A Real-Time Wearable Electromyography Measurement System for Small Animals

Summary

A protocol is presented for the installation and preparation of intramuscular electrodes, along with an animal-mountable, miniaturized measurement device for electromyography (EMG) analysis in locomotion studies. This system enables the wireless transmission of real-time EMG data for investigating locomotion recovery in stroke model rats.

Abstract

The intramuscular electromyography (EMG) measurement method for experimental animals has been implemented in various ways. Among these methods, tethering cables to external measurement devices can restrict the movement of experimental animals, while implantable devices may cause unwanted side effects due to the constant presence of a device with considerable size and weight. To address these issues, we propose a low-cost, wireless, detachable EMG measurement system and experimental procedure. This article focuses on the surgical installation of intramuscular wire electrodes with small connectors and the development of the wireless system. Notably, in this system, only the wire electrodes are inserted into the animal's body. Using this system, EMG measurements can be easily performed by attaching the circuit system to a connector installed on the animal's back, with real-time monitoring achievable on a laptop. The proposed method is explained in a detailed, step-by-step manner, followed by a demonstration involving the insertion of intramuscular electrodes into the hindlimbs of a rat. A treadmill experiment is conducted for a locomotion study, and the resulting electrophysiological signals are subsequently obtained and analyzed.

Introduction

Electromyography involves recording electrical potentials generated by muscle fibers during contraction. These properties are determined by neural activation signals sent from motor neurons to individual muscles. EMG is widely used in rehabilitation, motor, brain, and nerve-related studies, and the measurement methods can be broadly classified into surface EMG (sEMG) and intramuscular EMG (iEMG)¹. Surface electrodes offer several advantages, particularly in wearable applications, as they are non-invasive and require a simple preparation process². In implanted sEMG, the surgical process is simpler compared to iEMG, where the electrode does not need to penetrate the muscle. Despite these advantages, sEMG is prone to signal contamination, such as disturbances at the muscle-electrode interface, motion artifacts, the quality of the electrode contact, and signal crosstalk from adjacent muscles¹. These challenges are particularly problematic when the electrodes are placed in close proximity, as is often the case in studies involving small animals. On the other hand, iEMG requires an additional surgical procedure for electrode penetration. Despite the extra procedural steps, this method provides muscle-specific EMG recordings with greater precision and less crosstalk, as the electrodes are permanently embedded in the muscle tissue³. In small animal motor studies, iEMG is preferred since muscle-specific EMG information with reliable electrode installation is critical⁴.

Several approaches have been reported for acquiring EMG recordings from electrodes in small animals. Tether cables are commonly used to connect electrodes to external measurement equipment^{5,6,7,8,9,10,11}, devices can be implanted inside the body¹², or a wireless wearable platform can be placed on the animal¹³. Tether cables are the most widely reported method due to the availability of compatible commercial equipment for this purpose; however, the tether wires cause discomfort to the animals, and their movement is often constrained by the cables, which may impact the study. Implantable devices offer wireless solutions, but their limited battery life may restrict the duration of experiments. Additionally, the size and weight of permanently installed devices can cause stress and discomfort to the animals, which might affect the study. Wireless power transfer techniques have been proposed to address the issues in implantable devices, but maintaining a reliable energy link to a small device is typically very difficult¹⁴. Moreover, exposure to high electromagnetic fields can lead to unforeseen consequences, such as reduced immune function and potential neurodegenerative changes in the brain^15,16.

The acquisition system can also be implemented as a wireless, wearable platform that handles signal processing and wirelessly transmits the EMG recordings to a base station. Although this is the preferred method, it presents a technical challenge for the users, and experimental details are often not fully addressed in the literature.

In this work, we present a simple, low-cost, and reliable EMG acquisition method for locomotion studies in small animals. A pair of iEMG electrodes are implanted in the hindlimb muscles of a rat, while the rest of the signal acquisition system, including amplification, an analog-to-digital converter, and wireless telemetry, is mounted on the animal's back. The EMG data is transmitted to a personal computer for real-time monitoring, with data logged locally. A treadmill locomotion experiment is conducted to demonstrate the system in a stroke recovery study.

Protocol

Approval of all ethical and experimental procedures and protocols was granted by the Institutional Animal Care and Use Committee under Application No. CGU1-2021-IA0041. A 7-week-old male Sprague-Dawley rat was used in this study. The details of the reagents and equipment are listed in the Table of Materials.

1. Animal preparation

1. Prepare rats at the age of 7 weeks. For safety, house rats of similar weights together, with a maximum of three rats per cage.
2. Ensure the rats adapt without stress before surgery. Provide water and food consistently, and replace the bedding periodically.
3. During the adaptation period (about 7 days), train the animals to run on a treadmill at a speed of 16-25 m/min for 5 min each day to help them acclimate to the treadmill.
   NOTE: If a rat stops or refuses to move as intended, gently tap its buttocks for encouragement.

