Sage Journals: Discover world-class research

Abstract

In this study, a temperature responsive PGS/PLLA@PNIPAM core-shell nanofiber membrane was prepared by combining electrospinning with surface ATRP grafting polymer technology, in which the core layer of PGS/PLLA nanofiber was prepared by electrospinning, and then the shell layer of temperature responsive PNIPAM polymer was grafted on the nanofiber surface by ATRP reaction. In the experiment, a macromolecule-initiator PGS-Br was prepared and characterized by FTIR and ¹H NMR. The surface morphology, composition, element of the core-shell nanofiber membrane were characterized by SEM, FTIR, and XPS. In addition, it is worth noting that the core-shell nanofiber membrane can respond to temperature in drug release tests.

Keywords

Electrospinning surface ATRP grafting core-shell nanofibers

Introduction

Electrospinning is a simple, fast, and efficient method for preparing nanofibers with the diameter from a few nanometers to tens of nanometers.¹ As a kind of one-dimensional nanofiber material, electrospun nanofibers have attracted more and more researchers' attention.^2,3 Electrospun nanofibers have the advantages of length-to-diameter ratio, large specific surface area and high porosity. Electrospun nanofibers can be controlled by a variety of polymers and easy to be functionalized.^4,5 Electrospun nanofibers have been shown to different applications in many fields, such as energy,⁶ environment,^7,8 tissue engineering,⁹ medicine,¹⁰ and sensors,¹¹ which excellent performances are due to their design tunable structure and composition. Among them, the core-shell nanofibers have novel structures and important applications due to combining the advantages of the inner and outer layer materials. The traditional methods for preparing core-shell nanofibers include coaxial electrospinning,¹² in situ growth¹³ and the surface polymerization.^14,15 Among them, the method of grafting on the nanofiber surface has a good prospect in the field of drug carrier control and release.^16,17 In order to make the more intelligent carrier, a variety of conditional response drug carriers¹⁸ were designed and prepared, such as temperature response carrier^19,20 and pH response carrier.²¹ Among them, surface-grafted electron transfer-atom-transfer radical polymerization (AGET-ATRP) is a well-known controlled polymerization method to adjust the degree of cross-linking of the polymer shell.²²

Poly (glycerol sebacate) (PGS), which has good biocompatibility, flexibility and degradability, is a kind of biomedical material with excellent performance, and is widely used in various organs and wound patches. However, its spinnability is low. It is not to form nanofiber morphology alone, which limit its application.^23,24 Poly-L-lactic acid (PLLA), as a synthetic polymer that can be controlled to degrade, has been studied in clinical medicine for a long time and has good spinnability. It can be used as a spinning aid for PGS, so as to assist in the preparation of PGS nanofiber membrane.^25,26 Yan et al. reported a core-shell poly(glycerol sebacate)-poly(l-lactic acid) electrospun membranes for oil spill remediation.²⁷ However, it does not further functionalize its surface. The polyn-isopropyl acrylamide (PNIPAM) macromolecular chain has hydrophilic acyl amino group and hydrophobic isopropyl group at the same time, which makes the linear PNIPAM aqueous solution and the cross-linked PNIPAM hydrogel show temperature sensitive characteristics.²⁸ Therefore, as an environmental response polymer has been widely used in drug controlled release and other fields.^29–31 It would be very meaningful to combine PGS-PLLA nanofibers with PNIPAM polymer to realize the controlled drugs release of temperature-sensitive.

In this study, PGS/PGS-Br/PLLA nanofiber membrane was firstly prepared by coaxial electrospinning method, and PLLA was used as spinning aid.³² Then, through ATRP grafting reaction, the surface of the nanofiber membrane was grafted with PNIPAM polymer, an temperature responsive polymer.^33,34 Finally, the nanofiber membrane with PGS/PLLA as the core layer and PNIPAM polymer as the shell layer was obtained. It was used as a drug carrier to realize the temperature-sensitive controlled release of drugs.

