Expansion of Two-dimension Electrospun Nanofiber Mats into Three-dimension Scaffolds

Summary

This article demonstrates the technique of expanding a traditional, two-dimension (2D) electrospun nanofiber mat into a three-dimension (3D) scaffold through the depressurization of subcritical CO₂ fluid. These augmented scaffolds are 3D, closely mimic cellular nanotopographic cues, and preserve the functions of biologic molecules encapsulated within the nanofibers.

Abstract

Electrospinning has been the preferred technology in producing a synthetic, functional scaffold due to the biomimicry to extracellular matrix and the ease control of composition, structure, and diameter of fibers. However, despite these advantages, traditional electrospun nanofiber scaffolds come with limitations including disorganized nanofiber orientation, low porosity, small pore size, and mainly two-dimensional mats. As such, there is a great need for developing a new process for fabricating electrospun nanofiber scaffolds that can overcome the above limitations. Herein, a novel and simple method is outlined. A traditional 2D nanofiber mat is transformed into a 3D scaffold with desired thickness, gap distance, porosity, and nanotopographic cues to allow for cell seeding and proliferation through the depressurization of subcritical CO₂ fluid. In addition to providing a scaffold for tissue regeneration to occur, this method also provides the opportunity to encapsulate bioactive molecules such as antimicrobial peptides for local drug delivery. The CO₂ expanded nanofiber scaffolds hold great potential in tissue regeneration, wound healing, 3D tissue modeling, and topical drug delivery.

Introduction

The concept of developing a synthetic scaffold that can be implanted into patients to aid in tissue repair and regeneration is one that has permeated the regenerative medicine field for decades. The ideal synthetic scaffold serves to induce cell migration from surrounding healthy tissue, provides an architecture for cell seeding, adhesion, signaling, proliferation, and differentiation, supports vascularization, allows for adequate oxygenation and nutrition delivery, and promotes host immune activity to ensure success after implantation¹. Additionally, it can be used as a carrier for embedding antimicrobial molecules to assist in wound healing^1,3,6,7,8,9. The ability to control the temporal release of these biologic molecules from the synthetic scaffold is another desirable attribute that is considered when engineering scaffolds¹.

Electrospinning has been a well-utilized technique for producing nanofiber scaffolds^1,2,3,4,5,6. Previous attempts to create a nanofiber scaffold such as the one discussed here have been done to varying degrees of success. However, traditional nanofiber scaffolds have limited abilities to achieve these goals. Traditional nanofiber scaffolds have been mostly two-dimensional mats^1,3. These nonexpanded scaffolds are densely packed with small pore sizes; this limits cell infiltration, migration, and differentiation as it does not promote an environment similar enough to those found in vivo^1,7,8,9. For this reason, newer techniques of 3D electrospun nanofiber scaffold preparation have been established to amend the inherent flaws that come with 2D nanofiber mats. These techniques result in 3D scaffolds; however, they have limited applicability due to the production methods requiring aqueous solutions and freeze-drying procedures. This processing results in the random distribution of the nanofibers without restricted organization, proper thickness, and/or desired porosity to provide the adequate nanotopographic cues that are necessary for cell migration and proliferation. These factors result in the previous 3D electrospun nanofiber scaffolds that lack adequate mimicry of living tissues^1,7,8,9.

More recent attempts at developing an expanded, 3D scaffold with better biomimicry of extracellular matrix (ECM) have been performed using an aqueous sodium borohydride (NaBH₄) solution treatment and predesigned molds to aid in better control of the shape of the resulting scaffold^7,8. However, this method is not ideal as it requires the use of aqueous solutions, chemical reactions, and freeze-drying that may interfere with polymers and any encapsulated biomolecules that are water-soluble. The additives used may also cause side effects during tissue regeneration^8,9. The CO₂ expansion method outlined in this article greatly reduces processing time, eliminates the need for aqueous solutions, and preserves the amount and functionality of biologically active molecules to a greater extent than the previously established methods⁹.

In previous studies, antibiotics, silver, 1α,25 dihydroxyvitamin D₃, and antimicrobial peptide LL-37 were loaded into the nanofiber scaffolds individually and in combination to investigate the potential of these scaffolds to release agents to further aid in wound healing^9,10,12,13. For the purpose of demonstrating this method of nanofiber scaffold expansion, Coumarine 6, a fluorescent dye, will be loaded into the scaffold to demonstrate the potential of embedding the scaffold with various desired compounds. This method of expanded nanofiber scaffold fabrication in conjunction with encapsulated bioactive molecules holds great potential in tissue regeneration, wound healing, the creation of 3D tissue models, and the topical delivery of drugs.

