We thank the laboratory of Dr. Stephen Moss for providing embryonic rat brain tissues. M.D.T. designed the original protocol. This work was funded by National Institutes of Health P41 Tissue Engineering Resource Center Grant EB002520. K.C. was supported with Postdoctoral Fellowship from German Research Foundation (DFG) (CH 1400/2-1).

The brain tissue isolation protocol was approved by the Tufts University Institutional Animal Care and Use Committee and complies with the National Institutes of Health Guide for the Care and Use of Laboratory Animals (Institutional Animal Care and Use Committee B2011-45).
1. Silk Scaffold Preparation
<ol>
	<li>Preparation of silk solution from Bombyx mori cocoons as described previously19,20.
	<ol>
		<li>Cut each cocoon into 8 equal pieces using scissors. Use about 11 cocoons for 5 g of fragmented cocoons. (15 min)</li>
		<li>Prepare 2 L of 0.02 M Na2CO3 solution and bring it to boil using a hot plate. (15 min)</li>
		<li>Weigh 5 g of fragmented cocoons and boil them in Na2CO3 solution for 30 min. Stir the boiling silk every couple of minutes with a spatula. This step, also called de-gumming, purifies silk fibroin from hydrophilic proteins, sericins. (30 min)</li>
		<li>Wring the fibroin out by hand and rinse it in distilled water at least three times to wash out any remaining sericin and chemicals. (5 min)</li>
		<li>Place the wet fibroin on a petri dish and dry the fibroin extract in the flow hood O/N.</li>
		<li>The next day weigh the dry fibroin mass and place the fibroin in a glass beaker. (15 min)</li>
		<li>In order to dissolve the fibroin in 9.3 M LiBr solution, calculate the required volume (in ml) of LiBr by multiplying the mass of dry fibroin by 4. Slowly pour LiBr solution over the silk fibroin and immerse all the fibroin fibers using spatula. Cover the beaker to prevent evaporation and place it at 60 &#176;C for 4 hr to allow the fibers to dissolve. (15 min)</li>
		<li>Using the syringe, collect the fibroin solution from the beaker and load it into the MWCO 3,500 dialysis cassettes. Perform dialysis against distilled water for 48 hr. Change the water every couple of hours.</li>
		<li>Using the syringe, collect the fibroin solution from the cassettes into 50 ml conical tubes and centrifuge twice at 9,000 rpm (~12,700 x g) at 4 &#176;C for 20 min. Pour the supernatant into a fresh tube after each centrifugation step and discard the pellet. (40 min)</li>
		<li>Measure the concentration of the fibroin by estimating the dry weight. Pour 1 ml of silk solution into a weigh boat. Dry the sample in the oven at 60 &#176;C for 2 hr. Weigh the dry silk fibroin and calculate the concentration of silk fibroin solution by multiplying the obtained weight by 100. The expected concentration of silk solution is 6-9% (w/v).</li>
		<li>Adjust the silk concentration to 6% (w/v) by diluting it in distilled water. 
		Stopping point: The liquid silk fibroin can be stored at 4 &#176;C for up to one month in a closed container.</li>
	</ol>
	</li>
	<li>Preparation of porous scaffolds from silk solution.
	<ol>
		<li>Sieve the granular NaCl to separate the granules sized 500-600 &#181;m, which will be used in later steps. Discard the granules sized below 500 &#181;m and above 600 &#181;m. (15 min)</li>
		<li>Pour 30 ml of 6% silk solution into the polytetrafluoroethylene (PTFE) mold (Figure 1). Gently scatter 60 g of sieved NaCl over the silk. Tap the container to obtain a uniform layer of salt. Incubate 48 hr at RT to polymerize the silk.</li>
		<li>Place the scaffold-containing PTFE mold in the oven at 60 &#176;C for 1 hr to finalize the polymerization and evaporate any remaining liquid.</li>
		<li>Place the content of the PTFE mold in a beaker containing 2 L of distilled water for 48 hr to leach out the salt. Change the water 2-3 times per day. Remove the sponge scaffolds from the molds when the salt is completely leached out. Stopping point: The sponges can be stored immersed in water at 4 &#176;C in a closed container to prevent the scaffolds from dehydration.</li>
		<li>When ready, cut out the scaffolds with 5 mm diameter biopsy punch. Pre-cut the scaffolds to reach about 2 mm in height. Punch out the center of the scaffold with the 2 mm diameter biopsy punch (Figure 2A). (1 hr)</li>
		<li>Autoclave the scaffolds immersed in water to sterilize them (wet cycle, 121 &#176;C, 20 min). Stopping point: The sponges can be stored immersed in water at 4 &#176;C in a closed container to prevent the scaffolds from dehydration.</li>
		<li>Before the planned cell seeding, immerse the scaffolds in sterile 0.1 mg/ml poly-D-lysine (PDL) solution. Incubate for 1 hr at 37 &#176;C.</li>
		<li>Wash the scaffolds 3x with phosphate buffered saline (PBS) to remove non-bound PDL. (30 min)</li>
	</ol>
	</li>
</ol>
2. Isolation of Rat Cortical Neurons
<ol>
	<li>Dissect cortices from embryonic day 18 (E18) Sprague-Dawley rats as previously described by Pacifici and Peruzzi27after approved animal protocol is obtained. (2 hr)</li>
	<li>Incubate 10 cortices in 5 ml of 0.25% trypsin with 0.3% DNase I (from bovine pancreas) for 20 min at 37 &#176;C.</li>
	<li>Inactivate the trypsin by adding equal volume of 1 mg/ml soybean protein.</li>
	<li>Triturate the cortices using 10 ml Pasteur pipette by pipetting up and down 20 times until a single cell suspension is generated. Be gentle and avoid air bubble formation. (10 min)</li>
