Name: Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules (Video) | JoVE Journal
Uploaded: 2015-08-19T14:00:00.000+00:00
Duration: 11 min 13 s
Description: Learn to create composite scaffolds using interfacial polyelectrolyte fibers for controlled biomolecule release in tissue engineering. This method enables sustained delivery of growth factors with spatial precision.

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This work was supported by the Singapore National Research Foundation administered by one of its Research Centers of Excellence, the Mechanobiology Institute, Singapore. MFAC is supported by the Agency for Science, Technology and Research (Singapore) and National Agency for Research (France) joint program under project number 1122703037. BKKT is supported by the Mechanobiology Institute. We thank Mr. Daniel HC Wong for proof-reading the manuscript and Ms. Dawn JH Neo for assisting in the video production.

1. Preparation of Polyelectrolyte Solutions
<ol>
	<li>Purify chitosan, as detailed in Liao et al. Briefly, create a 1% (w/v) solution of chitosan in 2% (v/v) acetic acid and vacuum filter using grade 93 filter paper. Neutralize the filtrate using 5M NaOH until the pH stabilized to 7. Centrifuge the precipitated chitosan at 1,200 x g for 10 min. Decant the supernatant and add deionized water to wash the chitosan. Repeat the centrifugation and washing step two more times. Freeze the precipitated chitosan at -80 &#176;C and lyophilize O/N to obtain the purified form. Store purified chitosan in a dehumidified cabinet.</li>
	<li>Weigh out 1 g of purified chitosan into a sterile tissue culture dish. Place the chitosan in the tissue culture dish as close as possible to the UV lamp in the biological safety cabinet and expose to UV light for 15 min. Using sterile forceps, place the sterilized chitosan into a glass container. Dissolve chitosan using filtered 0.15M acetic acid to a final concentration between 0.5% and 1% (w/v).</li>
	<li>Weigh out 0.1 g of alginic acid sodium salt and dissolve in 10 ml distilled deionized (DDI) water to obtain a 1% (w/v) solution. Mix the alginic acid sodium salt for at least 2 hr on the vortex mixer to ensure complete dissolution. Filter the alginate solution through 0.2 &#181;m syringe filter. Store the alginate solution at 4 &#176;C.</li>
	<li>Reconstitute human recombinant growth factors such as vascular endothelial growth factor (VEGF) or beta - nerve growth factor (NGF), as recommended by manufacturer.</li>
</ol>
2. Drawing of IPC Fibers
<ol>
	<li>Mix proteins, growth factors or other biomolecules into 10-20 &#181;l aliquot of the polyelectrolyte solution that has a similar net charge. Biological molecules with net negative charge (eg bovine serum albumin [BSA]) should be mixed with alginate solution. Biological molecules with net positive charge (eg VEGF) should be mixed with chitosan solution.</li>
	<li>Place small aliquots (10-20 &#181;l) of chitosan and alginate on a stable flat surface that is covered with parafilm. The droplets of chitosan and alginate should be placed in close proximity but not in contact with each other.</li>
	<li>Lightly dip each tip on a pair of forceps into the chitosan and alginate droplets. Bring the droplets of polyelectrolytes together by pinching the forceps. When the droplets come into contact with each other, slowly pull the forceps vertically upward to draw the IPC fiber from the interface of the two droplets (Figure 1A).</li>
	<li>Carefully place the end of the drawn IPC fiber on the forceps on a collector, such as a flat polymeric scaffold affixed on a rotating mandrel (see section 3 and 4). Rotate the mandrel at a fixed speed of 10 mm/sec to allow formation of uniform and beadless IPC fibers. Increasing the speed of drawing the IPC fibers will form beads, which will cause a burst release of incorporated biochemical and premature fiber termination.10</li>
	<li>To determine incorporation efficiency, collect all the remaining liquids left on the parafilm by diluting with 500 &#181;l of 1X phosphate buffered saline (PBS). Measure the protein or growth factor content in the residue through BCA assay (for BSA), ELISA (for VEGF and NGF) or an appropriate assay to detect incorporated biomolecule.</li>
</ol>
3. Fabrication of&#160;Composite&#160;Hydrogel Scaffold of Pullulan-Dextran (PD) Polysaccharide and IPC Fibers
<ol>
	<li>Fabricating sacrificial pullulan frame for IPC fiber collection
	<ol>
		<li>Weigh out pullulan polysaccharide and mix with distilled deionized (DDI) water to create a 20% (w/v) aqueous solution. Mix the pullulan solution O/N to ensure homogeneity.</li>
		<li>Cast 15 g of pullulan solution into a 10&#160;cm diameter tissue culture polystyrene (TCPS) dish. Dry the pullulan solution O/N at 37&#160;&#176;C. Cut the pullulan films into 7 mm x 7 mm square frames.</li>
	</ol>
	</li>
	<li>Preparing pullulan-dextran polysaccharide solution
	<ol>
		<li>Create a 30% (w/v) solution of the polysaccharides pullulan and dextran (3:1 ratio) in DDI water. Mix O/N to ensure homogeneity of the polysaccharide solution. Slowly add in sodium bicarbonate to the polysaccharide solution to achieve a final concentration of 20% (w/v). Mix O/N to ensure homogeneity of the solution. Store the polysaccharide solution at 4 &#176;C.</li>
	</ol>
	</li>
	<li>Collecting IPC fibers on pullulan frame
	<ol>