Protocol

All in vivo procedures outlined below were approved by the IACUC Committee at the University of Nebraska Medical Center.

1. Prepare the Solutions for Standard Electrospinning

1. In a 20 mL glass tube, dissolve 2 g of poly(ε-caprolactone) (PCL, Mw= 80 kDa) in a solvent mixture of dichloromethane (DCM) and N,N-dimethylformamide (DMF) with a 4:1 ration (v/v) at a concentration of 10% (w/v).
   CAUTION: Handle DCM and DMF in a well-ventilated hood to avoid exposure to fumes. Do not expose DCM to plastic materials.
2. Place the glass tube into a lab rotator until the solution becomes clear. The solution may mix overnight.
3. If intending to embed bioactive materials such as peptides or drugs into the scaffold, create a separate solution and store at the 4 °C until ready to use.
   1. Prepare the fluorescent dye solution (50 μg/mL) using 20 mL of PCL solution.

2. Set Up the Electrospinning Apparatus (Figure 1A)

1. Add the PCL solution to a 20 mL syringe with a 21 gauge blunt needle attached. Ensure that there is no air in the syringe and associated tubing.
2. Place a rotating steel drum with the ground collector 12 cm from the needle tip.
3. Using alligator clips, connect the Direct Current (DC) High Voltage power supply to the needle and ensure that the collector is grounded.
   CAUTION: Always turn off the power supply before handling any connected materials.

3. Electrospinning

1. For the 20 mL of PCL solution, set the parameters of the syringe pump as follows: diameter = 20.27 mm, flow rate = 0.5 mL/h. Check if the droplets are forming at the tip of the needle.
2. If the incorporation of bioactive molecules is desired, set up the apparatus to allow for co-axial electrospinning (Figure 1B). Create a customized coaxial nozzle using hypodermic needles.
   NOTE: Such nozzles are also available commercially. Note that a solution of dye is prepared to simulate the adding such molecules.
   1. Prepare a 1% solution of the fluorescent dye Coumarin 6 in water. Add 3 mL of the 1% dye to a small syringe. Connect the syringe to the same coaxial nozzle as the PCL solution. Once again, ensure that there are no air bubbles.
   2. For this 3 mL solution, set the parameters of the syringe pump as follows: diameter = 9.49 mm, flow rate = 0.02 mL/h. Check if the droplets are forming at the tip of the needle.
3. Apply an electric potential of 20 kV between the spinneret (22-gauge needle) and a ground collector located 20 cm away from the spinneret. Collect the aligned nanofiber mats in a drum rotating at 2,000 rpm. Collect the PCL nanofiber mats once they reach a thickness of ~1 mm.

4. Generation of PCL Nanofiber Mats with Arrayed Holes.

1. Fabricate PCL nanofiber mats.
   1. Dissolve PCL beads in a solvent mixture consisting of DCM and DMF with a ratio of 4:1(v/v) at a concentration of 10% (PCL) (w/v). Pump the PCL solution at a flow rate of 0.7 mL/h using a syringe pump while a potential of 20 kV is applied between the spinneret (a 22-gage needle) and a grounded collector located 12 cm apart from the spinneret.
   2. Collect the nanofiber membrane using a rotating drum with a rotating speed larger than 500 rpm.
2. Immerse the PCL nanofiber mats in liquid N₂ for 5 min (i.e., become stiff). Keep the PCL nanofiber mats in liquid N₂ and punch PCL nanofiber mats with a 0.5 mm-diameter punch.

5. Expansion of 2D Nanofiber Mats with/without Arrayed Holes via Subcritical CO₂ Liquid (Figure 2).

1. Place the PCL nanofiber mats into liquid nitrogen for 5 min and cut into 1 cm x 1 cm squares using sharp surgical scissors while submerged in liquid nitrogen to avoid deformation of the edges.
2. Place the cut mat in a 30 mL centrifuge tube with ~1 g of dry ice. Tightly cap the lid and allow for the dry ice to change into liquid CO₂.
3. Once liquid has formed in the tube, quickly release the pressure by opening the cap.
   CAUTION: Use proper thermal protective gear when working with liquid nitrogen and dry ice. Do not open the pressurized tube towards the face. The centrifuge tube should not be used repeatedly.
4. Remove and observe the puffed scaffold from the tube. Place the scaffold in a new centrifuge tube with dry ice and repeat until the desired thickness is achieved. Sterilize the expanded nanofiber scaffolds in ethylene oxide prior to incubation with cells.

