Name: encapsulation of cardiomyocytes in a fibrin hydrogel for cardiac tissue engineering
Uploaded: 2011-09-19T13:00:00
Duration: 10 min 18 s
Description: Watch this Scientific Journal Video about Encapsulation of Cardiomyocytes in a Fibrin Hydrogel for Cardiac Tissue Engineering at JoVE.com

This work was supported by the National Institutes of Health - National Heart, Lung and Blood Institute (Award # R00HL093358 to L.D.B.).

<ol>
	<li>Stegemann, J. P., Hong, H., Nerem, R. M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Mechanical,+biochemical,+and+extracellular+matrix+effects+on+vascular+smooth+muscle+cell+phenotype.">Mechanical, biochemical, and extracellular matrix effects on vascular smooth muscle cell phenotype.</a> Journal of applied physiology. 98, 2321-2327 (2005).</li><li>Guarnieri, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Covalently+immobilized+RGD+gradient+on+PEG+hydrogel+scaffold+influences+cell+migration+parameters.">Covalently immobilized RGD gradient on PEG hydrogel scaffold influences cell migration parameters.</a> Acta. 6, 2532-2539 (2010).</li><li>Krebs, . <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Injectable+poly(lactic-co-glycolic)+acid+scaffolds+with+in+situ+pore+formation+for+tissue+engineering.">Injectable poly(lactic-co-glycolic) acid scaffolds with in situ pore formation for tissue engineering.</a> Acta. 5, 2847-2859 (2009).</li><li>Zimmermann, W. -. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Engineered+heart+tissue+grafts+improve+systolic+and+diastolic+function+in+infarcted+rat+hearts.">Engineered heart tissue grafts improve systolic and diastolic function in infarcted rat hearts.</a> Nature. 12, 452-458 (2006).</li><li>Chung, C., Burdick, J. A. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Influence+of+Three-Dimensional+Hyaluronic+Acid+Stem+Cell+Chondrogenesis.">Influence of Three-Dimensional Hyaluronic Acid Stem Cell Chondrogenesis.</a> Tissue engineering. 15, (2009).</li><li>Black, L. D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Cell-induced+alignment+augments+twitch+force+in+fibrin+gel-based+engineered+myocardium+via+gap+junction+modification.">Cell-induced alignment augments twitch force in fibrin gel-based engineered myocardium via gap junction modification.</a> Tissue engineering. 15, 3099-3108 (2009).</li><li>Syedain, Z. H., Weinberg, J. S., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Cyclic+distension+of+fibrin-based+tissue+constructs:+evidence+of+adaptation+during+growth+of+engineered+connective+tissue.">Cyclic distension of fibrin-based tissue constructs: evidence of adaptation during growth of engineered connective tissue.</a> Proceedings of the National Academy of Sciences of the United States of America. 105, 6537-6542 (2008).</li><li>Falvo, M. R., Gorkun, O. V., Lord, S. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+molecular+origins+of+the+mechanical+properties+of+fibrin.">The molecular origins of the mechanical properties of fibrin.</a> Biophysical chemistry. , 152-155 (2010).</li><li>Jockenhoevel, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Fibrin+gel+-+advantages+of+a+new+scaffold+in+cardiovascular+tissue+engineering.">Fibrin gel - advantages of a new scaffold in cardiovascular tissue engineering.</a> European journal of cardio-thoracic surgery : official journal of the European Association for Cardio-thoracic Surgery. 19, 424-430 (2001).</li><li>Ryan, E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Structural+Origins+of+Fibrin+Clot+Rheology.">Structural Origins of Fibrin Clot Rheology.</a> Biophysical Journal. 77, 2813-2826 (1999).</li><li>Williams, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Cell+sourcing+and+culture+conditions+for+fibrin-based+valve+constructs.">Cell sourcing and culture conditions for fibrin-based valve constructs.</a> Tissue engineering. 12, 1489-1502 (2006).</li><li>Grassl, E. D., Oegema, T. R., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+fibrin-based+arterial+media+equivalent.">A fibrin-based arterial media equivalent.</a> Journal of biomedical materials research. 66 (Part A. , 550-561 (2003).</li><li>Barocas, V. H., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=An+anisotropic+biphasic+theory+of+tissue-equivalent+mechanics:+the+interplay+among+cell+traction,+fibrillar+network+deformation,+fibril+alignment,+and+cell+contact+guidance.">An anisotropic biphasic theory of tissue-equivalent mechanics: the interplay among cell traction, fibrillar network deformation, fibril alignment, and cell contact guidance.</a> Journal of biomechanical engineering. 119, 137-145 .</li><li>Invitrogen. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> >LIVE/DEAD Viability/Cytotoxicity Kit *for mammalian cells. , (2005).</li></ol>

