The authors thank Jana Moon for her expert lab management and technical assistance and Charles Hwang for his imaging expertise. Experiments in this paper were in part funded through Plastic Surgery Foundation grants to SS (3135146.4) as well as the National Institute of Child Health and Human Development under Award Number 1F32HD100286-01 to SS, and the National Institute of Arthritis and Musculoskeletal and Skin Diseases of the National Institutes of Health under Award Number P30 AR069620.

All animal procedures and experiments were carried out with the approval of the University of Michigan&#39;s Institutional Care and Use of Animals Committee (IACUC). Male and female Fischer F344 and Lewis rats (~200-300 g) at 3-6 months of age are most frequently utilized in experiments, but any strain can theoretically be utilized. If utilizing donor rats instead of autologous muscle grafts, donor rats must be isogenic to the experimental strain. Rats are allowed free access to food and water both pre- and post-operativ...

The MC-RPNI is a novel construct that allows for amplification of an intact, peripheral motor nerve&#39;s efferent action potentials in order to accurately control an exoskeleton device. Specifically, the MC-RPNI confers a particular benefit to those individuals with extremity weakness caused by significant muscle disease and/or absence of muscle where EMG signals cannot be recorded. Reducing already compromised muscle function would be devastating in this population; however, the MC-RPNI has the ability to provide this ...

