Multifunctional aliphatic polyester nanofibers for tissue engineering.

Electrospun fibers based on aliphatic polyesters, such as poly(ε-caprolactone) (PCL), have been widely used in regenerative medicine and drug delivery applications due to their biocompatibility, low cost and ease of fabrication. However, these aliphatic polyester fibers are hydrophobic in nature, resulting in poor wettability, and they lack functional groups for decorating the scaffold with chemical and biological cues. Current strategies employed to overcome these challenges include coating and blending the fibers with bioactive components or chemically modifying the fibers with plasma treatment and reactants. In the present study, we report on designing multifunctional electrospun nanofibers based on the inclusion complex of PCL-α-cyclodextrin (PCL-α-CD), which provides both structural support and multiple functionalities for further conjugation of bioactive components. This strategy is independent of any chemical modification of the PCL main chain, and electrospinning of PCL-α-CD is as easy as electrospinning PCL. Here, we describe synthesis of the PCL-α-CD electrospun nanofibers, elucidate composition and structure, and demonstrate the utility of functional groups on the fibers by conjugating a fluorescent small molecule and a polymeric-nanobead to the nanofibers. Furthermore, we demonstrate the application of PCL-α-CD nanofibers for promoting osteogenic differentiation of human adipose-derived stem cells (hADSCs), which induced a higher level of expression of osteogenic markers and enhanced production of extracellular matrix (ECM) proteins or molecules compared with control PCL fibers.

Introduction

A scaffold plays important roles in dictating cell functions and manipulating tissue development by providing structural support and biophysical and biochemical signals, and transporting nutrients and wastes.- An ideal scaffold should have well-defined morphology, tunable degradation rate, sufficient mechanical strength for its intended application and a porous structure that has properties similar to those of the native extracellular matrix (ECM).- In this context, scaffolds based on electrospun nanofibers have been studied for tissue engineering applications.- These nano- and micro-scale fibers have mechanical strength similar to that of natural tissues and resemble the scale and arrangement of fibrous ECM components, in particular, collagen.,

The most widely employed electrospun nanofibrous scaffolds in tissue engineering and drug delivery are based on aliphatic polyesters, such as PCL or polylactide. These materials have a number of useful properties, such as easy processing, biocompatibility and low cost; however, their biological applications are limited because they are hydrophobic and lack active natural cell recognition sites or functional groups along their polyester backbones.- Therefore, depending upon the desired outcome, various polymer modification strategies, such as plasma treatment,- coating,, co-electrospinning with other polymers or bioactive components- or chemically modifying the fibers with a strong reactant, such as sodium hydroxide, are employed. These treatments introduce functionalities, improve hydrophilicity and enhance cell function and tissue formation., Another important strategy for polyester functionalization is through copolymerizing polyester with functional monomers prior to polymerization; however, incorporating monomers makes it difficult to obtain high molecular weight polymers for fabricating tissue engineering nanofibrous scaffolds.,

Here, we developed multifunctional electrospun nanofibers based on the inclusion complex (IC) of aliphatic polyester-α-cyclodextrin (e.g., PCL-α-CD), for tissue engineering applications (Fig. 1A–D). α-CD is a six-member oligosaccharide doughnut ring structure with an inner cavity (diameter ~0.6 nm) and an outside diameter of ~1.4 nm. α-CD rings physically thread onto the PCL chains via non-covalent interactions and resemble a molecular necklace structure (Fig. 1A and B).- α-CD bears hydroxyl groups that can be modified to create a variety of functionalities that also allow conjugation of multiple bioactive agents or ligands.- Previously, we employed α-CDs to create a modular multifunctional hydrogel design for stem cell differentiation that can be modulated at the nanoscale level. The versatility of this design enabled us to create precisely controlled 3D environments with independent mechanical, cell-adhesion and chemical properties. Here, we synthesized PCL-α-CD IC (Fig. 1A and B), electrospun this material into nanofibers (Fig. 1C), demonstrated the utility of functional groups on the nanofibers by conjugating a polymeric nanobead (Fig. 1D) and used the electrospun fiber as a scaffold for in vitro stem cell culture and differentiation for bone tissue formation. To our knowledge, this study demonstrates the first successful electrospinning of PCL-α-cyclodextrin nanofibers for creating tissue engineering scaffolds.

