Anatomically Inspired Three-dimensional Micro-tissue Engineered Neural Networks for Nervous System Reconstruction, Modulation, and Modeling

Laura A. Struzyna; Dayo O. Adewole; Wisberty J. Gordi&#225;n-V&#233;lez; Michael R. Grovola; Justin C. Burrell; Kritika S. Katiyar; Dmitriy Petrov; James P. Harris; D. Kacy Cullen

doi:10.3791/55609

JoVE Journal > Neuroscience

Neuroscience

Anatomically Inspired Three-dimensional Micro-tissue Engineered Neural Networks for Nervous System Reconstruction, Modulation, and Modeling

Published: May 31, 2017

doi:

10.3791/55609

Laura A. Struzyna*^1,2,3, Dayo O. Adewole*^1,2,3, Wisberty J. Gordián-Vélez^1,2,3, Michael R. Grovola^2,3, Justin C. Burrell^2,3, Kritika S. Katiyar^2,3,4, Dmitriy Petrov^2,3, James P. Harris^2,3, D. Kacy Cullen^2,3

¹Department of Bioengineering, School of Engineering and Applied Science,University of Pennsylvania, ²Center for Brain Injury & Repair, Department of Neurosurgery, Perelman School of Medicine,University of Pennsylvania, ³Center for Neurotrauma, Neurodegeneration & Restoration,Michael J. Crescenz Veterans Affairs Medical Center, ⁴School of Biomedical Engineering,Drexel University

Summary

This manuscript details the fabrication of micro-tissue engineered neural networks: three-dimensional micron-sized constructs comprised of long aligned axonal tracts spanning aggregated neuronal population(s) encased in a tubular hydrogel. These living scaffolds can serve as functional relays to reconstruct or modulate neural circuitry or as biofidelic test-beds mimicking gray-white matter neuroanatomy.

Abstract

Functional recovery rarely occurs following injury or disease-induced degeneration within the central nervous system (CNS) due to the inhibitory environment and the limited capacity for neurogenesis. We are developing a strategy to simultaneously address neuronal and axonal pathway loss within the damaged CNS. This manuscript presents the fabrication protocol for micro-tissue engineered neural networks (micro-TENNs), implantable constructs consisting of neurons and aligned axonal tracts spanning the extracellular matrix (ECM) lumen of a preformed hydrogel cylinder hundreds of microns in diameter that may extend centimeters in length. Neuronal aggregates are delimited to the extremes of the three-dimensional encasement and are spanned by axonal projections. Micro-TENNs are uniquely poised as a strategy for CNS reconstruction, emulating aspects of brain connectome cytoarchitecture and potentially providing means for network replacement. The neuronal aggregates may synapse with host tissue to form new functional relays to restore and/or modulate missing or damaged circuitry. These constructs may also act as pro-regenerative "living scaffolds" capable of exploiting developmental mechanisms for cell migration and axonal pathfinding, providing synergistic structural and soluble cues based on the state of regeneration. Micro-TENNs are fabricated by pouring liquid hydrogel into a cylindrical mold containing a longitudinally centered needle. Once the hydrogel has gelled, the needle is removed, leaving a hollow micro-column. An ECM solution is added to the lumen to provide an environment suitable for neuronal adhesion and axonal outgrowth. Dissociated neurons are mechanically aggregated for precise seeding within one or both ends of the micro-column. This methodology reliably produces self-contained miniature constructs with long-projecting axonal tracts that may recapitulate features of brain neuroanatomy. Synaptic immunolabeling and genetically encoded calcium indicators suggest that micro-TENNs possess extensive synaptic distribution and intrinsic electrical activity. Consequently, micro-TENNs represent a promising strategy for targeted neurosurgical reconstruction of brain pathways and may also be applied as biofidelic models to study neurobiological phenomena in vitro.

Introduction

A common characteristic of disorders and diseases of the central nervous system (CNS), such as traumatic brain injury (TBI), spinal cord injury (SCI), stroke, Alzheimer's disease, and Parkinson's disease, is the disconnection of axonal pathways and neuronal cell loss¹^,²^,³^,⁴^,⁵^,⁶. For instance, when an ischemic stroke goes untreated, it is estimated that axons are lost at a rate of 7 miles of axons per minute⁵. In the case of TBI, which approximately 1.7 million people experience each year in the U.S. alone, axonal degeneration may continue to occur years after trauma, as the initial injury precipitates a long-term neurodegenerative state⁴. Aggravating these deleterious effects, the CNS has a severely limited capacity for regeneration¹^,⁷^,⁸^,⁹. Following injury, an inhibitory environment develops that is characterized by a lack of directed guidance to distant targets, the presence of myelin-associated inhibitors that hinder neurite outgrowth, and the formation of a glial scar by reactive astrocytes⁸^,¹⁰^,¹¹^,¹². The glial scar serves as a biochemical and physical barrier to regeneration, with molecules such as chondroitin sulfate proteoglycans obstructing axon outgrowth⁸^,¹¹. Furthermore, even though neural stem cells have been found in the adult CNS, the production of new neurons is limited, as consistent evidence of neurogenesis has only been found in the olfactory bulb, the hippocampal subgranular zone, the periventricular area, and the central canal of the spinal cord¹³^,¹⁴. These obstacles prevent the functional recovery of lost neurons and white matter architecture following injury or disease, resulting in the often life-changing and prolonged effects of these conditions.

Despite the lack of regenerative capacity in the adult CNS, it has been demonstrated that axonal regeneration is possible if adequate environmental cues are presented to host neurons¹⁵^,¹⁶^,¹⁷^,¹⁸. Researchers have attempted to deliver and manipulate growth factors (e.g., nerve growth factor, epidermal growth factor, glial-dependent growth factor, and neurotrophic factor-3) and other guidance molecules to stimulate plasticity and axon regeneration¹⁴^,¹⁸^,¹⁹. Even though these studies have confirmed that adult axons are capable of responding to growth factors, these strategies are limited by the low permeability of the blood-brain barrier and the specific spatial and temporal gradients required to promote regeneration¹⁴^,¹⁸^,¹⁹. Other approaches have relied on the hyperactivation of regeneration-related transcription factors in CNS neurons. For example, overexpression of the Stat3 transcription factor stimulated axonal regeneration in the optic nerve²⁰. Nevertheless, both biomolecule delivery and overexpression of transcription factors fail to replace lost neuronal populations. Cell-based strategies have mainly centered on transplanting neural stem cells (NSCs) into the CNS, taking advantage of their capacity to replace CNS neurons, release trophic factors, and support the attempts at neurogenesis that occur after injury¹⁷. In spite of this, there are still pressing challenges hindering this approach, including the hampered ability of transplanted neural cells to survive, integrate with the host, and remain spatially restricted to the injured area⁶^,¹⁴^,¹⁷^,²¹. In addition, cell delivery alone is incapable of reinstating the cytoarchitecture of damaged or lost axonal pathways. An alternative approach that addresses the problems facing cell and drug/chemical delivery strategies is combining these approaches with the use of biomaterials¹⁴^,²²^,²³. Biomaterials such as hydrogels are capable of emulating the biochemical and physical properties of the extracellular matrix (ECM), aiding in cell delivery and retention within the injured area, and delivering growth factors and other bioactive molecules with controlled release²². The attractive characteristics of these biomaterial-based strategies have resulted in evidence of in vivo axonal regeneration after the transplantation of scaffolds to the lesioned area²⁴^,²⁵^,²⁶^,²⁷^,²⁸^,²⁹^,³⁰. However, acellular biomaterial strategies do not replace lost neuronal populations; when used as delivery vehicles for neuronal, glial, or neuronal precursor cells, biomaterials are incapable of reconstituting long-distance axonal networks. The challenge of developing an approach that tackles both the axonal pathway degeneration and neuronal loss associated with CNS injury and disease still remains³¹.

