1Materials Science and Engineering, University of Sheffield, 2Department of Biomedical Science, University of Sheffield, 3Department of Chemistry, University of Sheffield
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Bye, F. J., Wang, L., Bullock, A. J., Blackwood, K. A., Ryan, A. J., MacNeil, S. Postproduction Processing of Electrospun Fibres for Tissue Engineering. J. Vis. Exp. (66), e4172, doi:10.3791/4172 (2012).
Electrospinning is a commonly used and versatile method to produce scaffolds (often biodegradable) for 3D tissue engineering.1, 2, 3 Many tissues in vivo undergo biaxial distension to varying extents such as skin, bladder, pelvic floor and even the hard palate as children grow. In producing scaffolds for these purposes there is a need to develop scaffolds of appropriate biomechanical properties (whether achieved without or with cells) and which are sterile for clinical use. The focus of this paper is not how to establish basic electrospinning parameters (as there is extensive literature on electrospinning) but on how to modify spun scaffolds post production to make them fit for tissue engineering purposes - here thickness, mechanical properties and sterilisation (required for clinical use) are considered and we also describe how cells can be cultured on scaffolds and subjected to biaxial strain to condition them for specific applications.
Electrospinning tends to produce thin sheets; as the electrospinning collector becomes coated with insulating fibres it becomes a poor conductor such that fibres no longer deposit on it. Hence we describe approaches to produce thicker structures by heat or vapour annealing increasing the strength of scaffolds but not necessarily the elasticity. Sequential spinning of scaffolds of different polymers to achieve complex scaffolds is also described. Sterilisation methodologies can adversely affect strength and elasticity of scaffolds. We compare three methods for their effects on the biomechanical properties on electrospun scaffolds of poly lactic-co-glycolic acid (PLGA).
Imaging of cells on scaffolds and assessment of production of extracellular matrix (ECM) proteins by cells on scaffolds is described. Culturing cells on scaffolds in vitro can improve scaffold strength and elasticity but the tissue engineering literature shows that cells often fail to produce appropriate ECM when cultured under static conditions. There are few commercial systems available that allow one to culture cells on scaffolds under dynamic conditioning regimes - one example is the Bose Electroforce 3100 which can be used to exert a conditioning programme on cells in scaffolds held using mechanical grips within a media filled chamber.4 An approach to a budget cell culture bioreactor for controlled distortion in 2 dimensions is described. We show that cells can be induced to produce elastin under these conditions. Finally assessment of the biomechanical properties of processed scaffolds cultured with or without cells is described.
1. Electrospinning of Random and Aligned Fibres
Electrospinning creates fine fibrous networks by using electric potential to draw a polymer solution towards an earthed collector. Collectors can be in very many shapes and can be static or, more commonly, rotating. The solvent evaporates before the solution arrives at the collector and the jet solidifies into a fibre.
Each polymer requires its own set of conditions to produce a given type of fibre. The concentration of the polymer, the solvent, the distance between the pumped solution and the earthed collector, the potential difference between the two, the velocity of the rotating collector, the flow rate, temperature and humidity will all affect electrospinning. There are many studies describing the selection of electrospinning parameters and how these impact on the scaffolds produced (e.g. fibre diameter, morphology, and orientation).5, 6, 7, 8 In these experiments scaffolds were spun based on conditions selected in our previous studies.2, 9
The following methods are suitable for the production of electrospun scaffolds from PLGA, poly lactic acid (PLA), poly ε-caprolactone (PCL) and poly hydroxybutyrate-co-hydroxyvalerate (PHBV) using a rotating collector as shown in Figure 1. Throughout the solvent dichloromethane (DCM) is used. The method here produces microfibrous PLGA, PLA and PCL and nanofibrous PHBV scaffold with micro-sized beads ('pearl necklace' morphology).
2. Production of Complex Scaffolds by Sequential Spinning
Sequential spinning provides a method of combining the properties of different materials to create a material that has the best of both properties. PHBV produces a flat, dense, brittle sheet whereas PLA or PCL spinning produces low density elastic sheets. Both materials support cell attachment. Consecutively spinning these materials results in a dense cell-impermeable membrane that is elastic.
