The TD Drive: A Parametric, Open-Source Implant for Multi&#45;Area Electrophysiological Recordings in Behaving and Sleeping Rats

Tim Schr&#246;der; Jacqueline van der Meij; Paul van Heumen; Anumita Samanta; Lisa Genzel

doi:10.3791/66457

JoVE Journal > Neuroscience

神经科学

The TD Drive: A Parametric, Open-Source Implant for Multi-Area Electrophysiological Recordings in Behaving and Sleeping Rats

Published: April 26, 2024

doi:

10.3791/66457

Tim Schröder^1,2, Jacqueline van der Meij¹, Paul van Heumen^1,2, Anumita Samanta¹, Lisa Genzel¹

¹Donders Institute for Brain, Cognition and Behaviour,Radboud University, ²3D Neuro B.V.

Summary

Here, we present a unique, 3D-printable implant for rats, named TD Drive, capable of symmetric, bilateral wire electrode recordings, currently in up to ten distributed brain areas simultaneously.

Abstract

Intricate interactions between multiple brain areas underlie most functions attributed to the brain. The process of learning, as well as the formation and consolidation of memories, are two examples that rely heavily on functional connectivity across the brain. In addition, investigating hemispheric similarities and/or differences goes hand in hand with these multi-area interactions. Electrophysiological studies trying to further elucidate these complex processes thus depend on recording brain activity at multiple locations simultaneously and often in a bilateral fashion. Presented here is a 3D-printable implant for rats, named TD Drive, capable of symmetric, bilateral wire electrode recordings, currently in up to ten distributed brain areas simultaneously. The open-source design was created employing parametric design principles, allowing prospective users to easily adapt the drive design to their needs by simply adjusting high-level parameters, such as anterior-posterior and mediolateral coordinates of the recording electrode locations. The implant design was validated in n = 20 Lister Hooded rats that performed different tasks. The implant was compatible with tethered sleep recordings and open field recordings (Object Exploration) as well as wireless recording in a large maze using two different commercial recording systems and headstages. Thus, presented here is the adaptable design and assembly of a new electrophysiological implant, facilitating fast preparation and implantation.

Introduction

The multi-area nature of brain interactions during wake and sleep makes it difficult to exhaustively study the ongoing physiological processes. While approaches such as functional MRI (fMRI) and functional ultrasound (fUS) allow sampling of brain activity from whole brains¹^,², they exploit neurovascular coupling to infer brain activity from hemodynamic activity, limiting their temporal resolution². In addition, fMRI requires the placement of the research subject in an MRI scanner, prohibiting experiments with freely moving animals. Optical imaging of calcium dynamics with single or multiphoton imaging enables cell type-specific recordings of hundreds of neurons simultaneously³. However, head-mounted microscopes such as the Miniscope³, which do allow freely moving behavior, are usually limited to imaging superficial cortical areas in intact brains⁴. While the diameter of their field of view on the cortex can be in the order of 1 mm, the space requirements of these head-mounted microscopes can make it difficult to target several, especially adjacent, areas. Therefore, to capture multi-area brain dynamics in wake and sleep accurately, extracellular electrophysiology, recorded with electrodes implanted in the brain areas of interest, is one of the methods of choice due to its high temporal resolution and spatial precision⁵. In addition, it allows the characterization of sleep dynamics in animals compatible with analyses obtained from human EEG, increasing the translational value of this method⁶.

Classically, studies recording brain activity with extracellular electrodes have employed individual wire electrodes or electrode bundles, such as tetrodes⁷. State-of-the-art probes such as the Neuropixels probe⁸ allow targeting several areas simultaneously, given that they are aligned on an axis that allows implanting the probe along that axis without impairing the animal. However, accurate simultaneous recordings of multiple, spatially separated areas still remain challenging, with existing methods being either costly or time-intensive.

In recent years, additive manufacturing methods such as stereolithography have become broadly available. This allowed researchers to develop novel electrode implants that were adaptable to their experimental requirements⁹, for example, simplified repeatable targeting of multiple brain areas. Frequently, these implant designs are also shared with the academic community as open-source hardware, allowing other researchers to adapt them to their own purposes. The degree of adaptability of specific implants varies both as a result of how the implant is designed and how it is shared. Parametric modeling¹⁰ is a popular approach in computer-aided design, in which different components of the design are linked by interdependent parameters and a defined design history. Implementing a parametric approach for designing implants increases their reusability and adaptability¹⁰, as changing individual parameters automatically updates the complete designs without the need for complex re-modeling of the design. A consequential necessity is that the design itself is shared in an editable format that preserves the parametric relationships and design history. File formats that only represent geometric primitives, such as STL or STEP, make subsequent parametric modifications of published models unfeasible.

While tetrode hyperdrives¹¹^,¹²^,¹³ enable recordings from dozens of tetrodes, their assembly and implantation are time-intensive, and their quality is largely dependent on the skill and experience of the individual researcher. In addition, they usually combine the guide tubes that direct the recording electrodes to their target location in one or two larger bundles, therefore limiting the number and spread of areas that can be targeted efficiently.

Other implants¹⁴^,¹⁵ expose the complete skull and allow for the free placement of multiple individual microdrives that carry the recording electrodes. While the placement of independent microdrives¹⁶ during surgery time maximizes flexibility, it increases surgery time and can make it difficult to target multiple adjacent areas due to the space requirements of the individual microdrives. In addition, while the implants are open source, they are only published as STL files, making modification difficult.

An example of a drive with a more inherent parametric philosophy is the RatHat¹⁷. By providing a surgical stencil that covers the whole dorsal surface of the skull, it allows precise targeting of multiple brain targets without the use of a stereotactic frame during surgery. Multiple implant variations for cannulas, optrodes, or tetrodes are available. However, while the drive is free to use for academic purposes, it is not published open-source, creating a hurdle for researchers to evaluate and use the implant.