Figure 1. The chemical structures of PCL and α-CD (A), followed by inclusion complex (IC) formation (B). The IC is electrospun into fibers (C), and polystyrene nanobeads can be conjugated through the hydroxyl groups of α-CD on the fiber’s surface (D).

Results

Material characterization

PCL-α-CD IC was characterized for threading of α-CD on PCL chains by FTIR-ATR, WAXD and 1H NMR spectroscopy. FTIR-ATR screening of PCL-α-CD IC, PCL and α-CD showed three peaks at 1026 cm−1, 1079 cm−1 and 1158 cm−1 and confirmed the presence of α-CD. A distinct stretching band at 1735 cm−1 appeared as a result of the carbonyl bonds of PCL (Fig. 2A)., A broad band at 3382 cm−1 appeared because of the symmetric and antisymmetric OH stretching of α-CD in PCL-α-CD IC, which is absent in PCL. Also, in contrast to the α-CD spectrum, a slight shift of the OH stretching band in the IC arose resulting from the formation of hydrogen bonds between α-CD and its guest polymer in the channel form.

Figure 2. WAXD spectra (A), FTIR-ATR spectra (B) and 1H-NMR spectra of α-CD, PCL and PCL-α-CD IC (C).

WAXD result showed that PCL exhibited two typical strong peak reflections at 2θ = 22° and 23.8°, while α-CD displayed a series of peaks at 9.9°, 12.2°, 14.5°, 19.8° and 21.9° as previously reported (Fig. 2B)., In PCL-α-CD IC, most crystalline diffraction peaks due to PCL disappeared, which indicated suppression of guest crystallization by formation of IC. New peaks at ~20° and ~22.5° appeared due to formation of IC., The molar ratio of the two components in PCL-α-CD IC was quantified by integration of resonances for the 1H NMR spectra of α-CD and PCL (shown in Fig. 2C).

Nanofiber synthesis, characterization and modification

Unlike PCL alone, neither DMSO nor CH2Cl2 dissolved IC completely and, therefore, was unsuitable for electrospinning of the polymer solution. However, the polymer was successfully dissolved and electrospun in a mixture of DMSO/CH2Cl2 (3/2, v/v). These fibers were also tested for retention of threaded α-CD on PCL chains by utilizing the hydroxyl groups of α-CD on the surface for further chemical modifications and conjugations. First, both PCL and PCL-α-CD fibers were activated by CDI (Fig. 3A); second, CDI-activated hydroxyl groups were modified to amine groups by reacting with a short length diamine (e.g., ethylenediamine) (Fig. 3A). Subsequently, an amine-reactive fluorescent molecule, fluorescamine, was conjugated onto the fiber surfaces (Fig. 3A). The fibers modified with fluorescamine turned blue under UV light exposure (Fig. 3B). The hydroxyl groups on the nanofibers were also utilized to conjugate a structural component (amine-containing polystyrene nanobeads). SEM images at higher magnification showed no conjugated nanobeads on PCL fibers (Fig. 4A–D); however, PCL-α-CD fibers were decorated with nanobeads via hydroxyl sites (Fig. 4E–H). The CDI-untreated PCL or PCL-α-CD fibers did not conjugate to nanobeads.

Figure 3. (A) The hydroxyl groups of α-CD present in PCL-α-CD IC fibers can be conjugated with several biological or chemical moieties, including a fluorescent molecule. Step 1: Activation of α-CD with N,N’-carbonyldiimidazole (CDI) followed by its reaction with ethylenediamine. The hydroxyl groups are abundant and available for activation by N,N’- CDI in PCL-α-CD IC compared with only terminal hydroxyl groups of PCL. Step 2: Fluorescamine was conjugated to amine groups. (B) Optical microscope images of electrospun fibers of PCL before (i) and after fluorescamine labeling (ii); PCL/α-CD fibers before (iii) and after fluorescamine labeling (iv).