		<li>Affix the sacrificial pullulan frame (section 3.1) using an alligator clip. Stick the alligator clip and pullulan frame on the end of the rotating mandrel using plastic-coated adhesive tape. Rotate the mandrel with the affixed frame at a constant speed of 10 mm/sec.&#160;The pullulan frame can be affixed onto the rotating mandrel in desired orientations.</li>
	</ol>
	</li>
	<li>Draw the IPC fibers using a pair of forceps (section 1) and attach the drawn end of the IPC fibers onto the rotating pullulan frame. Draw the IPC fibers at a constant speed. Upon reaching the terminal end of the IPC fiber, dry the fibers-on-frame construct O/N at RT.</li>
	<li>Embedding IPC fibers into PD hydrogel scaffold</li>
	<li>To crosslink every gram of pullulan-dextran solution, add 100 &#181;l of 11% (w/v) sodium trimetaphosphate aqueous solution and 100 &#181;l 10M sodium hydroxide.7 Mix the solution at 60 rpm using a stirplate for 1 to 2 min. After the addition of sodium trimetaphosphate and sodium hydroxide, the polysaccharide solution will crosslink almost immediately. Pour the viscous polysaccharide solution onto the fibers-on-frame construct to fully embed the IPC fibers. Incubate the combined pullulan-dextran-IPC fibers (PD-IPC) at 60 &#176;C for 30 min&#160;to form a chemically crosslinked composite scaffolds (Figure 1B).</li>
	<li>CAUTION: Perform step 3.3.2 in the fume hood and use proper protective equipment as acetic acid is a corrosive and flammable.</li>
	<li>To induce pore formation in the PD-IPC scaffold, submerge the whole scaffold in 20% (w/v) acetic acid for 20 min.</li>
	<li>Remove unreacted reagents by washing PD-IPC scaffolds in 1X PBS for 5 min&#160;while shaking at 100 rpm. Repeat this step 2 times.</li>
	<li>Remove the excess PBS and immediately freeze the PD-IPC scaffolds at -80 &#176;C O/N. Lyophilize the scaffolds at least 24 hr before use in any controlled release or bioactivity assays.</li>
</ol>
4. Fabrication of Composite Scaffold of PCL and IPC Fibers
CAUTION: Dichloromethane is a hazardous material. Use the fume hood and personal protective equipment when handling dichloromethane.&#160;
<ol>
	<li>Creating pristine and patterned PDMS substrates
	<ol>
		<li>Create a pristine polydimethylsiloxane (PDMS) elastomeric substrate using a piece of TCPS of desired dimension using soft lithography process. Create patterned PDMS substrates by using standard soft lithographic methods on poly(methyl methacrylate) templates with the desired topography.12</li>
	</ol>
	</li>
	<li>Fabricating sacrificial PCL frame for IPC fiber collection
	<ol>
		<li>Weigh out PCL and dissolve in dichloromethane to create a 0.9% (w/v) solution. For every 1 cm2 area of the PDMS substrate, drop 500 &#181;l of 0.9% PCL solution. Allow all of the dichloromethane solvent to fully evaporate in the fume hood. Repeat the process of casting 0.9% PCL to thicken the film to the desired thickness. Remove the dried PCL film from the PDMS substrate. Create a hole in the PCL frame using a suitably-sized puncher.2</li>
	</ol>
	</li>
	<li>Collecting IPC fibers on the PCL frame
	<ol>
		<li>Affix the sacrificial PCL frame with hole (from 4.2.1) on an alligator clip. Stick the alligator clip onto the rotating mandrel by using plastic-coated adhesive tape. Attach the drawn end of the IPC fiber onto the PCL frame before starting the rotation at a constant speed of 10mm/sec (section 2). After the end of IPC fiber drawing, dry the fiber-on-frame construct O/N at 4 &#176;C.</li>
	</ol>
	</li>
	<li>Embedding fiber-on-frame construct into patterned PCL substrate
	<ol>
		<li>Drop 500 &#181;l of 0.9% PCL solution onto the PDMS substrate to create a pristine or patterned PCL base, as required. Cast multiple layers of 0.9% PCL solution to obtain a scaffold with the desired thickness. Allow all of the dichloromethane solvent to fully evaporate in the fume hood.</li>
		<li>Place the fiber-on-frame construct (section 4.3.1) on top of the PCL base. Add 0.9% PCL solution on the fiber-on-frame construct multiple times to get the desired thickness and fully embed the IPC fibers, fabricating a PCL-IPC composite scaffold (Figure 1C).</li>
	</ol>
	</li>
</ol>
5. Measurement of Release of Biological Agents from Composite IPC Scaffolds
<ol>
	<li>Place composite PD-IPC or PCL-IPC scaffolds and stand-alone IPC fibers separately in a 24-well plate.</li>
	<li>Immerse the scaffold and stand-alone IPC fibers with 500 &#181;l of 1X PBS. Incubate the samples at 37 &#176;C. Collect PBS at various time points (release media) and replace with 500 &#181;l of 1X PBS.</li>
	<li>Measure the amount of protein or growth factor in the release media using a BCA assay (BSA), ELISA (VEGF and NGF) or other appropriate assay to calculate the cumulative release profile for the incorporated biomolecule.</li>
</ol>
6. Seeding of Cells on Composite IPC Scaffolds to Test Bioactivity of Released Biological Agents
<ol>
	<li>Sterilize the lyophilized PD-IPC or PCL-IPC composite scaffolds using UV light in the biological safety cabinet for at least 20 min.</li>
	<li>Use standard cell culture techniques to obtain a cell suspension of 2 x 105 cells in 200 &#181;l growth media. Seed the concentrated cell suspension onto the composite scaffolds. After 20 min, top-up the volume of growth media to fully submerge the scaffolds.</li>
	<li>Measure cell activity through standard techniques such as Alamar blue metabolic activity assay, PC12 neurite outgrowth assay or immunofluorescence.</li>
</ol>

