effective pathway for the green synthesis of novel hybrid materials for various applications.


## 2. Experimental Procedure

### 2.1. Materials

Chitosan (CS) powder (medium molecular weight) was commercially obtained from Sigma-Aldrich Corporation (USA). Tetracycline hydrochloride (TCH) was purchased from Shanghai Macklin Biochemical Co. Ltd. (Shanghai, China). Poly (ε-caprolactone) (PCL) (Mn=80,000), tetramethyl orthosilicate (TMOS), glacial acetic acid, and the other chemical reagents used in this study were supplied by Aladdin Industrial Co., Ltd. (Shanghai, China).


### 2.2. Preparation of the Drug-Containing PCL-CS-SiO2 Hybrid Fibers

Firstly, PCL and CS powders were completely dissolved in 90% acetic acid to get a viscous solution containing 20% (w/v) PCL and 1.5% (w/v) CS, followed by the subsequent dissolution of TCH (4%, w/v). The silica sol was preobtained by fully hydrolyzing TMOS in distilled water under the catalysis of HCl (1 M). Then, the silica sol was slowly dropped into the above drug-containing PCL-CS solution and stirred for 2 h to form a homogeneous PCL-CS-SiO2 hybrid sol containing 20 wt% SiO2. For the electrospinning process, the PCL-CS-SiO2 sol was injected into the 5 mL syringe with a 21 G needle and then electrospun at the electric voltage, flow rate, and spinneret-to-collector distance of 15 kV, 1 mL/h, and 15 cm, respectively. For comparison, the drug-free PCL-CS and PCL-CS-SiO2 fibers as well as the drug-loaded PCL-CS fibers were also prepared using a similar procedure.


### 2.3. Characterizations of the Hybrid Fibers

The viscosity and conductivity of the solutions were measured by the rotational viscometer (Haake Viscotester C) and the conductivity meter (DDS-307), respectively. The wettability of the fibers was tested by the contact angle tester (JC2000D2A). The fiber morphology was investigated by using a SU8220 scanning electron microscope (SEM). The chemical groups of the fibers were identified with a PerkinElmer 983G Fourier transform infrared spectroscopy (FT-IR). In addition, the thermal behaviors of the fibers were characterized by STA 449 F3 Jupiter thermogravimetry/differential scanning calorimetry (TG/DSC).


### 2.4. Drug Release Behavior andIn Vitro Bioactivity of the Hybrid Fibers

The drug release evaluation was performed by soaking the TCH-loaded fibers in 20 mL of the phosphate-buffered saline (PBS) solution (pH 7.4, 0.01 M) at 37°C. At predetermined intervals, 5 mL supernatant was collected and tested using a UV-Vis spectrophotometer (Evolution 300) at 274 nm. The drug encapsulation efficiency of the samples was measured by immersing the drug-loaded fibrous membranes in the PBS solution for 24 h and then analyzing the concentration of the released drug in the supernatant by UV. The drug encapsulation efficiency was expressed as a percentage (%) of the actual drug loading amount divided by the theoretical drug amount contained in the fibers. In addition, the evaluation on the in vitro bioactivity of the PCL-CS-SiO2 fibers was performed by immersing the fibrous membrane in simulate body fluid (SBF) for 3 days, after which the sample was rinsed with distilled water carefully, air-dried, and finally observed by SEM.


## 2.1. Materials

Chitosan (CS) powder (medium molecular weight) was commercially obtained from Sigma-Aldrich Corporation (USA). Tetracycline hydrochloride (TCH) was purchased from Shanghai Macklin Biochemical Co. Ltd. (Shanghai, China). Poly (ε-caprolactone) (PCL) (Mn=80,000), tetramethyl orthosilicate (TMOS), glacial acetic acid, and the other chemical reagents used in this study were supplied by Aladdin Industrial Co., Ltd. (Shanghai, China).


## 2.2. Preparation of the Drug-Containing PCL-CS-SiO2 Hybrid Fibers

Firstly, PCL and CS powders were completely dissolved in 90% acetic acid to get a viscous solution containing 20% (w/v) PCL and 1.5% (w/v) CS, followed by the subsequent dissolution of TCH (4%, w/v). The silica sol was preobtained by fully hydrolyzing TMOS in distilled water under the catalysis of HCl (1 M). Then, the silica sol was slowly dropped into the above drug-containing PCL-CS solution and stirred for 2 h to form a homogeneous PCL-CS-SiO2 hybrid sol containing 20 wt% SiO2. For the electrospinning process, the PCL-CS-SiO2 sol was injected into the 5 mL syringe with a 21 G needle and then electrospun at the electric voltage, flow rate, and spinneret-to-collector distance of 15 kV, 1 mL/h, and 15 cm, respectively. For comparison, the drug-free PCL-CS and PCL-CS-SiO2 fibers as well as the drug-loaded PCL-CS fibers were also prepared using a similar procedure.