3. Production of Multilayered Scaffolds by Annealing Several Layers Together
4. Aseptic Production and Postproduction Sterilisation of Electrospun Scaffolds
5. Biomechanical Testing of Scaffolds
6. Visualising Cells on Scaffolds and Assessing ECM Production
Cells can be stained with vital fluorescent dyes which allow one to see cells on the scaffolds as they attach, migrate and proliferate. Post culture the presence of cells on scaffolds can be determined by staining for cell nuclei with 4',6-diamidino-2-phenylindole dihydrochloride (DAPI). The production of ECM by cells on the scaffold can be assessed by staining cells for a range of ECM proteins including elastin as shown in this example. All scaffolds used were measured to have a thickness of at least 0.2 mm and cut into squares 1.5 cm x 1.5 cm prior to seeding.
In these studies human dermal fibroblasts are used throughout because of the role they play in soft tissue reconstruction which is our laboratory's primary research interest.
Cells are obtained from skin samples from patients undergoing elective surgery for breast reduction or abdominoplasty (consent was given for their tissue to be used for research purposes). Tissues are collected and used anonymously under Research Tissue Bank Licence 12179. Tissues are washed with PBS containing streptomycin (0.1 mg/ml) and penicillin (100 IU/ml) and amphotericin B (0.5 μg/ml). Tissue samples are incubated in 0.1% w/v trypsin and 0.1% glucose in PBS (12-18 hours, 4 °C). The dermis is peeled off, minced finely and incubated with 10 ml of collagenase (0.5% w/v in DMEM and 10% FCS, 37 °C for 18 hours). Centrifugation of the resulting cell suspension (400 g for 10 mins), produces a pellet of cells that can be cultured and subcultured in DMEM supplemented with fetal calf serum (FCS, 10% v/v), streptomycin (0.1 mg/ml), penicillin (100 IU/ml) and amphotericin B (0.5 μg/ml). Only fibroblasts of passage 4-9 are used in experiments.
7. Subjecting Cells on Scaffolds to Biaxial Dynamic Conditioning
To examine the effect of dynamic conditioning on fibroblast ECM production we developed a simple proof-of-concept bioreactor to explore this.
8. Representative Results
The following figures are representative results that can be expected if the above methods are followed.
Electrospinning can be utilised to create scaffolds with random and ordered architectures (Figure 1), this is repeatable and the fibres are uniform. Many types of polymers can be electrospun with characteristics which can vary considerably as shown in Figure 2 for PHBV, PLA or PCL. Electrospinning can produce light fluffy scaffolds or dense cell impenetrable membranes (see Figure 3). All scaffolds shown here facilitated cell attachment and proliferation. Previous work has shown that cells can migrate through these scaffolds up to a depth of at least 500-600 μm.9 For PLA the average fibre diameter is 3 μm; for PHBV it is 0.3μm with pearls ranging from 5-20 μm; for PCL it is 3 μm; and for PLGA it is 11 μm. Other studies using other solvent systems report that PHBV can be electrospun as fibres without beads or polymer pearls.10,11
If thicker scaffolds are required vapour and heat annealing can be employed to anneal layers of scaffolds together (see Figure 4). These scaffold layers do not delaminate and it can be very difficult to find the junction between layers.
We show that bilayer membranes can be made where cells A and B can each be cultured on a separate membrane without intermingling as shown in Figure 5. Here we demonstrate this by using human dermal fibroblasts coloured with two different fluorescent cell tracker dyes. Such a bilayer membrane would be useful when culturing cells to form a hard tissue such as bone or cartilage on one side separated from cells designed to form a soft (and usually faster growing) tissue on the other side such as cleft palate repair or reconstructive periodontal surgery.12, 13
With respect to the impact of sterilisation on electrospun scaffolds we have previously reported that the method of sterilisation impacts on the scaffold and subsequent cell culture.9 This is illustrated in Figure 6 which shows the effects of peracetic acid, gamma irradiation and ethanol on the fibre diameter and ultimate tensile strength and Young's modulus of a PLGA scaffold.
Gamma irradiation has no significant effect on fibre diameter whereas peracetic acid and ethanol reduce fibre diameter by approximately 50%. With respect to ultimate tensile strength each of the methods of sterilisation changed the ultimate tensile strength and the elasticity of the scaffolds. Culture of cells on these scaffolds further reduced the ultimate tensile stress, but increased the elasticity.