Experimental section

Materials

Sebacic acid (99%, M_W = 202.25, C₁₀H₁₈O₄) and glycerol (A.R., M_W = 92.09, C₃H₈O₃) were purchased from Aladdin (China), and Sigma (USA), respectively. The poly-L-lactic acid (PLLA, Mn = 200 kDa) were purchased from the Jinan Daigang Biomaterial Co. Ltd (China). N-isopropylacrylamide (A.R., M_W = 113.16, C₆H₁₁NO) was obtained from Aladdin (China) and was recrystallized by water. 2-Bromoisobutyryl bromide (BiBB, 99%, M_W = 229.91, C₄H₆Br₂O) was purchased from Aladdin (China). Triethylamine (TEA, M_W = 101.19, C₆H₁₅N) was purchased from Sigma (USA). CuBr was purchased from Macklin (China) and was reduced by glacial acetic acid (98%, Aladdin, China). Pentamethyldiethylenetriamine (PMDETA, M_W = 173.3, C₉H₂₃N₃) and Ascorbic Acid (AA, M_W = 176.12, C₆H₈O₆) were obtained from Aladdin (China). Dichloromethane (DCM), ethyl acetate (EtOAc), methanol (MeOH), and N,N-dimethylformamide (DMF) were of reagent grade and purchased from Sigma (USA). Deionized water was prepared by water purification machine (UTP-1-10T). Diluted hydrochloric acid (0.01 mol/L) was prepared by diluting the concentrated hydrochloric acid (37.5% HCl) from Beijing Chemical Work (China). All solvents were used without further purification.

Fabrication of the macro-initiator pre-PGS-Br

First, sebacic acid was recrystallized using absolute ethyl alcohol. Then, equimolar ratios of glycerol and sebacic acid were mixed in the flack under 140°C oil bath to melt the sebacic acid, then heat up to 160°C for 8 h to form the PGS pre-polymer. And the nitrogen flow was blown at a gas flow of 0.2 m³ h⁻¹ during the reaction.³⁵

About 10 g pre-PGS was dissolved in dichloromethane (DCM) in the 50 mL flask, then 900 μL BiBB was added to solution drop by drop. 200 μL TEA was as acid-binding agent in order to promote the reactivity. The solution was stirred by magnetic stirrers at room temperature for 24 h. DCM of the solution was evaporated by rotatory evaporator after reaction ending. EtOAc was added to the above-mentioned product due to remove the reactive triethylamine hydrochloride. And 0.01 mol/L diluted hydrochloric acid was used to remove the remaining TEA by separating funnel. At the end, EtOAc was removed by rotatory evaporator (Yarong RE-52AA, Shanghai, China).

Fabrication of the PGS/PGS-Br/PLLA nanofiber membrane

During fabrication of the PGS/PGS-Br/PLLA nanofiber membrane, 0.8 g pre-PGS, 0.2 g pre-PGS-Br and 1.0 g PLLA were mixed and dissolved in the mixed solvent of DCM and DMF (v:v = 3:1. The concentration of PLLA in the mixed solvent was 10 wt%. The as-prepared solutions were loaded into two 5 mL syringe. The electrospinning equipment is QINGZI NANO E02 (China). The inner diameter of needle is 0.6 mm. And the flow rate of accesses was 0.6 mL h⁻¹. In addition, the electrospinning voltage was 18 kV and the distance between the needle and collector (aluminum foil) was set at 15 cm. The obtained PGS/PGS-Br@PLLA nanofiber membrane was exposed on room temperature to evaporate any residual solvent. Furthermore, the membrane was thermo-cured in 120°C under vacuum drying oven (101-2A, Tianjin, China) for 72 h to cure PGS nanofibers.