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</ol>

The authors have nothing to disclose.

IPC fibers are formed by the interaction of two oppositely charged polyelectrolytes. The process utilizes the extraction of the complex from the interface of the polyelectrolytes, facilitating a self-assembly process for stable fiber formation. The mechanism of IPC fiber formation ensures that any biomolecule added into a similarly charged polyelectrolyte can be incorporated during the complexation process.10,11 Conversely, addition of a biomolecule into the oppositely charged polyelectrolyte will result in in...

The extracellular matrix has inherent biochemical and biophysical cues that direct cell behaviors. Mimicking this physiological three-dimensional (3D) microenvironment is a widely explored strategy for regenerative medicine and tissue engineering applications. For example, both naturally-derived and synthetic substrates have been modified with topographical cues as a means to mimic the biophysical cellular environment.1 For example, polycaprolactone (PCL) scaffolds can be easily patterned by casting on patterned PDMS substrates.2 However, most synthetic scaffolds inadequately recapitulate the controlled biochemical environment in vivo. Bulk or surface modification of synthetic materials only present biochemical cues for cell attachment but still lack temporal regulation of biochemical delivery.3 Thus, there is a need for optimal scaffolds that can mimic the temporally regulated biochemical delivery system of the extracellular matrix. 
Biochemical delivery systems such as microspheres are plagued by problems of loss of bioactivity and low incorporation efficiency due to the severity and complexity of multi-step synthesis process.4-6 Alternative methods that use a one-step fabrication and incorporation method were proven to have excellent potential to create a favorable biochemical microenvironment without the accompanying inefficiency in incorporation and loss of bioactivity. One viable solution is the use of interfacial polyelectrolyte complexation (IPC) fibers to deliver and protect biological agents. When two oppositely charged polyelectrolyte aqueous solutions are brought together, IPC fibers can be drawn out from the interface. Virtually any type of hydrophlic biomolecule in aqueous solution can be added into either the negatively- or positively-charged polyelectrolyte solution, thus facilitating the incorporation of useful biomolecules into the IPC fiber during the complexation process. Furthermore, this process only requires aqueous and ambient conditions, thereby decreasing the risk of loss of bioactivity. Using this method, active growth factors2,7 even cells8,9 have been successfully delivered. In addition, the simple method of forming IPC fibers allows molding into any shape or orientation. The stability of such fibers has been advantageous in its incorporation into both hydrophobic2 and hydrophilic polymers7 to create composite scaffolds. These composite scaffolds with IPC fibers are beneficial for creating a physiologically relevant biochemical environment while providing physical anchorage for cells. 
In this study, we show a method to incorporate IPC fibers into a hydrophilic and a hydrophobic scaffold with topography for controlled release of active biomolecules. As a proof-of-concept, we incorporate IPC fibers made from chitosan and alginate into the biocompatible, non-immunogenic and non-antigenic pullulan-dextran hydrophilic hydrogel or the biocompatible polycaprolactone hydrophobic scaffold.