Finally, a method of testing the effect of dynamic biaxial distension on cells cultured on electrospun scaffolds is presented. This proof-of-concept approach shows that cells remain viable during dynamic distension but also produce increased amounts of elastin under these conditions. This contrasts markedly to the lack of elastin when the same cells on the same scaffold are maintained under static conditions (see Figure 7).
Figure 1. Shows a cartoon of an electrospinning rig and of the spinning of random and parallel fibres and then layers of fibres placed over each other. Perpendicular fibres can be created by electrospinning a set of aligned fibres onto aluminium foil, rotating the foil by 90° and then immediately electrospinning a second set of aligned fibres on top of these.
Figure 2. Shows the morphology of random electrospun mats of (A) PLA (scale bar is 100 μm), (B) PHBV (scale bar is 100 μm), (C) PCL (scale bar is 100 μm) and (D) PLGA (scale bar is 200 μm). Note that PLA, PCL and PLGA are all microfibrous uniform scaffolds. PHBV is spun as a 'pearl necklace' with nanofibres connecting 5-20 μm sized beads. Click here to view larger figure.
Figure 3. Production of a multilayered scaffold. Here the scaffolds are initially spun using PHBV and then syringes filled with PLA or PCL are used. These are spun on top of the PHBV scaffold. The figure shows the appearance of these multilayered scaffolds, (A) A single PHBV layer, (B) A cross section of a PHBV-PLA bilayer, showing the dense nanofibrous, 'pearl necklace' PHBV layer (left) and more open microfibrous PLA layer (right) and (C) A single PLA layer. Click here to view larger figure.
Figure 4. Thicker scaffolds can be produced by heat annealing and vapour annealing. (A) and (B) show a section through a vapour annealed PLA scaffold where initial fibrous scaffolds of approximately 150 μm are been placed together and dichloromethane vapour is used to make much thicker scaffolds of up to 500 μm. In (C) and (D) one can see that the scaffold consists of layers of much thicker fibres interspersed with layers of thinner fibres created by heat annealing layers of thin and thick fibres together. This approach can be used to produce scaffolds of complex mechanical properties. Click here to view larger figure.
Figure 5. Appearance of cells on a bilayer scaffold. In all cases the cells present are human dermal fibroblasts. (A) Fibroblasts on electrospun PLA where the cells are fixed and stained with DAPI. (B) DAPI stained cells on PHBV. In (C) the fibroblasts are pre-stained with a vital dye, CellTracker green, and you can see the appearance of them on the PLA side of the bilayer. (D) A section through the bilayer with red stained fibroblasts on the lower PHBV surface and green stained fibroblasts on the upper PLA surface. (E) Fibroblasts pre-stained with CellTracker red grown on the PHBV surface. The use of vital fluorescent dyes provides a convenient methodology for looking at the distribution of cells on the scaffold while the cells are still growing. One can routinely use these dyes for at least 7 days. However the concentration of dye becomes diluted as the cells divide. Scale bars are equal to 0.1 mm.
Figure 6. Biomechanical properties of electrospun scaffold are obtained using a Bose Electroforce tensiometer device (A). (B) Stress/strain curves of PLGA scaffolds sterilised by gamma irradiation, alcohol, peracetic acid, or aseptically produced. Three measurements can be obtained from such a graph: the ultimate tensile stress (UTS) to which the fibre can be subjected before it breaks, the ultimate tensile strain and the Young's modulus. The latter gives an indication of the elasticity of the scaffold. (C) The effect of each sterilisation method on PLGA fibre diameter in μm. Each sterilisation methodology decreased UTS. Both peracetic acid and gamma irradiation decrease the Young's modulus giving a more elastic scaffold, alcohol makes the scaffold particularly brittle. Click here to view larger figure.
Figure 7. This figure shows the use of a simple balloon to provide a biaxial bioreactor on which scaffolds (and cells growing within the scaffolds) can be subjected to biaxial distension for periods of time. (A) A deflated balloon onto which electrospun fibres, PHBV, have been deposited. At this stage the balloon is partially covered with fibres. (B) A balloon fully coated with PHBV and PLA fibres. (C) A cell suspension is repeatedly pipetted onto the balloon. (D) A balloon placed within a bottle of sterile media where the balloon is connected to a syringe pump and PBS (used as a conducting electrolyte) is used to gently inflate and allow deflation of the balloon against a programmed schedule. (E) Cells on scaffolds being removed from the balloon at the end of the experiment and analysis undertaken for cell viability shown in (F) where viable cells develop a dark blue colour using the metabolic indicator 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide. (G) Shows that cells (blue) cultured on this balloon and subject to biaxial distension develop elastin fibres (green, stained using elastin specific antibodies), whereas the same cells on an identical scaffold (H) cultured under static conditions have negligible elastin production. Scale bars are equal to 0.025 mm.
