Neuroprosthesis for Individuals with Spinal Cord Injury

Abstract

Individuals who sustain a traumatic spinal cord injury (SCI) often have loss of multiple body systems. Significant functional improvement can be gained by individuals SCI through the use of neuroprostheses based on electrical stimulation. The most common actions produced are: grasp, overhead reach, trunk posture, standing, stepping, bladder/bowel/sexual function, and respiratory functions. We review the fundamental principles of electrical stimulation, which are established, allowing stimulation to be safely delivered through implanted devices for many decades. We review four common clinical applications for SCI, including grasp/reach, standing/stepping, bladder/bowel function, and respiratory functions. Systems used to implement these functions have many common features, but are also customized based on the functional goals of each approach. Further, neuroprosthetic systems are customized based on the needs of each user. The results to date show that implanted neuroprostheses can have a significant impact on the health, function, and quality of life for individuals with SCI.

Introduction

Significant functional improvement can be gained by individuals with spinal cord injury (SCI) through the use of neuroprostheses based on electrical stimulation. This paper focuses on implanted neuroprostheses that use electrical pulses to generate action potentials in targeted peripheral nerves. In the case of SCI, the stimulation is applied to paralyzed motor nerves and produces contraction of the desired muscle. In most cases, multiple nerves and muscles are targeted and the stimulation is patterned and coordinated so that the resulting muscle contractions produce the desired functional action. The most common actions produced are: grasp, overhead reach, trunk posture, standing, stepping, bladder/bowel/sexual function, and respiratory functions. We will begin this review by considering the perspectives and needs of spinal cord injured neuroprosthetic users.

Although this paper focuses on implantable neuroprostheses designed to provide functional independence, it should be noted that electrical stimulation can also be applied using electrodes applied to the surface and is often used as a means of exercise weak and partially paralyzed muscles. The most common application of this approach is for strengthening lower extremity muscles, and such exercise is often combined with bike riding and standing [Tefertiller et al., 2017]. Similar approaches have been applied for upper extremity strengthening [Popovic et al., 2006; Alon & McBride, 2003]. Prolonged use of electrical stimulation for exercise may result in recovery of function, although the mechanism is unknown [Inanici et al., 2018]. It may even be possible to strengthen denervated muscles if sufficient electrical current is applied [Kern et al., 2010; Lomo et al., 2014; Albertin et al., 2018]. In general, systems utilizing surface stimulation are applied temporarily to achieve strengthening and recovery. For permanent function requiring electrical stimulation, surface stimulation has been used for walking [Gallien et al., 1995] but implanted systems are typically utilized due to the repeatability of the response and the minimal donning and doffing required.

Neuroprosthesis User Perspectives in SCI

There is a growing recognition that inclusion of persons living with a disease/disorder as part of the research process is critically important for many reasons. Among those reasons are the opportunity to learn about everyday realities of living with that disease/disorder, the identification of research priorities, and the intention to target research efforts in a clinically relevant manner. When it comes to assistive technologies, the end user perspective is critical to design choices, risk mitigation, ease of use, cosmetic appearance, and benefits to target. With respect to applications involving electrical stimulation and neuroprostheses for SCI, there is some literature revealing the preferences of people living with SCI.

What do we know about the views of people with SCI about electrical stimulation in general? There are perceived physical benefits (improvements in muscle activity and function) as a result of using electrical stimulation [Donovan-Hall et al., 2011]. These benefits are perceived to have a positive impact on activities of daily living and, thus, quality of life. Barriers that were identified include access to equipment and inconveniences with donning/doffing, and not enough information and guidance about different types of neuroprostheses. An overarching recommendation from that study is the importance of getting user input early on in the design process.

A different group of investigators surveyed veterans living with SCI about their knowledge of and experience with various assistive technologies in general, including neuroprostheses using electrical stimulation, and design preferences for brain computer interface (BCI) technology specifically [Collinger et al., 2013]. For the other assistive technologies, including computer access equipment, functional electrical stimulation (FES), robotic gait training, spinal cord stimulator, robotic arm assistant, tendon transfers, transcutaneous electrical nerve stimulation (TENS), and hand orthoses, the majority of respondents had either never heard of them or had heard of them but never used them. This demonstrates a disturbing lack of knowledge and access to clinically available technology. With regard to BCI technology, the majority of respondents were interested in using BCI to control neuroprostheses for bladder/bowel, hand grasp, and lower body function. Important design characteristics included independent operation, non-invasiveness, cost, number of functions, and daily set-up time.

