Characterization of dielectrophoresis-aligned nanofibrous silk fibroin–chitosan scaffold and its interactions with endothelial cells for tissue engineering applications
Graphical abstract
Introduction
Natural polymers have been successfully used as scaffold materials for tissue engineering [1]. In particular, Bombyx mori silk fibroin (SF) has been investigated for surgical implantation owing to its biocompatibility, relatively low thrombogenicity, low inflammatory response, degradation kinetics, high tensile strength with flexibility, and permeability to oxygen and water [2], [3], [4]. Another polymer used as a scaffold is the naturally occurring polysaccharide chitosan (CS), a partially deacetylated product of chitin. CS, which has been applied clinically as hemostatic wound dressing [5], is generally inert in vivo, has favorable degradation kinetics and mimics the glycosaminoglycan component of the extracellular matrix (ECM). Researchers have explored blending SF and CS to develop three-dimensional (3-D) SFCS scaffolds that mimic the in vivo extracellular matrix [6], [7], [8]. In addition to their excellent biocompatibility, SFCS scaffolds have biological, structural and mechanical properties that can be adjusted to meet specific clinical needs. The first generation of SFCS scaffolds have produced promising outcomes both in vitro and in vivo in repairing abdominal wall defects, healing skin wounds and regenerating bone and tracheal cartilage [9], [10], [11], [12], [13].
In vitro studies have shown that nanofibrous structures affect cellular morphology and various cellular activities, including cell attachment, proliferation and differentiation [14]. In particular, recent studies have suggested that aligned nanostructures enhance endothelial cell capillary networks in vitro, which fulfills an important need for neovascularization in tissue engineering [15], [16]. The first generation of SFCS scaffolds were smooth sheet-like structures with microfibrillar extensions that lacked the nanofibrous architecture found in the native ECM. Various methods have been used to fabricate nanofibrous scaffolds, including electrospinning, phase separation and self-assembly [1], [17], [18].
Our laboratory previously investigated the use of dielectrophoresis (DEP) to create nanofibrous structures in SFCS scaffolds [25] by manipulating current frequency and applied voltage to generate a non-uniform electric field on a microfabricated gold electrode. The electric field resulted in movement of particles in solution on the electrode surface due to polarization effects [26]. In the presence of a field gradient, an alternating current (AC) electric field induces positive DEP force (toward the high field intensity region) or negative DEP force (toward the low field intensity region). Recent work by our group and others has shown that dielectrophoresis (DEP) is a promising technique for fabricating nanofibrous scaffolds.
DEP is a non-destructive electrokinetic mechanism with great potential for manipulation of micro- or nanoparticles such as DNA, proteins, nanotubes and nanoparticles in aqueous solutions [19], [20], [21], [22], [23], [24]. Allowing scaling for massively parallel electronic manipulation of bioparticles, DEP has become an important technique in the field of microfluidics for separating DNA, viruses and bacterial spores. Recent studies have shown that DEP can be used to align actin filaments into nanofibers in vitro [19], [24]. The previous study’s model of SF fibrils self-assembly in a 3-D SFCS scaffold using DEP was based on exposing rod-shaped particles in solution to an inhomogeneous alternating electric field, generating a time-averaged, translational DEP force due to induced dipolar effects. Small-radius (<100 nm) molecules experience DEP attraction to electrode tips even at high frequencies. Molecular assembly into solid fibers of sufficiently large radius results in a sharp decrease in crossover frequency and negative DEP. The threshold radius for which the crossover frequency drops off rapidly is determined by the suspension medium conditions. The model showed that it should be possible to concentrate and orient small-radius molecules in solution by using strong attractive DEP forces at the electrode tips and repel larger-radius fibers toward low-field regions between the electrodes in the bay region. The proposed mechanism of fiber assembly is orientation of molecules in 3-D via repulsion from two-dimensional (2-D) electrode planes due to positive DEP in high-field regions at localized electrode tips and movement away from electrode tip surface structures due to negative DEP. In addition to experimentally applying DEP to a SFCS solution to fabricate nanofibrous SFCS scaffolds and aligned structures, we studied interactions of endothelial with stem cells on these scaffolds [25].
Although our previous work provided proof of concept for using DEP to create aligned nanofibrous SFCS scaffolds, little is known about the effects of system parameters such as voltage, AC frequency and solution ionic concentration on the DEP-processed SFCS scaffolds (eSFCS). In the present study, we investigated the effects of AC frequency, sodium chloride (NaCl) presence, SF:CS ratio, and post-DEP freezing temperature on scaffold properties. We used polarized light microscopy (PLM) to analyze SF polymer chain alignment within the SFCS scaffolds and scanning electron microscopy (SEM) and atomic force microscopy (AFM) to analyze the topography of the scaffolds. The interaction of human umbilical vein endothelial cells (HUVECs) with the eSFCS scaffolds was studied using AFM and immunostaining to determine the cell mechanical properties and patterning on the eSFCS scaffolds, respectively.