Electrospinning is a very popular technique for producing scaffolds for tissue engineering.14, 15, 16 While it is relatively simple to produce basic electrospun scaffolds for experimental use the technique is also complex and multifaceted with many variables.6 There are many studies describing how the electrospinning parameters determine the scaffold produced. In this study the focus is on the considerable challenges post production to make scaffolds of appropriate architectures and mechanical properties and to encourage cells within them to make extracellular proteins to achieve tissue fit for implantation in man.
Our aim in this article is to describe methods to equip readers to design and characterise scaffolds for a wide range of purposes. In this article we describe methodologies to make complex and thicker scaffolds and to sterilise scaffolds for experimental and clinical use. We also describe imaging cells on the scaffolds and the induction of elastin fibre production by subjecting cells to biaxial distension.
Many of the desired features of scaffolds can be achieved post production (such as annealing several layers) and sterilisation. However these in turn will affect the mechanical properties of scaffolds. We report that sterilisation methodologies all tend to change ultimate tensile strength and Young's modulus to varying extents. A recent study from our group compared gamma irradiation, peracetic acid and ethanol for their effects as potential sterilising regimes for PLGA scaffolds.9 The adverse effects of sterilisation techniques can be avoided by producing scaffolds under aseptic conditions - the latter requires the use of a cleanroom. Different users may select different methodologies but all should be aware that current sterilisation methodologies will impact negatively on the properties of the scaffolds.
Culture of cells on scaffolds also affects the scaffolds' mechanical properties. Induction of ECM production by subjecting cells on scaffolds to biaxial distension may be used to affect the mechanical properties.
The methodology of spinning one scaffold over another to make a bilayer membrane is easily understood and we describe bilayer scaffolds capable of supporting two diverse populations of cells illustrated in this paper by pre-labelling cells with two vital cell tracker dyes. These were used to illustrate that the bilayer membrane achieved its stated purpose.
Finally the budget biaxial distension rig described in this study can be used to deliver a range of regimes. Cyclic, linear, and random regimes can be readily programmed and applied. This versatility will allow the system to be utilised for many of the problems faced in tissue engineering such as, cleft palate, pelvic floor, bladder, and skin.
In the tissue engineering literature the use of uniaxial testing systems for culturing cells on scaffolds has been reported.4 However we were unable to find any published literature dealing with how soft tissues respond to biaxial distension. This simple approach demonstrates that cells respond to biaxial distension with the production of elastin - a key component of the extracellular matrix which gives soft tissues elastic recoil. This gives a clear indication of how conditioning soft tissues as they grow in the laboratory offers a route to produce tissues appropriate for implantation for areas of the body where the native tissues have intrinsic elasticity. This is an area where further development will clearly be merited by the tissue engineering community and bioreactor manufacturers.
No conflicts of interest declared.
We thank BBSRC for funding a PhD for Mr. Frazer Bye.
|Poly lactic-co-glycolic acid||Sigma Aldrich|
|Poly lactic acid||Sigma Aldrich||81273||Inherent viscosity ~2.0dl/g|
|Poly ε-caprolactone||Sigma Aldrich|
|Poly hydroxybutyrate-co-hydroxyvalerate 12:1||Goodfellow||578-446-59||PHB88/PHV12|
|Dichloromethane||Sigma Aldrich or Fisher||270997 or D/1850/17||>99.8% contains 50-150ppm amylene stabiliser|
|50 multi coloured balloons||Wilkinson’s Hardware Stores Ltd.||0105790|
|Goat anti-rabbit IgG (FC):FITC||AbDserotec||STAR121F|
|Rabbit anti-human alpha elastin||AbDserotec||4060-1060|
|Screw Cap GL45 PP 2 Port, pk/2||SLS||1129750|
|4′,6-Diamidino-2-phenylindole dihydrochloride||Sigma Aldrich||32670|
|CellTracker green CMFDA||Invitrogen||C7025|
|CellTracker red CMTX||Invitrogen||C34552|