Our research group previously reported the development of implantable micro-tissue engineered neural networks (micro-TENNs), which are a type of "living scaffold" consisting of neuronal cell bodies restricted to one or both ends of an agarose hydrogel-ECM micro-column, with aligned axonal tracts extending throughout the interior of this three-dimensional (3D) encasement¹^,¹⁰^,³¹^,³². One of the main differences between this technique and previous approaches is that the cytoarchitecture of micro-TENNs is created completely in vitro and is transplanted afterwards³³^,³⁴^,³⁵^,³⁶^,³⁷^,³⁸^,³⁹^,⁴⁰^,⁴¹. In vitro fabrication offers extensive spatial and temporal control of cellular phenotype and orientation, mechanical/physical properties, biochemical cues, and exogenous factors, which benefits the integration of these scaffolds with the host after implantation⁴¹^,⁴². Micro-TENNs are anatomically inspired because they emulate brain neuroanatomy, displaying axonal tracts similar to those that bridge distinct functional regions of the brain (Figure 1A)¹. Therefore, this strategy may be able to physically replace lost white matter tracts and neurons following implantation into a lesioned region. This technique is also inspired by developmental mechanisms in which "natural living scaffolds" formed by radial glial cells and pioneering axons act as pathfinding guides for cell migration from the subventricular zone and axonal outgrowth, respectively⁴³. These mechanisms are recapitulated in the aligned axonal tracts of micro-TENNs, which can present living pathways for neural cell migration and axonal regeneration by axon-mediated axonal outgrowth (Figure 1C)⁴³. Furthermore, this strategy takes advantage of synaptic integration between the micro-TENN neurons and native circuitry, forming new relays that may contribute to functional recovery (Figure 1B)⁴³. The capacity for synapse formation may also grant this approach the ability to modulate the CNS and respond to host tissue according to network feedback. For example, optogenetically active neurons in the living scaffolds may be stimulated to modulate host neurons through synaptic interactions (Figure 1D).

In addition, the biomaterial-based tubular construction of micro-TENNs offers an adequate environment for cell adhesion, growth, neurite extension, and signaling, while the miniature dimensions of the constructs potentially permit minimally invasive implantation and provide a partially sequestered microenvironment for gradual integration into the brain. Indeed, recent publications have demonstrated the potential of micro-TENNs to mimic neural pathways following implantation into the rat brain. Following stereotaxic microinjection, we previously reported evidence of micro-TENN neuronal survival, maintenance of axonal tract architecture, and neurite extension into the host cortex out to at least 1 month in vivo¹⁰^,³¹. Moreover, labeling with synapsin provided histological evidence of synaptic integration with native tissue¹⁰^,³¹. Overall, micro-TENNs may be uniquely suited to reconstruct and modulate damaged CNS by replacing lost neurons, synaptically integrating with host circuitry, restoring lost axonal cytoarchitecture, and, in certain cases, providing regenerating axons with the appropriate pathfinding cues.

Figure 1: Principles and inspiration behind the development of micro-tissue engineered neural networks (micro-TENNs). (A) Micro-TENNs mimic the cytoarchitecture of the brain connectome (purple), in which functionally distinct regions are connected by long, aligned axonal tracts in a unidirectional (red, green) or bidirectional (blue) manner. As an example, micro-TENNs could reconstitute lost connections in corticothalamic and nigrostriatal pathways or in the perforant pathway from the entorhinal cortex to the hippocampus (adapted from Struzyna et al., 2015)¹. (B) Diagram of a unidirectional and bidirectional micro-TENN (red and blue, respectively) synaptically integrating with the host circuitry (purple) to serve as a functional relay between both ends of a lesion. (C) Schematic of the axonal tracts of a unidirectional micro-TENN (green) serving as a guide for axon-facilitated regeneration of host axons (purple) towards a target with which the micro-TENN interacts. (D) Conceptual diagram of the use of optogenetically active micro-TENNS as neuromodulators, taking advantage of synaptic integration with excitatory or inhibitory neurons (bottom). Please click here to view a larger version of this figure.

The current manuscript details the methodology utilized to fabricate micro-TENNs using embryonically derived cerebral cortical neurons. Notably, micro-TENNs could be fabricated with other types of neural cells. For example, the initial reports of successful micro-TENN development featured dorsal root ganglion (DRG) neurons³². The hydrogel micro-columns can be generated (Figure 2A) by adding liquid agarose to a custom-made, laser-cut cylindrical channel array or to capillary tubes, both containing aligned acupuncture needles. The needle forms the lumen and determines the inner diameter (ID) of the micro-column, while the capillary tube ID and the diameter of the cylinders in the laser-cut device dictate the outer diameter (OD) of the constructs. The OD and ID can be chosen according to the desired application by selecting different diameters for the device/capillary tubes and the acupuncture needles, respectively. The length of the micro-columns can also be varied; to date, we have reported the construction of micro-TENNs up to 20 mm in length¹⁰ and are actively pursuing even longer lengths. After the agarose gels and the acupuncture needles are removed, an ECM solution generally consisting of type I collagen and laminin is added to the lumen of the constructs (Figure 2C). The ECM core provides a scaffold to support neuronal cell adhesion and axonal outgrowth. Initially, primary rat cortical neurons were plated in the micro-columns using dissociated cell suspensions¹⁰^,³¹^,³². However, this approach did not produce the target cytoarchitecture in all cases, which was defined as the neuronal cell bodies restricted to the ends of the micro-columns, with the central lumen comprised of pure aligned axonal tracts. Since then, the use of a forced neuronal aggregation method (based on protocols adapted from Ungrin et al.) has enabled a more reliable and consistent fabrication of micro-TENNs with the ideal structure (Figure 2B)⁴⁴. In addition to describing the current methodology, this article will show representative phase-contrast and confocal images of micro-TENNs that demonstrate the formation of axonal tracts over time, as well as the finalized target cytoarchitecture. This manuscript will also expand on noteworthy aspects of the protocol and remaining challenges and future directions of the micro-TENN technology.

Figure 2: Schematic diagram of the three-stage micro-TENN fabrication process. (A) Development of the agarose hydrogel: (i) Initially, a small acupuncture needle (e.g., 180-350 µm in diameter) is inserted into the cylindrical channels of a custom-made, laser-cut mold or a capillary tube (e.g., 380-700 µm in diameter). In the next step, liquid agarose in DPBS is introduced into the cylindrical channels or capillary tubes. (ii) After the agarose gels, the needle is removed and the mold is disassembled to yield the hollow agarose micro-columns. (iii) These constructs are then sterilized and stored in DPBS. (B) Primary neuron culture and the aggregate method: (i) Neuronal aggregation is performed in pyramidal micro-well arrays, cast from 3D-printed molds, that fit in the wells of a 12-well culture plate. (ii) Micro-TENNs include primary rat neurons dissociated from fetal brains of embryonic-day-18 rats. Following tissue dissociation with trypsin-EDTA and DNase I, a cell solution with a density of 1.0-2.0 x 10⁶ cell/mL is prepared. (iii) 12 µL of this solution are transferred to each well in the pyramidal micro-well array. The plate containing these micro-wells is centrifuged to produce cell aggregates. (iv) These are then incubated overnight prior to plating in the micro-columns. (C) ECM core fabrication and cell seeding: (i) Prior to cell seeding, an ECM solution containing 1 mg/mL type I collagen and 1 mg/mL laminin is transferred to the interior of the micro-TENNs and allowed to polymerize. (ii) Depending upon whether unidirectional or bidirectional micro-TENNs are being fabricated, an aggregate is placed at either one or both extremes of the micro-column, respectively. (iii) Following a period of incubation to promote adhesion, micro-TENNs are cultured in Petri dishes flooded with supplemented embryonic neuronal basal medium. (iv) After 3-5 days in culture, the final micro-TENN structure should demonstrate cell aggregates at the extremes of the micro-column, with axonal tracts spanning its length. Please click here to view a larger version of this figure.

Protocol

All procedures involving animals were approved by the Institutional Animal Care and Use Committees at the University of Pennsylvania and the Michael J. Crescenz Veterans Affairs Medical Center and adhered to the guidelines set forth in the NIH Public Health Service Policy on Humane Care and Use of Laboratory Animals (2015).