Presented in this article is the TD Drive (see Figure 1), a novel 3D-printable implant for extracellular electrode recordings in rats. The TD Drive aims to overcome some of the drawbacks of existing solutions: it allows to target multiple brain areas, mirrored across both hemispheres, with independent wire electrodes simultaneously. Due to its simple design, it can be assembled in a few hours at a relatively low cost by less experienced researchers. The TD Drive is published open-source, in easily modifiable file formats to allow researchers to adjust it to their specific needs. Incorporating a parametric 3D modeling approach from the beginning of the TD Drive's design process allows the parameters necessary to be changed to be abstracted: to change target locations, researchers can simply edit the parameters representing their dorsoventral and anteroposterior coordinates, without the need for re-designing the drive themselves. The files to modify and manufacture the TD Drive can be found at https://github.com/3Dneuro/TD_Drive.

Figure 1: Overview of the TD Drive. (A) Rendering of a TD Drive with a protective cap. (B) Rendering with inner parts shown. The TD Drive features (a) multiple, parametrically adjustable recording locations for fixed and moveable electrode wires, an EIB with (b) a high-density Omnetics connector compatible with common tethered and wireless data acquisition systems, and (c) an intuitive channel mapping optimized for recordings with Intan/Open Ephys systems (see Supplementary Figure 1) and (d) a cap to protect the implant during tethered recordings and when no headstage is connected. (C) A guide stencil on the bottom of the TD Drive facilitates the placement of guide cannulas and serves as a redundant verification of implant locations during surgery. Please click here to view a larger version of this figure.

The implant design was piloted in n = 4, validated in n = 8, and confirmed in n= 8 Lister Hooded rats that performed different tasks. The first 4 animals were used to develop the drive and adjust parameters. Then, a full pilot was run with 8 animals (shown in results). A second cohort of 8 animals was run and included in the implant survival analysis. The implant was compatible with tethered sleep recordings and open field recordings (Object Exploration) as well as wireless recording in a large maze (HexMaze 9 m x 5 m) using two different commercial recording systems and headstages. The two cohorts of 8 were recorded with two different acquisition systems – tethered for longer sleep recordings and wireless for large maze exploration recordings. We can conclude that this simple wire drive allows for long-running experiments with larger cohorts by less experienced researchers to enable sleep stage analysis as well as oscillation analysis in multiple brain areas. This is in contrast to most electrophysiology implants to date, which, due to difficulty and time intensity, allow for smaller animal cohorts and usually need very experienced experimenters. However, with this drive, no individual neuron activity can be recorded; thus, the use is limited to investigations of local field potential (LFP) and summation activity.

Protocol

The present study was approved by the Dutch Central Commissie Dierproeven (CCD) and conducted according to the Experiments on Animals Act (protocol codes: 2020-0020-006 & 2020-0020-010). Male Lister Hooded rats of 9-12 weeks on arrival were used. The reagents and the equipment used in the protocol are listed in the Table of Materials. See Supplementary Figure 1 and Supplementary Figure 2 for the steps of the drive-building process.

1. Adjusting and creating 3D models and electrode interface board (EIB) data

Open the drive body design in Autodesk Fusion. Click on Change Parameters under the Modify tab. Adjust the coordinates for the first recording location by entering the anteroposterior coordinate in anteroPosteriorSite1 and the mediolateral coordinate in medioLateralSite1. One can adjust the diameter of the hole for the guide tube or electrodes by adjusting diameterSite1. Repeat for recording locations 2 and 3, and the model design will be automatically adjusted.
NOTE: The three locations used for the current protocol are hippocampus (HPC), containing moveable wire bundles, and prefrontal (PFC) and retrosplenial (RSC) cortex, both with fixed wire bundles (the PFC wire bundle targets both prelimbic (PRL) and anterior cingulate (ACC) cortex). Table 1 provides the manually imposed limits on the parameters controlling the mediolateral coordinates of the recording sites.
Export the updated drive body by right-clicking on it in the browser and selecting Save As Mesh. Select type STL (binary), units mm, and refinement high.
Select either the prepared STL files for the regular cap or, if needed (for example, when targets are very lateral), the prepared STL files for the large caps.
Depending on which cap one chooses, select either the regular or large EIB for production. The Gerber production files for both EIBs are provided as zip archives that can be sent directly to a manufacturing service.

2. Printing the 3D models and manufacturing the EIB

NOTE: For the present study, a commercially available 3D printer was used to produce the parts (see Table of Materials). When using different printers or outsourcing the production, different, comparable resins for producing the parts might need to be used.

Print the drive body and shuttles using stereolithography⁹ with a high resolution in a regular or biocompatible resin (e.g., Clear, Black, or White resin) with 25 µm layer height. Print the parts for the cap with a strong and sturdy resin (e.g., Tough 2000).
Either manufacture the EIB in-house or have it produced by an external service provider. Solder the high-density connector to the EIB using SMD (Surface Mounted Device) soldering techniques.
NOTE: When not experienced in soldering fine electronic components, it is recommended to have the soldering done externally, for example, at the university's electronics workshop or a commercial supplier. Reinforce the soldered high-density connector by applying a strong epoxy around the connector. Be careful not to cover the holes for the electrodes with epoxy.

3. Post-processing of the 3D-printed body

NOTE: Cap and shuttles should not need post-processing. Depending on the quality of the 3D prints, they might need to be lightly sanded or have leftover support traces removed. When sanding and drilling, take care not to break the walls of the drive body. If necessary, clean post-processed parts with isopropanol and, a soft cloth, and/or compressed air.

Drill out the holes for the guide tubes on top and on the bottom of the drive body with a 0.5 mm drill bit mounted in a pin vise. This ensures that the dimensions are correct and consistent across sites.
Drill out the two countersink holes (as in Figure 2E) on the drive body for the shuttle brass insert using a 2 mm drill bit in a pin vise.
Clean the countersink holes from drilling debris with compressed air. Then tap the guide holes for the shuttle screws, which are the extension of the countersink holes, with an M1 tap. Perform the tapping in two or more iterations, cleaning off debris from the tap and hole in between iterations. Optionally lubricate the tap with a drop of mineral oil.
Clean the drive body from drilling and tapping debris with compressed air.