## 2.3. Characterizations of the Hybrid Fibers

The viscosity and conductivity of the solutions were measured by the rotational viscometer (Haake Viscotester C) and the conductivity meter (DDS-307), respectively. The wettability of the fibers was tested by the contact angle tester (JC2000D2A). The fiber morphology was investigated by using a SU8220 scanning electron microscope (SEM). The chemical groups of the fibers were identified with a PerkinElmer 983G Fourier transform infrared spectroscopy (FT-IR). In addition, the thermal behaviors of the fibers were characterized by STA 449 F3 Jupiter thermogravimetry/differential scanning calorimetry (TG/DSC).


## 2.4. Drug Release Behavior andIn Vitro Bioactivity of the Hybrid Fibers

The drug release evaluation was performed by soaking the TCH-loaded fibers in 20 mL of the phosphate-buffered saline (PBS) solution (pH 7.4, 0.01 M) at 37°C. At predetermined intervals, 5 mL supernatant was collected and tested using a UV-Vis spectrophotometer (Evolution 300) at 274 nm. The drug encapsulation efficiency of the samples was measured by immersing the drug-loaded fibrous membranes in the PBS solution for 24 h and then analyzing the concentration of the released drug in the supernatant by UV. The drug encapsulation efficiency was expressed as a percentage (%) of the actual drug loading amount divided by the theoretical drug amount contained in the fibers. In addition, the evaluation on the in vitro bioactivity of the PCL-CS-SiO2 fibers was performed by immersing the fibrous membrane in simulate body fluid (SBF) for 3 days, after which the sample was rinsed with distilled water carefully, air-dried, and finally observed by SEM.