1. Development of the Agarose Hydrogel (Acellular Component of micro-TENNs)

Agarose solution preparation
1. Within a biosafety cabinet, prepare reservoirs for the micro-columns by transferring 20 mL of Dulbecco's phosphate-buffered saline (DPBS) to each of two 10-cm Petri dishes. Sterilize fine forceps and microscalpels with a hot bead sterilizer.
2. Weigh 3 g of agarose and transfer it to a sterile beaker inside the biosafety cabinet. Add 100 mL of DPBS for a final concentration of 3% weight/volume (w/v). Include a clean magnetic bar and cover the beaker with aluminum foil.
3. With a hot plate/stirrer, warm the beaker at 100 °C and stir at 120-200 rpm to completely dissolve the agarose (the solution will turn from cloudy to clear). Maintain the heating and stirring afterwards to prevent gelation and change the heating temperature as necessary to avoid burning the agarose.
  NOTE: Fabrication with both the laser-cut device and capillary tubes is presented below in sub-sections 1.2 and 1.3, respectively. Proceed to sub-section 1.4 after finishing the steps described in either sub-section. For both micro-column fabrication methods, add the liquid agarose quickly, as agarose solidifies rapidly as it cools. When sterilizing with an autoclave in any of the following steps, use the standard conditions applied to glassware.
Micro-column preparation using a laser-cut device
NOTE: The laser-cut device is cut from transparent acrylic using a commercial CO₂ laser cutter. The fabrication of structures and devices through laser cutting is well-documented for a range of engineering and research applications⁴⁵^,⁴⁶^,⁴⁷. This mold (Figure 3) consists of an array of five cylindrical channels, each with a diameter of 398 µm and a length of 6.35 mm. These cylindrical arrays are formed along their length by two pieces: a bottom half (length: 25.4 mm, width: 6.35 mm, height: 6.0 mm) and a top half (length: 31.5 mm, width: 6.35 mm, height: 12.7 mm), as shown in Figures 3A and 3B, respectively. The two halves can be clamped together by the anterior and posterior caps observed in Figure 3C (length: 31.5 mm, width: 6.35 mm, height: 12.7 mm), which feature four alignment holes that coincide with two holes each on the top and bottom pieces and that help secure all the parts together when screwed. These caps also include five holes, concentric to the cylindrical channels, into which the acupuncture needles can be inserted to form the lumen of the micro-columns.
1. Sterilize the device shown in Figure 3 by covering it with aluminum foil and autoclaving. Assemble the device as shown in Figure 3D by aligning the anterior and posterior caps with only the bottom-half piece and securing the three parts with two #4-40 screws and nuts (thread diameter: 3.05 mm) in the bottom alignment holes.
2. Fully introduce an acupuncture needle (diameter: 180 µm, length: 30 mm) into the needle holes on either the anterior or posterior cap of the device (Figure 3D). With a micropipette, pour enough liquid agarose (~1 mL for the five channels) on the bottom-half piece to completely fill each of the cylindrical channel halves.
3. Immediately place the top-half piece of the device over the bottom half and apply pressure until it is firmly in place to complete the cylindrical channels (friction between the caps and the top piece will keep the latter in place). Wait ~5 min at room temperature after agarose addition to permit its gelation inside the channels of the device.
4. Manually extract the needle from each of the holes on the caps of the device. Remove the screws and manually separate the two caps and the top half from the bottom-half piece, where the latter will be holding the hydrogel micro-columns.
5. Use fine forceps to gently remove the micro-columns from the channels on the bottom-half piece and place them into the previously prepared Petri dish containing DPBS (step 1.1.1). Reutilize the device for another round of micro-column fabrication. Proceed to sub-section 1.4.
Micro-column fabrication using capillary tubes
1. Transfer glass capillary tubes (diameter: 398.78 µm, length: 32 mm) to the inside of the biosafety cabinet. Manually break the long tubes into 2.0–2.5-cm fragments and fully insert one acupuncture needle (diameter: 180 µm, length: 30 mm) into each fragment (Figure 2A).
2. Transfer 1 mL of liquid agarose from the beaker to the surface of an empty Petri dish. Holding the capillary tube and the introduced needle, place one end of the tube in contact with the liquid agarose pool to fill it by capillary action. Agitate the tube to promote capillary rise.
  NOTE: Fill the capillary tubes with liquid agarose as high as the capillary action permits; afterwards, these micro-columns can be cut into smaller constructs depending on the desired length. The 1-mL agarose pool is typically used for only one tube, since the agarose cools and gels rapidly, preventing further capillary action.
3. When the liquid ceases to rise, remove the capillary tube from the pool and place it horizontally on the surface of a Petri dish. Wait for 5 min to let the agarose gel inside the tubes.
4. Situate the thumb and index finger on either side of the tube and press against it. Use the other hand to quickly pull the needle out while using the thumb and index finger to prevent the micro-column itself from sliding out of the tube. Insert a 30-gauge needle into the capillary tube to slowly push the micro-column out into a dish containing DPBS (step 1.1.1).
Micro-column trimming and sterilization
1. Delicately transfer one micro-column from DPBS to an empty dish using fine forceps. Add 10 µL of DBPS to the top of the micro-column with a micropipette to prevent drying. Place the latter dish below a stereoscope for visual guidance.
  NOTE: Throughout the protocol, micro-column drying or dehydration refers to the acquisition of a crumpled structure that is visually distinguishable from the typical, hydrated appearance of these constructs. Dehydrated micro-columns firmly attach to the surface of Petri dishes and cannot be easily moved, whereas hydrated constructs tend to slide across the surface after being manipulated with forceps. A phase-contrast image of a completely dried micro-column is shown in Figure 8A.
2. Trim the micro-column with a microscalpel to shorten it to the desired length (here, 2-5 mm). Transport the trimmed micro-column with fine forceps to the other DPBS Petri dish prepared in step 1.1.1.
3. Repeat steps 1.4.1 and 1.4.2 for each fabricated micro-column.
4. Sterilize the micro-columns in the DPBS-containing Petri dishes under ultraviolet (UV) light for 1 h. Store the Petri dishes at 4 °C prior to ECM addition and cell plating.