<table><tbody><tr><td>Pullulan&amp;nbsp;</td><td>Hayashibara Inc Okayama Japan</td><td></td><td>Molecular weight (MW) 200 kDa. This material is pharmaceutical grade pullulan used to make pullulan frames and PD-IPC scaffolds.</td></tr><tr><td>Dextran</td><td>Sigma Aldrich</td><td>D1037</td><td>MW 500 kDa. This material is no longer being produced by Sigma Aldrich. Alternative suggested is catalog number 31392 (Sigma Aldrich). This material is used to make PD-IPC scaffolds.</td></tr><tr><td>Sodium Bicarbonate&amp;nbsp;</td><td>Sigma Aldrich</td><td>S5761</td><td>Sodium bicarbonate must be slowly added to the pullulan-dextran polysaccharide solution. Rapid addition of sodium bicarbonate will result in precipitation.&amp;nbsp;</td></tr><tr><td>Sodium Trimetaphosphate</td><td>Sigma Aldrich</td><td>T5508</td><td>This chemical is hygroscopic and must be stored in the dehumidifying cabinet. Aqueous solution of sodium trimetaphosphate must always be made fresh.</td></tr><tr><td>Sodium Hydroxide</td><td>Sigma Aldrich</td><td>S5881</td><td>This material is hazardous and must be handled with proper protective equipment such as nitrile gloves.</td></tr><tr><td>Chitosan</td><td>Sigma Aldrich</td><td>448877</td><td>MW 190-310 kDa. Acetylation degree of 75% to 85%. Purification of chitosan is required to create stable IPC fibers.</td></tr><tr><td>Acetic Acid</td><td>Merck</td><td></td><td>This can be replaced by another brand type. This material is corrosive and flammable. Protective equipment such as face shield, nitrile gloves, lab coat and shoe cover must be worn when handling this chemical in the fume hood.&amp;nbsp;</td></tr><tr><td>Alginic acid sodium salt from brown algae, low viscosity</td><td>Sigma Aldrich</td><td>A2158</td><td>Dissolve in water overnight. Filter through sterile 0.2&amp;nbsp;&amp;micro;m syringe filter before use. Store at 4 &amp;deg;C.</td></tr><tr><td>Bovine Serum Albumin</td><td>Sinopharm Chemical Reagent</td><td></td><td>Dissolve in sterile PBS and filter using 0.2 &amp;micro;m syringe filter before use.&amp;nbsp;</td></tr><tr><td>BCA assay kit</td><td>Pierce</td><td>23225</td><td>This kit was used to measure BSA release from PD-IPC scaffolds.&amp;nbsp;</td></tr><tr><td>Human Recombinant Vascular Endothelial Growth Factor</td><td>R&amp;amp;D systems</td><td>293-VE</td><td>Dissolve growth factor in 0.2% heparin solution to a final concentration of 5&amp;nbsp;mg/ml.</td></tr><tr><td>Heparin Sodium Salt From Porcine</td><td>Sigma Aldrich</td><td>H3393</td><td>This can be replaced by another brand type. Dissolve heparin salt in sterile water at a final concentration of 1% and filter through 0.2 &amp;micro;m syringe filter before use.&amp;nbsp;</td></tr><tr><td>Human Umbilical Vein Endothelial Cells (HUVEC)</td><td>Lonza</td><td>C2517A</td><td>This primary cell type was used in the assay to determine VEGF bioactivity after release from PD-IPC scaffolds.&amp;nbsp;</td></tr><tr><td>Alamar blue</td><td>Life Technologies</td><td>DAL1025</td><td>This is used to measure cell metabolic activity. Incubate Alamar blue with cells and maintain in standard cell culture conditions for 2 to 4 hours. Measure absorbance at 570 nm to determine Alamar blue percent reduction, which is correlated to the cell activity.