	<li>Centrifuge the cell suspension at 127 x g for 5 min.</li>
	<li>Re-suspend the cell pellet in 10 ml of culture medium (Neurobasal medium, 1x B27 supplement, 1x Glutamax, 1% penicillin/streptomycin). Count the cells. The expected cell concentration is about 2x107/ml. (20 min)</li>
</ol>
3. Construct Assembly and Culture
<ol>
	<li>Scaffold seeding with cells.
	<ol>
		<li>Move the sterile scaffolds and all the required utensils inside a cell culture hood. Using sterile forceps place the scaffolds in a 96-well cell culture plate allocating one scaffold per well. (10 min)</li>
		<li>Immerse the scaffolds in cell culture medium to equilibrate them prior to cell seeding. Incubate for 1 hr at 37 &#176;C. (10 min)</li>
		<li>Aspirate the excess of the medium from the scaffolds.</li>
		<li>Apply 100 &#181;l of cell suspension/scaffold. (10 min)</li>
		<li>Incubate the cells at 37 &#176;C O/N to allow for cell attachment to the scaffold.</li>
		<li>The following morning aspirate the non-attached cells and apply 200 &#181;l/well of fresh culture medium. (10 min)</li>
	</ol>
	</li>
	<li>Scaffold embedding with collagen matrix. (2 hr)
	<ol>
		<li>Place 10x PBS, water, 1 N NaOH and rat tail I collagen on ice. Prepare a working solution of collagen as per the manufacturer instructions. Maintain on ice until the cell-seeded constructs are ready (up to 1 hr).</li>
		<li>Remove the cell-seeded silk constructs from the incubator and aspirate the excess of medium.</li>
		<li>Using sterile forceps transfer the scaffolds to the empty wells on the well plate and immerse each scaffold in 100 &#181;l of 3 mg/ml collagen solution. Place the tissue culture plate back in the incubator for 30 min to allow polymerization of collagen.</li>
		<li>Apply 100 &#181;l of pre-warmed cell culture medium/well. Culture the constructs for one week changing the medium every day by replacing only half the volume of the medium.</li>
	</ol>
	</li>
</ol>
4. Microscopy Analysis
<ol>
	<li>Live/dead staining (1 hr)
	<ol>
		<li>Prepare stock solution of propidium iodide (PI) 1 mg/ml (1.5 mM) in distilled water.</li>
		<li>Prepare stock solution of fluorescein diacetate (FDA) 2 mg/ml in acetone.</li>
		<li>Prepare working solution containing 10 &#181;M PI and 0.15 &#181;M FDA diluted in PBS. Pre-warm the solution to 37 &#176;C in a water bath.</li>
		<li>Wash the cells with pre-warmed PBS to remove the serum esterases. Aspirate the PBS.</li>
		<li>Apply the pre-warmed working solution on the cells for 2 min and wash it with PBS.</li>
		<li>Use epifluorescent microscope to image the cells (PI ex &#955;=490 nm, em &#955;=570 nm; FDA ex &#955;=490 nm, em &#955;=514 nm). The stain remains stable over 40 min. Prolonged staining may result in unspecific staining resulting from PI uptake by the cells and co-localization of PI/FDA in cells.</li>
	</ol>
	</li>
	<li>Immunostaining
	<ol>
		<li>At the desired time point of culture fix the cells with 4% paraformaldehyde (PFA) for 30 min at RT. Due to the toxicity of the PFA fumes the fixing step should be performed in the chemical fume hood.</li>
		<li>Wash scaffolds with 3x PBS. Stopping point: The PFA-fixed constructs can be stored in PBS at 4 &#176;C for several days before proceeding with further steps.</li>
		<li>Incubate the scaffolds in 0.2% Triton, 0.25% bovine serum albumin (BSA) in PBS containing primary antibody O/N at 4 &#176;C.</li>
		<li>The following day discard the staining solution and wash the scaffolds 3 x 30 min with PBS to remove the unbound primary antibody.</li>
		<li>Incubate the samples with secondary antibody diluted in 0.2% Triton, 0.25% BSA in PBS for 2 hr at RT.</li>
		<li>Remove the staining solution and wash the scaffolds 3 x 30 min with PBS to remove the unbound secondary antibody.</li>
		<li>Image the scaffolds using a confocal microscope with 20X objective by taking 100 &#181;m z-sections of the sample with 1 &#181;m step. To visualize the thin neurites the image resolution should be of minimum 1,024 x 1,024 pixels.</li>
	</ol>
	</li>
	<li>RNA, DNA and protein isolation 
	Note: RNA, DNA and protein isolation is performed using a commercial AllPrep DNA/RNA/Protein Mini Kit according to the manufacturer instructions.
	<ol>
		<li>Using sterile forceps transfer the scaffolds out of culture plate to a 2 ml sterile tube. Place one scaffold per tube.</li>
		<li>Add 200 &#181;l of RLT buffer to each tube.</li>
		<li>Disrupt the construct by fragmenting it with sterile microscissors.</li>
		<li>To homogenize the disrupted tissue, transfer the content of the tube to the spin column. Spin for 2 min at full speed in a microcentrifuge. The lysate is homogenized as it passes through the spin column.</li>
		<li>Collect the flow through and use it immediately to isolate RNA, DNA and protein following the manufacturer protocol.</li>
		<li>Quantify the yield of the nucleic acids any other compatible method (e.g., NanoDrop).</li>
		<li>Quantify the protein yield using BCA Protein Assay according to the manufacturer instructions. Measure the outcome of assay using microplate reader at wavelength 562 nm. 
		Note: The expected yield of nucleic acids and protein per construct in relation to the cell density is shown in Figure 4.</li>
	</ol>
	</li>
</ol>