Fabrication of the PGS/PLLA@PNIPAM core-shell nanofiber membrane by surface ATRP grafting

The above-mentioned nanofiber membrane containing the macromolecule initiator was added to the three-mouth flask containing methanol or water, and nitrogen was rinsed under the ice water bath for 20 min. The ligand pentamethyldiethylenetriamine (PMDETA) and the monomer NIPAM were added to the flask and degassed with nitrogen for 10 min. Next, the reducing agent AA and catalyst CuBr were added to the flask in a nitrogen atmosphere, and then changed to an oil bath (dimethyl silicone oil), and then reacted at 60°C for 60 min. Finally, the reaction is terminated by removing nitrogen atmosphere and touching the air. After the reaction is completed, the nanofiber membrane is washed with deionized water for three times and then put into a vacuum drying oven (101-2A, Tianjin, China) for drying 24 h.

Characterizations of pre-PGS-Br and the PGS/PLLA@PNIPAM nanofiber membrane

The pre-PGS and pre-PGS-Br were smeared on the potassium bromide (KBr) tablet and characterized by Fourier-transform infrared spectrometer from 4000 to 500 cm⁻¹(FTIR, Nicolet 5700, Thermo Company, USA). The structure of pre-PGS and pre-PGS-Br were characterized by hydrogen nuclear magnetic resonance (¹H NMR, AV400 NMR, Bruker Company, Germany). It was tested at 600 MHz using DCl₃ as solvent. The morphology of the PGS/PLLA@PNIPAM nanofiber membrane was examined by scanning electron microscopy (SEM, FEI Quanta 250, The Netherlands). At the same time, SEM could also be used with electronic energy spectrum, qualitative test sample elements. The dry membrane sample ensuring they are completely free of moisture was pasted on the sample table and then were sputter coated with gold (Model 550; Electron Microscope Sciences) in preparation for SEM.³⁵ X-ray photoelectric spectroscopy (XPS, ESCALAB 250, Thermo VG Scientiﬁc, USA.) was used to detect the N elements, the corresponding content and to analyze the chemical state within 10 nm of the sample surface.

Characterization of physical properties

The wettability of membranes was characterized by water contact angle measurements (WCA, Samsung FA-CED camera, Korea). To illustrate the thermoresponsive property of PGS/PLLA@PNIPAM membranes.

Drug release test in different temperature

In order to test the temperature responsive effect of drug release, the characteristic absorption peak of gatifloxacin (model drug) at 285.5 nm was measured by ultraviolet spectrophotometry (UV, u-3900, Hitachi, Japan). The quantitative PGS/PLLA@PNIPAM nanofibers loading gatifloxacin were immersed into 50 mL deionized water under different temperature (20°C and 50°C), respectively in oscillation incubator (BS-2F, Dingfeng, China). 1 mL solution was taken out at different times (0, 5, 15, 30, 60, 90, 120, 180, 240, 360, 480, and 600 min) respectively, then tested by ultraviolet absorption three times to calculate the drug release concentration.

Results and discussions

As shown in Scheme 1, the preparation process of the PGS/PLLA@PNIPAM nanofiber membrane consists of two main steps: synthesis of the macro-initiator PGS-Br and grafting PNIPAM polymer by AGET-ATRP on the surface of electrospun PGS/PGS-Br/PLLA nanofiber membrane.

Scheme 1.

(a) The material synthesis process and (b) the preparation process of the PGS/PLLA@PNIPAM.