With respect to implanted neuroprosthetic technology, a concerted effort has been made to understand user preferences. A group of developers of neuroprostheses held a Consumer Forum to help them better understand the priorities of people living with SCI and how technology may impact their lives [Kilgore et al., 2001]. They included neuroprosthesis users and non-users in the forum. They found that research priorities depended on the individual, personal priorities, preferences, background, history, level of injury, etc., but there were some common themes that emerged. These included wanting technology that increased independence, ease of movement, ease of control, and spontaneity.

Brown-Triolo et al [2002] surveyed 94 individuals with paraplegia to identify preferences related to mobility issues. Among various mobility tasks involving the lower extremities, walking and standing were identified as high priorities to people with paraplegia. With respect to neuroprosthetic devices to provide those functions, devices requiring invasive procedures were as acceptable as those not requiring non-invasive procedures. Furthermore, restoration of function by the neuroprosthetic devices did not need to reach pre-injury levels. What was of high concern, however, was the external visibility of devices.

Return of bladder function is a high priority to individuals with SCI regardless of injury level [Anderson, 2004]. Neuroprostheses can be used to restore bladder function in some individuals. A choice-based conjoint analysis was conducted [Sanders et al., 2011] to determine the importance of various features of three neuroprostheses targeting bladder function (sacral root stimulation with rhizotomy, rhizotomy-free sacral root stimulation, and pudendal nerve stimulation). Rhizotomy-free sacral root stimulation was preferred over pudendal nerve stimulation. Sacral root stimulation with rhizotomy was least preferred. Importantly, it was revealed that side effects had the greatest impact on preferences followed by effect on continence and voiding, which were further followed by the degree of invasiveness, degree of user friendliness, and cost.

User satisfaction is high for implanted neuroprosthetic devices to improve hand grasp [Stroh Wuolle et al., 1999] and standing [Agarwal et al., 2003]. Electrically-stimulated hand grasp resulted in improvements in activities of daily living and independence, which had a positive impact on life [Stroh Wuolle et al., 1999]. From the perspective of users of an implanted neuroprosthetic standing system, the system increased quality of life, improved health status, decreased spasticity, improved emotional well-being, increased the sense of self-worth, increased mobility, increased function in social settings, made them feel more “normal”, decreased the need for caregivers, and enhanced the ability to work [Rohde et al., 2012].

Basic principles of Electrical Stimulation and Neuroprostheses

Neuroprostheses using electrical stimulation have been well-characterized over the past few decades. As we review here, the mechanism of action is known in detail. The parameters for safely delivering electrical stimulation have been established. The technology for delivering electrical stimulation to nerves has been refined over time and coupled with electronic control systems. The means of producing practical, deliverable systems using this approach have been developed. Figure 1 shows examples of the implanted neuroprosthetic components used to achieve the functions described in this review.

Figure 1.

Implanted neuroprostheses components utilized for motor functions described in this review. a) Eight channel implanted pulse generator, used for grasp/reach and for trunk/standing applications. b) Electrodes used to activate skeletal muscle. Electrode on the left is an epimysial style that is sutured to the muscle epimysium. Electrode on the right is an intramuscular electrode that is inserted inside the muscle via a probe. c) Probe and sheath used for intraoperative testing and insertion of intramuscular electrodes. d) Three channel implantable stimulator used for sacral anterior root stimulation for bladder function and also used for epidural stimulation to generate cough. e) Extradural electrodes that are sutured next to anterior roots for bladder function.

Mechanism of Action.

An electrical pulse produces an action potential in nerves through the depolarization of the voltage-gated ion channels in the nerve membrane. If the stimulus strength exceeds membrane threshold, the neuron will depolarize, generating an action potential. Action potentials generated along an axon in this manner will travel both orthodromically and antidromically, but otherwise are identical to a naturally-occurring action potential, and thus it is indistinguishable at the end organ. When the stimulus pulse is above threshold, every pulse will generate an action potential. The rate of activation is directly correlated with the stimulation rate.

Safe Stimulation.

Electrical stimulation can be safely delivered to nerves through the proper selection of stimulus parameters and electrode design. The critical electrical stimulation parameters include charge per phase, charge density per phase, and maintaining a zero net charge. The electrode geometry and electrode materials also contribute to long term biocompatibility and safety.

Biphasic stimulation with zero net charge should be used as this allows pulse to pulse reversal of the electrochemical reactions at the electrode-tissue interface [Mortimer, 1981; Merrill et al., 2005]. In general, the first phase is cathodic (at the activating electrode) and is typically a rectangular pulse defined by the pulse duration (PD) and pulse amplitude. Charge per phase and charge density per phase of the cathodic activating pulse have been identified as primary factors in determining safe stimulus levels [Pudenz, et al., 1977; Mortimer, 1981; Agnew, et al., 1990a; McCreery, et al., 1990]. In general, charge densities in the range of 10–100 µC/cm² per phase are in the safe region for brain tissue, and even higher charge densities can be tolerated in the peripheral nervous system. The maximum stimulation output for a number of commercial and research-based neurostimulation and neuromodulation devices are shown in Table 1. The maximum charge per phase and charge density per phase are also shown for these devices.