2. Primary Neuron Culture and Forced Cell Aggregation Method

Preparation of the pyramidal micro-well array
NOTE: This section employs a 3D-printed mold consisting of a cylindrical base (diameter: 2.2 cm, height: 7.0 mm) and nine square pyramids on top (side length: 4.0 mm, slant angle: 60°), organized in a 3 x 3 array, as shown in Figure 3E. The additive manufacturing process using commercially available 3D printers is well-documented. Computer-aided design software can be used to design the mold. The resultant design file can then be digitally converted into a tool-path for a 3D printer. Each printer has different specifications, and the instructions for setting up and operating a 3D printer vary accordingly.
1. Use a 3/32" drill bit to puncture 16 holes in a 4 x 4 array (side length: 4 cm, hole separation: 1 cm), centered in the lid of a 10 cm Petri dish. Inside a chemical fume hood, use the bottom piece of the Petri dish to weigh 27 g of polydimethylsiloxane (PDMS) and 3 g of curing agent (for a 1:10 ratio). Stir with a micro-spatula to distribute the agent evenly.
2. Cover the PDMS/curing agent with the punctured lid. Connect one end of a hose to the vacuum port of the fume hood and insert the other end into the stem of a funnel (mouth diameter: 10 cm, stem length: 3 cm, stem diameter: 1.5 cm).
3. Make an opening with a 3/32" drill bit at the top of a 1 mL pipette bulb and insert and secure a 1,000 µL micropipette tip into the opening (with the pointed end upwards). Place the bulb and tip into the hose and pull the hose upwards until the bulb seals the hose into the stem of the funnel.
4. Place the funnel on the punctured dish lid and secure the hose with an available sturdy support. Open the vacuum valve for 5 min to suction and bring the air bubbles to the surface.
5. Close the valve, remove the funnel, and hit the Petri dish against the surface of the fume hood ~3 times to burst any remaining air bubbles.
6. Place a pyramidal-well 3D-printed mold into each of the wells in a 12-well culture plate, with the pyramids pointing up. Pour the PDMS/curing agent on top of the molds until each well of the plate is filled. Cover the 12-well plate with its lid and transfer it to an oven for 1 h at 60 °C to dry.
7. Carefully remove each PDMS micro-well array (Figure 3F) from the plate with a micro-spatula. Cover the PDMS arrays with aluminum foil and sterilize by autoclaving. Inside a biosafety cabinet, insert one micro-well array into each well of a 12-well plate (Figure 2B).
Cortical neuron isolation from rat fetuses
1. Add ~20 mL of Hank's balanced salt solution (HBSS) to each of four to six 10 cm Petri dishes (one for each dissected tissue) inside a biosafety cabinet. Transfer these dishes to a dissection hood and place them on ice. Sterilize dissection instruments, such as microscalpels, scissors, and forceps, with a hot bead sterilizer.
2. Pre-warm embryonic neuron basal medium + 2% serum-free supplement + 0.4 mM L-glutamine (referred to as "culture medium" hereafter) and 0.25% trypsin + 1 mM ethylenediaminetetraacetic acid (EDTA) at 37 °C. Thaw deoxyribonuclease (DNase) I by placing it at room temperature. Prepare 1.5 mL of a 0.15 mg/mL DNAse I solution in HBSS and maintain the solution on ice.
3. Euthanize a timed-pregnant embryonic-day-18 rat by carbon dioxide inhalation and confirm death by decapitation. Transfer the carcass to a sterile dissection hood and lay it ventral-side up. Rinse the abdomen thoroughly with 70% ethanol.
4. Open the uterus and remove the fetuses (usually ~11) from the amniotic sacs with scissors and transfer them with forceps to a Petri dish containing cold HBSS, as described⁴⁸. Place a chilled (-20 °C) granite block below the stereoscope. Place the Petri dish on the surface of this cold block to conserve the low temperature of the HBSS throughout the dissection procedure.
5. Rinse the pups by swishing the HBSS around and then transfer them to the next clean dish containing HBSS. With the aid of the stereoscope and the dissection instruments, sequentially remove the heads, cerebral hemispheres, and cortices of the fetuses and transfer each tissue with forceps to a new HBSS-filled dish after each dissection⁴⁸.
6. Aspirate only the cortices with a Pasteur pipette and place the tissue into a sterile 15 mL centrifuge tube. Discard the other dissected tissues. Rinse the cortices three times by sequentially adding and removing ~5 mL of HBSS with a serological pipette. Place the tube on ice when not in use.
7. Transfer the cortices with a Pasteur pipette to a 15 mL tube containing pre-warmed trypsin-EDTA (4-6 cortices per 5 mL of trypsin-EDTA). Manually agitate the tube once and place it at 37 °C. Invert the tube every 3 min to prevent the tissue from clumping.
8. Stop the exposure to trypsin after ~10 min by removing the tissue with a Pasteur pipette and transferring it to a clean 15 mL centrifuge tube. Add the 0.15 mg/mL DNase I solution (1.5 mL) to the tube with a pipette.
9. Use a Pasteur pipette to manually break up tissue clumps and then vortex (~30 s) until the solution appears homogeneous and there are no remaining tissue fragments in the liquid. If it is not possible to completely homogenize the solution, extract the insoluble fragments by pulling them into the tip of a Pasteur pipette.
10. Centrifuge the homogeneous cell solution obtained in step 2.2.9 at 200 x g for 3 min. Remove the supernatant with a Pasteur pipette, taking care not to disturb the pelleted cells. Add 2 mL of culture medium with a serological pipette and vortex to resuspend the cells.
11. Count the number of cells in the solution prepared in step 2.2.10 using a hemocytometer; the expected yield is 3.0-5.0 x 10⁶ cells/cortical hemisphere. Prepare 1 mL or more of cell suspension in culture medium, with a density of 1.0-2.0 x 10⁶ cells/mL.
Formation of neuronal cell aggregates
1. With a micropipette, add 12 µL of the 1.0-2.0 x 10⁶/mL cell suspension into each micro-well of the PDMS array (that was placed in the plate in step 2.1.7).
  NOTE: The cell concentration can be adjusted depending on micro-column ID and the desired cell aggregate size, as higher concentrations yield larger aggregates.
2. Centrifuge the plate at 200 x g for 5 min to force the aggregation of cells at the bottom of the micro-wells (Figure 2B). Carefully add ~2 mL of culture medium to the top of each PDMS array to cover all the seeded micro-wells, taking care not to disturb the aggregated cells.
3. If cells will not be transduced with a viral vector, incubate the plate for 12-24 h at 37 °C and 5% CO₂ and then proceed to section 3. If the aggregates will be transduced, skip the incubation and proceed to section 2.4.
Transduction with a viral vector to observe calcium signaling
Note: These steps are performed to transduce neurons with a viral vector containing a genetically encoded calcium indicator (GECI). The results shown in this article were obtained using a commercially available adeno-associated virus (AAV) (serotype 1) with GCaMP6f, a GECI with fast kinetics consisting of green fluorescent protein (GFP), calmodulin (CaM), and the M13 peptide, driven by the human Synapsin I promoter. The viral vector solution may require dilution in sterile DPBS prior to transduction, depending on the concentration of the stock solution. Cell health/morphology and GCaMP6f signal strength must be observed over time for a range of vector concentrations. This optimization procedure must be performed by each investigator to determine the appropriate titer for their own cell cultures. The typical GCaMP6f expression time is 7-8 days following the transduction that occurs during the incubation done in step 2.4.2.
1. With a micropipette, add the required volume of viral vector solution (for a final concentration of ~3.0 x 10⁹ genomic copies per aggregate) to the culture medium, covering the aggregates. Slowly pipette up and down to ensure that that the vector solution is homogeneously distributed throughout the culture medium.
2. Incubate the plate with the seeded pyramidal micro-wells for 24 h at 37 °C and 5% CO₂ to allow for the viral transduction of GCaMP6f.

3. Development of the Cellular Component of micro-TENNs

ECM core fabrication
1. After aggregate incubation, add type I collagen and laminin to the culture medium (for a concentration of 1 mg/mL each) in a microcentrifuge tube to prepare the ECM solution. Perform steps 3.1.2-3.1.4 at room temperature, but maintain the tube with ECM on ice when not in use to prevent premature gelation.
  NOTE: The typical expenditure is 4 µL of ECM solution for each micro-column (length: 5 mm, ID: 180 µm).
2. Adjust the pH of the ECM solution by transferring 1-2 µL to litmus paper to verify the initial pH, adding 1 µL of 1 N sodium hydroxide (NaOH) and/or 1 N hydrochloric acid (HCl) to the ECM, as needed, and repeating until the pH is 7.2-7.4. Ensure homogenization of the ECM solution by pipetting up and down while avoiding the formation of air bubbles.
3. Transfer the micro-columns with sterilized forceps from the dishes in step 1.4.3 to empty 35- or 60-mm Petri dishes. Work on 4-5 micro-columns at a time to prevent dehydration. Attach a 10-µL tip attached to a 1,000-µL tip to a micropipette. Using the stereoscope for visual guidance, place the tip at one end of the micro-columns and suction to extract residual DPBS and air bubbles from the lumen.
4. Quickly draw up 4-5 µL of ECM in a micropipette. Observing under a stereoscope, place the tip of the micropipette at one of the ends of the micro-columns and discharge enough ECM to fill the lumen. Confirm the absence of air bubbles in the lumen, as these may inhibit axonal outgrowth through the ECM. If air bubbles exist, remove the ECM, as explained in step 3.1.3, and add the ECM again.
5. To prevent dehydration, add ~2 µL of ECM around each micro-column. Incubate the hydrogel/ECM micro-columns in the Petri dishes at 37 °C and 5% CO₂ for 25 min. Proceed to cell seeding immediately after incubation.
  NOTE: The incubation period in step 3.1.5 is intended to allow time for the polymerization of collagen and laminin inside the micro-columns.
Neuronal cell seeding in the micro-columns
NOTE: To change the culture medium of the transduced aggregates, tilt the plate, use a micropipette to remove the medium that pools on the wall of the well, and then slowly add ~1 mL against the wall (to avoid disturbing the aggregates in the pyramidal micro-wells). Repeat this medium change a second time.
1. Following the incubation period in step 3.1.5, transfer approximately 10-20 µL of culture medium to two free areas in the Petri dishes holding the micro-columns. Use a micropipette to individually transfer the aggregates to the Petri dish containing the constructs and move them with forceps to one of the small pools of culture medium to preserve cell health.
2. While observing under a stereoscope, insert an aggregate at each end of the micro-columns for bidirectional micro-TENNs or at one end for a unidirectional architecture (as desired) using forceps. Confirm the placement of the aggregates inside the micro-columns using the stereoscope. Use forceps to move the seeded micro-columns to the other small pool of culture medium to avoid dehydration and to preserve aggregate health.
3. Incubate at 37 °C and 5% CO₂ for 45 min to allow the aggregates to adhere to the ECM. Verify that the aggregates remain at the ends of the micro-columns using the stereoscope; reintroduce the cell aggregates and repeat the incubation step as necessary.
4. Carefully flood the Petri dishes containing the micro-TENNs with culture medium (3 or 6 mL for a 35 or 60 mm Petri dish, respectively) using a serological pipette. Place the dishes in an incubator at 37 °C and 5% CO₂ for long-term culture.
5. Perform half-media changes every 2 days with culture medium. Carefully remove half of the old medium with a pipette and use the stereoscope for visual guidance to avoid suctioning the micro-TENNs. Replace by slowly adding fresh, pre-warmed medium with a pipette.
6. To reutilize the PDMS micro-well arrays, remove the culture medium, boil the arrays in deionized water for 30 min, and sterilize in an autoclave for another round of aggregate formation and culture.
  NOTE: At desired timepoints, the cytoarchitecture of micro-TENNs can be verified using phase-contrast microscopy. Here, an exposure time of 5-8 ms and 10X (0.64 µm/pixel) and 20X (0.32 µm/pixel) objectives were utilized to capture the phase-contrast images. The fluorescence associated with calcium concentration changes in virally transduced micro-TENNs was captured using a high-speed fluorescence microscope with a 50 ms exposure time, a 10X objective (0.64 µm/pixel), and solid-state light with bandpass filters of ~480 nm and ~510 nm for excitation and emission, respectively, to visualize the GCaMP6f fluorescence signal.