## 3. Results and Discussion

Conventionally, the CS fibers were usually prepared by using strong organic acids as the solvent, and the PCL fibers were generally obtained by using toxic organic solvents. To avoid the above problems, 90% acetic acid was used as a green solvent in our experiments to one-pot synthesize the TCH-containing PCL-CS-SiO2 hybrid fibers. As illustrated in Figure 1, a viscous PCL-CS solution was firstly prepared, and then, TCH as a model drug was subsequently dissolved to get a clear yellow TCH-containing PCL-CS solution, followed by a thorough mixing with the SiO2 sol. After such mixing, no precipitation or aggregation was observed, indicating the sufficient combination of the drug molecules with the PCL-CS-SiO2 hybrid sol at a molecular level. Finally, the TCH-containing PCL-CS-SiO2 hybrid sol was electrospun to form continuous fibers. The whole preparation process was green and facile. Moreover, the drug loading capacity of the hybrid fibers can be adjusted by simply changing the TCH amount added.Figure 1
Schematic illustration showing the facile preparation process of the PCL-CS-SiO2 hybrid fibers.Figure2 shows the SEM images of the different fibers. It was revealed in Figure 2(a) that the PCL-CS fibers coexisted with many beads and droplets, which was mainly attributable to the relatively high viscosity but low conductivity of the PCL-CS solution (Table 1). After TCH was loaded, the viscosity of the PCL-CS solution was greatly decreased to 620 mPa·s while the conductivity was increased to 354 μS/cm. As a result, the electrospinnability of the PCL-CS solution was significantly improved, eventually producing a bead-free morphology and an average fiber diameter of about 290 nm (Figure 2(b)). Such morphology was very similar to that of the PCL-based composite fibers reported by Miele et al. [20].Figure 2
SEM images of (a) PCL-CS, (b) drug-loaded PCL-CS, and (c) drug-loaded PCL-CS-SiO2 fibers.
(a)(b)(c)Table 1
Viscosity, conductivity, and contact angles of different fibers.
SamplesViscosity (mPa·s)Conductivity (μS/cm)Contact angle (°)Drug entrapment efficiency (%)PCL-CS1535±2433±4122.6±10.1—Drug-loaded PCL-CS620±17354±1043.2±5.794.0±1.3Drug-loaded PCL-CS-SiO2349±6367±15~096.4±0.8As exhibited in Figure2(c), a further mixing of the TCH-containing PCL-CS solution with the SiO2 sol generated continuous and defect-free hybrid fibers having a mean diameter of approximately 430 nm. By comparing Figures 2(b) and 2(c), it was suggested that, even though the drug-loaded PCL-CS-SiO2 hybrid fibers displayed an increased average diameter and a wider diameter distribution than the PCL-CS equivalents, they presented an obvious improvement in the continuity and dispersity of the fibers probably due to the increase of the conductivity. In addition, the hydrophilicity of the PCL-CS fibers was also significantly enhanced by the addition of TCH and SiO2. Particularly, the contact angle of water on the drug-loaded PCL-CS hybrid fibers decreased to nearly zero after combination with the SiO2 sol.The FT-IR spectra of three samples were shown in Figure3(a). The absorption peaks between 2800 and 3000 cm-1 corresponded to the C-H stretching vibrations of the PCL and CS molecules [21]. The strong peaks around 1732 and 1175 cm-1 were assigned to the C=O and C-O-C stretching vibrations of PCL, respectively [22]. In the spectra of the drug-loaded PCL-CS and PCL-CS-SiO2 fibers, TCH exhibited a characteristic absorption peak of the C=C groups at 1610 cm-1. It was also found that the weak adsorption peak at 3300-3600 cm-1 became stronger and wider after combination with SiO2 probably due to the abundant presence of the Si-OH groups in silica xerogel [23].Figure 3
(a) FT-IR spectra, (b) TG curves, and (c) DSC profiles of different samples.
(a)(b)(c)The presence of silica xerogel could be further confirmed by TG/DSC. As depicted in Figures3(b) and 3(c), the sharp weight loss between 300°C and 550°C was mainly related to the decomposition of PCL and CS together with a polycondensation process of the SiO2 xerogel [24]. The appearance of the new exothermic peak located at about 390°C in the DSC profile of the PCL-CS-SiO2 fibers was probably indicative of the successful combination of PCL-CS with silica xerogel. The shift of the exothermic peak of the PCL-CS fibers at 400°C to a higher temperature implied the increase of their thermal stability by incorporating SiO2 xerogel. In addition, the actual content of SiO2 contained in the PCL-CS-SiO2 hybrid fibers was calculated from the TG curve to be 15.8%, slightly lower than its theoretical value (20%).It was revealed in Table1 that the PCL-CS-SiO2 fibers exhibited a higher drug entrapment efficiency (96.4%) than the PCL-CS fibers (94.0%), which was probably attributable to the strong adsorption ability of the SiO2 xerogel to the TCH molecules by virtue of its abundant –OH groups [25, 26]. The cumulative TCH release profiles of the drug-loaded fibers were depicted in Figure 4(a). Within the first 1 h, both samples displayed a burst drug release due to their highly hydrophilic nature. As shown in the inset of Figure 4(a), about 91.6% and 77.5% of TCH were released during this period from the PCL-CS and PCL-CS-SiO2 fibers, respectively. Subsequently, the drug release rate slowed down and the PCL-CS-SiO2 hybrid fibers exhibited a more sustained release behavior than the PCL-CS fibers, which can be attributed to their good fiber morphology and the formation of the three-dimensional network by the combination of PCL-CS with SiO2 sol. After 24 h of testing, the cumulative amount of TCH released from the PCL-CS and PCL-CS-SiO2 fibers reached about 95.3% and 97.2%, respectively.Figure 4
(a) Drug release profiles of the PCL-CS and PCL-CS-SiO2 fibers and (b) SEM image of the PCL-CS-SiO2 fibers after immersion in the SBF solution for 3 days.
(a)(b)In addition, it was revealed from Figure4(b) that the PCL-CS-SiO2 hybrid fibers possessed a good in vitro bioactivity. After immersion in the SBF solution for 3 days, some particle aggregates were found to precipitate on the surface of the fibrous membrane, with a typical morphology of the bone-like apatite particles formed on the SiO2-related materials [27, 28]. In the PCL-CS-SiO2 hybrid fibers, SiO2 xerogel as a well-known bioactive ceramic was homogeneously incorporated into the PCL-CS matrix, which was beneficial to improve the drug release behavior and in vitro bioactivity of the hybrid fibers. Furthermore, even though the fibers were immersed in SBF for 3 days, they still presented an intact morphology without obvious fiber integration or degradation, suggesting their good stability in aqueous system.


## 4. Conclusions

Novel drug-containing PCL-CS-SiO2 hybrid fibers were facilely synthesized by using nontoxic acetic acid (90%) as a suitable solvent. The SEM results revealed that the continuous and dispersed hybrid fibers were generated, with an average diameter of about 430 nm. The chemical compositions of the hybrid fibers were identified by TG and FT-IR analysis. Moreover, the drug-loaded PCL-CS-SiO2 hybrid fibers exhibited super-hydrophilicity (θwater≈0°) and a drug entrapment efficiency of about 96.4%. In addition, they possessed a good in vitro bioactivity and an improved drug release performance as compared with the PCL-CS fibers, which makes them more suitable to serve as a novel drug carrier for bone tissue engineering than the PCL-CS fibers.



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