Figure 2: Rendering of the TD Drive. (A,B) TD Drive (A) without and (B) with a protective cap on a rat skull model. (C) Polyimide guide tubes correctly inserted into each of the six recording sites. (D) An isolated, completed shuttle assembly featuring the guide screw, 3D-printed shuttle, and the soldered brass insert. (E) TD Drive body with two shuttles inserted. Marked in red: (a) countersink holes for the shuttle, (b) shuttle guide, (c) center pedestals of the drive body, (d) guide stencil.(F,G) Important locations on the top (F) and bottom (G) of the drive body that might require post-processing after 3D printing are indicated by a red arrow each. Please click here to view a larger version of this figure.

4. Shuttle assemblies

Slide a 3D-printed shuttle onto an M1x16 screw. Use an M1 brass insert to hold the 3D-printed shuttle in place. The shuttle needs to be able to rotate freely without moving up or down after the insert is placed.
CAUTION: The following steps contain burn hazards (soldering). Depending on the solder and soldering flux used, they might include exposure to respiratory irritants and lead. Always wear eye protection when soldering (as solder can splutter) and follow appropriate guidelines for safe handling of potentially harmful substances, including appropriate ventilation of the workspace to extract soldering fumes. Follow the local regulations and operating procedures or consult available material online¹⁸^,¹⁹.
Using a small amount of soldering paste, solder the brass insert to the screw. Take care not to overheat the insert and screw in order to not melt the 3D-printed shuttle. Depending on the resin used for 3D printing the shuttle, a small amount of melting (and, subsequently, the shuttle sticking to the insert) is hard to avoid.
NOTE: When using stainless steel screws, solder flux might be required. It is recommended to use brass or machine steel screws, as those are easier soldered.
After the shuttle assembly is cooled down, gently rotate the 3D-printed shuttle multiple times around the screw. If the shuttle fused to the insert during soldering, this should release it.
NOTE: Ensure that the shuttle can rotate freely and that it does not wobble. If it does, discard the shuttle assembly and start a new one. Carefully try to rotate the brass insert. If it rotates with respect to the screw, repeat the soldering process.

5. Assembling the drive

Cut commercially available polyimide tubes to approximately 25 mm in length, but at least long enough to extend through the complete drive body.
Insert the polyimide guide tubes into the drive body. Each tube should be inserted through one hole on the top of the drive and the corresponding hole in the guide stencil on the bottom of the drive ("d" in Figure 2E). The tubes should be inserted until they are flush with the top of the drive body.
Using a thin needle or toothpick, apply a small amount of liquid cyanoacrylate glue to the holes at the top of the drive body to fix the guide tubes in place. Apply the glue from the bottom side of the body to avoid glue running into the guide tubes. The glue will be drawn into the space between the drive body and guide tube by capillary forces and thus connect the two.
Apply a small amount of cyanoacrylate glue to the interface between the guide tubes and the guide stencil at the bottom of the drive body. Again, take care not to clog the guide tubes with glue. Let the glue dry for a few minutes.
NOTE: The exact amount of time necessary depends on the drive material and clearance between the drive body and guide tubes. Generally, 5-10 min should be sufficient.
Turn the drive body upside down and cut the polyimide guide tubes on the bottom so that they extend approximately 1 mm beyond the center pedestals of the drive body ("c" in Figure 2E and Supplementary Figure 2). In this configuration, the end of the guide tubes will be flush with the brain surface at implantation.
NOTE: The drive was developed to target deeper areas of the brain. If superficial cortical areas are targeted, shorter polyimide guide tubes might be necessary so as not to injure the brain surface in case of initial brain swelling.
Insert two shuttle assemblies in the drive body. While screwing them into the tapped guide holes, ensure that the screws are parallel to the shuttle guides ("b" in Figure 2E). Use fingers to gently align the shuttles with the shuttle guides.
Fully screw the shuttles down into the countersink holes to verify that the brass inserts of the shuttle assembly do not get stuck in the drive body or collide with the polyimide guide tubes. For this protocol, a minimum distance of 16 full turns is required. If this is not reached, cut the polyimide tube on top of the drive body further to create more space. Do not over-tighten the shuttle in the drive body – this can destroy the trapped threads on the drive body and the solder connection of the shuttle assembly.
NOTE: If a shuttle assembly gets stuck, remove it completely and check whether the solder connection loosened. In that case, use a new shuttle assembly. If the shuttle assembly collides with a guide tube, shorten the guide tube so that it does not extend beyond the drive body.
Screw the EIB to the drive body with M2.5×5 polyimide screws. Apply a few drops of cyanoacrylate glue between the drive body and EIB. Ensure not to clog the through holes for electrode connection.

6. Preparing the protective cover

Insert a stainless steel M2 nut into the extrusion on the left cap half and fix it with cyanoacrylate glue.
If necessary, drill out the hole at the front of the left cap with an M1 drill bit in a pin vise. Tap the hole on the front of the right cap half with an M1 tap.