4. Immunocytochemistry for In Vitro Studies

Note: For the images shown here, the following primary antibodies were used: mouse anti-Tuj-1/beta-III tubulin (1:500) and rabbit anti-synapsin-1 (1:500) for the labeling of axons and pre-synaptic boutons, respectively. The secondary antibodies were donkey anti-mouse 568 (1:500) and donkey anti-rabbit 488 (1:500). The requisite volumes of the prepared primary and secondary antibody solutions, as well as the volumes of the formaldehyde, horse serum, and detergent solutions, depend on the volume required to entirely cover the constructs. These volumes may be minimized using a hydrophobic barrier pen to limit the area surrounding each micro-column.

CAUTION: This section employs formaldehyde and Hoechst. Formaldehyde is a toxic compound known to be carcinogenic, and Hoechst is a known mutagen. Therefore, these compounds must be disposed of in an appropriate waste container. Always handle them in a chemical fume hood while using appropriate personal protection equipment, such as a lab coat, safety glasses, and gloves.

Prepare a 4.0% volume/volume (v/v) formaldehyde solution in 1x phosphate-buffered saline (PBS) inside a chemical fume hood.
Remove the culture medium from the Petri dishes containing the micro-TENNs with a micropipette. Add enough volume of the formaldehyde solution to the dishes to completely cover the micro-TENNs. Soak the micro-TENNs in the formaldehyde solution for 35 min at 18-24 °C to fix the cells within the micro-columns.
Remove the 4.0% formaldehyde solution from the Petri dishes with a pipette and discard following appropriate hazardous material disposal guidelines.
Perform two quick rinses by adding enough PBS to entirely cover the fixed micro-TENNs and then removing the PBS with a pipette. Perform a third long rinse by soaking the constructs in the PBS for 10 min.
CAUTION: Discard the PBS used for rinsing as possibly containing traces of formaldehyde.
Prepare a 0.3% v/v solution of non-ionic detergent in 4% v/v horse serum in PBS. Remove the PBS from the Petri dishes containing the fixed micro-TENNs and add a sufficient volume of the 0.3% detergent solution to cover the constructs. Soak for 60 min at 18-24 °C to permeabilize the cells.
Remove the detergent solution with a pipette. Perform two quick rinses by adding and subsequently removing the PBS. Afterwards, perform three longer rinses by soaking the constructs in PBS for 5 min during each rinse.
Dilute primary antibodies in 4% horse serum. Remove the PBS from the Petri dishes containing the fixed and permeabilized micro-TENNs. Add enough primary antibody solution to the micro-columns to cover them completely. Seal the Petri dishes with parafilm to prevent evaporation and incubate overnight (12-16 h) at 4 °C.
Remove the primary antibody solution from the dishes and rinse as explained in step 4.6. In the dark, prepare the secondary antibody solution in 4.0% horse serum. Add enough secondary antibody solution to fully cover the constructs, cover the dishes with aluminum foil, and incubate for 2 h at 18-24 °C.
Prepare the Hoechst solution (1:10,000) in PBS to stain the nuclei.
Remove the secondary antibody solution and incubate the micro-TENNS in the Hoechst solution for 10 min at 18-24 °C. Perform five rinses with PBS, each for 5-10 min. Flood the Petri dish with PBS to cover the stained micro-TENNs, wrap the dish in aluminum foil, and store at 4 °C until imaging is performed.
NOTE: Images for the immunolabeled micro-TENNs were taken with a laser confocal microscope with a resolution of 2,048 (~8 s/frame), a 10X objective (0.64 µm/pixel), 487-nm excitation and ~525 nm emission wavelengths for green fluorescence, 561 nm excitation and ~595 nm emission wavelengths for red fluorescence, and ~3.22 µm/slice with ~60 slices on average for the z-stacks.

Representative Results

Micro-TENNs were monitored using phase-contrast microscopy to assess their cytoarchitecture and axonal outgrowth (Figure 4). Within unidirectional, 2 mm long micro-TENNs, neuronal aggregates were restricted to one end of the micro-column and projected a bundle of axons through the inner core. Axons spanned the entire length of the column by 5 days in vitro (DIV) (Figure 4A). There was a greater initial axonal growth rate in bidirectional 2 mm-long micro-TENNs, as axons spanned the entire micro-column by 3 DIV (Figure 4B). By 5 DIV, bidirectional micro-TENNs featured dense axonal tracts that connected the aggregates maintained at the extremes of the micro-column. This cytoarchitecture was also observed in 5-mm micro-TENNs, with axons spanning the micro-column by 5 DIV (Figure 4C). As observed in all instances, the ECM in the lumen and the geometric restriction presented by the agarose provided the directionality required to form axonal tracts that structurally mimic features of native neuroanatomy.

Immunocytochemistry techniques were applied in this protocol, and confocal images were taken to verify the components of the micro-TENN architecture. Cell nuclei stained with Hoechst (blue) were localized almost exclusively within aggregates at the extremes of unidirectional and bidirectional micro-columns, with essentially no Hoechst staining in the interior (Figure 5). This observation confirmed what was inferred from the phase-contrast images: neuronal populations were restricted to the ends, and only axons (in red) spanned the lumen of the micro-TENNs. However, after axons crossed the aggregates, cell migration was observed along the axonal tracts into the inner lumen, as observed by the presence of nuclei (blue) in the interior at 28 DIV for a 2 mm-long bidirectional micro-TENN (Figure 6). Furthermore, synapsin I immunolabeling (green) was found throughout the cell bodies and axonal tracts (Figure 6). Synapsin I is a pre-synaptic terminal protein implicated in the regulation of neurotransmitter release and is indicative of the presence of pre-synaptic terminals when found in a punctate distribution; it has been previously correlated with the formation of active synapses by whole-cell patch recordings⁴⁹. The synapsin staining in the axon-rich central zone of the micro-TENN is likely a combination of puncta as well as synapsin being transported down axons towards pre-synaptic terminals. Nevertheless, the presence of synapsin puncta within the micro-TENN aggregates suggests that these constructs have the capacity to communicate through synapses, although the colocalization of synapsin with a post-synaptic protein would be required for further structural evidence of functional synapses.

Micro-TENNs were also fabricated with aggregated neurons that were transduced with an AAV containing the GCaMP6f calcium indicator to preliminarily probe the electrophysiological properties of these constructs. These constructs expressed the calcium indicator throughout their entire length, as shown by fluorescence in both the neuronal aggregates and the axonal tracts (Figure 7A). Note that due to microscope settings aimed at maximizing the intensity in the aggregates, the fluorescence in the axonal tracts appeared fainter. These transduced micro-TENNs were analyzed over time with high-speed fluorescence microscopy (without external electrical stimulation), and several cell-sized regions of interest (ROIs) were selected at random in a representative micro-TENN to characterize the signaling capacity of these constructs. Calcium concentration bursts were observed in almost all ROIs, as reflected with associated fluctuating fluorescence intensities throughout time (Figure 7B). Particularly, various ROIs seemed to show a near-constant periodicity of calcium concentration increases (Figure 7B). These calcium concentration changes are inferred to be the result of spontaneous, inherent action potentials, cell signaling within individual aggregates, and/or signaling across axons from distinct aggregates. Further analyses are required to fully characterize the electrophysiological properties of neurons and axonal tracts within micro-TENNs. Nevertheless, these initial results demonstrate that micro-TENNs exhibit robust endogenous/baseline electrical activity.

Figure 3: Blueprints of the laser-cut micro-column fabrication device and the 3D-printed pyramidal micro-well mold for cell aggregation. (A)-(B) Blueprint and image of the bottom and top halves of the cylindrical channel array, respectively, used to fabricate the hydrogel micro-columns. (C) Blueprint and image of the caps used to hold the device together. Both anterior and posterior pieces share the same dimensions. (D) Image of the assembled device required to fabricate the micro-columns. Only the two caps and the bottom half are clamped together with screws in the lower two alignment holes (left). The broken lines show the placement of the acupuncture needles through the five holes on each cap. The liquid agarose is added to the bottom half of the cylinders and, afterwards, the top half (right) is placed on the device to mold the liquid agarose into shape. (E) Blueprint of the 3D-printed molds used to make PDMS micro-well arrays. (F) Images of the 3D-printed mold (left) and the PDMS micro-well arrays (right). All dimensions are in millimeters (mm). Please click here to view a larger version of this figure.