2. Electrode preparation

1. Prepare five stainless steel wires coated with polytetrafluoroethylene, four of them at a length of 140 mm and one at a length of 60 mm.
2. Tie three overhand knots on a 140 mm long wire, placing them at 40 mm and 100 mm relative to the knot (Figure 1A).
   NOTE: During the insertion of the wire electrode into the muscle, it can be challenging to ensure precise contact and to keep the exposed part of the electrode properly positioned. To address this, a blocking knot is created in the wire to prevent further insertion when pulled, ensuring that the electrode remains stable within the muscle.
3. For the 140 mm wires, leave a 2 mm gap from the knot on the short side, then partially strip off the insulation using a soldering iron for 2 mm. Fully strip the insulation from the end of the long side by 2 mm. For the 60 mm electrodes, completely remove the insulation at one end by 2 mm and at the other end by 10 mm (Figure 1).
   NOTE: The tip of the soldering iron should be thoroughly cleaned to prevent contamination.
4. Fix the wire by soldering it to the connector accessory after fully removing the insulation (Figure 2B,C).
5. Assemble the metal part to which the wire is connected into the plastic housing (Figure 2D,E).
6. Attach the connector to a 3D-printed plastic guide (see Table of Materials) that includes holes for securing it to the skin. To prevent the soldered part from contacting the incision site, apply biocompatible cyanoacrylate (Figure 2F).
7. Cut a 0.2 mm thick nickel plate and bend it to wrap around the connector, shielding it to prevent potential damage by the animal.

3. Surgery

1. Place the rat in an induction chamber (custom fabricated using a transparent synthetic resin) and administer anesthesia using a mixture of 70% nitrous oxide and 30% oxygen, with an isoflurane concentration of 2%-3%. Prepare the necessary surgical instruments (Figure 3).
2. Remove the fur using an electric hair clipper and prepare skin with chlorhexidine and alcohol to prevent infection during surgery (Figure 4A). 
3. Make an incision of about 10-15 mm using surgical scissors on the skin where the target muscle to be measured is located. Since the fascia lies beneath the skin, and muscles below that, first use scissors to cut the skin, then remove the fascia by gently wiping it away with a clean cloth.
4. Make an incision of 5-10 mm around the lumbar region where the connector will be attached.
5. Use sterile trochar to create a passage under the skin for the wire to pass from the connector to the target muscle position (Figure 4B).
6. Pass the trochar from the muscle position, under the skin, toward the incision site on the lumbar side.
7. Prepare the electrode and the connector from the previous stage. Pinch the wire electrodes at the incision site on the lumbar side using the forceps and carefully pull them through to the incision at the target muscle. Once the wire has been pulled out to the location of the target muscle, refer to Figure 4C.
8. As shown in Figure 4D, use a suture needle to penetrate the electrode wire into the target muscle.
   NOTE: The target muscle for this experiment is the medial gastrocnemius (MG), which is one of the key muscles for analyzing motor tasks¹⁷. Since the length of the MG is approximately 18 mm in 7-week-old rats, electrodes should be placed around the muscle's center, with a spacing of about 5 mm, to minimize muscle damage and ensure accurate EMG measurements. It is recommended that the length of the wire penetrating the muscle exceeds 5 mm to ensure that the part with the insulation removed is in good contact with the muscle.
9. Guide the wire that has passed through and exited the muscle back to its insertion point and secure it with an overhand knot. Cut the remaining wire (Figure 4E).
10. After installing the wire electrode in the target muscle, suture the incision site with 4-0 monofilament suture.
11. Suture the incision under the connector. Ensure that the entire wire is inserted into the body and securely sutured (Figure 5A).
12. Secure the connector to the animal's dorsal skin using a suture thread, as shown in Figure 5B.
    NOTE: Ensure the shield is securely fastened to prevent the animal from chewing on the connector. For analgesia, Carprofen (5 mg/kg) was given subcutaneously.
13. Once the surgical operation is complete, discontinue anesthesia and prepare a cage for the animal's recovery.
14. Turn on a heat lamp to prevent the animal's body temperature from dropping, and monitor the surgical site for any abnormalities, such as signs of infection, inflammation, or swelling. Disinfect the incision site thoroughly and apply ointment if necessary. Once the rat has recovered from anesthesia, remove the heat lamp.
15. Monitor the rat's behavior, including appetite, drinking, and urination.
    NOTE: After the surgery, allow the animal to rest for about 2 days before conducting any tests.

4. Printed circuit board (PCB) design and fabrication

1. Design the circuit for EMG measurement and digitization to include two analog amplifier integrated circuits (ICs) and a microcontroller unit (MCU). Ensure the amplifier has a bandwidth from 5-740 Hz and a gain of 1300 V/V.
   NOTE: Modify the amplifier gain and bandwidth according to the specific requirements of the animal if necessary¹⁸.
2. Include an integrated Bluetooth module in the MCU for wireless communication to transmit the measured data to the host device. A chip antenna operating at 2.4 GHz was used for this experiment.
3. Utilize a rechargeable 3.7 V Li-po battery along with a dedicated power management IC for this study.
4. Fabricate a PCB for the above ICs on an FR4 substrate. Create the PCB in various forms to meet specific requirements. Refer to Supplementary Figure 1, Supplementary Figure 2, and Supplementary Figure 3.
5. Populate the electronic components on the PCB either by soldering or using a heat gun.