7. Preparing the wire electrodes

Prepare two metal plates as the surface for creating the electrode wire bundles. The plates serve as a flat, stable, but moveable surface on which the wire bundle assembly, gluing, and cutting will occur. Attach plotting paper to the first plate and knot two sticky painters' tape onto the second plate, with the sticky surface pointing up.
Three out of the four wires in the HPC bundles will be cut at a 60-degree angle to create an offset in the dorsoventral direction. This will allow for the placing of a wire above, in, and below the hippocampal pyramidal layer, respectively. To facilitate the cut, draw a clear line with an angle of 60 degrees on the plotting paper (60-degree line).
For each HPC electrode bundle, cut 4 pieces of electrode wire with a length of 4.5 cm each. For each PFC and RSC electrode bundle, cut 4 pieces of electrode wire with a length of 3.5 cm each.
Gently pick up 4 wires by touching them with a fingertip (they will stick to it) and place them as close as possible next to each other on the painters' tape. Ensure not to put them on top of each other.
Under a microscope, use forceps to place the wires together as close as possible. Apply a thin layer of liquid cyanoacrylate glue to the first 2 cm of the top of the bundle. For the HPC bundle, glue > 2 cm and < 3.5 cm of the wire. Wait for the glue to dry.
Touch the wires gently with some forceps under a microscope. If they do not separate, they are glued correctly. As a sanity check, ensure that the layer of glue shines under the illumination of the microscope.
Once fully dried, remove the wire bundle from the tape and transfer it to the plate with the plotting paper. Under a microscope, check the wire bundle for excess glue on top or on the sides, and remove it carefully with a scalpel blade.
For the RSC bundles, make a straight cut at the bottom of the array, perpendicular to the direction of the wires.
For the HPC bundles, place the array on the plotting paper so that it intersects the 60-degree line, and use the line as a guide to make a cut angled 60 degrees to the direction of the wires.
1. Then, use a scalpel blade to carefully split the shortest of the 4 wires off the bundle. Cut the wire perpendicular to the wire direction, shortening it to approximately 0.75 mm compared to the second-longest wire in the bundle.
For the PFC bundles, split the bottom of the array into two 2-wire bundles. Ensure that the two wires are glued together well. Shorten one of the 2-wire bundles by 1 mm by cutting it perpendicular to the wire direction. See Supplementary Figure 1 (bottom) and Supplementary Figure 2b for images of the cut wire bundles.

8. Preparing the ground wire and EEG wires

Push at least 10 of the SIP/DIP pins out of a 1.27 mm pitch interconnected SIP/DIP socket strip.
Cut 2 pieces of 6 cm length for the ground (GND) wire. Cut 8 pieces of 6 cm length for the EEG wire. Use a scalpel blade to carefully remove some of the insulation from both ends of all wires.
Place a M1x3 stainless steel screw in a third hand, leaving as much space as possible accessible below the screw head. Wrap a de-insulated side of a GND or EEG wire around the shank of the screw, just underneath the head of the screw.
Apply a small amount of solder flux with a small needle or toothpick. Solder the wire to the screw. Ensure not to accidentally clog the slot of the screw head.
Place a SIP/DIP pin in the third hand so that the female side is accessible. Insert the de-insulated part of the opposite side of the wire into the SIP/DIP pin. Apply a small amount of solder flux and solder the wire to the pin.
Remove the soldered screw-wire assembly from the holder. This assembly will be implanted in the skull during implantation surgery.
Place another SIP/DIP pin in the holder, rotated 180 degrees (i.e., male side accessible). Apply a small amount of solder flux and solder a de-insulated side of the other wire to the male side of the pin.
Remove the soldered wire-pin assembly from the holder. This assembly will be later connected to the EIB, and the screw-wire assembly as well as wire-pin assembly will be connected to each other during implantation surgery using their two pins.
To reinforce the soldered connections, apply a small amount of cyanoacrylate glue to the connection between wires and pins.
After the glue has dried, verify that the SIP/DIP pins of the two assemblies can be connected smoothly. Use the check continuity option of a multimeter to verify that there is a continuous connection between the screw and the de-insulated wire end of the wire-pin assembly when both assemblies are connected. Optionally, color code each set of wires with nail polish (see Table of Materials) to simplify correct connection during implant surgery.

9. Loading the wire bundles into the drive

Attach the drive to a holder. Be careful not to apply too much pressure to the EIB or damage the high-density connector in this step.
Once the drive body is in a stable position, take one of the wire bundles and carefully slide it into the respective polyimide tube, either by hand or using a pair of fine forceps. Ensure the wire array is placed in the correct orientation (e.g., for the PFC array, the two longer wires of the array should be facing medial), and be careful not to bend the wire array.
Repeat the last step for all other wire bundles.
Use a thin forceps to grab one of the wires and carefully bend it towards the hole one wants to insert it in. Once inserted, use a gold pin to pin it into the EIB hole. Repeat this for all wires of the bundle and for all bundles.
1. Ensure that, during this stage, the wires make a nice loop above the EIB (this way, there is still room to move the bundle up and down the polyimide tube in order to adjust the length at the bottom of the tube) and that the array that is sticking out from the bottom of the polyimide tube does not become accidentally bent. Ensure to note down which wire of each wire bundle connects to each channel on the EIB. See Supplementary Figure 1 for an elaboration on the channel mapping of the TD Drive.
  NOTE: Alternatively, after loading each wire bundle (step 9.2), one can directly connect the wires to the EIB (step 9.4) and then proceed with step 9.2 + 9.4 for the remaining wire bundles. This can be varied based on the experimenters' personal preferences. See Supplementary Figure 2b for an example of a loaded TD Drive.
Adjust the length of the wire bundles to correctly target the recording locations by gently pushing or pulling the wire bundles in or out of the guide tube (see Supplementary Figure 2d).
NOTE: As the guide tubes are cut to be flush with the brain surface, the distance to which a wire bundle extends beyond the guide tube corresponds to the dorsoventral location of the target area. The moveable HPC wire bundles should be flush with the bottom of the guide tube, the fixed RSC bundles should extend 1.5 mm, and the fixed PFC bundles should extend 3.5 mm beyond the guide tubes. When pushing or pulling the wire assemblies, be careful not to pull individual wires out of the EIB on the top or to bend the bottom of the wire bundle.
When the fixed wire arrays (RSC and PFC) are aligned, apply a small amount of strong epoxy glue to the top of the guide tubes, gluing the bundles in place. While the epoxy is curing, ensure the wire bundles are still correctly aligned at the bottom.
To fix the moveable HPC wire arrays, first move the shuttle to the highest required position (in the experiments described in this article, at least 16 full turns/4 mm above the lowest position). Then push the wire bundles into the u-shaped opening of the shuttle and glue them in place with a small amount of a strong epoxy glue.
NOTE: Ensure the epoxy does not run down the bundle into the polyimide tube. When the epoxy is cured, apply a second layer of epoxy at the same spot to reinforce the connection and make it less likely for the connection to break when the shuttle is moved.
Carefully insert the open end of the wire-pin assembly of a GND wire through one of the through-holes marked GND. Fix it using a gold pin.
NOTE: When using a headstage in which GND and reference (REF) channels are shorted, a REF channel can also be used if more convenient.
Remove the drive from the holder; take care not to bend any of the wire assemblies. Re-attach the drive's front part in the same holder and insert 4 EEG wire-pin assemblies into the through-holes for the EEG channels (marked 2,4, 29, 31) and fix them with a gold pin each.
For all GND and EEG wires, use a multimeter on the continuity setting to verify the continuous connection between the gold pin on the EIB and the pin of the connected wire-pin assembly.
Store the drive. This can be done, for example, by attaching the cap to the drive body and storing it upside down.
NOTE: Prior to surgical implantation, sterilize the bottom of the drive using ethanol. All bone screws and GND/EEG wire assemblies should be sterilized in ethanol. Surgical instruments should be sterilized via an autoclave.