In the United States alone, approximately 130 million people are affected by neuromuscular and musculoskeletal disorders, resulting in over $800 billion in annual economic impact1,2. This group of disorders is typically secondary to pathology within the nervous systems, at the neuromuscular junction, or within the muscle itself3. Despite the variety of pathologic origins, the majority share some degree of extremity weakness1,3. Unfortunately, this weakness is often permanent given the limitations in neural and muscle tissue regeneration, especially in the setting of severe trauma4,5,6.
Extremity weakness treatment algorithms have classically focused on rehabilitative and supportive measures, often relying on harnessing the capabilities of the remaining intact limbs (canes, wheelchairs, etc.)7. This strategy falls short, however, for those whose weakness is not limited to a single extremity. With recent innovations in robotic technologies, advanced exoskeleton devices have been developed that restore extremity functionality to those living with extremity weakness8,9,10,11,12,13. These robotic exoskeletons are often powered, wearable devices that can assist with initiation and termination of movement or maintenance of limb position, providing a varying amount of force that can be individually tailored for the user8,9,10,11,12,13. These devices are classified as either passive or active depending on how they provide motor assistance to the user: active devices contain electrical actuators that augment power to the user, whereas passive devices store energy from the user&#39;s motions in order to release it back to the user when necessary14. As active devices have the ability to increase a user&#39;s power capabilities, these devices are utilized far more frequently in the setting of extremity weakness[14].
In order to determine motor intent in this population, modern exoskeletons commonly rely on pattern recognition algorithms generated from either electromyography (EMG) of distal limb muscles8,15,16,17 or surface electroencephalography (sEEG) of the brain18,19,20. Despite the promise of these detection modalities, both options have significant limitations that preclude widespread utilization of these devices. As sEEG detects microvolt-level signals transcranially18,19,20, criticisms frequently focus on the inability to differentiate these signals from background noise21. When background noise is similar to the desired recording signal, this produces low signal-to-noise ratios (SNRs), resulting in inaccurate motor detection and classification22,23. Accurate signal detection additionally relies on stable, low-impedance scalp contact21, which can be significantly affected by the presence of coarse/thick hair, user activity, and even sweating22,24. In contrast, EMG signals are several magnitudes larger in amplitude, facilitating greater motor signal detection accuracy15,18,25. This comes at a cost, however, as nearby muscles can contaminate the signal, decreasing the degrees of freedom able to be controlled by the device16,17,25 and an inability to detect deep muscle motion25,26,27,28. Most importantly, EMG cannot be used as a control method when there is significant muscle compromise and complete absence of tissue29.
In order to advance the development of robotic exoskeletons, consistent and accurate detection of motor intent of the intended user is required. Interfaces that utilize the peripheral nervous system have arisen as a promising interface technique, given their relatively simple access and functional selectivity. Current peripheral nerve interfacing methods can be invasive or non-invasive and typically fall within one of three categories: extraneural electrodes30,31,32,33, intrafascicular electrodes34,35,36 and penetrating electrodes37,38,39,40. As peripheral nerve signals are generally on the level of microvolts, it can be difficult to differentiate these signals from similar amplitude background noise41,42, which reduces the overall motor detection accuracy capabilities of the interface. These low signal-to-noise (SNR) ratios often worsen over time secondary to worsening electrode impedance43 produced from either degradation of the device39,43, or local foreign body reaction producing scar tissue around the device and/or local axonal degeneration37,44. Although these shortcomings can generally be resolved with reoperation and implantation of a new peripheral nerve interface, this is not a viable long-term solution as foreign-body-associated reactions would continue to occur.
To avoid these local tissue reactions generated from peripheral nerves&#39; interaction with abiotic interfaces, an interface incorporating a biologic component is necessary. To address this shortcoming, the Regenerative Peripheral Nerve Interface (RPNI) was developed to integrate transected peripheral nerves in the residual limbs of those with amputations with prosthetic devices45,46,47,48. Fabrication of the RPNI involves surgical implantation of a transected peripheral nerve into a segment of autologous free muscle graft, with revascularization, regeneration, and reinnervation occurring over time. Through the generation of milli-volt level compound muscle action potentials (CMAPs), the RPNI is able to amplify its contained nerve&#39;s micro-volt level signal by several magnitudes, facilitating accurate detection of motor intent45,48,49. There has been considerable development of the RPNI over the past decade, with notable success in amplifying and transmitting efferent motor nerve signals in both animal50,51 and human47 trials, facilitating high accuracy prosthetic device control with multiple degrees of freedom.
Individuals with extremity weakness but intact peripheral nerves would similarly benefit from high accuracy detection of motor intent through peripheral nerve interfaces in order to control exoskeleton devices. As the RPNI was developed for integration with transected peripheral nerves, such as in persons with amputations, surgical modifications were necessary. Building from experience with the RPNI, the Muscle Cuff Regenerative Peripheral Nerve Interface (MC-RPNI) was developed. Consisting of a similar segment of free muscle graft as in the RPNI, it is instead secured circumferentially to an intact peripheral nerve (Figure 1). Over time, it regenerates and becomes reinnervated through collateral axonal sprouting, amplifying and translating these efferent motor nerve signals to EMG signals that are several orders of magnitude larger52. As the MC-RPNI is biologic in origin, it avoids the inevitable foreign body reaction that occurs with peripheral nerve interfaces currently in use52. Furthermore, the MC-RPNI confers the ability to control multiple degrees of freedom simultaneously as they can be placed on distally dissected nerves to individual muscles without significant cross-talk, as has been previously demonstrated in RPNIs49. Finally, the MC-RPNI can operate independent of distal muscle function as it is placed on the proximal nerve. Given its advantages over current peripheral nerve interfaces, the MC-RPNI holds substantial promise for providing a safe, accurate, and reliable method of exoskeleton control.