No conflicts of interest declared.

The encapsulation of neonatal rat cardiomyocytes in fibrin gels results in a consistent and viable three-dimensional in vitro model of the myocardial system. Fibrin is a preferred biomaterial because when the cells are entrapped, they are metabolically active and capable of compacting, remodeling and recreating an extracellular matrix that is consistent with native heart tissue 12. Because we allow the cardiomyocytes to align themselves in this environment, their functionality is more characteristic of cardiac muscle resulting in larger contraction force as compared to isotropic tissues 6. For potential therapeutic applications, it is necessary to encapsulate cells within a material that promotes both viability and functionality. The protocols presented here demonstrate an efficient and accurate means for creating a fibrin network to control cardiac cell behavior in a three dimensional microenvironment.
A few potential issues may arise during the creation and culture of these constructs. One potential issue is the maintenance of cell viability prior to encapsulation, which will significantly affect the functionality of the construct. Effort should be made to limit cell death following the isolation by reducing the time between the isolation and the encapsulation of the cells within the fibrin gel. Constructs should be provided media every other day on a strict schedule. In addition, it is important to ensure homogeneity in all of the solutions used. If the mixture of fibrinogen, thrombin and cells produces a heterogeneous environment, the ability of the cells to remodel the ECM, mechanically couple and contract is potentially obstructed. It is also important to prevent the formation of air bubbles during the injection of the constructs in order to prevent disturbances in the continuity of the engineered tissue. One way to alleviate this issue is draw more gel than is needed to make the construct into the syringe and inject slowly. Lastly, once the fibrin matrix has set and has been in culture medium for 24 hours, it is essential to detach the construct from the sides of the ring mold to promote the cell-based compaction of the fibrin gel. Keeping the construct in the middle of the mold facilitates gas and nutrient exchange. Adherence to the sides of the ring mold may also disrupt the desired cellular alignment.
It is important to note that conscious decapitation is used as the method of euthanization in this protocol, which is an acceptable method under the guidelines from both the National Institutes of Health and the American Veterinary Medical Association. However, some institutions recommend anesthetic use followed by decapitation for neonatal rats. We have chosen conscious decapitation because it ensures the minimal amount of time under hypoxic conditions for the excised heart tissue/cells. Relatively small amounts of hypoxia can lead to myocyte ischemia and potentially myocyte death, which could significantly affect the outcomes of this protocol.