10. Drive implant surgery

NOTE: This step briefly outlines the surgical procedures for implanting the TD Drive. A more extensive implantation protocol, including a description of tools, as well as doses and concentrations of drugs, can be found in Supplementary File 1.

Sterilize the surgical tools and clean and sanitize the surgical area following the local institutional guidelines. To sterilize the implants, place the parts of the electrode wires that will be in contact with the brain in ethanol for at least one minute.
NOTE: Long exposure to ethanol or its fumes can weaken the cyanoacrylate glue. If the fumes are not trapped, prolong the immersion time of the wires in ethanol. In order to verify the integrity of the glue, it is recommended to find the optimal time with a test implant that is not used in an actual experiment.
Provide necessary pre-emptive analgesia, antibiotics, and gas anesthesia (isoflurane) in accordance with institutional and local guidelines.
Place the rat in the stereotactic apparatus. Shave the top of the head and disinfect the skin with povidone-iodine. Subcutaneously apply local anesthetic (lidocaine) and make a small incision on the skull on top of the midline.
Expose the skull by pulling the skin to the side. Remove connective tissue on top of the skull, dry, and clean the skull surface. Gently detach the muscles on the side of the skull to allow placement of anchoring screws.
Measure the bregma and lambda coordinates. For precise targeting, ensure that the skull surface is parallel to the anteroposterior-mediolateral plane of the stereotax by measuring the difference in the dorsoventral position of bregma and lambda. If the coordinates differ, adjust the position of the rat in stereotax by raising or lowering the mouthpiece.
Mark the craniotomies around the target locations (prelimbic cortex (AP +3.5 mm and ML + -1 mm), retrosplenial (AP+5.8 mm and ML +-1mm and hippocampus (AP -3.8 mm and ML + – 2.5 mm)).
Drill holes for GND/EEG screws and anchoring screws. Insert the screws and cover them with liquid dental acrylic. Drill the craniotomies and carefully remove the dura mater. Prevent craniotomies from drying out by applying sterile saline.
Carefully position the TD Drive on top of the craniotomies, ensuring the guide tubes are flush with the skull. Protect the guide tubes with petroleum jelly and attach the TD Drive to the skull with dental acrylic.
Lower the wire arrays targeting HPC slowly from their initial location (~1.5 mm DV from the brain surface) towards the pyramidal layer of hippocampal CA1. The pyramidal layer was reached progressively in the subsequent days during signal checks in the rats' recovery period.
Place the protective cap around the drive.
Turn off gas anesthesia and remove the rat from the stereotactic frame. Place the rat in a clean cage inside a heated chamber and provide wet food and water for recovery. Monitor the rat until it is active again, moving in the cage, eating, and drinking.
Bring the rat back to the housing room. Provide post-operative analgesia and care according to the institutional guidelines. For example, see the example of surgery protocol in Supplementary File 1.

11. EIB recovery

At the end of the experiment, recover the drive and remove the protective cover.
Remove the gold pins and connect electrode wires carefully. Unscrew the EIB from the drive body. By gently pushing soft tweezers between the EIB and the drive body or carefully lifting the EIB by hand, release the remaining cyanoacrylate bond that holds the EIB to the body.
Clean the EIB and gold pins for reuse on subsequent TD Drive implants. Before reusing an EIB, check the gold pin vias and high-density connector for wear. Only reuse the EIB if the vias are intact enough to allow a good connection between gold pins, electrode wires, and EIB and if the high-density connector's connection to the headstage is still sufficiently stable.

Representative Results

Using the instructions provided in the protocol, the TD Drive could be built easily by multiple experimenters. After drive development (n = 4), a full pilot was run with eight animals. An additional batch of eight animals was implanted, and experimental data collection was performed. As data analysis has not been completed on these animals, they have been included in the survival analysis, but not in other analyses (e.g., targeting or histology). Implant surgery was performed 2 weeks after arrival (see Figure 3A for the target locations used in the pilot). The implant was performed with usual surgical procedures and lasted ~3 h. An experienced surgeon performed initial implants and could teach both experienced as well as novice experimenters with 2-3 surgeries to independence.

Figure 3: Implant surgery, sleep data, and broadband activity. (A) Schematic overview showing the target locations for craniotomies (blue circles) and skull screws (green: EEG, blue: GND, gray: anchoring screws, note that two anchoring screws are on the side of the skull). (B) Photograph of implanted animals with a tethered headstage during sleep and wakefulness. (C) Example sleep data from tethered animal PFC (Prelimbic) and HPC (Ca1), divided in REM sleep with theta and NonREM sleep with delta, spindles and ripples. Y axis: microvolt, x axis: seconds. This data can be used for example for sleep scoring or oscillation event detection and analysis (D) Example broadband activity recorded wirelessly in an awake animal (noisy channels on the left were not connected). Please click here to view a larger version of this figure.