Figure 4. Electrospun fibers of PCL-10% (w/v) in CH2Cl2/DMSO (17/9, v/v) with magnification X1 (A), X10 (B) and (C), X20 (D); PCL-α-CD IC-10% (w/v) in CH2Cl2/DMSO (2/3 v/v); with magnification X1 (E), X10 (F) and (G), X20 (H). These fibers were chemically modified with N,N’-carbonyldiimidazole in acetonitrile followed by conjugation of amine functionalized polystyrene nanobeads (200 nm diameter size). *denotes beads

Cell response to PCL-α-CD nanofibers

hADSCs’ viability and spreading were studied over 3, 7, 14 and 21 d with LIVE/DEAD® (InvitrogenTM, Life Technologies) and F-actin staining. hADSCs attached to both PCL and PCL-α-CD fibers (Fig. 5A and B), and exhibited an elongated fibroblast-like morphology after 3 d, which indicated a viable state. A continuous increase in cell number was visually observed for both fibers. After 21 d, LIVE/DEAD® staining determined the presence of 96.5 ± 2.5% and 97.1 ± 1.5% live cells for PCL and PCL-α-CD fibers, respectively.

Figure 5. hADSCs cultured on either PCL or PCL-α-CD fibers are stained for (A) LIVE/DEAD® Viability/Cytotoxicity (InvitrogenTM, Life Technologies, Grand Island, NY) using calcein AM, ethidium homodimer-1 and Hoechst dye; (B) F-actin using Texas Red-X® phalloidin, and Hoechst dye; (C) alizarin red for mineralization (calcium deposition) and ALP for alkaline phosphatase activity.

Positive staining with alizarin red and ALP (Fig. 5C) was observed on both fibers, which confirmed calcium deposition and mineralization. A substantial increase in the intensity of alizarin red staining was observed from day 14 to day 21 on both fibers, suggesting that by day 21, mineral deposition was greatly enhanced (Fig. 5C).

We then performed quantitative analysis of osteogenic gene-expression. Four osteogenic markers were selected for this study: osteogenesis transcription factor Runx2, and three bone collagen structural proteins: osteopontin, collagen type I and collagen type X. In general, PCL-α-CD fibers induced greater amounts of osteogenic gene expression compared with PCL fibers (Fig. 6A–D). Similarly, relatively higher collagen deposition was obtained on PCL-α-CD fibers (Fig. 6E and F). In summary, ADSCs proliferated at a similar rate on both types of fibers, while PCL-α-CD fibers enhanced osteogenesis.

Figure 6. The relative gene expression of some osteogenic markers during osteogenesis of hADSCs seeded on PCL and PCL-α-CD fibers, including RunX2 (A), osteopontin (B), collagen type I (C) and collagen type X (D); biochemical assays showing DNA content (E) and collagen deposition (F) on the fibers. Each gene expression level was compared with the expression level on day 7 for PCL samples. The DNA assay did not show any significant differences between the DNA values for PCL and PCL-α-CD samples during the time period of the experiment except on day 14; however, the collagen contents for these two samples were significantly different on both day 14 and day 21.

Discussion

Scaffolds based on aliphatic polyesters, such as PCL nanofibers, have been successfully used in biomedical applications, including stem cell culture and differentiation.,,, However, depending on the desired cell function and tissue formation outcomes, aliphatic polyester nanofibers are often chemically modified with bioactive molecules and cell-recognizable ligands by mimicking natural ECM’s chemical and biological cues.

In this context, our reported PCL-α-CD-based electrospun nanofibrous scaffold has unique advantages: first, it is as easy to fabricate as PCL fibers; second, it has multiple functional sites for further conjugation and third, it is independent of the PCL-main chain modification as α-CD physically threads onto PCL chains. The ease of conjugation of various chemical and biological components to create user-specific unique cell environments without PCL modification, makes these nanofibers a powerful biomaterial tool for tissue engineering. For example, we showed the utility of the hydroxyl groups of the α-CD on the fiber surface by conjugating a fluorescent small molecule, fluorescamine, and a polystyrene nanobead (Figs. 3 and 4). Similarly, we can conjugate various small molecules; cell-interactive peptides, such as the cell-binding peptide Arg-Gly-Asp (RGD) and other biological components to improve cell-binding capability of the nanofibers and provide necessary chemical and biological signals for cell functions. A previously reported strategy to improve cell adhesion on PCL nanofibers is co-electrospinning PCL with naturally derived materials, including gelatin or mineralized ECM., Another potential application of PCL-α-CD nanofibers can be for the controlled release of biological components from the fiber surface.