<table border="1">
	<tbody>
		<tr>
			<th>Name of reagent</th>
			<th>Company</th>
			<th>Catalogue number</th>
			<th>Comments</th>
		</tr>
 <tr>
			<td>Sodium chloride</td>
			<td>Sigma</td>
			<td>S7653</td>
			<td>PBS</td>
		</tr>
		<tr>
			<td>Potassium chloride</td>
			<td>Sigma</td>
			<td>P9333</td>
			<td>PBS</td>
		</tr>
		<tr>
			<td>Sodium phosphate dibasic</td>
			<td>Sigma</td>
			<td>S7907</td>
			<td>PBS</td>
		</tr>
		<tr>
			<td>Potassium phosphate monobasic</td>
			<td>Sigma</td>
			<td>P5655</td>
			<td>PBS</td>
		</tr>
		<tr>
			<td>Glucose</td>
			<td>Sigma</td>
			<td>G5400</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>hemostat</td>
			<td>Fine Science Tools</td>
			<td>91308-12</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>fine tweezers</td>
			<td>Fine Science Tools</td>
			<td>11251-20</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>large scissors</td>
			<td>Fine Science Tools</td>
			<td>91401-14</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>micro-scissors</td>
			<td>Fine Science Tools</td>
			<td>91501-09</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>scalpel handle</td>
			<td>Fine Science Tools</td>
			<td>10008-13</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>scalpel blade</td>
			<td>Fisher Scientific</td>
			<td>08-918-5A</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>Absorbent bench underpad</td>
			<td>VWR</td>
			<td>56617-014</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>sterile drape</td>
			<td>Fisher Scientific</td>
			<td>GM42526</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>autoclave bag</td>
			<td>Fisher</td>
			<td>01-812-54</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>gauze pad</td>
			<td>Fisher Scientific</td>
			<td>13-761-52</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>betadine</td>
			<td>Purdue Products</td>
			<td>67618-150-01</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>sterile gloves</td>
			<td>Fisher Scientific</td>
			<td>19-020</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>sterile transfer pipette</td>
			<td>Fisher Scientific</td>
			<td>9962</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>collagenase</td>
			<td>Worthington</td>
			<td>CLS2</td>
			<td>Isolation</td>
		</tr>
		<tr>
			<td>Teflon rod 1/4 inch diameter</td>
			<td>McMaster-Carr</td>
			<td>8546K11</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>Teflon tube 1/4 inch ID, 1/2 inch OD</td>
			<td>McMaster-Carr</td>
			<td>8547K31</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>Silicone O-Ring 1/4 inch ID, 1/2 inch OD</td>
			<td>McMaster-Carr</td>
			<td>9396K204</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>Teflon tube 1/4 inch ID, 5/16 inch OD</td>
			<td>McMaster-Carr</td>
			<td>52355K14</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>Kendall monoject syringes 6cc</td>
			<td>Fisher Scientific</td>
			<td>05-561-41</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>BD syringe 3cc</td>
			<td>Fisher Scientific</td>
			<td>309585</td>
			<td>Mold part</td>
		</tr>
		<tr>
			<td>Bovine Fibrinogen</td>
			<td>Sigma</td>
			<td>F8630</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>Bovine Thrombin</td>
			<td>Sigma</td>
			<td>T7513</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>1 M HEPES</td>
			<td>Sigma</td>
			<td>H0887</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>Sodium Chloride</td>
			<td>Sigma</td>
			<td>S7653</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>DMEM</td>
			<td>Invitrogen</td>
			<td>10569</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>Pluronic F-127</td>
			<td>Sigma</td>
			<td>P2443</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>Calcium Chloride</td>
			<td>Sigma</td>
			<td>383147</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>0.2 micron filter</td>
			<td>Fisher Scientific</td>
			<td>SCGVT05RE</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>40 micron cell strainers</td>
			<td>Fisher Scientific</td>
			<td>22-363-547</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>0.45 micron bottle top filter</td>
			<td>Corning</td>
			<td>430627</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>glass pre-filter</td>
			<td>Millipore</td>
			<td>AP2007500</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>18G 1 1/2 inch long needle</td>
			<td>Fisher Scientific</td>
			<td>14-826-5D</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>21G 1 inch needle</td>
			<td>Fisher Scientific</td>
			<td>14-826C</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>construct jars</td>
			<td>Fisher Scientific</td>
			<td>2116</td>
			<td>Construct</td>
		</tr>
		<tr>
			<td>Penicillin-streptomycin</td>
			<td>Invitrogen</td>
			<td>15140</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>horse serum</td>
			<td>Sigma</td>
			<td>H1138</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>Fetal bovine serum</td>
			<td>Invitrogen</td>
			<td>16000</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>aminocaproic acid</td>
			<td>Acros Organics</td>
			<td>103305000</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>ascorbic acid</td>
			<td>Sigma</td>
			<td>A5960</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>insulin</td>
			<td>Sigma</td>
			<td>I9278</td>
			<td>Media</td>
		</tr>
		<tr>
			<td>Paraformaldehyde, 16%</td>
			<td>Electron Microscopy Sciences</td>
			<td>15710</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Optimal cutting temperature (OCT)</td>
			<td>Ted Pella</td>
			<td>27050</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>2-methylbutane</td>
			<td>Fisher</td>
			<td>03551-4</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Mouse MYH1/2/4/6 primary antibody</td>
			<td>Santa Cruz Biotechnology</td>
			<td>SC-32732</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Rabbit Connexin 43 primary antibody</td>
			<td>Cell Signaling Technology</td>
			<td>3512</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Dylight 549-conjugated donkey anti-mouse secondary antibody	</td>
			<td>Jackson ImmunoResearch Laboratories</td>
			<td>715-505-151</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Dylight 488-conjugated Donke anti-rabbit secondary antibody</td>
			<td>Jackson ImmunoResearch Laboratories</td>
			<td>711-485-152</td>
			<td>Histology</td>
		</tr>
		<tr>
			<td>Live/dead assay</td>
			<td>Invitrogen</td>
			<td>L-3224</td>
			<td>Analysis</td>
		</tr>
	</tbody>
</table>