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Publication of this video-article is sponsored by Corning.

Here we described the guidelines to assemble a compartmentalized 3D brain-like tissue model. The model is characterized by dense polarized culture of neurons resulting in the development of two morphologically different compartments: one containing densely packed cell bodies, second containing pure axonal networks. Overall, the scaffold architecture and growth pattern mimic brain cortical tissue including the six laminar layers and white matter tracts21.
The donut-shaped silk protein-based tissue model allows for modifications and tuning of mechanical properties, versatile structural forms, hydrogel fillers and cellular components. Thus, this tissue model establishes a base platform for a wide range of studies. Silk is a favorable candidate for biomaterial platforms due to its biocompatibility, aqueous-based processing, and robust mechanical and degradation properties22. The silk matrix also serves as a stable anchor to reduce collagen gel contraction over time in culture. The properties such as silk concentration and porosity of the scaffold used in this model have been previously adjusted to achieve optimal cell growth and mechanical properties resulting in brain-like tissue elasticity18,23,24. We suggest to keep these parameters constant to ensure the successful outcome and reproducibility of the experiments.
The 3D neuronal network formation was achieved by combining two types of biomaterials with different mechanical properties: a stiff scaffold to provide neuronal anchoring and a softer gel matrix to permit axon penetration and connectivity in 3D. Selective material preferences of the silk scaffold and soft hydrogel provide the underlying principle for compartmentalizing the neurons from the axonal connections. Due to the inert nature of the silk scaffold, functionalization with poly-D-lysine is required for neuronal attachment. However, other cell adhesion promoting factors can be applied such as RGD25 or fibronectin26. To achieve the 3D network formation the silk scaffold needs to be filled with hydrogel in a timely manner as soon as neurons are attached to the scaffold. Likewise, the collagen matrix filler can be replaced by other hydrogels, thus allowing the study of the influence of 3D extracellular environments on axonal network formation to serve as a platform to evaluate novel hydrogels in terms of neuronal compatibility. Additionally, apart from rat cortical neurons other neuronal sources such as hippocampal neurons or induced pluripotent cell (iPSc)-derived neurons can be utilized. Moreover, the tissue model can be used to study heterocellular interactions by including glial cells along with neurons and to build more complex brain-like tissue.
As shown previously, our model can be utilized to evaluate neuronal functionality in 3D microenvironment with a variety of assays such as cell viability, gene expression, LC-MS/MS and electrophysiology, thus demonstrating physiological relevance of the model18. Other methods, which are frequently utilized to evaluate 3D tissue-engineered constructs, such as immunostaining and microscopy8,9,11 can also be used to assess cell distribution and extent of axonal network formation. However, it has to be noted, that due to the high density of the collagen matrix, the penetration of antibodies and depth of the imaging is limited to few hundred micrometers. Moreover, the signal to noise ratio may be affected by nonspecific background fluorescence. This can be overcome by using lipophilic cell tracers and genetically expressed fluorescent proteins which diminish the need for immunostaining11. Alternatively, the imaging can be performed with 2-photon microscopy instead of usual one-photon technique, which may reduce the signal loss, photobleaching, and can be extended to several hundred micrometers of depth.
Summarizing, the silk and collagen-based brain-like tissue offers a robust platform to study neuronal networks in 3D and is a starting point for the development of more advanced models of neurological disorders in the future. Independent from the mode of evaluation, the relative simplicity of this tissue model supports its utility, success and reproducibility.

The central nervous system (CNS) can be affected by a variety of disorders involving vascular, structural, functional, infectious or degenerative. An estimated 6.8 million people die every year as a result of neurological disorders, which represents a growing socioeconomic burden worldwide1. However, only few of the disorders have available treatments. Therefore, there is a critical need for innovative therapeutic strategies for patients suffering from neurological disorders. Unfortunately, many CNS-targeted therapeutics fail during clinical trials, in part due to the utilization of inadequate pre-clinical research models, which do not allow assessment of acute and chronic impacts with physiologically-relevant functional readouts.
Despite significant research efforts over the past decades, there is a vast amount unknown about the structure and function of CNS. In order to gain more knowledge, animal models are frequently used to model pathological states, such as traumatic brain injury (TBI) or dementia, especially in pre-clinical studies. However, animals differ significantly from humans both in anatomy of CNS, as well as in function, gene expression and metabolism2-4. On the other hand, 2D in vitro cultures are the common method to investigate cell biology and are routinely used for drug discovery. However, 2D cell cultures lack the complexity and physiological relevance as compared to human brain5-7. While there is no substitute for the low cost and simplicity of 2D cell culture studies or the complexity provided by animal models, 3D tissue engineering could generate improved research models to close the gap that exists between the 2D in vitro and in vivo approaches. 3D tissue engineering provides more physiologically-relevant experimental conditions achieved by 3D cell-cell interactions and extracellular cues provided by the biomaterial scaffolds. Despite the significant evidence behind the value of 3D cultures, there are currently only a few 3D CNS tissue models such as stem cell-derived organoid cultures8-10, neurospheroids11 and dispersed hydrogel cultures12,13. Advanced technical methods including multilayer lithography14, and 3D printing15 have been utilized for studying lung, liver, and kidney tissue. However, there is lack of 3D CNS models that allow for compartmentalized neuronal growth, such as mimicking the cortical architecture and biology. Separated growth of neurites from neuronal cell bodies has been previously demonstrated in 2D cultures by using microfabrication16,17 allowing the study of axon tract tracing, calcium influx, network architecture and activities. This idea inspired us to develop a 3D polarized neural tissue where cell bodies and axonal tracts are located in different compartments mimicking the layered architecture of the brain18. Our approach is based on the use of unique silk scaffold design which accommodates high density of cells in a confined volume and allows outgrowth of dense axonal network into a collagen gel. Here we demonstrate the full assembly procedure of brain-like tissue including the scaffold fabrication and neuronal culture.