For desirable cellular functions, tissue engineering often needs to deliver bioactive agents via the scaffold. These components are incorporated into PCL fibers and can enhance desirable cell functions upon the agents’ leakage and release from the fibers. For example, Martins et al. incorporated dexamethasone, an osteogenesis inducer, into PCL fibers to enhance osteogenic differentiation of mesenchymal stem cells (MSCs). However, they observed a burst of dexamethasone released as a result of uncontrolled surface erosion, as water penetrated the fiber surface first, leading to sudden drug release. Bioactive components could be conjugated to our PCL-α-CD fiber via external-stimulus-sensitive bonds through functionalized CDs, such as hydrolyzable ester or photocleavable bonds. This would allow the drug to have a greater sustained-release time profile, which is highly desirable in a scaffold design for controlled drug release.

We also investigated application of PCL-α-CD nanofibers as a 2D substrate for cell growth and osteogenic differentiation potential of hADSCs. Recently, there has been much attention focused on hADSCs because of their biological similarity to hBM-MSCs (human bone marrow-MSCs), ease of isolation through abundant and readily accessible adipose tissue, replication capability and multi-lineage differentiation potential. This makes hADSCs a promising source of adult stem cells for bone tissue engineering applications.-

We hypothesized that PCL-α-CD nanofibers can be employed as a scaffold for osteogenic differentiation of hADSCs, as can PCL nanofibers. Therefore, we cultured hADSCs onto 2D substrates of PCL and PCL-α-CD nanofibers in osteogenic media. Morphologically, cells were fully extended and elongated at early time points, indicating cell viability and adhesion, as shown in Figures 5A and B. By three weeks, hADSCs appeared to be completely integrated into the structure of the fibers.

We monitored the extent of osteogenic differentiation of hADSCs on nanofibers by gross-images of positive staining for calcium mineralization and alkaline phosphatase (ALP) activity (Fig. 5C). ALP is an enzyme responsible for dephosphorylation of phosphates and initiating mineralization of ECM, which induces matrix mineralization by restricting matrix nucleation inhibitors. However, ECM mineralization occurs in the later stage of osteogenic differentiation and requires long-term culture before any measurable matrix production occurs. As such, ALP is regarded as an early-stage marker in osteogenesis, and its turning to plateau from upregulation is considered a signal for the initiation of mineralization. We observed a substantial increase in the intensity of alizarin red staining from day 14 to day 21 on both fibers, suggesting that by day 21, mineral deposition was greatly enhanced (Fig. 5C). However, ALP staining did not show much visual difference between PCL and PCL-α-CD samples. This might be due to a possible plateauing of ALP generation at the mid-to-later stage of osteogenesis.

PCR studies showed that ADSCs seeded onto PCL-α-CD fibers exhibited equal or marginally higher relative expressions of osteogenesis markers than on PCL fibers, as shown in Figures 6A–D. The selected markers are critical transcription factors or proteins involved in osteogenesis. Runx2 is an important transcription factor during osteogenesis, while osteopontin, collagen type I and collagen type X are main structural proteins of collagens found in bone. As we observed in this study, their higher expressions with time indicated a greater tendency to differentiate into bone-related cell types. We also found that while the DNA content of the two samples remained the same at each time point (Fig. 6E), collagen deposition on PCL-α-CD fibers was significantly higher than on PCL fibers (Fig. 6F). An increase in DNA content over time indicated that cells proliferated equally well on both PCL-α-CD and PCL fibers (Fig. 6E). Collagen is a major organic component of mineralized ECM, comprising ~90% of all the organic material in bone, and it serves as a template for mineral deposition. Our result suggests that the PCL-α-CD fibers could enhance collagen production, making a relatively better substrate to induce bone formation; possibly due to a change in the substrate hydrophilicity via the hydroxyl groups of α-CD. Furthermore, the chemical composition of the nanofiber with α-CD played an important role in cell growth and differentiation, while fiber morphology or topography was unchanged. Earlier, we showed that functionalized α-CDs in PEG hydrogels could enhance tissue formation. These findings support the concept that α-CDs promote stem cell differentiation into musculoskeletal tissues, regardless of the type of polymers used for creating an artificial environment in the form of hydrogels or nanofibrous scaffolds.