encapsulation of cardiomyocytes in a fibrin hydrogel for cardiac tissue engineering

Culturing cells in a three dimensional hydrogel environment is an important technique for developing constructs for tissue engineering as well as studying cellular responses under various culture conditions in vitro. The three dimensional environment more closely mimics what the cells observe in vivo due to the application of mechanical and chemical stimuli in all dimensions 1. Three-dimensional hydrogels can either be made from synthetic polymers such as PEG-DA 2 and PLGA 3 or a number of naturally occurring proteins such as collagen 4, hyaluronic acid 5 or fibrin 6,7. Hydrogels created from fibrin, a naturally occurring blood clotting protein, can polymerize to form a mesh that is part of the body's natural wound healing processes 8. Fibrin is cell-degradable and potentially autologous 9, making it an ideal temporary scaffold for tissue engineering.
Here we describe in detail the isolation of neonatal cardiomyocytes from three day old rat pups and the preparation of the cells for encapsulation in fibrin hydrogel constructs for tissue engineering. Neonatal myocytes are a common cell source used for in vitro studies in cardiac tissue formation and engineering 4. Fibrin gel is created by mixing fibrinogen with the enzyme thrombin. Thrombin cleaves fibrinopeptides FpA and FpB from fibrinogen, revealing binding sites that interact with other monomers 10. These interactions cause the monomers to self-assemble into fibers that form the hydrogel mesh. Because the timing of this enzymatic reaction can be adjusted by altering the ratio of thrombin to fibrinogen, or the ratio of calcium to thrombin, one can injection mold constructs with a number of different geometries 11,12. Further we can generate alignment of the resulting tissue by how we constrain the gel during culture 13.
After culturing the engineered cardiac tissue constructs for two weeks under static conditions, the cardiac cells have begun to remodel the construct and can generate a contraction force under electrical pacing conditions 6. As part of this protocol, we also describe methods for analyzing the tissue engineered myocardium after the culture period including functional analysis of the active force generated by the cardiac muscle construct upon electrical stimulation, as well as methods for determining final cell viability (Live-Dead assay) and immunohistological staining to examine the expression and morphology of typical proteins important for contraction (Myosin Heavy Chain or MHC) and cellular coupling (Connexin 43 or Cx43) between myocytes.

Watch this Scientific Journal Video about Encapsulation of Cardiomyocytes in a Fibrin Hydrogel for Cardiac Tissue Engineering at JoVE.com

Encapsulation of Cardiomyocytes in a Fibrin Hydrogel for Cardiac Tissue Engineering

We describe the isolation of neonatal cardiomyocytes and the preparation of the cells for encapsulation in fibrin hydrogel constructs for tissue engineering. We describe methods for analyzing the tissue engineered myocardium after the culture period including active force generated upon electrical stimulation and cell viability and immunohistological staining.

Culturing cells in a three dimensional hydrogel environment is an important technique for developing constructs for tissue engineering as well as studying ...

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