<table border="0" cellpadding="0" cellspacing="0">
	<tbody>
		<tr>
			<td>Na2CO3</td>
			<td>Sigma-Aldrich</td>
			<td>223530</td>
			<td>-</td>
		</tr>
		<tr>
			<td>LiBr</td>
			<td>Sigma-Aldrich</td>
			<td>213225</td>
			<td>-</td>
		</tr>
		<tr>
			<td>MWCO 3500 dialysis cassettes&#160;</td>
			<td>Thermo Fisher</td>
			<td>66110</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Heating plate</td>
			<td>Fisher Scientific</td>
			<td>Isotemp</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Centrifuge 5804 R</td>
			<td>Eppendorf</td>
			<td>-</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Sieve</td>
			<td>Fisher Scientific</td>
			<td>-</td>
			<td>No. 270, No. 35, No. 30</td>
		</tr>
		<tr>
			<td>PTFE mold</td>
			<td>-</td>
			<td>-</td>
			<td>made in house (Figure 1) 10 cm diameter, 2 cm height</td>
		</tr>
		<tr>
			<td>NaCl</td>
			<td>Sigma-Aldrich</td>
			<td>71382</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Biopsy Punch 5mm</td>
			<td>World Precision Instrument</td>
			<td>501909</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Biopsy Punch 2mm</td>
			<td>World Precision Instrument</td>
			<td>501908</td>
			<td>-</td>
		</tr>
		<tr>
			<td>poly-D-lysine</td>
			<td>Sigma-Aldrich</td>
			<td>P6407-5MG</td>
			<td>final concentration 10 ug/ml, dissolved in water</td>
		</tr>
		<tr>
			<td>PBS</td>
			<td>Sigma-Aldrich</td>
			<td>D1283-500ML</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Trypsin</td>
			<td>Sigma-Aldrich</td>
			<td>T4049-500ML</td>
			<td>-</td>
		</tr>
		<tr>
			<td>DNase</td>
			<td>Roche</td>
			<td>10104159001</td>
			<td>final concentration 0.3%</td>
		</tr>
		<tr>
			<td>Soybean protein</td>
			<td>Sigma-Aldrich</td>
			<td>T6522-100MG</td>
			<td>final concentration 1 mg/ml</td>
		</tr>
		<tr>
			<td>Neurobasal medium</td>
			<td>Gibco</td>
			<td>21103049</td>
			<td>warm up to 37&#176;C before use</td>
		</tr>
		<tr>
			<td>B27 supplement 50x</td>
			<td>Gibco</td>
			<td>17504-044</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Glutamax</td>
			<td>Gibco</td>
			<td>35050-061</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Penicilin Streptomycin</td>
			<td>Corning</td>
			<td>30-002-CI</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Collagen I, rat tail, 100 mg</td>
			<td>Corning</td>
			<td>354236</td>
			<td>final concentration 3 mg/ml</td>
		</tr>
		<tr>
			<td>NaOH</td>
			<td>Sigma-Aldrich</td>
			<td>S2770</td>
			<td>corrosive</td>
		</tr>
		<tr>
			<td>Propidium Iodide</td>
			<td>Sigma-Aldrich</td>
			<td>P4170-10MG</td>
			<td>toxic</td>
		</tr>
		<tr>
			<td>Fluorescein Diacetate</td>
			<td>Sigma-Aldrich</td>
			<td>F7378-5G</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Olympus MVX10</td>
			<td>Olympus</td>
			<td>-</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Paraformaldehyde</td>
			<td>Sigma-Aldrich</td>
			<td>P6148</td>
			<td>toxic, final concentration 4%</td>
		</tr>
		<tr>
			<td>Bovine Serum Albumin</td>
			<td>Sigma-Aldrich</td>
			<td>A7906-10G</td>
			<td>-</td>
		</tr>
		<tr>
			<td>anti-&#946;IIITubulin antibody&#160;</td>
			<td>Sigma-Aldrich</td>
			<td>T2200</td>
			<td>rabbit 1:500</td>
		</tr>
		<tr>
			<td>anti-rabbit Alexa-546</td>
			<td>Molecular Probes</td>
			<td>A11010</td>
			<td>goat 1:250</td>
		</tr>
		<tr>
			<td>goat serum</td>
			<td>Sigma-Aldrich</td>
			<td>G9023-5ML</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Leica SP2 confocal microscope</td>
			<td>Leica</td>
			<td>-</td>
			<td>objective 20x</td>
		</tr>
		<tr>
			<td>QIAshredder</td>
			<td>Qiagen</td>
			<td>79654</td>
			<td>-</td>
		</tr>
		<tr>
			<td>AllPrep DNA/RNA/Protein Mini Kit</td>
			<td>Qiagen</td>
			<td>80004</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Ethyl alcohol, Pure</td>
			<td>Sigma-Aldrich</td>
			<td>E7023&#160;</td>
			<td>-</td>
		</tr>
		<tr>
			<td>2-Mercaptoethanol</td>
			<td>Sigma-Aldrich</td>
			<td>63689</td>
			<td></td>
		</tr>
		<tr>
			<td>NanoDrop 2000c/2000 UV-Vis Spectrophotometer</td>
			<td>Thermo Scientific</td>
			<td>-</td>
			<td>-</td>
		</tr>
		<tr>
			<td>BCA protein assay</td>
			<td>Thermo Scientific</td>
			<td>23225</td>
			<td>-</td>
		</tr>
		<tr>
			<td>Plate reader Spectramax M2</td>
			<td>Molecular Devices</td>
			<td>-</td>
			<td>absorbance 562 nm</td>
		</tr>
		<tr>
			<td>Micro Scissors, Economy, Vannas-type</td>
			<td>TedPella</td>
			<td>1346</td>
			<td>-</td>
		</tr>
	</tbody>
</table>

engineered 3d silk-collagen-based model of polarized neural tissue

Despite huge efforts to decipher the anatomy, composition and function of the brain, it remains the least understood organ of the human body. To gain a deeper comprehension of the neural system scientists aim to simplistically reconstruct the tissue by assembling it in vitro from basic building blocks using a tissue engineering approach. Our group developed a tissue-engineered silk and collagen-based 3D brain-like model resembling the white and gray matter of the cortex. The model consists of silk porous sponge, which is pre-seeded with rat brain-derived neurons, immersed in soft collagen matrix. Polarized neuronal outgrowth and network formation is observed with separate axonal and cell body localization. This compartmental architecture allows for the unique development of niches mimicking native neural tissue, thus enabling research on neuronal network assembly, axonal guidance, cell-cell and cell-matrix interactions and electrical functions.