<table border="1" fo:keep-together.within-page="1" fo:keep-with-next.within-page="always">
	<tbody>
		<tr>
			<td>#15 Scalpel</td>
			<td>Aspen Surgical, Inc</td>
			<td>Ref 371115</td>
			<td>Rib-Back Carbon Steel Surgical Blades (#15)</td>
		</tr>
		<tr>
			<td>2-N-thin film load cell (S100)</td>
			<td>Strain Measurement Devices, Inc</td>
			<td>SMD100-0002</td>
			<td>Measures force generated by the attached muscle</td>
		</tr>
		<tr>
			<td>4-0 Chromic Suture</td>
			<td>Ethicon</td>
			<td>SKU# 1654G</td>
			<td>P-3 Reverse Cutting Needle</td>
		</tr>
		<tr>
			<td>5-0 Chromic Suture</td>
			<td>Ethicon</td>
			<td>SKU# 687G</td>
			<td>P-3 Reverse Cutting Needle</td>
		</tr>
		<tr>
			<td>8-0 Monofilament Suture</td>
			<td>AROSurgical</td>
			<td>T06A08N14-13</td>
			<td>Black polyamide monofilament suture on a threaded tapered needle</td>
		</tr>
		<tr>
			<td>Experimental Rats</td>
			<td>Envigo</td>
			<td>F344-NH-sd</td>
			<td>Rats are Fischer F344 Strain</td>
		</tr>
		<tr>
			<td>Fine Forceps - mirror finish</td>
			<td>Fine Science Tools</td>
			<td>11413-11</td>
			<td>Fine tipped forceps with mirror finish ideal for handling delicate structures like nerves</td>
		</tr>
		<tr>
			<td>Fluriso (Isofluorane)</td>
			<td>VetOne</td>
			<td>13985-528-40</td>
			<td>Inhalational Anesthetic</td>
		</tr>
		<tr>
			<td>Force Measurement Jig</td>
			<td>Red Rock</td>
			<td>n/a</td>
			<td>Custom designed force measurement jig that allows for immobilization of hindlimb to allow for accurate muscle force recording</td>
		</tr>
		<tr>
			<td>MATLAB software</td>
			<td>Mathworks, Inc</td>
			<td>PR-MATLAB-MU-MW-707-NNU</td>
			<td>Calculates active force for each recorded force trace from passive and total force measurements</td>
		</tr>
		<tr>
			<td>Nicolet Viasys EMG EP System</td>
			<td>Nicolet</td>
			<td>MFI-NCL-VIKING-SELECT-2CH-EMG</td>
			<td>Portable EMG and nerve signal recording system capable of simultaneous 2 channel recordings from nerve and/or muscle</td>
		</tr>
		<tr>
			<td>Oxygen</td>
			<td>Cryogenic Gases</td>
			<td>UN1072</td>
			<td>Standard medical grade oxygen canisters</td>
		</tr>
		<tr>
			<td>Potassium Chloride</td>
			<td>APP Pharmaceuticals</td>
			<td>63323-965-20</td>
			<td>Injectable form, 2 mEq/mL</td>
		</tr>
		<tr>
			<td>Povidone Iodine USP</td>
			<td>MediChoice</td>
			<td>65517-0009-1</td>
			<td>10% Topical Solution, can use one bottle for multiple surgical preps</td>
		</tr>
		<tr>
			<td>Puralube Vet Opthalmic Ointment</td>
			<td>Dechra</td>
			<td>17033-211-38</td>
			<td>Corneal protective ointment for use during procedure</td>
		</tr>
		<tr>
			<td>Rimadyl (Caprofen)</td>
			<td>Zoetis, Inc.</td>
			<td>NADA# 141-199</td>
			<td>Injectable form, 50 mg/mL</td>
		</tr>
		<tr>
			<td>Stereo Microscope</td>
			<td>Leica</td>
			<td>Model M60</td>
			<td>User can adjust magnification to their preference</td>
		</tr>
		<tr>
			<td>Surgical Instruments</td>
			<td>Fine Science Tools</td>
			<td>Various</td>
			<td>User can choose instruments according to personal preference or from what is currently available in their lab</td>
		</tr>
		<tr>
			<td>Triple Antibiotic Ointment</td>
			<td>MediChoice</td>
			<td>39892-0830-2</td>
			<td>Ointment comes in sterile, disposable packets</td>
		</tr>
		<tr>
			<td>Vannas Spring Scissors - 2mm cutting edge</td>
			<td>Fine Science Tools</td>
			<td>15000-04</td>
			<td>Curved micro-dissection scissors used to perform the epineurial window</td>
		</tr>
		<tr>
			<td>VaporStick 3</td>
			<td>Surgivet</td>
			<td>V7015</td>
			<td>Anesthesia tower with space for isofluorane and oxygen canister</td>
		</tr>
		<tr>
			<td>Webcol Alcohol Prep</td>
			<td>Coviden</td>
			<td>Ref 6818</td>
			<td>Alcohol prep wipes; use a new wipe for each prep</td>
		</tr>
	</tbody>
</table>

the muscle cuff regenerative peripheral nerve interface for the amplification of intact peripheral nerve signals