Figure 4: Implant durability, delta detections, and histology. (A) Survival plot for the implant for two rounds of longer-running experiments. Of note, on day 85, n = 8 finished the experiment and were planned to be perfused. (B) Data example for stability. Shown is the count of delta detections in the hippocampal channel over recording days (~3 days per week). Each animal showed a normal variation depending on the amount of sleep, but there was no general drift over time in the signal and thus detections. (C) Representative histology showing bilateral targeting for one rat. Left column: left hemisphere, right column: right hemisphere. AP coordinates indicate anteroposterior coordinates of the depicted slice, and arrows point to lesions in targeted areas. Magnification: 1.6x. Please click here to view a larger version of this figure.

All animals recovered well and tolerated the implant (Figure 3B). Frontal and retrosplenial electrodes were fixed, but the hippocampal bundles were movable. Hippocampal bundles were implanted at a dorsoventral depth of 2 mm and adjusted to maximize HPC coverage during 2 weeks of surgery recovery, where the signal was checked live during sleep habituation periods. In 7 out of 8 animals, all target sites were reached on at least one hemisphere (Table 2 for hit rates, see Figure 4C for representative histology). Wake and sleep recordings were performed successfully tethered in a recording box, as well as wireless recordings in a larger maze (example data Figure 3C,D). Animals kept the implants for 2 months, when individual animals would start losing them; however, the majority of animals kept the implants until the experimental end day 85-100 after implant (Figure 4A). During this time, the LFP remained stable, as can be seen in an example analysis where delta oscillations were detected (Figure 4B). There was normal variability across time but no systematic drift of the signal in any of the recorded brain areas (including the pyramidal layer of CA1). It is recommended that experiments be ended within 10-15 weeks after surgery. All EIBs could be recovered.

We have applied this implant mainly to measure sleep stages and sleep oscillations in response to learning and other interventions. For example, how oral CBD intake influences oscillation occurrence and coherence across brain areas (see Samanta et al.²⁰).

Parameter	Minimum value (mm)	Maximum value (mm)
medioLateralSite1	0.75	2
medioLateralSite2	1.5	5
medioLateralSite3	0.75	2

Table 1: Overview of the manually imposed limits on the parameters controlling the mediolateral coordinates of the recording sites.

Hemisphere	PFC	RSC	CA1 pyr.
Right	8 of 8	5 of 8	6 of 8
Left	8 of 8	7 of 8	7 of 8

Table 2: Hit rate for pilot of 8 animals. In 4 out of 8 animals, all electrodes were placed correctly. However, in 7 out of 8 animals, all brain areas were correctly targeted in at least one hemisphere (with the exception of 1 rat missing the CA1 pyramidal layer).

Supplementary Figure 1: TD Drive architecture. (Top) Overview of the channel mapping for the TD Drive when used with an Intan RHD32 headstage. (Bottom) An additional illustration of the wire bundle configurations.Please click here to download this File.

Supplementary Figure 2: Additional pictures of the TD Drive at several stages of the building process. Please click here to download this File.

Supplementary File 1: An example protocol for implantation of the TD Drive. The procedures and target locations are adjusted to the authors' research questions and institutional policies.Please click here to download this File.

Discussion

Presented in this article is an adaptable implant for bilateral, symmetric multi-area wire electrode recordings for freely-moving rats.

The ability to easily adjust the implant by changing predefined parameters was one of the motivations for the creation of the TD Drive. While aiming to maximize the flexibility for changing parameters, inherent constraints in the relations between them necessarily impose limits to this adaptability. No limits are set by default for the anteroposterior parameters, with these coordinates instead being governed by logical inter-site interactions and the overall size of the drive body. The parameters controlling the mediolateral coordinates of all recording sites are subject to manually imposed limits (see Table 1). Underlying the many parametric options are numerous interactions between the design features. These interactions can become disjointed under certain conditions. In an ideal situation, all possible combinations of parameter values are valid. However, with the more complex design of the TD Drive, it was opted to limit the mediolateral coordinates to within the tested range. Choosing coordinates outside the tested limits is, in principle, possible. However, making such changes is not recommended as the integrity of the design can become compromised, and restoring it while maintaining the out-of-limit coordinates might require CAD modeling experience. This is an inherent result of the trade-off between ease of drive production and flexibility – larger degrees of freedom do make the parametric definition of the drive more complex and can result in overly fine-grained, undesired outcomes (for example, the need to produce different EIBs for small changes in the drive design).

The parameter choices made in this manifestation of the TD Drive are guided by the preferences of the current experimenters. It was opted, for example, to increase the height of the TD Drive's pedestals, improving ease of implantation during surgery at the cost of a slightly higher final implant. However, the implant is still much smaller than drives with individually moveable tetrodes and was well-accepted by the animals. The two pedestals used to anchor the drive ("c" in Figure 2E) are deliberately placed in the center plane, parallel to the midline suture of the rat's skull. This limits recording locations to mediolateral coordinates > 0.75 mm. Often, the presence of the sagittal sinus below the midline imposes a similar limit for craniotomies anatomically. The current design of the TD Drive has been created in Autodesk Fusion. While it is one of the most advanced programs for parametric 3D computer-aided design and, at the time of publication, does provide a free license for academic use, the commercial and cloud-based nature of the program does pose a risk for the free availability of the design. Therefore, porting the design to a true open-source parametric CAD software²¹, such as FreeCAD, might be necessary for a future iteration.