Preparation of the pre-PGS-Br

As depicted in ¹H NMR spectrum of Figure 1(a), it showed –CH₂ groups in the backbone supported by sebacic acid at 1.3, 1.6, and 2.34 ppm, and –CH₂, –CH– at 4.18 and 3.7 ppm from glycerol, which were influenced by the distance from ester groups. As shown in Figure 1(b), macro-initiator pre-PGS-Br was evidenced by –CH₃ group from BiBB at 2.0 ppm, which means BiBB was successfully grafted on pre-PGS. The pre-PGS was synthesized by the condensation reaction, the FTIR spectrum of pre-PGS in Figure 1(c) shows the peaks for –C=O at 1740 cm⁻¹ and the peaks for –OH at 3438 cm⁻¹, which is completely consistent with the previous report.³⁵ And in Figure 1(d), the peak of C–Br was showed at 737 cm⁻¹. It also confirmed the formation of pre-PGS-Br. X-ray photoelectron spectroscopy (XPS) results show the co-presence of C, O, N, and Br in the as-prepared samples (Figure 2(b)) compared to the PGS/PLLA membrane (Figure 2(a)), suggesting the successful reacting of BiBB. The high resolution Br 3d spectrum provided in Figure 2(e).

Figure 1.

¹H NMR spectrum of (a) PGS and (b) PGS-Br. The FTIR spectrum of (c) pre-PGS and (d) pre-PGS, PGS-Br and PGS/PLLA@PNIPAM.

Preparation of PGS/PLLA@PNIPAM nanofiber membrane

The PGS/PGS-Br/PLLA-grafting-PNIPAM polymer was synthesized by AGET-ATRP reaction, the FTIR spectrum of PGS in Figure 1(d) shows the peaks for –CO–NH– at 1640 cm⁻¹ and the peaks for –NH– at 3440 cm⁻¹, which is completely consistent with the previous report. X-ray photoelectron spectroscopy (XPS) results show the co-presence of C, O, and H in the PGS/PLLA nanofiber membrane (Figure 2(a)). The high resolution C 1s shows that the peak more can be deconvoluted into four peaks (Figure 2(d)), O=C–O, C=O, C–O, and C–C, C–H, respectively. After grafting PNIPAM, it shows the co-presence of C, O, N, and H in the PGS/PLLA@PNIPAM nanofiber membrane (Figure 2(c)). The peak more can be deconvoluted into four peaks in the high resolution C 1s (Figure 2(f)), O=C–O, C=O, C–O, C–N, and C–C, C–H, respectively.³⁶ No significant difference can be obtained from the C 1s XPS spectra in the PGS/PGS-Br/PLLA nanofiber membrane and PGS/PLLA@PNIPAM nanofiber membrane. So N1s spectra of PGS/PLLA@PNIPAM nanofiber membrane was tested as shown in Figure 2(g). The high-resolution N 1s spectrum in Figure 2(g) shows the peak at 129.9 eV, revealing the presence of C–N bonds, which indicating the successful grafting of PNIPAM.

Figure 2.

XPS survey spectra: (a) PGS/PLLA, (b) PGS/PGS-Br/PLLA, and (c) PGS/PLLA@PNIPAM nanofiber membrane; (d) high resolution C 1s spectrum of PGS/PGS-Br/PLLA nanofiber membrane, (e) high resolution Br 3d spectrum of PGS/PGS-Br/PLLA nanofiber membrane, (f) high resolution C1s, and (g) N1s spectrum of PGS/PLLA@PNIPAM nanofiber membrane.

Further, in order to prove the successful preparation of PGS/PLLA@PNIPAM, the prepared ground nanofiber membrane was characterized by SEM images and EDS elemental analysis, as shown in Figure 3. Figure 3(a) and (d) showed the SEM images of the nanofiber membranes before and after grafting PNIPAM polymer, and the distributions of N and Br elements were investigated on the nanofiber surface, respectively. From SEM images, as we can see the surface of nanofiber membrane changed from smooth to rough folded surface, which indirectly demonstrates the successful polymerization of PNIPAM polymer on the surface of the nanofiber. Figure 3(b), (c), (e), and (f) show the distribution of N and Br elements of PGS/PGS-Br/PLLA nanofiber membrane and PGS/PLLA@PNIPAM nanofiber membrane, respectively. It can be seen from the Figure 3(b) that there was no distribution of N elements before grafting PNIPAM on PGS/PGS-Br/PLLA nanofiber membrane, and the distribution of Br elements was relatively large. After grafting PNIPAM polymer, there had been appeared N elements. Accordingly, the distribution of Br elements was reduced. Therefore, PNIPAM polymer was successfully grafted onto the nanofiber membrane in the experiments.