Figure 4: Observation of axonal growth in micro-TENNS by phase-contrast imaging of unidirectional and bidirectional constructs as a function of days in vitro. (A) Unidirectional 2 mm long micro-TENNs show axonal tracts extending almost the entire length of the micro-column by 5 DIV. (B) Compared to unidirectional micro-TENNs, bidirectional 2 mm micro-TENNs display a faster axonal growth rate. (C) For 5 mm bidirectional micro-TENNs, axonal tracts populate the length of the micro-column at 5 DIV. This architecture is maintained at least until 10 DIV. Scale bars = 200 µm. Please click here to view a larger version of this figure.

Figure 5: Micro-TENN cytoarchitecture observed with confocal images of immunolabeled unidirectional and bidirectional micro-TENNs. Cells were stained for cell nuclei (Hoechst; blue) and axons (Tuj1; red). (A) Phase-contrast image of a 5 mm bidirectional micro-TENN (28 DIV). Confocal reconstructions (D)-(F) and (I)-(K) of a 5 mm bidirectional (28 DIV) and a unidirectional (25 DIV) micro-TENN, respectively, show labeled cell nuclei (D), (I) and axons (E), (J), as well as the overlay (F), (K). Scale bars: 500 µm. Insets in (A), (F), and (K) refer to phase-contrast (B)-(C) and confocal (G)-(H), (L)-(M) zoom-ins of neuronal aggregates and axonal tracts. The images show the aggregates restricted to the ends of the micro-TENN, while the lumen is spanned by aligned axonal tracts. Scale bars = 100 µm. Please click here to view a larger version of this figure.

Figure 6: Expression of the pre-synaptic terminal protein synapsin I in a representative bidirectional micro-TENN. The construct was stained for cell nuclei (Hoechst; blue), axons (Tuj1; red), and pre-synaptic boutons (synapsin I; green). (A) Phase-contrast image of a 2 mm bidirectional micro-TENN at 28 DIV. (D)-(G) Confocal reconstructions showing the cell nuclei (D), axons (E), pre-synaptic boutons (F), and an overlay (G) of the three channels. Boxes show zoom-ins (B)-(C), (H)-(I) of the phase-contrast and overlay images for the neuronal aggregates, respectively. Scale bars = 100 µm. Please click here to view a larger version of this figure.

Figure 7: Spontaneous signaling activity in a bidirectional micro-TENN observed through the expression of a genetically encoded calcium indicator. (A) Fluorescence microscopy confirmed the expression of the GCaMP reporter, as observed by fluorescence throughout the aggregates and axons. Scale bar = 100 µm. (B) Fluorescence changes associated with calcium concentration variations were measured without external stimulation at several regions of interest (ROIs) as a function of time. The numbered colored circles in (A) designate these ROIs. Please click here to view a larger version of this figure.

Figure 8: Phase-contrast images of common modes of failure in the micro-TENN methodology. (A) A completely dehydrated/dried agarose micro-column as a result of the removal and/or evaporation of DPBS in the initial stages of fabrication. Scale bar = 50 µm. (B) Hydrogel micro-column with the lumen lining the outer wall of the construct due to the lack of concentric alignment of the acupuncture needle with the capillary tube. Scale bar = 100 µm. (C) Seeded micro-TENN with both aggregates present at 1 DIV. (D) One of the aggregates fell off from the same micro-column as (C) at 3 DIV. (E) Unidirectional micro-TENN at 4 DIV. (F) The aggregate and axonal tracts fell out from the micro-column in (E) and remained floating in the culture medium at 5 DIV. Scale bar for (C)-(E) = 300 µm. Please click here to view a larger version of this figure.

Discussion

CNS injury and disease typically result in the loss or dysfunction of the long-distance axonal pathways that comprise the brain connectome, with or without concomitant neuronal degeneration. This is compounded by the limited capacity of the CNS to promote neurogenesis and regeneration. Despite the pursuit of repair strategies such as growth factor, cell, and biomaterial delivery as individual or combinatorial approaches, these techniques fail to simultaneously account for both the degeneration of neuronal cells and the loss of axonal connections¹⁴^,²². These gaps in technology limit the ability to repair, alter, and probe neural networks in a controlled and sustained fashion. Accordingly, the micro-TENN technology was developed to address the need for a neural repair strategy that, in contrast to existing methods, facilitates both neuronal replacement and the reconstruction of long axonal connections. Micro-TENNs are implantable living scaffolds with a preformed cytoarchitecture that approaches the systems-level building blocks of the brain connectome that are specifically designed for the targeted reconstruction, replacement, and modification of host neural circuits. These scaffolds are comprised of discrete population(s) of neurons connected by long axonal tracts within the ECM-containing lumen of miniature cylindrical agarose hydrogels. These constructs may be capable of functioning as synaptic relays to replace lost pathways and dynamically modulating native circuitry. In addition, in cases of isolated axonal degeneration (with source neurons remaining intact), micro-TENNs may possibly serve as guides for axonal regeneration based on the mechanism of axon-facilitated axon regeneration. This manuscript presented the fabrication protocol to reliably create micro-TENNs, with controlled geometry, phenotype, and functional characteristics. Phase-contrast microscopy, immunocytochemistry, and confocal microscopy demonstrated that micro-TENNs produced with the protocol exhibit the required cytoarchitecture and express the pre-synaptic terminal protein synapsin. Furthermore, it was shown that micro-TENNs possess intrinsic signaling activity, possibly due to action potentials, in the absence of external simulation. This was ascertained by the presence of near-synchronous fluctuations in the fluorescence associated with a genetically encoded calcium reporter.

Micro-TENN development can be summarized by three steps: (1) the fabrication of the hollow hydrogel tube, (2) the addition of ECM solution to the lumen of the tube, and (3) the seeding of aggregates of isolated neurons into the ends of the tube. The micro-columns can be fabricated with glass capillary tubes or with a micro-fabricated device containing cylindrical channels. This device can be created with any high-precision micro-fabrication method available to the investigator. Liquid agarose is poured into the channels of the device or into capillary tubes containing a centered acupuncture needle to create the hydrogel micro-columns. Following agarose gelation, the acupuncture needle is removed to produce the hollow lumen. Several common pitfalls occurring during fabrication or growth are highlighted in Figure 8. Note that some of the images displayed in Figure 4 and an extreme case in Figure 8B show the luminal portion precariously close to the wall of the cylinder. In order to produce an even wall thickness when using the capillary tube method, the tube-needle assembly should be held upright when put into contact with agarose, and the needle should be maintained in the center of the tube. Keeping the tube-needle assembly at an angle relative to the agarose surface promotes decentralization of the needle. Nevertheless, these precautions are difficult to implement, and the needle is more often than not resting along the walls of the capillary tubes. On the contrary, the main asset of the micro-fabricated device is that it features needle holes concentrically aligned with the cylindrical channels, promoting an adequate centralization of the needle and the lumen relative to the channel and micro-column, respectively. In addition, the device increases throughput by facilitating the fabrication of several micro-columns at the same time. Despite the benefit provided by the device, off-center lumens can still be created by using bent acupuncture needles. Micro-fabrication techniques also have an inherent tolerance that limits their effectiveness. In general, micro-column dehydration, for which an extreme case is shown in Figure 8A, should not be a hindrance if the recommendations provided throughout the protocol are followed. Note that the physical properties of the agarose used for outer encasement may need optimization for alternative neuronal subtypes, as improved cortical neuron survival and neurite outgrowth at higher (3-4%) versus lower (1-2%) agarose concentrations was observed¹⁰.