&amp;nbsp;</td></tr><tr><td>ScanVac Coolsafe Lyophilizer</td><td>Labogene</td><td>7.001.200.060</td><td>This is a non-programmable freeze dryer that operates at -105 to -110&amp;nbsp;&amp;deg;C. This can be replaced by other standard lab lyophilizers.</td></tr><tr><td>Polycaprolactone (PCL)</td><td>Sigma Aldrich</td><td>181609</td><td>MW 65 kDa. This is no longer being manufactured by Sigma Aldrich. This can be replaced by Sigma Aldrich catalog number 704105.</td></tr><tr><td>Dichloromethane</td><td>Sigma Aldrich</td><td>V800151</td><td>This can be replaced by another brand type. This material is hazardous and must be handled in the fume hood. Protective equipment must be worn at all times when handling this chemical.</td></tr><tr><td>Polydimethylsiloxane (PDMS; 184 Silicone Elastomer Kit)</td><td>Dow Corning</td><td>(240)4019862</td><td>The elastomer kit comes with polymer base and crosslinker. Mixing the polymer base and crosslinker in different ratios will result in different stiffness of the PDMS.</td></tr><tr><td>Human Recombinant Beta-Nerve Growth Factor (NGF)</td><td>R&amp;amp;D systems</td><td>256-GF</td><td>Reconstituted in sterile DI water to a final concentration of 100&amp;nbsp;&amp;micro;g&amp;#8288;/&amp;#8288;ml. Aliquot and store in -20 &amp;deg;C until use.</td></tr><tr><td>Human Mesenchymal Stem Cells (hMSC)</td><td>Cambrex</td><td></td><td>This cell type was used in the assay to determine synergistic effect of NGF and nanotopography.</td></tr><tr><td>Rat PC12 Pheochromocytoma Cells&amp;nbsp;</td><td>ATCC</td><td></td><td>This cell type was used in the neurite outgrowth assay to determine bioactivity of NGF. After exposure to release media with NGF, measure number of cells with neurite extensions and normalize to total number of cells.</td></tr><tr><td>Grade 93 filter paper</td><td>Whatman</td><td>Z699675</td><td>This is used for the purification of chitosan after its precipitation with sodium hydroxide at pH&amp;nbsp;7.</td></tr><tr><td>Swing bucket centrifuge</td><td>Eppendorf</td><td>5810R</td><td>To be used during the purification of chitosan using 1,200 x g speed.</td></tr><tr><td>Motor with mandrel rotating at constant speed</td><td>Rhymebus</td><td>RM5E</td><td>The motor is used for the fabrication of IPC fibers on pullulan or PCL frame.</td></tr><tr><td>Phosphate buffered saline</td><td>FirstBase</td><td></td><td>Sterilize through filtration (0.2 &amp;micro;m filter) and autoclave.&amp;nbsp;</td></tr><tr><td>10-mm diameter Tissue Culture Polystyrene Dish (TCPS)</td><td>Greiner</td><td></td><td>The TCPS dish is used for casting of pullulan frame.&amp;nbsp;</td></tr><tr><td>Human VEGF ELISA kit</td><td>R&amp;amp;D systems</td><td>DVE00</td><td>The ELISA kit is used for detection of VEGF in the release medium.</td></tr><tr><td>Human NGF ELISA kit</td><td>R&amp;amp;D systems</td><td>DY256</td><td>The ELISA kit is used for detection of NGF in the release medium.</td></tr><tr><td>Plastic Coated Adhesive Tape</td><td>Bel-Art</td><td>9040336</td><td>The adhesive tape is used to securely stick the alligator clip to the rotating mandrel</td></tr></tbody></table>