Figure 3.

The magnification SEM images (2000 and 15,000 times) and corresponding EDS element mappings of PGS/PGS-Br/PLLA and PGS/PLLA@PNIPAM nanofiber membrane: (a, d) SEM, (b, e) N element mapping, and (c, f) Br element mapping.

As shown in Figure 4, the wettability of nanofiber membranes were characterized by water contact angle tests. The PGS/PGS-Br/PLLA nanofiber membrane has a water contact angle of about 47°, while the nanofiber membranes with PNIPAM polymer modiﬁcation were hydrophobic at room temperature with a water contact angle of about 129°. The difference are related to the increased surface roughness of electrospun nanofiber membranes at the nanoscale. After modiﬁcation with PNIPAM polymer, water droplets were permeating into the membrane within 30 s at room temperature (20°C, <LCST) and showed a slow spreading. The main force for the absorption in this state is the hydrophilicity of PNIPAM polymer layer and the capillary effect in the microporous membranes. In addition, the pore size in nanofiber membranes increased upon passing the transition. Here, we draw the conclusion that regarding variations of permeability, the eﬀect of surface roughness change caused by the increases of pore size is stronger than the eﬀect of the permeability reduced by the hydrophobic force.³³

Figure 4.

Wettability of different membranes at 20°C for 30 s.

Furthermore, the temperature sensitivity and application prospect of the drug release were studied by controlled release tests at different temperatures. As we can see from Figure 5, the maximum release is only 38.40% at 20°C (T < LCST), but 61.05% at 50°C (T > LCST). At the same time, comparing Figure 5(a) and (b), we found that the drug was released slowly at 20°C, while the drug was released suddenly at 50°C, which phenomenon is secretly related to thermosensitive PNIPAM polymer, it is hydrophilic swelling at low temperature, inter-molecular hydrogen bond strengthening at high temperature, and nanofiber surface fold exposing more nuclear layer surface, which enhances drug release rate. This results show that the core-shell PGS/PLLA@PNIPAM nanofibers can be used as drug carriers and realize temperature response control.

Figure 5.

Drug release tests at different temperatures: (a) 20°C (T < LCST) and (b) 50°C (T > LCST).

Conclusion

A novel core-shell structure PGS/PLLA@PNIPAM nanofiber membrane was prepared by the combination of electrospinning and surface ATRP grafting technology. In the experiment, a macromolecule-initiator PGS-Br was prepared and characterized by FTIR and ¹H NMR. The surface morphology, composition, element of the nanofiber was characterized by SEM, FTIR, and XPS. In addition, it is worth noting that the core-shell nanofiber membrane can respond to temperature in drug release tests. This work provides a new idea for the preparation of functional core-shell nanofibers.

Footnotes

Declaration of conflicting interests

The author(s) declared no potential conflicts of interest with respect to the research, authorship, and/or publication of this article.

Funding

The author(s) disclosed receipt of the following financial support for the research, authorship, and/or publication of this article: This work was supported by the China Postdoctoral Science Foundation (Grant no. 2020M671359) and Natural Science Foundation of Jiangsu Province (Grant no. BK20200914).

ORCID iD

Qijian Niu

References

Greiner

Wendorff

JH.

Electrospinning: a fascinating method for the preparation of ultrathin fibers. Angew Chem Int Ed 2007; 46: 5670–5703.

Wang

Wei

One-dimensional composite nanomaterials: synthesis by electrospinning and their applications. Small 2019; 5: 2349–2370.

Wang

Ding

Sun

, et al. Electrospinning/netting: a strategy for the fabrication of three dimensional polymer nanofiber/nets. Prog Mater Sci 2013; 58: 1173–1243.