Section snippets
Simulation of electric field distribution
Electrodes (200 nm thick) fabricated with gold on glass slides with triangular castellation array geometry (Fig. 1A) were connected to an AC power supply (10 Vpp sine wave). Four pieces of castellation arrays were treated as a unit for simulation. Electrical potential (V) and electrical field (E) distributions were studied by simulation using COMSOL Multiphysics 4.1 (COMSOL, Burlington, MA). The electrostatic model was applied for simulation at V0 = 10 volts based on the equations ∇·(ε0εrE) = ρv and E
Simulation of electric field distribution
Electrodes with triangular castellation arrays were used to establish a non-uniform electric field for DEP (Fig. 1). A 2-D profile of four electrode units is shown in Fig. 1B. The units shown in purple were connected to a 10 Vpp input, and the units shown in grey were grounded. The electrode structure was divided into smaller elements by creating a fine mesh (Fig. 1C). The electrostatic model was applied to simulate the electrical potential distribution and electrical field distribution. The
Discussion
In this study, PLM was utilized to examine silk fibroin polymer chain alignment on the macroscale. The relationship between polymer chain alignment and fiber alignment could be straightforwardly observed, as shown in Fig. 3. Based on PLM and SEM examination, our study revealed that, when DEP is used to fabricate nanofibrous eSFCS scaffolds, the AC frequency, presence of salt, SF:CS ratio and post-DEP freezing temperature affect SF polymer chain alignment and fibril size in the eSFCS scaffolds.
Conclusion
This study investigated the effects of AC frequency, presence of salt, SF:CS ratio and post-DEP freezing temperature on eSFCS scaffold properties. Endothelial cell interactions with eSFCS scaffolds were studied to understand vascular guidance via biomaterial surfaces. The eSFCS (50:50) samples prepared at 10 MHz with NaCl had the highest percentage of aligned area than scaffolds prepared with other SFCS ratios and DEP frequencies. As DEP frequency increased from 100 kHz to 10 MHz, fibril sizes
Acknowledgements
This study was supported by a NIH grant (R01AG034658) and by the Gillson-Logenbaugh Foundation. We thank Dr. S. Hudson (North Carolina State University) for donating raw silk. We thank the core facility at MD Anderson Cancer Center: High Resolution Electron Microscopy Facility (supported by Cancer Center Core Grant CA16672) for SEM imaging and the Flow Cytometry and Cellular Imaging Facility for confocal imaging.
References (36)
- et al.
Biodegradable polymer matrix nanocomposites for tissue engineering: a review
Polym Degrad Stab
(2010) - et al.
Engineering adipose-like tissue in vitro and in vivo utilizing human bone marrow and adipose-derived mesenchymal stem cells with silk fibroin 3D scaffolds
Biomaterials
(2007) - et al.
Silk fibroin microtubes for blood vessel engineering
Biomaterials
(2007) - et al.
Chitin and chitosan polymers: chemistry, solubility and fiber formation
Prog Polym Sci
(2009) - et al.
Perichondrium directed cartilage formation in silk fibroin and chitosan blend scaffolds for tracheal transplantation
Acta Biomater
(2011) - et al.
Polymer nanofibrous structures: fabrication, biofunctionalization, and cell interactions
Prog Polym Sci
(2010) - et al.
Endothelial, cardiac muscle and skeletal muscle exhibit different viscous and elastic properties as determined by atomic force microscopy
J Biomech
(2001) - et al.
Three-dimensional aqueous-derived biomaterial scaffolds from silk fibroin
Biomaterials
(2005) - et al.
Conformation transition kinetics of regenerated Bombyx mori silk fibroin membrane monitored by time-resolved FTIR spectroscopy
Biophys Chem
(2001) - et al.
Matrix elasticity directs stem cell lineage specification
Cell
(2006)
Porous silk fibroin 3-D scaffolds for delivery of bone morphogenetic protein-2 in vitro and in vivo
J Biomed Mater Res
Structural and mechanical characteristics of silk fibroin and chitosan blend scaffolds for tissue regeneration
J Biomed Mater Res
Preparation and cytocompatibility of silk fibroin/chitosan scaffolds
Front Mater Sci Chin
Novel genipin-cross-linked chitosan/silk fibroin sponges for cartilage engineering strategies
Biomacromolecules
IFATS collection: human adipose-derived stem cells seeded on a silk fibroin–chitosan scaffold enhance wound repair in a murine soft tissue injury model
Stem cells
Repair and regeneration of the abdominal wall musculofascial defect using silk fibroin–chitosan blend
Tissue Eng
GNAS1 and PHD2 short-interfering RNA support bone regeneration in vitro and in an in vivo sheep model
Clin Orthop Relat Res
In vivo bone formation in silk fibroin and chitosan blend scaffolds via ectopically grafted periosteum as a cell source: a pilot study
Tissue Eng Part A
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