composite scaffolds of interfacial polyelectrolyte fibers for temporally controlled release of biomolecules

Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules

Various scaffolds used in tissue engineering require a controlled biochemical environment to mimic the physiological cell niche. Interfacial polyelectrolyte complexation (IPC) fibers can be used for controlled delivery of various biological agents such as small molecule drugs, cells, proteins and growth factors. The simplicity of the methodology in making IPC fibers gives flexibility in its application for controlled biomolecule delivery. Here, we describe a method of incorporating IPC fibers into two different polymeric scaffolds, hydrophilic polysaccharide and hydrophobic polycaprolactone, to create a multi-component composite scaffold. We showed that IPC fibers can be easily embedded into these polymeric structures, enhancing the capability for sustained release and improved preservation of biomolecules. We also created a composite polymeric scaffold with topographical cues and sustained biochemical release that can have synergistic effects on cell behavior. Composite polymeric scaffolds with IPC fibers represent a novel and simple method of recreating the cellular niche.

In this article, we sought to create composite scaffolds with IPC fibers for the sustained release of various biomolecules. Characteristics of the biomolecules used in this study are found in Table 1. IPC fibers were first embedded into a hydrophilic PD hydrogel to create a PD-IPC composite scaffold (Figure 1B). Model molecule BSA was first tested to determine the feasibility of using a composite scaffold for controlled biomolecule release. BSA was incorporated into PD-IPC scaffolds with...

Scaffolds for tissue engineering need to recapitulate the complex biochemical and biophysical microenvironment of the cellular niche. Here, we show the use of interfacial polyelectrolyte complexation fibers as a platform to create composite, multi-component polymeric scaffolds with sustained biochemical release.

Various scaffolds used in tissue engineering require a controlled biochemical environment to mimic the physiological cell niche. Interfacial ...

The overall goal of this procedure is to provide controlled biomolecule delivery with spatial control to mimic the cellular niche from hydrophilic or hydrophobic polymeric composites scaffolds. This is accomplished by first creating a sacrificial framework of desired polymers to provide the spatial arrangement of the biomolecule releasing fibers called interfacial poly electrolyte, or IPC fibers. The second step is to incorporate IPC fibers containing the targeted hydrophilic biomolecule on a sacrificial frame.Next, the IPC fibers on frame constructs are embedded onto a larger scaffold using a micro pattern substrate as a casting mold incorporating topographical cues on the substrate. The final step is to allow full assimilation of the fibers on frame, construct, and solidification of the polymers to create un patterned or micro patterned substrates. Ultimately, standard assays can be used to show the release profiles and bioactivity of the target molecules.The main advantage of this technique offer other existing method like microencapsulation that the incorporation of hydrophilic biomolecule into a wide range of hydrophilic or hydrophobic polymer scaffold is now possible to be do

composite-scaffolds-interfacial-polyelectrolyte-fibers-for-temporally

Research

JoVE Journal

Bioengineering

The process of electrospinning polymers for tissue engineering and cell culture is addressed in this article.  Specifically, the electrospinning of photoreactive macromers with additional processing capabilities of photopatterning and multi-polymer electrospinning is described.