Xue

Dai

, et al. Electrospinning and electrospun nanofibers: methods, materials, and applications. Chem Rev 2019; 119: 5298–5415.

Han

Xiong

Jiang

, et al. Bio-functional electrospun nanomaterials: from topology design to biological applications. Prog Polym Sci 2019; 91: 1–28.

Guo

Chen

Hao

, et al. Pod-like structured Co/CoO_x nitrogen-doped carbon fibers as efficient oxygen reduction reaction electrocatalysts for Zn-air battery. Appl Surf Sci 2018; 456: 959–966.

Cui

Wang

, et al. Electrospun nanofiber membranes for wastewater treatment applications. Sep Purif Technol 2020: 250: 117116.

Yang

Chen

, et al. Functionalized chitosan electrospun nanofiber membranes for heavy metal removal. Polymer 2019; 163: 74–85.

Zhao

Liang

Ding

, et al. Application of conductive PPy/SF composite scaffold and electrical stimulation for neural tissue engineering. Biomaterials 2020; 255: 120164.

10.

Wei

Liu

Gao

, et al. Mechanical on-off gates for regulation of drug release in cutaneous or musculoskeletal tissue repairs. Mater Sci Eng C 2020; 115: 111048.

11.

Wang

Shen

, et al. Ar plasma treatment on ZnO-SnO₂ heterojunction nanofibers and its enhancement mechanism of hydrogen gas sensing. Ceram Int 2020; 46: 21439–21447.

12.

Zheng

Xin

, et al. Coaxial electrospinning: jet motion, core-shell fiber morphology, and structure as a function of material parameters. Ind Eng Chem Res 2020; 59: 6301–6308.

13.

Niu

Guo

Chen

, et al. Bimetal-organic frameworks/polymer core-shell nanofibers derived heteroatom-doped carbon materials as electrocatalysts for oxygen reduction reaction. Carbon 2017; 114: 250–260.

14.

Amokrane

Humblot

Jubeli

, et al. Electrospun poly(ε-caprolactone) fiber scaffolds functionalized by the covalent grafting of a bioactive polymer: surface characterization and influence on in vitro biological response. ACS Omega 2019; 4: 17194–17208.

15.

Chung

Park

Choi

, et al. The graft-polymerization of poly(ethylene glycol) phenyl ether acrylate onto polyurethane and its impact on the mechanical properties and chain packing. Fibers Polym 2020; 21: 290–299.

16.

Constantin

Bucatariu

Ascenzi

, et al. Poly(NIPAAm-co-b-cyclodextrin) microgels with drug hosting and temperature-dependent delivery properties. React Funct Polym 2014; 84: 1–9.

17.

Luo

Zheng

Wang

, et al. The ethanol-sensing propertirs of porous GaN nanofibers synthesized by electrospinning. Sens Actuators, B 2014; 202: 1010–1018.

18.

Rapoport

Physical stimuli-responsive polymeric micelles for anti-cancer drug delivery. Prog Polym Sci 2007; 32: 962–990.

19.

Zhang

Niu

Wang

, et al. Thermo-sensitive drug controlled release PLA core/PNIPAM shell fibers fabricated using a combination of electrospinning and UV photo-polymerization. Eur Polym J 2015; 71: 440–450.

20.

Loh

Peh

Liao

, et al. Controlled drug release from biodegradable thermoresponsive physical hydrogel nanoﬁbers. J. Controlled Release 2010; 143: 175–182.

21.

Boas

Gradys

Vasilyev

, et al. Electrospinning polyelectrolyte complexes: pH-responsive ﬁbers. Soft Matter 2015; 11: 1739–1747.

22.

Kampferbeck

Vossmeyer

Weller

, et al. Cross-linked polystyrene shells grown on iron oxide nanoparticles via surface-grafted AGET-ATRP in microemulsion. Langmuir 2019; 35: 8790–8798.