The surgery for the TD Drive can be performed in 2-3 h. The target locations of the wire are marked stereotactically (PFC +3.5AP next to the midline, HPC -3.8AP -/+ 2.5 ML, RSC -5.8 next to the midline), and the screw electrodes, GND, and additional skull screws for stability are placed relative to those locations. While the TD Drive stencil does provide stereotactic locations, imprecisions in the placement of the polyimide tube and the use of less stiff tubing material can introduce small variations in the position of the electrodes. Therefore, it is recommended to drill small craniotomies (instead of guide tube-sized 0.5 mm burr holes) to account for this variability. In this surgery, a single, larger craniotomy for the RSC and HPC targets is drilled. For PFC and RSC, it was chosen to have wire bundles implanted at a fixed depth. The PFC bundle had wires targeted at two different depths to record from the prelimbic as well as the anterior cingulate cortex. The HPC bundles were movable and were built with 3 wires at varying heights to facilitate reaching the Ca1 pyramidal layer as well as the stratum radiatum. The last, shorter wire allowed recording from the PPC. We achieved the best results for targeting the hippocampal Ca1 when the longest electrode wire was moved to the target depth (2 mm ventrally from the brain surface) during surgery time, with only small adjustments in the two weeks after surgery during live-signal checks to accommodate for individual variances and brain swelling after surgery.

A problem with large implants, such as tetrode hyperdrives, in rats, is the chance of the implant stability degrading and animals losing the implant. For the TD Drive, individual failures were observed due to degradation of implant stability after 2 months (3 out of 16 animals). Therefore, the TD Drive is recommended for experiments with an intended maximum duration of 8 weeks. We show that for this time period, the signal is stable – even the precise hippocampal pyramidal layer recordings – and there is no systematic drift or significant wobble affecting the LFP recordings. One factor in achieving this long-term stability is the use of multiple skull screws (see Figure 3A). In certain situations, the amount of used skull anchoring screws can increase the risk of infections²². However, this is likely mostly relevant in head-fixed rats, where the repeated stress of the head fixation on the headplate and connected anchoring screws can result in degradation of the implant that facilitates infections. Another factor that increases the risk of implant failure (and can induce discomfort in behaving animals) is the weight of the implant. A complete TD drive implant with anchoring screws and dental cement weighs around 7 g, with the 3D printed parts and EIB accounting for approximately half of the weight. Due to the low weight of the TD drive (less than 1/3 of other large tetrode hyperdrives), excessive implant weight is unlikely to be a significant factor for failures of the TD drive. Generally, the main factor for stable, infection-free implants is a sterile surgery procedure and good adhesion of the dental cement that is coating the implant to the implant, anchoring screws, and skull²³. We only evaluated the TD Drive for the recording of local field potentials and did not attempt to acquire single-unit activity. While we expect the implant to be generally stable enough to do so, following the same units within and between sessions might require optimization of the shuttle stability, for example, by optimizing the shuttle guide rail ("b" in Figure 2E). The addition of moveable shuttles to the other recording sites would allow for additional use of moveable wire electrodes, which are the preferred way of ensuring better long-term signal quality in unit recordings.

With a total assembly time of around 3 h and surgery time of around 2-3 h, the TD Drive offers a compromise between tetrode hyperdrives and simpler, less adjustable multi-wire implants²⁴. With the chosen targets, recordings from 10 brain areas with 6 bundles were achieved. Compared to other implants for non-moveable wire bundles, the symmetric placement of recording sites yields another advantage: if lateralization is not relevant, simultaneously implanting wires in both hemispheres doubles the chance of hitting the correct target and the data yield per animal. In the pilot, 4 out of 8 animals had all 5 target sites (PFC including prelimbic (PRL) and anterior cingulate (ACC) cortex, RSC, PPC, and Ca1 pyramidal layer of HPC) targeted correctly bilaterally, but 7 out of 8 had at least each brain area on one side recorded. Thus, this drive is advisable for those who want a quick and easy-build solution to record LFP that can be applied by less experienced researchers, especially when higher animal numbers are needed, such as in sleep studies. With many high-end tetrode hyperdrives that would allow for the recording of individual neuronal activity, even very skilled and experienced researchers can only build and implant 2-6 implants per year of which many will not successfully reach any brain area of interest. It takes many years of training to achieve higher success rates, and even then, the number of animals that can be recorded efficiently remains low.

In summary, the TD Drive presents an easy and fast-to-build wire drive with 6 bundles that can be easily adapted to contain different recording sites and other implants such as cannulas and fibers.

Disclosures

The authors have nothing to disclose.

Acknowledgements

The authors would like to thank Angela Gomez Fonseca for the inspiration to develop the drive and all the students who ran pilot experiments with the animals, Milan Bogers, Floor van Ravenswoud, and Eva Severijnen. This work was supported by the Dutch Research Council (NWO; Crossover Program 17619 "INTENSE").