Electrospinning Fibrous Polymer Scaffolds for Tissue Engineering and Cell Culture

Electrospun scaffolds can be processed post production for tissue engineering applications. Here we describe methods for spinning complex scaffolds (by consecutive spinning), for making thicker scaffolds (by multi-layering using heat or vapour annealing), for achieving sterility (aseptic production or sterilisation post production) and for achieving appropriate biomechanical properties.

Postproduction Processing of Electrospun Fibres for Tissue Engineering

Here we describe a unique strategy for creating biocompatible, layered matrices with continuous interfaces between distinct layers for tissue engineering. Such a scaffold could provide an ideal customizable environment to modulate cell behavior by various biological, chemical or mechanical...

Density Gradient Multilayered Polymerization (DGMP): A Novel Technique for Creating Multi-compartment, Customizable Scaffolds for Tissue Engineering

In this video, we will demonstrate modification techniques for porous metallic implants to improve their functionality and to control cell migration. Techniques include development of pore gradients to control cell movement in 3D and production of basement membrane mimics to control cell movement in 2-D. Also, a HPLC-based method for monitoring implant integration in-vivo via analysis of blood proteins is described.

Multi-Scale Modification of Metallic Implants With Pore Gradients, Polyelectrolytes and Their Indirect Monitoring In vivo

This protocol combines electrospinning and microspheres to develop tissue engineered scaffolds to direct neurons. Nerve growth factor was encapsulated within PLGA microspheres and electrospun into Hyaluronic Acid (HA) fibrous scaffolds.  The protein bioactivity was tested by seeding the scaffolds with primary chick Dorsal Root Ganglia and culturing for 4-6 days.

Electrospinning Growth Factor Releasing Microspheres into Fibrous Scaffolds

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Electrospun Nanofiber Scaffolds with Gradations in Fiber Organization

Scaffolds capable of fitting within cranio-maxillofacial (CMF) bone defects while exhibiting osteoconductivity and bioactivity are of interest. This protocol describes the preparation of a shape memory scaffold based on polycaprolactone diacrylate (PCL-DA) using a solvent-casting particulate-leaching (SCPL) method employing a fused salt template and application of a bioactive polydopamine coating.

Fabrication of a Bioactive, PCL-based "Self-fitting" Shape Memory Polymer Scaffold

Two- and three-dimensional superhydrophobic polymeric materials are prepared by electrospinning or electrospraying biodegradable polymers blended with a lower surface energy polymer of similar composition.

Fabricating Superhydrophobic Polymeric Materials for Biomedical Applications

In this work, poly(lactic acid)/polyethylene glycol (PLA/PEG) scaffolds were prepared by using a combination of melt mixing and selective leaching. The method herein discussed permitted to develop three-layer scaffolds by highly controlling both porosity and pore size. The mechanical properties were also evaluated in a physiological environment.

A Facile and Eco-friendly Route to Fabricate Poly(Lactic Acid) Scaffolds with Graded Pore Size

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.

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

Microgel rods with complementary reactive groups are produced via microfluidics with the ability to interlink in aqueous solution. The anisometric microgels jam and interlink into stable constructs with larger pores compared to spherical-based systems. Microgels modified with GRGDS-PC form macroporous 3D constructs that can be used for cell culture.

Interlinked Macroporous 3D Scaffolds from Microgel Rods

Learn to create composite scaffolds using interfacial polyelectrolyte fibers for controlled biomolecule release in tissue engineering. This method enables sustained delivery of growth factors with spatial precision.

Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules

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