Robotic exoskeletons have gained recent acclaim within the field of rehabilitative medicine as a promising modality for functional restoration for those individuals with extremity weakness. However, their use remains largely confined to research institutions, frequently operating as a means of static extremity support as motor detection methods remain unreliable. Peripheral nerve interfaces have arisen as a potential solution to this shortcoming; however, due to their inherently small amplitudes, these signals can be difficult to differentiate from background noise, lowering their overall motor detection accuracy. As current interfaces rely on abiotic materials, inherent material breakdown can occur alongside foreign body tissue reaction over time, further impacting their accuracy. The Muscle Cuff Regenerative Peripheral Nerve Interface (MC-RPNI) was designed to overcome these noted complications. Consisting of a segment of free muscle graft secured circumferentially to an intact peripheral nerve, the construct regenerates and becomes reinnervated by the contained nerve over time. In rats, this construct has demonstrated the ability to amplify a peripheral nerve's motor efferent action potentials up to 100 times the normal value through the generation of compound muscle action potentials (CMAPs). This signal amplification facilitates high accuracy detection of motor intent, potentially enabling reliable utilization of exoskeleton devices.

MC-RPNI surgical fabrication is considered a peri-operative failure if rats do not survive emergence from surgical anesthesia or develop an infection within a week of the operation. Previous research has indicated a 3 month maturation period will result in reliable signal amplification from this constructs42,45,48,49. At that time or thereafter, surgical exposure of the constructs and evaluatio...

Watch this Scientific Journal Video about The Muscle Cuff Regenerative Peripheral Nerve Interface for the Amplification of Intact Peripheral Nerve Signals at JoVE.com

The Muscle Cuff Regenerative Peripheral Nerve Interface for the Amplification of Intact Peripheral Nerve Signals

This manuscript provides an innovative method for developing a biologic peripheral nerve interface termed the Muscle Cuff Regenerative Peripheral Nerve Interface (MC-RPNI). This surgical construct can amplify its associated peripheral nerve's motor efferent signals to facilitate accurate detection of motor intent and the potential control of exoskeleton devices.

Robotic exoskeletons have gained recent acclaim within the field of rehabilitative medicine as a promising modality for functional restoration for those ...