5. Software configuration

1. Firmware
   1. Prepare the firmware (Supplementary Coding File 1) to configure a 2-channel ADC with 8-bit resolution and a sampling rate of 2 kSPs. Format the digitally converted data into an array and transmit it via Bluetooth Low Energy (BLE) using the designated software development tool.
   2. Upload the firmware to the MCU prior to deployment.
2. Real-time monitoring program
   1. Prepare a program to plot the data received via BLE in real-time. For this study, a Python-based plotting application is developed, which also stores the raw data in a specified location (Supplementary Coding File 2).
      NOTE: The system can experience a sampling buffer delay of at most 50 ms and a wireless communication delay of approximately 10 ms^19,20.

6. Treadmill test

1. Connect the battery to the prepared circuit and attach the PCB to the connector, as shown in Figure 6A.
2. Execute the monitoring program on the PC and establish wireless connectivity with the circuit PCB.
3. Place the rat on the treadmill and monitor the EMG waveform. For this study, the treadmill is set at a speed of 25 m/min (Figure 6B).

7. Data analysis

1. Load the EMG data stored in .CSV format.
2. Apply signal processing methods to remove unwanted noise and interference signals.
   NOTE: Envelope detection and spectral analysis can be further performed to analyze muscle fatigue and symmetry in motor activity.

Results

In this study, a simple wireless method for EMG acquisition is presented. While a surgical procedure is necessary, only the specific area for electrode insertion and connector fixation is partially incised, significantly reducing the burden on the animal. In this demonstration, electrodes were inserted into the lower extremities, but similar electrophysiological studies can be conducted in various other areas using the same method. This approach offers the advantage of continuous electrop...

Discussion

This work presents an electromyography (EMG) acquisition system that is small, easy to implement, low-cost, and wireless. The system effectively prevents signal degradation caused by cables, as it does not rely on any wired external measurement equipment. By mounting the connector on the back instead of the head, the surgical process becomes significantly easier, reducing the risk of complications. This setup also minimizes the chances of the platform bumping into side walls, which can lead to signal artifacts. Additiona...

Materials

Name	Company	Catalog Number	Comments
0.2 mm thickness nickel plate	Any available vender
3D-printing filament	cubicon	A-100
7 weeks old RAT	JABIO	SD (DBL) [7W M]
Adhesive	Okong	1028453	for securing shield
ANT1	Johanson Technology Inc.	2450AT07A0100001T
C1, C15, C16, C20	Vishay	1n	0201(0603)metric
C10, C13	Vishay	100p	0201(0603)metric
C11, C12	Vishay	4p	0201(0603)metric
C14, C19	Vishay	0.39n	0201(0603)metric
C2, C17	Vishay	22n	0201(0603)metric
C3, C5, C6	Vishay	0.1u	0201(0603)metric
C4, C18	Vishay	2.2u	0201(0603)metric
C7	Vishay	4.7u	0402(1005)metric
C8, C21	Vishay	1u	0201(0603)metric
C9	Vishay	1p	0201(0603)metric
Cage	JEUNG DO B&P	JD-C-02
Clean cloth	kimberly	41112
Connector accessory	Harwin	M20-1060400	Plastic housing
Connector accessory	Harwin	M20-1180042	Metal part
Electric hair clipper	Buzz	RFC-928
Heat gun	QUICK	861DW
IC1, IC3	Analog Device	AD8232	For EMG measurement AFE
IC2	Nordic semiconductor	nRF52832-CIAA
Isoflurane	Hana Pharm	657801261
L1	Vishay	3.3n	0201(0603)metric
Li-po battery	TheHan	TW402025	13 mm *10 mm * 4 mm, 30mAh
Pin header	Harwin	M22-2530505
R1, R2, R9, R10, R13, R14, R21, R22	Vishay	10M	0201(0603)metric
R11, R23	Vishay	100k	0201(0603)metric
R12, R24	Vishay	1M	0201(0603)metric
R3, R4, R5, R7, R15, R16, R17, R19	Vishay	180k	0201(0603)metric
R6, R18	Vishay	160k	0201(0603)metric
R8, R20	Vishay	768k	0201(0603)metric
Solder wire	Alpha metal	SACX0307
Soldering iron	Hakko	FX-951
Stainless steel wires coated with Teflon	A-M Systems	793200
Suture needle	AILEE	301289
Suture wire	Ethicon	604G
Treadmill	Daejong Bio	DJ2-243
U1	Torex Semiconductor	XC6204B332DR-G
Y1	Murata Electronics	XRCTD32M000N1P1AR0