Solid silk sponges precut to the donut shape represent a unique and simple idea to achieve a compartmentalized architecture resembling neural tissue (Figure 2A). The highly porous structure of the scaffold with the pore size of about 500 &#181;m results in exceptionally high surface area allowing the seeding and growth of high cell density within a small volume (2x107/ml) (Figure 2B). Additionally, the high porosity of the scaffold allows for unrestricted diffusion of nutrients and wastes resulting in superior viability of dense cell cultures over extended time frames. Upon seeding the neurons rapidly and uniformly attach to the surface of the scaffold pores.
After cell attachment is complete and cells are equilibrated on the silk substrate, the sponge scaffold is filled with the soft collagen matrix in order to provide a 3D environment for axonal network formation (Figure 3). In the absence of the collagen matrix the compartmentalization of axons and cell bodies is not possible as neurons grow extensions only on the surface of the pores resulting in mixed networks as found with 2D surfaces (Figure 3B). In contrast, the collagen gel provides a meshwork which supports extensive axonal outgrowth in 3D, while neuronal cell bodies remain attached to the silk scaffold (Figure 3C). This growth pattern leads to compartmentalization of cell bodies and pure axonal networks (Figure 3D), which resembles the gray and white matter of the cortex in the brain.
Apart from microscopy, the constructs can be evaluated with a variety of other methods18, depending on the question behind the experiment. For example, the isolation of DNA, RNA and protein from the constructs can be easily performed using commercial kits (Figure 4). The yield of nucleic acids and protein per construct depends on the number of cells initially seeded on the silk scaffolds. The more cells seeded the higher the yield of DNA, RNA and protein.
<img alt="Figure 1" src="/files/ftp_upload/52970/52970fig1.jpg" /> 
Figure 1. PTFE mold used for silk sponge scaffold preparation. The dimensions: 10 cm diameter, 2 cm height. <a href="https://www.jove.com/files/ftp_upload/52970/52970fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/52970/52970fig2.jpg" /> 
Figure 2. 3D brain-like tissue model.&#160;(A) Porous silk sponge scaffold. (B) Live/dead staining of neurons at day 1 upon seeding on silk scaffold before collagen embedding (green-live cells, red-dead cells). Panels on right side show the magnification of area captured in red frames. <a href="https://www.jove.com/files/ftp_upload/52970/52970fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" src="/files/ftp_upload/52970/52970fig3.jpg" /> 
Figure 3. Neuronal compartmentalized outgrowth in the 3D brain-like tissue model.&#160;(A) Scaffold compartments: Red-cell body compartment, Blue-axonal compartment. (B) Neuronal growth pattern at day 1 upon seeding before collagen embedding. (C). Neuronal outgrowth at day 7 upon seeding in the cell body compartment. (D) Neuronal outgrowth at day 7 upon seeding in the axonal compartment. Green &#8212; &#946;IIITubulin. <a href="https://www.jove.com/files/ftp_upload/52970/52970fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" src="/files/ftp_upload/52970/52970fig4.jpg" /> 
Figure 4. Expected yield of (A) RNA and DNA, and (B)&#160;protein per construct in relation to the amount of cells seeded per scaffold (&#177;SD, n=5). <a href="https://www.jove.com/files/ftp_upload/52970/52970fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>

Watch this Scientific Journal Video about Engineered 3D Silk-collagen-based Model of Polarized Neural Tissue at JoVE.com

Engineered 3D Silk-collagen-based Model of Polarized Neural Tissue

Insight into the complex actions of the brain requires advanced research tools. Here we demonstrate a novel silk-collagen-based 3D engineered model of neural tissue resembling brain-like architecture. The model can be used to study neuronal network assembly, axonal guidance, cell-cell interactions and electrical activity.

Despite huge efforts to decipher the anatomy, composition and function of the brain, it remains the least understood organ of the human body. To gain a ...

engineered-3d-silk-collagen-based-model-of-polarized-neural-tissue

Research

JoVE Journal

Bioengineering

12.3K vues.  Tufts University. Insight into the complex actions of the brain requires advanced research tools. Here we demonstrate a novel silk-collagen-based 3D engineered model of neural tissue resembling brain-like architecture. The model can be used to study neuronal network assembly, axonal guidance, cell-cell interactions and electrical activity.

Vidéo: Engineered 3D Silk-collagen-based Model of Polarized Neural Tissue

Electric Field-controlled Directed Migration of Neural Progenitor Cells in 2D and 3D Environments

Endogenous electric fields (EFs) occur naturally in vivo and play a critical role during tissue/organ development and regeneration, including that of the central nervous system1,2. These endogenous EFs are generated by cellular regulation of ionic transport combined with the electrical resistance of cells and tissues. It has been reported that applied EF treatment can promote functional repair of spinal cord injuries in animals and humans3,4. In particular, EF-directed cell migration has been demonstrated in a wide variety of cell types5,6, including neural progenitor cells (NPCs)7,8. Application of direct current (DC) EFs is not a commonly available technique in most laboratories. We have described detailed protocols for the application of DC EFs to cell and tissue cultures previously5,11. Here we present a video demonstration of standard methods based on a calculated field strength to set up 2D and 3D environments for NPCs, and to investigate cellular responses to EF stimulation in both single cell growth conditions in 2D, and the organotypic spinal cord slice in 3D. The spinal cordslice is an ideal recipient tissue for studying NPC ex vivo behaviours, post-transplantation, because the cytoarchitectonic tissue organization is well preserved within these cultures9,10. Additionally, this ex vivo model also allows procedures that are not technically feasible to track cells in vivo using time-lapse recording at the single cell level. It is critically essential to evaluate cell behaviours in not only a 2D environment, but also in a 3D organotypic condition which mimicks the in vivo environment. This system will allow high-resolution imaging using cover glass-based dishes in tissue or organ culture with 3D tracking of single cell migration in vitro and ex vivo and can be an intermediate step before moving onto in vivo paradigms.