Materials and Methods

Synthesis of PCL-α-CD IC

PCL (1.0 g, Mw 70 k ~ 90 k Da; Sigma-Aldrich) was dissolved in acetone (60 mL) and heated at 50°C in a silicon oil bath. α-CD (0.5 g, Sigma-Aldrich) was dissolved in 10 mL of dimethylformamide (DMF) and added dropwise to the heated PCL-acetone solution. After stirring for 2 h, the mixture was air-cooled to room temperature. This solution was poured into a glass flat-bottom PYREX® container (Corning Inc. Life Sciences) and stirred slowly overnight at room temperature to evaporate the acetone. A thin layer of PCL-α-CD film was formed, which was soaked in and washed multiple times with water to remove any unthreaded α-CD. PCL-α-CD IC was further characterized by 1H-NMR (300 or 400 MHz; Bruker), wide-angle X-ray diffraction (WAXD) from 2θ = 5° to 35° (PANalytical MPD Pro Diffractometer, Cu-Kα radiation; PANalytical B.V.) and Fourier transform infrared-attenuated total reflectance (FTIR-ATR) (Bruker, Vector 22 with a Pike Miracle ATR attachment) spectroscopy within a range of wavenumber 700–3,800 cm−1. WAXD and FTIR-ATR were also performed on PCL only and α-CD only samples, as controls.

Electrospinning of PCL and PCL-α-CD IC nanofibers

PCL was dissolved in a mixture of dichloromethane (DCM) and dimethyl sulfoxide (DMSO) (17/9, v/v) at a concentration of 10% (w/v). The solution was drawn into a 1 mL syringe (Norm-Ject, Henke-Sass Wolf GmbH) with a 30 G needle (Becton, Dickinson and Co.) and electrospun at 8 kV and 5 mL/h. PCL-α-CD was dissolved in a mixed solvent of DCM and DMSO (2/3, v/v) at a concentration of 10% (w/v) and filled into the same kind of syringe and needle. The PCL-α-CD fibers (605 ± 85 nm, n = 100 nm) were electrospun at 5.5 kV and 6 mL/h to obtain fibers with similar diameter to those of PCL (617 ± 170 nm, n = 100). Fibers were collected onto aluminum foil covered with 15 mm diameter microscope coverslips (Thermo Fisher Scientific), which were kept at a distance of 16 cm from the tip of the syringe needle. Electrospun fibers-covered coverslips were cut off from the aluminum foil and kept for further use. Before seeding with cells, fiber samples were put into 24-well plates and sterilized by overnight UV exposure.

Fluorescamine conjugation to PCL-α-CD IC fibers

PCL and PCL-α-CD fibers on microscope coverslips (dia ~15 mm) were soaked in DMSO containing N,N′-carbonyldiimidazole (N,N′-CDI; Sigma-Aldrich) at room temperature. Ethylenediamine (Sigma-Aldrich) was added to these fibers, and after 30 min of shaking, both fibers were taken out, washed with fresh DMSO and soaked in fluorescamine-DMSO solution. After subsequent washing with fresh DMSO and water, fluorescence images of two different samples were taken on a Nikon DXM1200 microscope under both bright field and UV light.

Polystyrene nanobeads conjugation to PCL-α-CD IC fibers

PCL and PCL-α-CD fibers were soaked in N,N′-CDI/DMSO solution while undergoing shaking. After 1 h, both fibers were taken out, washed with fresh DMSO and soaked in DMSO containing polystyrene nanobeads with amine functional groups (0.2 μm dia; Invitrogen™, Life Technologies). After shaking for ~4 h, fibers were washed with ethanol to remove any unconjugated nanobeads that had settled on the fiber surface. The fibers on coverslips were placed vertically in both DMSO and ethanol to avoid any gravitational settling or physical adsorption of beads on the fibers. These fibers were vacuum dried, sputter coated (Anatech Hummer 6.2) with platinum and characterized by SEM (FEI Quanta 200).