Micro-TENN development continues with the introduction of ECM into the micro-column lumen, which serves to provide an environment adequate for neuronal adhesion, survival, and outgrowth. In addition, the ECM, in combination with the geometric restriction and low porosity provided by the agarose hydrogel, restricts axonal growth to the longitudinal direction to produce the requisite architecture. The contents of the ECM solution can be optimized for the type of neuron used. For example, collagen alone promotes survival and axonal outgrowth in DRG micro-TENNs, whereas a combination of collagen and laminin is required for cortical neurons¹⁰. Moreover, ECM polymerization inside the micro-column is critical prior to cell plating, as the co-delivery of cells with unpolymerized ECM leads to decreased neurite outgrowth and fasciculation³¹. Note that even though the micro-column is initially filled with ECM solution, its contents polymerize into a soft gel and tend to contract during the incubation period, creating a space that permits the insertion of the cell aggregates. In addition, it is important to confirm that the ECM has entered the micro-column interior by inspecting under the stereoscope; complete absence and/or pockets of missing ECM results in a lack of axonal outgrowth from the aggregates. Micro-TENN fabrication culminates in the seeding of cortical neuron aggregates at the extremes of the scaffold. These neurons were dissected from rat fetuses using known procedures⁴⁸. It can be inferred that the majority of isolated cells are neurons because the embryonic rat cortex at the gestation time used for isolation is comprised of 99% neurons, and the defined culture medium used in the protocol is metabolically limiting for glial proliferation⁴⁹. Consequently, there should be minimal glial contamination, although staining for specific markers is required for confirmation. While this manuscript presented micro-TENN fabrication with cortical neurons, neurons from different brain regions (e.g., nigral, thalamic, and hippocampal) or with different phenotypes (e.g., excitatory, inhibitory, and dopaminergic) could be utilized according to the desired application and area of implantation. Previous iterations of the micro-TENN fabrication protocol involved seeding dissociated cells¹⁰^,³¹^,³². Although the desired cytoarchitecture has been obtained using the dissociated method, it was not achieved in all cases. In many instances, dissociated cells flooded the interior and resulted in several cell body clusters throughout the lumen, with processes connecting them in an extensive 3D network¹⁰^,³¹. The aggregate method, on the other hand, ensures the containment of cell bodies to the extremes, and is therefore integral to the success of the micro-TENN technology (Figure 5). The representative micro-TENNs shown in Figures 4-6 were fabricated with larger aggregates that were not completely inserted, and this can occasionally result in aggregates falling out of the micro-columns in culture, like the examples shown in Figure 8D and 8E. To prevent this, the aggregates can be fully inserted within the micro-column interior. If this situation presents itself even after applying the previous strategy, the initial incubation period can be extended to provide sufficient time for aggregate adhesion to the ECM. During culture, gentle handling of micro-TENNs is recommended to preserve the integrity of the hydrogel encasement and the cytoarchitecture; problems during micro-TENN manipulation are the cause of the curvatures obtained in the otherwise-aligned axonal tracts (Figure 5). Nevertheless, following the protocol presented in this article should result in the consistent fabrication of micro-TENNs with the expected neuronal/axonal architecture, pre-synaptic bouton distribution, and intrinsic electrical activity.

In spite of the promise that micro-TENNs hold, there are remaining challenges that may limit the applications of this technology. The current micro-column fabrication technique is limited by the decentralization of the micro-column lumen, which may cause an inconsistent presentation of mechanical cues to cells (e.g., stiffness), rupturing of the micro-column wall and the subsequent exposure of axonal tracts to the exterior, and problems during implantation. Even though the use of a micro-fabricated device has improved the outcome compared to capillary tubes, higher precision micro-fabrication techniques are required to increase the dimensional reproducibility of these constructs. The results in this manuscript showed that the micro-TENN methodology can reliably produce living scaffolds comprised of neurons and axonal tracts that resemble native neuroanatomy, particularly the axonal tracts that connect distinct brain regions. Nevertheless, micro-TENN length is a hurdle, depending on the length of the host axonal pathway that needs to be replaced. For example, tissue engineered nerve grafts (TENGs) are a separate living scaffold strategy utilized by our research group to repair extremely long nerve injuries. To replace these long gaps, the axons in TENGs can be lengthened to tens of centimeters by applying continuous mechanical tension in custom mechano-bioreactors¹^,²³^,⁵⁰. This "stretch growth" technique has also been applied to manipulate astrocytic process length to better imitate the structure of radial glial pathways⁵¹. On the contrary, the present micro-TENN technology does not yet offer this extent of control; the maximum attainable length is currently limited by how long the axonal tracts can grow in vitro based on traditional growth-cone-mediated extension. Moreover, even though the CNS has an intrinsic capacity for neurophysiological rewiring in response to various stimuli, and transplanted cells have the capacity of synaptically integrating with native circuitry, another limitation of this technology is that micro-TENNs rely upon the plasticity of the native brain and the ability of host networks to functionally integrate with the implanted construct⁵²^,⁵³^,⁵⁴^,⁵⁵. Finally, an innate deficiency of all implant-based approaches, such as micro-TENNs, is their invasiveness. Since neurons are generally in close proximity to capillaries, any type of surgical procedure can cause disruption in the blood-brain barrier, leakage of blood factors into the brain parenchyma, and an acute (and even a chronic) inflammatory response³¹. This response can damage host and micro-TENN neurons, negating the beneficial aspects of this technique. Nevertheless, micro-TENNs implanted into the corticothalamic pathway of rats survived for at least 1 month and showed evidence of structural integration with the host cerebral cortex¹⁰^,³¹. Furthermore, a previous publication from our research group presented a methodology enabling the needle-less implantation of micro-TENNs into rat brains³¹. In that approach, this hydrogel encasement strategy was augmented to include a thin (~20 µm) coating of carboxymethylcellulose, which, upon mild dehydration, presented sufficient stiffness to penetrate the brain without requiring a needle or guide³¹. This needle-less implantation method, coupled with the small cross-section of the micro-columns, should minimize damage to the brain during and after the stereotaxic implantation procedure.

Despite the preliminary success of micro-TENNs in vivo, future studies will need to confirm that these constructs synaptically integrate with native tissue and to investigate whether functional recovery is obtained in models of CNS injury and neurodegenerative disease¹⁰^,³¹. For example, tailored micro-TENNs may be designed with specific cell phenotypes and implanted into the corresponding degenerated pathway to reconstruct the network and restore function. To reduce the acute inflammatory response following implantation, the micro-TENN hydrogel shell may be doped with anti-inflammatory and pro-survival agents. Alternative fabrication techniques (e.g., 3D printing) may be developed to generate the hydrogel micro-columns with greater ease and with more precise features, including consistent centralization of the lumen and reproducibility of dimensions. The same biomaterial scheme employed with micro-TENNs may be modified to tackle other characteristic pathologies of CNS injury and disease. For example, our group has previously developed constructs comprised of longitudinally aligned astrocytic bundles along the collagen-coated lumen of an agarose hydrogel that structurally emulate radial glial pathways and the glial tube to facilitate axonal regeneration and neuronal migration⁵⁶. Additionally, stem cells, such as human embryonic stem cells (HESCs), induced pluripotent stem cells (iPSCs), and adipose-derived stem cells (ASCs), may be incorporated to fabricate autologous micro-TENNs on a per-patient basis to more closely resemble the lost cytoarchitecture and cell phenotype. These future modifications would increase the capability of micro-TENNs to replace degenerated pathways in vivo and would allow for the reconstruction of more sophisticated tissue architectures, incorporating astroglial support and axonal myelination, amongst other features. Genetically engineered neurons could also be seeded to either augment the regenerative action of micro-TENNs through the release of trophic factors or enable modulation of the CNS by the optogenetic stimulation of light-gated ion channels⁴³. These scaffolds could be fabricated with excitatory or inhibitory neurons to synaptically modulate existing dysfunctional host connections in conditions such as epilepsy, depression, drug addiction, or pain disorders¹. For instance, micro-TENNs forming predominantly GABAergic or glutamatergic synapses may be constructed to suppress or stimulate, respectively, up- or de-regulated pathways via synaptic integration and/or by bulk neurotransmitter release. Importantly, such self-contained modulatory constructs would theoretically be responsive based on host-network feedback¹. Similarly, micro-TENNs could be applied as brain-computer interfaces (BCIs), with optogenetically engineered micro-TENNs serving as intermediates between the brain and inorganic stimulating or recording devices. This application can be an alternative to microelectrode BCIs, which lack specific cell targeting and mechanical stability and have caused inflammatory responses, glial scar formation, and neuronal migration or loss when penetrated into the brain⁵⁷^,⁵⁸.