This protocol demonstrates methods used to establish 2D and 3D environments in custom-designed electrotactic chambers, which can track cells in vivo/ex vivo using time-lapse recording at the single cell level, in order to investigate galvanotaxis/electrotaxis and other cellular responses to direct current (DC) electric fields (EFs).

Endogenous electric fields (EFs) occur naturally in vivo and play a critical role during tissue/organ development and regeneration, including that of the ...

Magnetic Resonance Elastography Methodology for the Evaluation of Tissue Engineered Construct Growth

Traditional mechanical testing often results in the destruction of the sample, and in the case of long term tissue engineered construct studies, the use of destructive assessment is not acceptable. A proposed alternative is the use of an imaging process called magnetic resonance elastography. Elastography is a nondestructive method for determining the engineered outcome by measuring local mechanical property values (i.e., complex shear modulus), which are essential markers for identifying the structure and functionality of a tissue. As a noninvasive means for evaluation, the monitoring of engineered constructs with imaging modalities such as magnetic resonance imaging (MRI) has seen increasing interest in the past decade1. For example, the magnetic resonance (MR) techniques of diffusion and relaxometry have been able to characterize the changes in chemical and physical properties during engineered tissue development2. The method proposed in the following protocol uses microscopic magnetic resonance elastography (&mu;MRE) as a noninvasive MR based technique for measuring the mechanical properties of small soft tissues3. MRE is achieved by coupling a sonic mechanical actuator with the tissue of interest and recording the shear wave propagation with an MR scanner4. Recently, &mu;MRE has been applied in tissue engineering to acquire essential growth information that is traditionally measured using destructive mechanical macroscopic techniques5. In the following procedure, elastography is achieved through the imaging of engineered constructs with a modified Hahn spin-echo sequence coupled with a mechanical actuator. As shown in Figure 1, the modified sequence synchronizes image acquisition with the transmission of external shear waves; subsequently, the motion is sensitized through the use of oscillating bipolar pairs. Following collection of images with positive and negative motion sensitization, complex division of the data produce a shear wave image. Then, the image is assessed using an inversion algorithm to generate a shear stiffness map6. The resulting measurements at each voxel have been shown to strongly correlate (R2&gt;0.9914) with data collected using dynamic mechanical analysis7. In this study, elastography is integrated into the tissue development process for monitoring human mesenchymal stem cell (hMSC) differentiation into adipogenic and osteogenic constructs as shown in Figure 2.

The procedure demonstrates the methodology of magnetic resonance elastography for monitoring the engineered outcome of adipose and osteogenic tissue engineered constructs through noninvasive local assessment of the mechanical properties using microscopic magnetic resonance elastography (&mu;MRE).

Traditional mechanical testing often results in the destruction of the sample, and in the case of long term tissue engineered construct studies, the use ...

Protocol for Relative Hydrodynamic Assessment of Tri-leaflet Polymer Valves

Limitations of currently available prosthetic valves, xenografts, and homografts have prompted a recent resurgence of developments in the area of tri-leaflet polymer valve prostheses. However, identification of a protocol for initial assessment of polymer valve hydrodynamic functionality is paramount during the early stages of the design process. Traditional in vitro pulse duplicator systems are not configured to accommodate flexible tri-leaflet materials; in addition, assessment of polymer valve functionality needs to be made in a relative context to native and prosthetic heart valves under identical test conditions so that variability in measurements from different instruments can be avoided. Accordingly, we conducted hydrodynamic assessment of i) native (n = 4, mean diameter, D = 20 mm), ii) bi-leaflet mechanical (n= 2, D = 23 mm) and iii) polymer valves (n = 5, D = 22 mm) via the use of a commercially available pulse duplicator system (ViVitro Labs Inc, Victoria, BC) that was modified to accommodate tri-leaflet valve geometries. Tri-leaflet silicone valves developed at the University of Florida comprised the polymer valve group. A mixture in the ratio of 35:65 glycerin to water was used to mimic blood physical properties. Instantaneous flow rate was measured at the interface of the left ventricle and aortic units while pressure was recorded at the ventricular and aortic positions. Bi-leaflet and native valve data from the literature was used to validate flow and pressure readings. The following hydrodynamic metrics were reported: forward flow pressure drop, aortic root mean square forward flow rate, aortic closing, leakage&#160;and regurgitant volume, transaortic closing, leakage, and total energy losses. Representative results indicated that hydrodynamic metrics from the three valve groups could be successfully obtained by incorporating a custom-built assembly into a commercially available pulse duplicator system and subsequently, objectively compared to provide insights on functional aspects of polymer valve design.

There has been renewed interest in developing polymer valves. Here, the objectives are to demonstrate the feasibility of modifying a commercial pulse duplicator to accommodate tri-leaflet geometries and to define a protocol to present polymer valve hydrodynamic data in comparison to native and prosthetic valve data collected under near-identical conditions.

Limitations of currently available prosthetic valves, xenografts, and homografts have prompted a recent resurgence of developments in the area of ...

Tissue Engineering of a Human 3D in vitro Tumor Test System

Cancer is one of the leading causes of death worldwide. Current therapeutic strategies are predominantly developed in 2D culture systems, which inadequately reflect physiological conditions in vivo. Biological 3D matrices provide cells an environment in which cells can self-organize, allowing the study of tissue organization and cell differentiation. Such scaffolds can be seeded with a mixture of different cell types to study direct 3D cell-cell-interactions. To mimic the 3D complexity of cancer tumors, our group has developed a 3D in vitro tumor test system.	
	Our 3D tissue test system models the in vivo situation of malignant peripheral nerve sheath tumors (MPNSTs), which we established with our decellularized porcine jejunal segment derived biological vascularized scaffold (BioVaSc). In our model, we reseeded a modified BioVaSc matrix with primary fibroblasts, microvascular endothelial cells (mvECs) and the S462 tumor cell line. For static culture, the vascular structure of the BioVaSc is removed and the remaining scaffold is cut open on one side (Small Intestinal Submucosa SIS-Muc). The resulting matrix is then fixed between two metal rings (cell crowns).	
	Another option is to culture the cell-seeded SIS-Muc in a flow bioreactor system that exposes the cells to shear stress. Here, the bioreactor is connected to a peristaltic pump in a self-constructed incubator. A computer regulates the arterial oxygen and nutrient supply via parameters such as blood pressure, temperature, and flow rate. This setup allows for a dynamic culture with either pressure-regulated pulsatile or constant flow.	
	In this study, we could successfully establish both a static and dynamic 3D culture system for MPNSTs. The ability to model cancer tumors in a more natural 3D environment will enable the discovery, testing, and validation of future pharmaceuticals in a human-like model.