Materials

0.5 mm drill bit	McMaster	2951A38
1.27 mm pitch interconnected SIP/DIP socket (Mill-Max)	Mouser Electronic	575-003101	For essembling and connection of EEG & GND screws
5 minute epoxy	Bison	Commercially available	regular off-the-shelf epoxy
cyanoacrylate glue	Loctite		Super Glue-3
EEG wire	Science Products GmbH	7SS-2T
Electrode wire	Science Products GmbH	NC7620F
Ethanol	LC		For standard pre-operative sterilization procedure of drive
Fine forceps (5)	FST	91150-20	For wire bundle preperation and handling
Form 3B	Formlabs		3D printer used to 3D print the self-printed parts of the TD drive
Gold pins (small)	Neuralynx, Inc.	9885	Attachment of electorde wires to EIB board
Ground wire	Science Products GmbH	SS-3T/A
High-density connector	LabMaker GmbH/Omnetics	A79026-001
Lister Hodded rats	Charles River Laboratories	Crl:LIS	we used male rats, 9-12 weeks of age at arrival
M1 brass insert	AliExpress	Commercially available	https://aliexpress.com/item/33047616164.html
M1 tap	McMaster	2504A33
M1x16 screw	Bossard	1096613
M1x3 stainless steel screws	Screws and More	84213_14985
M2.5×5 polyimide screws	Screws and more	7985PA25S_50
mineral oil	McMaster	1244K14
Nail polish	Etos	Commercially available	For color coding EEG and GND wires
painter's tape	Gamma	Commercially available	For wire bundle preperation
Pin vise	McMaster	8455A16
plotting paper	Canson	Commercially available	For wire bundle preperation
polyimide tubes	Amazon / Small Parts	TWPT-0159-30-50	AWG, 0.0159" ID, 0.0219" OD, 0.0030" Wall, 30" Length
RHD 32-channel headstage with accelerometer	Intan Technologies, LLC	C3324	For tethered recordings in the sleepbox
RHD 3-ft (0.9 m) standard SPI cables	Intan Technologies, LLC	C3203	From commutator to headstage
RHD 6-ft (1.8 m) standard SPI cables	Intan Technologies, LLC	C3206	From OpenEphys box to commutator
Slip Ring with Flange	Adafruit	1196	Commutator: 22 mm diameter, 12 wires
Solder flux	Griffon S-39 50 ml	Commercially available	For soldering EEG & GND screws
soldering paste	Amazon	B08CBZ5HC5
stainless steel M2 nut	McMaster	93935A305
Tethered recording setup	OpenEphys	Acquasition Board
Wireless recording logger	SpikeGadgets	miniLogger 32	For wireless recordings in the task
Wireless recording setup	SpikeGadgets	Main Control Unit (MCU) incl. breakout board and RF transceiver	For wireless recordings in the task

References

Deffieux, T., Demené, C., Tanter, M. Functional Ultrasound Imaging: A New Imaging Modality for Neuroscience. 神经科学. 474, 110-121 (2021).
Finn, E. S., Poldrack, R. A., Shine, J. M. Functional neuroimaging as a catalyst for integrated neuroscience. Nature. 623 (7986), 263-273 (2023).
Aharoni, D., Federico Guo, C. Aharoni-Lab/Miniscope-v4: Release for generating. GitHub. , (2023).
Takasaki, K., Abbasi-Asl, R., Waters, J. Superficial bound of the depth limit of two-photon imaging in mouse brain. eNeuro. 7 (1), (2020).
Buzsáki, G., et al. Tools for probing local circuits: High-density silicon probes combined with optogenetics. Neuron. 86 (1), 92-105 (2015).
Lacroix, M. M., et al. Improved sleep scoring in mice reveals human-like stages. bioRxi.v. , (2018).
Wilson, M. A., McNaughton, B. L. Dynamics of the hippocampal ensemble code for space. Sci New Ser. 261 (5124), 1055-1058 (1993).
Jun, J. J., et al. Fully integrated silicon probes for high-density recording of neural activity. Nature. 551 (7679), 232-236 (2017).
Headley, D. B., DeLucca, M. V., Haufler, D., Paré, D. Incorporating 3D-printing technology in the design of head-caps and electrode drives for recording neurons in multiple brain regions. J Neurophysiol. 113 (7), 2721-2732 (2015).
Camba, J. D., Contero, M., Company, P. Parametric CAD modeling: An analysis of strategies for design reusability. Comput Aided Des. 74, 18-31 (2016).
Kloosterman, F., et al. Micro-drive array for chronic in vivo recording: Drive fabrication. J Vis Exp. (26), e1094 (2009).
Voigts, J., Siegle, J. H., Pritchett, D. L., Moore, C. I. The flexDrive: An ultra-light implant for optical control and highly parallel chronic recording of neuronal ensembles in freely moving mice. Front Syst Neurosci. 7, (2013).
Voigts, J., Newman, J. P., Wilson, M. A., Harnett, M. T. An easy-to-assemble, robust, and lightweight drive implant for chronic tetrode recordings in freely moving animals. J Neural Eng. 17 (2), 026044 (2020).
Sheng, T., et al. A novel 3D-printed multi-driven system for large-scale neurophysiological recordings in multiple brain regions. J Neurosci Methods. 361, 109286 (2021).
Vöröslakos, M., Petersen, P. C., Vöröslakos, B., Buzsáki, G. Metal microdrive and head cap system for silicon probe recovery in freely moving rodent. eLife. 10, e65859 (2021).
Mishra, A., Marzban, N., Cohen, M. X., Englitz, B. Dynamics of neural microstates in the VTA-striatal-prefrontal loop during novelty exploration in the rat. bioRxiv. , (2020).
Allen, L. M., et al. RatHat: A self-targeting printable brain implant system. eNeuro. 7 (2), (2020).
. Soldering Safety Available from: https://safety.eng.cam.ac.uk/safe-working/copy_of_soldering-safety (2018)
. Harvard Soldering Safety Guidelines Available from: https://www.ehs.harvard.edu/sites/default/files/soldering_safety_guidelines.pdf (2019)
Samanta, A., et al. CBD lengthens sleep but shortens ripples and leads to intact simple but worse cumulative memory. iScience. 26 (11), 108327 (2023).
Machado, F., Malpica, N., Borromeo, S. Parametric CAD modeling for open source scientific hardware: Comparing OpenSCAD and FreeCAD Python scripts. PLOS One. 14 (12), e0225795 (2019).
Schwarz, C., et al. The head-fixed behaving rat: Procedures and pitfalls. Somatosens Mot Res. 27 (4), 131-148 (2010).
Gardiner, T. W., Toth, L. A. Stereotactic surgery and long-term maintenance of cranial implants in research animals. Contemp Top Lab Anim Sci. 38 (1), 56-63 (1999).
França, A. S. C., van Hulten, J. A., Cohen, M. X. Low-cost and versatile electrodes for extracellular chronic recordings in rodents. Heliyon. 6 (9), e04867 (2020).

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Schröder, T., van der Meij, J., van Heumen, P., Samanta, A., Genzel, L. The TD Drive: A Parametric, Open-Source Implant for Multi-Area Electrophysiological Recordings in Behaving and Sleeping Rats. J. Vis. Exp. (206), e66457, doi:10.3791/66457 (2024).