Electrospinning is a technique used to produce micron to submicron diameter polymeric fibers. The surface of electrospun fibers is important when considering end-use applications. For example, the ability to introduce porous surface features of a known size is required if nanoparticles need to be deposited on the surface of the fiber or if drug molecules are to be incorporated for controlled release. Surface features, or pores, became evident when electrospinning in an atmosphere with more than 30% relative humidity. Increasing humidity causes an increase in the number, diameter, shape, and distribution of the pores. Increasing the molecular weight of the polystyrene (PS) results in larger, less uniform shaped pores. This work includes an investigation of how humidity and molecular weight affect the surface of electrospun PS fibers. The results of varying the humidity and molecular weight on the surface of electrospun PS fibers were studied using optical microscopy, field emission scanning electron microscopy (FESEM), and atomic force microscopy (AFM) coupled with image analysis.

The development of functionalized polymers that can elicit specific biological responses is of great interest in the biomedical community, as well as the development of methods to fabricate these biologically functionalized polymers. For example, the generation of fibrous matrices with biological properties and fiber diameters commensurate with those of the natural extracellular matrix (ECM) may permit the development of novel materials for use in wound healing or tissue engineering. The goal of this work is, therefore, to create a biologically active functionalized electrospun matrix to permit immobilization and long-term delivery of growth factors. In this work, poly(ethylene glycol) functionalized with low molecular weight heparin (PEG-LMWH) was fabricated into fibers for possible use in drug delivery, tissue engineering, or wound repair applications. Electrospinning was chosen to process the LMWH into fiber form due to the small fiber diameters and high degree of porosity that can be obtained relatively quickly and using small amounts of starting material. Both free LMWH and PEG-LMWH were investigated for their ability to be incorporated into electrospun fibers. Each of the samples were mixed with a carrier polymer consisting of either a 10 wt % poly(ethylene oxide) (PEO) or 45 wt % poly(lactide-co-glycolide) (PLGA). Field emission scanning electron microscopy (FESEM), energy-dispersive X-ray analysis (EDX), UV-vis spectroscopy, and multiphoton microscopy were used to characterize the electrospun matrices. The incorporation of heparin into the electrospun PEO and PLGA fibers did not affect the surface morphology or fiber diameters. The fibers produced had diameters ranging from approximately 100 to 400 nm. Toluidine blue assays of heparin suggest that it can be incorporated into an electrospun matrix at concentrations ranging from 3.5 to 85 mug per milligram of electrospun fibers. Multiphoton microscopy confirmed that incorporation of PEG-LMWH into the matrix permits retention of the heparin for at least 14 days. Improvements in the binding of basic fibroblast growth factor to the electrospun fibers were also observed for fibers functionalized with PEG-LMWH over those functionalized with LMWH alone. The combination of these results suggests the utility for producing electrospun fibers that are appropriately functionalized for use in biomaterials applications.

Electrospun natural polymer membranes were fabricated from collagen or gelatin coated with a bioactive recombinant fragment of perlecan, a natural heparan sulfate proteoglycan. The electrospinning process allowed the facile processing of a three-dimensional, porous fibril (2-6 microm in diameter) matrix suitable for tissue engineering. Laser scanning confocal microscopy revealed that osteoblast-like MG63 cells infiltrated the depth of the electrospun membrane evenly without visible apoptosis. Tissue engineering scaffolds ideally mimic the extracellular matrix; therefore, the electrospun membrane must contain both structural and functional matrix features. Fibers were coated, after processing, with perlecan domain I (PlnDI) to improve binding of basic fibroblast growth factor (FGF-2), which binds to native heparan sulfate chains on PlnDI. PlnDI-coated electrospun collagen fibers were ten times more effective than heparin-BSA collagen fibers at binding FGF-2. Because FGF-2 modulates cell growth, differentiation, migration and survival, the ability to effectively bind FGF-2 to an electrospun matrix is a key improvement in creating a successful tissue engineering scaffold.

The effects of molecular weight and atmospheric conditions on the electrospinning process have been investigated. Electrospun polymer microfibers with a nanoporous surface texture have been produced in the presence of humidity. The density of pores, their depth, and their shape have been shown to vary with relative humidity, molecular weight of the polymer, and solvent volatility. Although polystyrene (PS) was investigated in detail, other commodity polymers were also shown to exhibit the nanoporous surface structure under a judicious choice of spinning conditions.The effect of molecular weight on electrospun fiber formation was also studied. It was determined that sufficient chain entanglements are necessary for fiber formation. Molecular weight was also found to affect fiber diameters. Understanding the effects of molecular weight and humidity on electrsospun fibers allows for a greater understanding of how to control the electrospinning process to meet specific applications needs. Utilizing this knowledge, we have investigated the use of electrospun collagen and gelatin fibers as tissue engineering scaffolds. This study shows that cells readily attach to this unique fiber morphology.