Tissue Engineering of a Human 3D in vitro Tumor Test System

Methods to create human 3D tumor tissues as test systems are described. These technologies are based on a decellularized Biological Vascularized Scaffold (BioVaSc), primary human cells and a tumor cell line, which can be cultured under static as well as under dynamic conditions in a flow bioreactor.

Cancer is one of the leading causes of death worldwide.  Current therapeutic strategies are predominantly developed in 2D culture  systems, which ...

Generation and Grafting of Tissue-engineered Vessels in a Mouse Model

The construction of vascular conduits is a fundamental strategy for surgical repair of damaged and injured vessels resulting from cardiovascular diseases. The current protocol presents an efficient and reproducible strategy in which functional tissue engineered vessel grafts can be generated using partially induced pluripotent stem cell (PiPSC) from human fibroblasts. We designed a decellularized vessel scaffold bioreactor, which closely mimics the matrix protein structure and blood flow that exists within a native vessel, for seeding of PiPSC-endothelial cells or smooth muscle cells prior to grafting into mice. This approach was demonstrated to be advantageous because immune-deficient mice engrafted with the PiPSC-derived grafts presented with markedly increased survival rate 3 weeks after surgery. This protocol represents a valuable tool for regenerative medicine, tissue engineering and potentially patient-specific cell-therapy in the near future.

Here, we present a protocol to generate tissue engineered vessel grafts that are functional for grafting into mice by double seeding partially induced pluripotent stem cell (PiPSC) - derived smooth muscle cells and PiPSC - derived endothelial cells on a decellularized vessel scaffold bioreactor.

The construction of vascular conduits is a fundamental strategy for surgical repair of damaged and injured vessels resulting from cardiovascular diseases. ...

Production, Characterization and Potential Uses of a 3D Tissue-engineered Human Esophageal Mucosal Model

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore esophageal adenocarcinoma generally has a poor prognosis, with little improvement in survival rates in recent years. These are difficult conditions to study and there has been a lack of suitable experimental platforms to investigate disorders of the esophageal mucosa.
A model of the human esophageal mucosa has been developed in the MacNeil laboratory which, unlike conventional 2D cell culture systems, recapitulates the cell-cell and cell-matrix interactions present in vivo and produces a mature, stratified epithelium similar to that of the normal human esophagus. Briefly, the model utilizes non-transformed normal primary human esophageal fibroblasts and epithelial cells grown within a porcine-derived acellular esophageal scaffold. Immunohistochemical characterization of this model by CK4, CK14, Ki67 and involucrin staining demonstrates appropriate recapitulation of the histology of the normal human esophageal mucosa.
This model provides a robust, biologically relevant experimental model of the human esophageal mucosa. It can easily be manipulated to investigate a number of research questions including the effectiveness of pharmacological agents and the impact of exposure to environmental factors such as alcohol, toxins, high temperature or gastro-esophageal refluxate components. The model also facilitates extended culture periods not achievable with conventional 2D cell culture, enabling, inter alia, the study of the impact of repeated exposure of a mature epithelium to the agent of interest for up to 20 days. Furthermore, a variety of cell lines, such as those derived from esophageal tumors or Barrett&#8217;s Metaplasia, can be incorporated into the model to investigate processes such as tumor invasion and drug responsiveness in a more biologically relevant environment.

This manuscript describes the production, characterization and potential uses of a tissue engineered 3D esophageal construct prepared from normal primary human esophageal fibroblast and squamous epithelial cells seeded within a de-cellularized porcine scaffold. The results demonstrate the formation of a mature stratified epithelium similar to the normal human esophagus.

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore ...

A Combined 3D Tissue Engineered In Vitro/In Silico Lung Tumor Model for Predicting Drug Effectiveness in Specific Mutational Backgrounds

In the present study, we combined an in vitro 3D lung tumor model with an in silico model to optimize predictions of drug response based on a specific mutational background. The model is generated on a decellularized porcine scaffold that reproduces tissue-specific characteristics regarding extracellular matrix composition and architecture including the basement membrane. We standardized a protocol that allows artificial tumor tissue generation within 14 days including three days of drug treatment. Our article provides several detailed descriptions of 3D read-out screening techniques like the determination of the proliferation index Ki67 staining&#39;s, apoptosis from supernatants by M30-ELISA and assessment of epithelial to mesenchymal transition (EMT), which are helpful tools for evaluating the effectiveness of therapeutic compounds. We could show compared to 2D culture a reduction of proliferation in our 3D tumor model that is related to the clinical situation. Despite of this lower proliferation, the model predicted EGFR-targeted drug responses correctly according to the biomarker status as shown by comparison of the lung carcinoma cell lines HCC827 (EGFR -mutated, KRAS wild-type) and A549 (EGFR wild-type, KRAS-mutated) treated with the tyrosine-kinase inhibitor (TKI) gefitinib. To investigate drug responses of more advanced tumor cells, we induced EMT by long-term treatment with TGF-beta-1 as assessed by vimentin/pan-cytokeratin immunofluorescence staining. A flow-bioreactor was employed to adjust culture to physiological conditions, which improved tissue generation. Furthermore, we show the integration of drug responses upon gefitinib treatment or TGF-beta-1 stimulation - apoptosis, proliferation index and EMT - into a Boolean in silico model. Additionally, we explain how drug responses of tumor cells with a specific mutational background and counterstrategies against resistance can be predicted. We are confident that our 3D in vitro approach especially with its in silico expansion provides an additional value for preclinical drug testing in more realistic conditions than in 2D cell culture.