Cell culture on nanofibers

Human adipose-derived stem cells (hADSCs) were isolated as previously described, received via a material transfer agreement, and expanded up to passage 4 before usage. For expansion, cells were cultured in a medium consisting of low glucose (1.0 g/L) DMEM supplemented with 876 mg/L of L-glutamine, 10% fetal bovine serum (FBS), 100,000 U/L penicillin, 10 mg/L streptomycin and 1 µg/L basic fibroblast growth factor (InvitrogenTM, Life Technologies). For osteogenic induction, cells were seeded onto nanofibers at a cell density of 5,000/cm2 in an osteogenic medium composed of high glucose (4.5 g/L) DMEM supplemented with 100,000 U/L penicillin, 10 mg/L streptomycin, 10% FBS, 50 µM ascorbic acid, 0.1 µM dexamethasone and 10 mM glycerol-2-phosphate disodium salt. Cells were harvested and analyzed on days 7, 14 and 21.

Gene expression

Cellular mRNAs were extracted as previously described by Strehin et al. Briefly, the mRNA was extracted with 1 mL trizol per well and then precipitated, washed with isopropanol and 75% ethanol, and redissolved in diethylpyrocarbonate-treated water (DEPC-treated water). This solution of mRNA was incubated at 60°C for 10 min and quickly put on ice. The concentration of mRNA was quantified using a NanodropTM 2000 spectrophotometer (Thermo Scientific). The cDNA was synthesized according to the manufacturer’s protocol for the Superscript 1st Strand System Kit (InvitrogenTM, Life Technologies). The cDNA was used for real-time polymerase chain reaction (PCR) with SYBR® Green PCR Master Mix (Applied Biosystems, Life Technologies) using the primers shown in Table 1 with β-actin as a reference gene. The level of expression was calculated using the Pfaffl method.

Table 1. Primer sequences for real-time PCR

Gene	Sequence (forward and reverse)	Annealing temperature
collagen type I	5′- GCCAAGAGGAAGGCCAAGTC -3′5′- AGGGCTCGGGTTTCCACAC -3′	60°C
collagen type X	5′- GGAATGCCTGTGTCTGCTTT -3′5′- TGGGTCATAATGCTGTTGCC -3′	60°C
Osteopontin	5′- GACACATATGATGGCCGAGGTGATAG -3′5′- GGTGATGTCCTCGTCTGTAGCATC -3′	60°C
Runx2	5′- CTTCACAAATCCTCCCCAAGTAGCTACC -3′5′- GGTTTAGAGTCATCAAGCTTCTGTCTGTG -3′	60°C
β-actin	5′- GCTCCTCCTGAGCGCAAGTAC -3′5′- GGACTCGTCATACTCCTGCTTGC -3′	60°C

Biochemical assays

Biochemical assays were performed using a revised version of the method described by Strehin et al. Briefly, after aspirating off media, samples were rinsed thrice with PBS, removed from the 24-well plate and lyophilized. After measuring the dry weight of the samples, they were incubated overnight at 60°C in 500 µL papainase buffer, which contained 1 M Na2HPO4, 10 mM disodium EDTA.2H2O, 10 M l-cysteine and 9.3 units/mL papain type III (Worthington Biochemical Corp.). Supernatants were collected after centrifugation and used for DNA and collagen assays.

For DNA assays, 30 µL of sample digest was mixed with 3 mL of pH 7.4 DNA buffer solution, which contained 100 µg/mL Hoechst 33258, 10 mM Tris base, 200 mM NaCl and 1 mM disodium EDTA.2H2O. The mixture was then analyzed with a DyNA Quant 200 Fluorometer (Hoefer, Inc.), with an excitation/emission of 365/460 nm. The measurements were analyzed with a calibration curve using DNA solutions made with calf thymus DNA (InvitrogenTM, Life Technologies).

For collagen assays, 100 µL of papain digest was added to 100 µL of 37% (v/v) conc. HCl and the mixture was hydrolyzed at 115°C for 18 h. Samples were neutralized with aq. NaOH and the volume was brought up to 3.5 mL with deionized water. Added to this solution (1 mL) was 0.5 mL of chloramine-T solution [69 mM chloramine-T in 89% (v/v) pH 6 buffer and 11% (v/v) isopropanol]; it was maintained at room temperature for 20 min. The pH 6.0 buffer solution contained 0.57 M NaOH, 0.16 M citric acid monohydrate, 0.59 M sodium acetate trihydrate, 0.8% (v/v) glacial acetic acid, 20% (v/v) isopropanol, 79.2% (v/v) dd H2O and 5 drops of toluene. Added to this solution was 0.5 mL of 4-(dimethylamino)benzaldehyde (pDAB) [1.17 M pDAB in 70% (v/v) isopropanol, 30% (v/v) of 60% perchloric acid in water]; and it was incubated at 60°C for 30 min. After cooling to room temperature, the samples were analyzed for their absorbance at 557 nm using a DU500 UV-Vis spectrophotometer (Beckman Coulter, Inc.) and compared with a standard solution of hydroxyproline.