As in vitro test-beds, micro-TENNs can provide a powerful platform for the study of neurobiology and electrophysiology, serving as biofidelic models of the nervous system. Additionally, 3D constructs can serve as test-beds for treatment strategies when used as neural injury and disease models⁵⁹. As 3D constructs, micro-TENNs are capable of simulating the in vivo environment, which is characterized by complex cell-cell and cell-ECM interactions in all spatial directions that cannot be accurately represented in planar cultures⁴²^,⁶⁰^,⁶¹^,⁶²^,⁶³^,⁶⁴^,⁶⁵. Indeed, numerous investigations have established that the type of environment is critical for cells to present the morphology, proliferation, migration, gene expression, differentiation, and signaling exhibited in the native setting⁶⁰. The similarities between the 3D environment of these scaffolds and the brain itself are complemented by the degree of control that these constructs offer over their physical and biochemical properties⁴². This permits the engineering of micro-TENNs with different sets of mechanical, haptotaxic, and chemotaxic signals to study the effect of these cues, individually or synergistically, on neuronal survival, maturation, axonal extension, synaptogenesis, and mechanotransduction³²^,⁴²^,⁶³. Furthermore, the design flexibility of this micro-tissue engineering technique permits the construction of living scaffolds that mimic other features of brain tissue, such as the columnar, compartmentalized structure of the neocortex, spanned by the axonal tracts of the connectome, to further increase the power of this system as an in vitro platform to study the brain⁶⁵. As investigational platforms, micro-TENNs take advantage of the controlled setting of typical in vitro models, the expansive availability of design parameters in tissue engineering approaches, and the increased physiological- and pathophysiological-relevance of 3D platforms to become an ideal test-bed to advance neurobiological knowledge. The myriad of future directions for this technology epitomizes the versatility of micro-TENNs. This manuscript has demonstrated that the micro-TENN protocol can reliably produce tissue-engineered living scaffolds that mimic crucial features of brain neuroanatomy to offer new insights into neurobiological phenomena, including development, disease, and repair processes. These constructs may also synaptically integrate with native tissue to reconstruct damaged white matter tracts, replace lost neuronal cells, and modulate dysregulated pathways following CNS injury and disease.

Disclosures

The authors have nothing to disclose.

Acknowledgements

Financial support was provided by the National Institutes of Health U01-NS094340 (Cullen), T32-NS043126 (Harris), and F31-NS090746 (Katiyar)), the Michael J. Fox Foundation (Therapeutic Pipeline Program #9998 (Cullen)), the Penn Medicine Neuroscience Center Pilot Award (Cullen), the National Science Foundation (Graduate Research Fellowships DGE-1321851 (Struzyna and Adewole)), the Department of Veterans Affairs (RR&D Merit Review #B1097-I (Cullen)), the American Association of Neurological Surgeons and Congress of Neurological Surgeons (2015-2016 Codman Fellowship in Neurotrauma and Critical Care (Petrov)), and the U.S. Army Medical Research and Materiel Command (#W81XWH-13-207004 (Cullen) and W81XWH-15-1-0466 (Cullen)).

Materials

Laser cutter	Universal Laser Systems	PLS4.75	Used to fabricate the laser-cut micro-channel mold.
Laser-cut micro-column fabrication device	Custom-made	————–	Contact our research group if interested. Dimensions and blueprints provided in the manuscript.
Screws	————–	————–	#4-40 with a thread diameter of 3.05 mm
Nuts	————–	————–	#4-40 with a thread diameter of 3.05 mm
Acupuncture needle (180 µm diameter)	Lhasa Medical	sj.16X40	The diameter may be varied according to the desired size for the micro-column lumen.
Petri dish	Fisher	08772B
Dulbecco's phosphate buffered saline (DPBS)	Invitrogen	14200075
Polystyrene disposable serological pipet	Fisher	13-678-11D
Agarose	Sigma	A9539-50G
Capillary tube (398 µm diameter)	Fisher	21170D	The diameter may be varied according to the desired size for the micro-column shell.
Hot plate	Fisher	SP88857200
Magnetic bar	Fisher	1451352
Micropipette	Sigma	Z683884-1EA
25 mm gauge needle	Fisher	14-826-49
Microscalpel	Roboz Surgical	RS-6270
Scissors	Fine Science Tools	14081-09
Forceps	World Precision Instruments	501985
Hot bead sterilizer	Sigma	Z378550-1EA
Stereoscope	Nikon	SMZ800N	Used for all dissection steps and for micro-TENN fabrication.
Rat tail type I collagen	Corning	354236	Maintain at 4 ºC and remove only when needed. Use ice to preserve its temperature when in use.
Microcentrifuge tube	Fisher	02-681-256
Mouse laminin	Corning	354232	Maintain at 4 ºC and remove only when needed. Use ice to preserve its temperature when in use.
Neurobasal medium	Invitrogen	21103049	Basal medium for the culture of pre-natal and embryonic neuronal cells. Store at 4ºC and warm at 37 ºC before use.
Sodium hydroxide (NaOH)	Fisher	SS2661
Hydrochloric acid (HCl)	Fisher	SA48-1
Litmus paper	Fisher	09-876-18
Hank's balanced salt solution (HBSS)	Invitrogen	14170112	Store at 4 ºC.
0.25% Trypsin-EDTA	Invitrogen	25200056	Store at -20 ºC and warm at 37 ºC before use.
Bovine pancreatic deoxyribonuclease (DNase) I	Sigma	10104159001	Store at -20 ºC and warm at 37 ºC before use.
B-27 Supplement	Invitrogen	12587010	Supplement added to Neurobasal medium for the culture of hippocampal and cortical neurons. Store at -20 ºC and warm at 37 ºC before use.
L-glutamine	Invitrogen	35050061	Store at -20 ºC and warm at 37 ºC before use.
Sprague Dawley embryonic day 18 rats	Charles River	Strain 001
Pasteur pipette	Fisher	22-042816
15 mL centrifuge tube	EMESCO	1194-352099
Vortex	Fisher	02-215-414
Centrifuge	Fisher	05-413-115
Hemocytometer	Fisher	02-671-6
Objet30 3D-Printer	Stratasys	————–	Used to fabricate the pyramidal micro-well molds.
3D-printed pyramidal well mold	Custom-made	————–	Contact our research group if interested. Dimensions and blueprints provided in the manuscript.
Polydimethylsiloxane (PDMS) and curing agent	Fisher	NC9285739	Comes as kit with elastomer and curing agent. Use inside a chemical fume hood.
Funnel	Fisher	10-348C
1 ml pipette bulb	Sigma	Z509035
Micro-spatula	Fisher	S50821
12-well culture plate	EMESCO	1194-353043
Oven	Fisher	11-475-154
Incubator	Fisher	13 998 076
AAV1.Syn.GCaMP6f.WPRE.SV40	UPenn Vector Core	36373	Store at -80ºC. Commercially available adeno-associated virus (AAV) with the GCaMP6f calcium indicator.
Formaldehyde 40%	Fisher	F77P-4	Formaldehyde is a toxic compound known to be carcinogenic, and must be disposed of in a separate container.
Triton X-100	Sigma	T8787	Non-ionic surfactant used to permeabilize cell membranes.
Horse serum	Gibco	16050-122
Mouse anti-Tuj-1/beta-III tubulin primary antibody	Sigma	T8578-200UL	Store at -20ºC.
Rabbit anti-synapsin 1 primary antibody	Synaptic Systems	106-001	Store at -20ºC.
Donkey anti-mouse 568 secondary antibody	Invitrogen	A10037	Store at 4ºC.
Donkey anti-rabbit 488 secondary antibody	Invitrogen	A21206	Store at 4ºC.
Hoechst 33342, Trihydrochloride	Invitrogen	H3570	Store at 4ºC. Hoechst is a known mutagen that should be treated as a carcinogen. Therefore, it must be disposed of in a separate container.
A1RSI Laser Scanning Confocal Microscope	Nikon	————–	Used for taking the confocal reconstructions of immunolabeled constructs.
Eclipse Ti-S Microscope	Nikon	————–	Used for taking the phase-contrast images. With digital image acquisition using a QiClick camera interfaced with Nikon Elements Basic Research software (4.10.01).
High-speed Fluorescence Microscope	Nikon	————–	Nikon Eclipse Ti microscope paired with an ANDOR Neo/Zyla camera for calcium imaging.
NIS Elements AR 4.50.00 Software	Nikon Instruments	————–	Used to identify calcium transients from the recordings taken with the high-speed fluorescence microscope.

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Struzyna, L. A., Adewole, D. O., Gordián-Vélez, W. J., Grovola, M. R., Burrell, J. C., Katiyar, K. S., Petrov, D., Harris, J. P., Cullen, D. K. Anatomically Inspired Three-dimensional Micro-tissue Engineered Neural Networks for Nervous System Reconstruction, Modulation, and Modeling. J. Vis. Exp. (123), e55609, doi:10.3791/55609 (2017).

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