A Combined 3D Tissue Engineered In Vitro/In Silico Lung Tumor Model for Predicting Drug Effectiveness in Specific Mutational Backgrounds

We present a three-dimensional (3D) lung cancer model based on a biological collagen scaffold to study sensitivity towards non-small-cell-lung-cancer-(NSCLC)-targeted therapies. We demonstrate different read-out techniques to determine the proliferation index, apoptosis and epithelial-mesenchymal transition (EMT) status. Collected data are integrated into an in silico model for prediction of drug sensitivity.

In the present study, we combined an in vitro 3D lung tumor model with an in silico model to optimize predictions of drug response based on a specific ...

Bioprinting of Cartilage and Skin Tissue Analogs Utilizing a Novel Passive Mixing Unit Technique for Bioink Precellularization

Bioprinting is a powerful technique for the rapid and reproducible fabrication of constructs for tissue engineering applications. In this study, both cartilage and skin analogs were fabricated after bioink pre-cellularization utilizing a novel passive mixing unit technique. This technique was developed with the aim to simplify the steps involved in the mixing of a cell suspension into a highly viscous bioink. The resolution of filaments deposited through bioprinting necessitates the assurance of uniformity in cell distribution prior to printing to avoid the deposition of regions without cells or retention of large cell clumps that can clog the needle. We demonstrate the ability to rapidly blend a cell suspension with a bioink prior to bioprinting of both cartilage and skin analogs. Both tissue analogs could be cultured for up to 4 weeks. Histological analysis demonstrated both cell viability and deposition of tissue specific extracellular matrix (ECM) markers such as glycosaminoglycans (GAGs) and collagen I respectively.

Cartilage and skin analogs were bioprinted using a nanocellulose-alginate based bioink. The bioinks were cellularized prior to printing via a single step passive mixing unit. The constructs were demonstrated to be uniformly cellularized, have high viability, and exhibit favorable markers of differentiation.

Bioprinting is a powerful technique for the rapid and reproducible fabrication of constructs for tissue engineering applications. In this study, both ...

Seeding and Implantation of a Biosynthetic Tissue-engineered Tracheal Graft in a Mouse Model

Treatment options for congenital or secondary long segment tracheal defects have historically been limited due to an inability to replace functional tissue. Tissue engineering holds great promise as a potential solution with its ability to integrate cells and signaling molecules into a 3-dimensional scaffold. Recent work with tissue engineered tracheal grafts (TETGs) has seen some success but their translation has been limited by graft stenosis, graft collapse, and delayed epithelialization. In order to investigate the mechanisms driving these issues, we have developed a mouse model for tissue engineered tracheal graft implantation. TETGs were constructed using electrospun polymers polyethylene terephthalate (PET) and polyurethane (PU) in a mixture of PET and PU (20:80 percent weight). Scaffolds were then seeded using bone marrow mononuclear cells isolated from 6-8 week-old C57BL/6 mice by gradient centrifugation. Ten million cells per graft were seeded onto the lumen of the scaffold and allowed to incubate overnight before implantation between the third and seventh tracheal rings. These grafts were able to recapitulate the findings of stenosis and delayed epithelialization as demonstrated by histological analysis and lack of Keratin 5 and Keratin 14 basal epithelial cells on immunofluorescence. This model will serve as a tool for investigating cellular and molecular mechanisms involved in host remodeling.

Graft stenosis poses a critical obstacle in tissue engineered airway replacement. To investigate cellular mechanisms underlying stenosis, we utilize a murine model of tissue engineered tracheal replacement with seeded bone marrow mononuclear cells (BM-MNC). Here, we detail our protocol, including scaffold manufacturing, BM-MNC isolation, graft seeding, and implantation.

Treatment options for congenital or secondary long segment tracheal defects have historically been limited due to an inability to replace functional ...

Tissue-Engineered Graft for Circumferential Esophageal Reconstruction in Rats

The use of biocompatible materials for circumferential esophageal reconstruction is a technically challenging task in rats and requires an optimal implant technique with nutritional support. Recently, there have been many attempts at esophageal tissue engineering, but the success rate has been limited due to difficulty in early epithelization in the special environment of peristalsis. Here, we developed an artificial esophagus that can improve the regeneration of the esophageal mucosa and muscle layers through a two-layered tubular scaffold, a mesenchymal stem cell-based bioreactor system, and a bypass feeding technique with modified gastrostomy. The scaffold is made of polyurethane (PU) nanofibers in a cylindrical shape with a three-dimensional (3D) printed polycaprolactone strand wrapped around the outer wall. Prior to transplantation, human-derived mesenchymal stem cells were seeded into the lumen of the scaffold, and bioreactor cultivation was performed to enhance cellular reactivity. We improved the graft survival rate by applying surgical anastomosis and covering the implanted prosthesis with a thyroid gland flap, followed by temporary nonoral gastrostomy feeding. These grafts were able to recapitulate the findings of initial epithelialization and muscle regeneration around the implanted sites, as demonstrated by histological analysis. In addition, increased elastin fibers and neovascularization were observed in the periphery of the graft. Therefore, this model presents a potential new technique for circumferential esophageal reconstruction.

Esophageal reconstruction is a challenging procedure, and development of a tissue-engineered esophagus that enables regeneration of esophageal mucosa and muscle and that can be implanted as an artificial graft is necessary. Here, we present our protocol to generate an artificial esophagus, including scaffold manufacturing, bioreactor cultivation, and various surgical techniques.

The use of biocompatible materials for circumferential esophageal reconstruction is a technically challenging task in rats and requires an optimal implant ...