Live/dead staining

Cells seeded on both fibers were stained with the LIVE/DEAD® Viability/Cytotoxicity Kit (InvitrogenTM, Life Technologies) as per the manufacturer’s protocol. Briefly, DMEM supplemented with 4 µM calcein-AM, 4 µM ethidium homodimer-1 and 4 µM Hoechst 33258 was added to cells and incubated at 37°C and 5% CO2 for 30 min. After rinsing the samples thrice with PBS, fluorescent images were taken with a Zeiss Axio optical microscope (HXP 120 fluorescent illuminator) (Carl Zeiss Microscopy). ImageJ (US National Institutes of Health) was used to merge images for further analysis.

F-actin staining

Cells were fixed with 4% paraformaldehyde for 10 min and incubated with 0.1% Triton™ X-100 at room temperature for 5 min. Subsequently, cells were rinsed with PBS, before adding 2.5% (v/v) Texas Red-X® phalloidin (200 U/mL; InvitrogenTM, Life Technologies) solution containing 4 μM Hoechst 33258. After being maintained in the dark for 30 min, samples were rinsed thrice with PBS. Images of these stained cells were taken with a Zeiss Axio optical microscope, merged and analyzed using ImageJ.

Alizarin red staining

The samples were rinsed twice with PBS after carefully aspirating off media from each well. Cells were fixed with 4% paraformaldehyde at room temperature for 15 min and rinsed thrice with deionized water. Subsequently, 1 mL of 40 mM alizarin red S solution (pH 4.1) was added to each well. Dye was aspirated off after 20 min, and fibers were rinsed thrice with distilled water. Images of the wells were taken with an Olympus C-765 camera (Olympus America).

Alkaline phosphatase (ALP) staining

Cells were rinsed with Tyrode’s balanced salt solution (TBSS, Sigma-Aldrich) twice, and fixed with a citrate-buffer acetone solution for 30 sec. The citrate-buffer acetone solution was composed of a 60% (v/v) citrate working solution and 40% (v/v) acetone. The citrate working solution was made by adding 2 mL of citrate concentrated solution (Sigma-Aldrich) to 98 mL of water. Cells were rinsed twice with PBS after removing the salt solution. One mL of fast violet-naphthol solution was added to each well, and incubated in the dark for 45 min at room temperature. Fast violet-naphthol solution was made by adding 0.5 mL of naphthol AS-MX alkaline solution (Sigma-Aldrich) to 12 mL of fast violet solution, which was made by dissolving one capsule of fast violet (Sigma-Aldrich) in 48 mL of water. Images of the stained cells were taken with an Olympus C-765 camera.

Statistical analysis

Data are expressed as mean ± standard deviation. Statistical analysis was performed using SPSS v.19 (IBM Corp.). One-way ANOVA was performed among groups to determine any statistically significant differences in values of means. Samples with equal variances and sizes were analyzed using Tukey’s post-hoc test, while the Games-Howell post-hoc test was used for samples with unequal variances and unequal sample sizes. p ≤ 0.05 was considered statistically significant.

Conclusions

In this work, we successfully electrospun PCL-α-CD nanofibers and showed the utility of the α-CD hydroxyl groups functional sites through labeling fluorescent small molecule and polymeric nanobead attachments. We also demonstrated that PCL-α-CD nanofibers supported hADSCs viability, induced a higher level of expression of osteogenic markers and enhanced production of ECM proteins or molecules, compared with control PCL fibers. We believe that by using our design approach, scaffolds based on the electrospun nanofibers with various functional groups, such as amine or carboxylic acid on the polymer chains of functionalized α-CDs, can easily be created to modulate material properties. Furthermore, cell-sensitive biological moieties can also be conjugated to and immobilized on the fibers through these functional sites.