Physiologic nerve signals are on the level of microvolts, which is far too small to record with currently available electrodes reliably. The MC-RPNI can interface with intact peripheral nerves, amplifying the small signals over a hundred times to facilitate reliable and accurate detection of motor intent. The primary advantage of this technique is its biological nature.It can interface with intact peripheral nerves long term without causing a detrimental effect on the nerve itself or distally innervated muscle targets. Powered exoskeleton devices capable of restoring function to those with extremity weakness are rarely utilized to their full potential due to an inability to detect motor intent reliably and accurately. Due to its biological nerve signal amplification capabilities, the muscle cuff RPNI is the answer to these shortcomings.Make a longitudinal incision along the anterior aspect of the desired donor hindlimb, extending from just above the ankle to just below the knee with a number 15 scalpel. Dissect the underlying subcutaneous tissue with sharp iris scissors to expose the underlying musculature and distal tendons just proximal to the ankle joint. Isolate the EDL muscle and its distal tendon from the surrounding musculature.Ensure isolation of the correct tendon by inserting both tines of a forceps or iris scissor underneath the distal tendon just proximal to the ankle joint. Open the forceps or scissors to exert upward pressure on the tendon. Perform a distal tenotomy of the EDL muscle at the ankle level with sharp iris scissors and dissect the muscle free from surrounding tissues working proximally towards its tendinous origin.Once the proximal tendon is visualized, perform a proximal tenotomy with sharp iris scissors to free the graft, trim both tendinous ends of the muscle graft and cut to the desired length with sharp iris scissors. Make a longitudinal incision along the entire trimmed length on one side of the muscle graft to facilitate placement of the nerve within the muscle graft and provide contact of the nerve with the endomysium. Place the prepared muscle graft in a saline-moistened gauze to prevent tissue desiccation.Mark the surgical incision, extending from a line approximately 5 millimeters from the sciatic notch to the inferior knee joint. Incise through the skin and subcutaneous tissues along the marked incision line with a number 15 blade. Carefully incise through the underlying biceps femorous fascia, taking care not to extend through the entire depth of the muscle as the sciatic nerve lies just below.Then dissect carefully through the biceps femorous muscle with blunt-tipped small scissors or a hemostat. Identify the common perineal or CP nerve and carefully isolate it from the surrounding nerves with a pair of micro forceps and micro scissors. Remove any surrounding connective tissue from the middle 2 centimeters of the nerve, taking care not to crush the nerve.Hold the proximal epineurium with micro forceps over the central most portion of the freed CP nerve and cut into the epineurium immediately with microdissection scissors. Then, travel distally along the nerve to make an epineurial window matching the muscle graft length and remove around 25%of the epineurium. Take care to remove this segment in one piece.Remove the muscle graft from the saline-moistened gauze and place it under the central portion of the CP nerve where the epineurial window was created. Rotate the nerve 180 degrees so that the epineurial window section touches the intact muscle and does not underlie the eventual suture line. Suture the CP nerve epineurium with an 8-O nylon suture proximally and distally to the muscle graft within the groove with simple interrupted sutures to secure epineurium to endomysium.Circumferential wrap the edges in the muscle graft surrounding the now secured nerve and suture in place with interrupted 8-O nylon stitches. Once hemostasis is achieved, close the biceps femorous fascia over the construct with 5-O chromic suture in running fashion. Close the overlying skin with a 4-O chromic suture in a running fashion.H&E staining of an MC-RPNI cross section shows the muscle and the nerve. Cross section of the ipsilateral distally innervated EDL muscle in a rat with an MC-RPNI demonstrated viable nerve and muscle tissue without any significant fibrosis or scarring compared to the cross section in a control rat without an MC-RPNI. Immunohistochemistry of a longitudinal section of an MC-RPNI specimen shows nuclei stained blue with DAPI and nerve tissue stained green.A closeup of another successful MC-RPNI shows multiple innervated neuromuscular junctions stained with alpha-bungarotoxin in red for acetylcholine receptors. Electrophysiologic testing performed at the MC-RPNI constructs showed that the generated compound muscle action potentials or CMAPs waveforms are similar in appearance to native muscle, further supporting that they have become reinnervated by their contained nerve. CMAPs generated by physiologic EDL muscle following proximal CP nerve stimulation typically range from 20 to 30 millivolts.EDL CMAPs in rats with implanted MC-RPNIs are not significantly different, averaging 24.27 millivolts plus or minus 1.34 millivolts. It is crucial to practice making an epineurial window before using it in a study. The epineurium is a very thin, fragile covering on the nerve, and damaging the underlying nerve fibers can alter results in highly unpredictable ways.These constructs are considered mature in rats after 3 months, and their customization capabilities are endless. Following maturation, the MC-RPNI can be utilized in physiologic assessments, electrophysiologic analysis and muscle force testing to name a few. End-to-side neurorrhaphy is a relatively newer concept within surgery where a transected nerve is coapted to an intact peripheral nerve inducing collateral sprouting from the intact nerve into the grafted segment.We've discovered this phenomenon also occurs in muscle grafted directly to the intact nerve and the possibilities for further research are fascinating.

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1.9K vistas.  The University of Michigan Health System. Las señales nerviosas fisiológicas están en el nivel de microvoltios, que es demasiado pequeño para registrar con los electrodos disponibles actualmente de manera confiable. El MC-RPNI puede interactuar con nervios periféricos intactos, amplificando las pequeñas señales más de cien veces para facilitar la detección confiable y precisa de la intención del motor. La principal ventaja de esta técnica es su naturaleza biológica.Puede interactuar con nervios periféricos intacto...