6. Characterization of Expanded Nanofiber Scaffolds

1. Characterize the morphology and structure of the expanded nanofiber scaffolds using scanning electron microscopy (SEM).
   1. Place the samples with double-sided conductive tape to the metallic stud and coat with platinum for 40 s using a sputter coater at 40 mA.
   2. Examine the fibers using SEM according to previous studies⁹. Collect the images at an accelerating voltage of 15 kV.
2. Characterize in vitro release profiles and bioactivity of released peptides.
   1. Weight 10 mg of nanofiber membranes before and after the expansion in CO₂.
   2. Immerse the samples in PBS buffer and collect 10 μL of supernatant at different time points (0-28 days).
   3. Use Enzyme-Linked Immuno Sorbent Assay (ELISA) kit to quantify the LL-37 peptide concentration in the collected supernatant.
3. Examine cellular infiltration in vivo and host response.
   1. Put the 9-week old Sprague-Dawley (SD) rats in an anesthesia chamber, connect to isoflurane vapor and anesthetize the rats. Transfer the rats to an operating table after the rats become complete anesthesia without feelings. Continuously anesthetize the rats using an isoflurane-nose cone with vaporizer during the surgery. Shave the hair of rat’s backs by an animal’s shaver and sterilize it with iodine and alcohol skin scrub. Create subcutaneous pockets via 1.5 cm incisions at supraspinal sites on the dorsum using a scalpel.
   2. Insert one expanded nanofiber scaffold (1.5 mm-thick) into the subcutaneous pocket using tweezers for each incision. Close the incision using a stapler.
   3. At 1, 2, and 4 weeks, euthanize the rats with 95% CO₂. Gently dissect the explant and the surrounding tissue using surgical scissors. Prior to histological analysis, immerse the tissue in formalin for at least 3 days, and then embed with paraffin. Section the tissue with a microtome, then perform hematoxylin and eosin (H&E), Masson’s trichrome staining.

Results

The efficacy of expanding traditional 2D electrospun nanofiber mats into 3D scaffolds via depressurization of subcritical CO₂ fluid was demonstrated in different capacities: the thickness of the scaffolds increased from 1 mm when untreated to 2.5 mm and 19.2 mm with one and two CO₂ treatments, respectively (Figure 3A-C). The porosity-a characteristic of the architecture critical for cell seeding-also increased in a manne...

Discussion

Transforming traditional 2D electrospun nanofiber mats into expanded 3D scaffolds via CO₂ depressurization was investigated. Traditional 2D nanofiber mats are successfully expanded via subcritical CO₂ fluid. The critical steps are to fabricate 2D nanofiber mats under an optimized condition and cut the mats without deforming the edges (e.g., using sharp surgical scissors). This CO₂-expanded nanofiber scaffolds have many benefits over traditional 2D mats including...

Materials

List of materials used in this article

Name	Company	Catalog Number	Comments
Polycaprolactone	Sigma-Aldrich	440744
N,N-Dimethlyformamide	Fisher Chemical	D-199-1
Dichloromethane	Fisher Chemical	AC61093-1000
Coumarin 6	Sigma-Aldrich	546283
Rotating Steel Drum	customized		This serves as a collector during electrospinning.
Syringe Pump	Fisher Scientific	14-831-200	Coaxial spinning requires two single syringe pumps.
Revolver	Lab Net International	H5600	Adjustable lab rotator for mixing solutions
Hypodermic Needle (27G x 1 1/2")	EXCELINT International Co	26426	This is part of the example customized coaxial nozzel shown.
Hypodermic Needle (21G x 1 1/2")	EXCELINT International Co	26416	This is part of the example customized coaxial nozzel shown.
High Voltage DC Power Supply	Gamma High Voltage Research	ES30
Scanning Electron Microscope	FEI	Nova 2300
Fluorescence Microscope	Zeiss	Axio Imager 2
LL 37 ELISA Kit	Hycult Biotech	HK321-02