23.

Wang

Ameer

Sheppard

, et al. A tough biodegradable elastomer. Nat Biotechnol 2002; 20: 602–606.

24.

Jeffries

Allen

Gao

, et al. Highly elastic and suturable electrospun poly(glycerol sebacate) fibrous scaffolds. Acta Biomater 2015; 18: 30–39.

25.

Roussaki

Gaitanarou

Diamanti

, et al. Encapsulation of the natural antioxidant aureusidin in biodegradable PLA nanoparticles. Polym Degrad Stab 2014; 108: 182–187.

26.

Huan

Liu

Cheng

, et al. Electrospun poly(lactic acid)-based fibrous nanocomposite reinforced by cellulose nanocrystals: impact of fiber uniaxial alignment on microstructure and mechanical properties. Biomacromolecules 2018; 19: 1037–1046.

27.

Yan

Sencadas

Zhang

, et al. Superomniphilic poly(glycerol sebacate)-poly(l-lactic acid) electrospun membranes for oil spill remediation. Adv Mater Interfaces 2017; 4: 1700484.

28.

You

Kalebaila

Brock

, et al. Temperature-controlled uptake and release in PNIPAM-modified porous silica nanoparticles. Chem Mater 2008; 20: 3354–3359.

29.

Ravichandran

Venugopal

Sundarrajan

, et al. Expression of cardiac proteins in neonatal cardiomyocytes on PGS/fibrinogen core/shell substrate for cardiac tissue engineering. Int J Cardiol 2013; 167: 1461–1468.

30.

Luo

Yang

, et al. Thermosensitive PNIPAM-b-HTPB block copolymer micelles: molecular architectures and camptothecin drug release. Colloids Surf, B 2014; 114: 150–157.

31.

Lin

Tang

Cui

, et al. Controllable drug release of electrospun thermoresponsive poly(N-isopropylacrylamide)/poly(2-acrylamido-2-methylpropanesulfonic acid) nanoﬁbers. J Biomed Mater Res A 2012; 100A: 1839–1845.

32.

Cao

Wang

, et al. Effect of mixed solvents on the structure and properties of PLLA/PDLA electrospun fibers. Fibers Polym 2020; 21: 970–977.

33.

Liu

Tas

Zhang

, et al. Thermoresponsive membranes from electrospun mats with switchable wettability for eﬃcient oil/water separations. Macromolecules 2018; 51: 8435–8442.

34.

Elashnikov

Slepicka

Rimpelova

, et al. Temperature-reponsive PLLA/PNIPAM nanofibers for switchable release. Mater Sci Eng C 2017; 72: 293–300.

35.

Yang

, et al. Electrospun core-shell fibrous 2D scaffold with biocompatible poly(glycerol sebacate) and poly-l-lactic acid for wound healing. Advanced Fiber Materials 2020; 2: 105–117.

36.

Liu

Zheng

, et al. A novel bacterial cellulose aerogel modified with PGMA via ARGET ATRP method for catalase immobilization. Fibers Polym 2019; 20: 520–526.

Preparation and characterization of PGS/PLLA@PNIPAM core-shell nanofiber membrane by electrospinning and surface ATRP grafting

Abstract

Keywords

Introduction

Experimental section

Materials

Fabrication of the macro-initiator pre-PGS-Br

Fabrication of the PGS/PGS-Br/PLLA nanofiber membrane

Fabrication of the PGS/PLLA@PNIPAM core-shell nanofiber membrane by surface ATRP grafting

Characterizations of pre-PGS-Br and the PGS/PLLA@PNIPAM nanofiber membrane

Characterization of physical properties

Drug release test in different temperature

Results and discussions

Preparation of the pre-PGS-Br

Preparation of PGS/PLLA@PNIPAM nanofiber membrane

Conclusion

Footnotes

Declaration of conflicting interests

Funding

ORCID iD

References