Table 1.

Safe Levels of Electrical Stimulation

Parameter	Safe Level	Tissue	Reference
Charge Density	0.4 μC/mm2	muscle	Mortimer, 1981
	0.3 μC/mm2	brain	Pudenz, et al., 1975
	0.18 μC/mm2	nerve	Yuen, et al., 1984
	0.032 μC/mm2	nerve	McCreery, et al., 1992
	0.01 μC/mm2	nerve	Proposed Waveform
Charge per Phase	2.0 μC/ph	muscle	Mortimer, 1981
	1.0 μC/ph	brain	McCreery, 1990
	0.45 μC/ph	brain	Pudenz, et al., 1975
	0.4 μC/ph	nerve	Yuen, et al., 1984
	0.1 μC/ph	nerve	Proposed Waveform

The tissue response is independent of stimulus frequency when the frequency is below 50Hz. Most motor neuroprosthetic applications use frequencies of 20Hz or lower, so frequency is not a factor. For stimulation rates above 50Hz, there is some evidence of a “mass action” effect, in which damage occurs in the nerves due to the increased overall nerve activity [Agnew, et al., 1990b; McCreery, et al., 1992; McCreery, et al., 1995]. This has the effect of reducing the expected safe levels of charge density per phase when higher frequencies are used.

A variety of safe and durable electrode materials have been identified and utilized in pre-clinical and clinically deployed electrical stimulation devices. Common electrode materials are 316LVM stainless steel, platinum and platinum-iridium (90%−10% most commonly) [Smith et al., 1987; Naples et al., 1990]. Titanium is commonly used as the return current electrode, particularly when the pulse generator case serves as the return. Other materials have been evaluated due to their potential for increased charge density, such as tantalum and activated iridium, but these are of primary interest for use in intra-cortical activation, where the tissue is more sensitive and where very small surface areas are required.

Electrode geometry is primarily important for the direct mechanical effect of the electrode on the tissue rather than the electrochemical impact. Electrodes should not have sharp surfaces and should be anchored in the tissue to avoid abrasion effects during movement. Lead routing should be oriented so that the lead tethering does not place significant torques on the electrode. Leads should also be routed so that they do not lay next to a nerve, which may result in compression damage. The sizing of nerve cuff electrodes has been studied extensively, and it is important that the cuff be sized appropriately for the target nerve [Naples et al., 1988].

It is important to note that the anterior horn cell, axon, neuromuscular junction, and muscle fiber must be intact for electrical stimulation to be effective [Bryden et al., 2018]. Direct activation of muscle faces challenges due to the large current and charge required for depolarization, which is approximately two orders of magnitude higher than the threshold for nerve stimulation [Mortmer, 1981]. This is true even for electrodes inserted into muscle tissue.

The stimulus threshold of any neuron is inversely proportional to the diameter of the neuron. Large-diameter neurons, which have the lowest threshold for stimulation, are activated first, followed by smaller neurons down to the smallest C-fiber [Kayagil et al., 2008]. This property of electrical stimulation is called the reverse recruitment order, as normal volitional motor activation adheres to Henneman’s size principle [Bawa et al., 1984] which entails progressive activation of smaller motor units recruited before large motor units. It is commonly reported that this reverse recruitment results in rapid fatigue, severely limiting the usefulness of neuroprostheses. In practice, however, this has not proven to be a major issue except for high force activities such as standing and walking.

Electrical stimulation can produce graded muscle force output either through spatial or temporal summation. Spatial summation is by far the most commonly utilized in neuroprostheses. As the intensity of the stimulus pulse (either current amplitude or pulse duration, or both) is increased, the current spreads and activates a progressively larger region of neurons, resulting in increased muscle contraction strength. Current can also spread to nearby nerve fibers innervating additional muscles, a characteristic referred to as spillover. In most functional applications, it is desirable to isolate the recruitment to single muscles or muscle groups. Temporal summation occurs when the rate of stimulation is increased, resulting in a more rapid contraction of muscle fibers. In practice however, low frequencies (less than 10Hz) produce individual twitches that are generally not useful for producing the tonic forces necessary for functional tasks. Higher frequencies (greater than 25Hz) result in rapid fatigue. Given these constraints, the frequency range of neuroprosthetic systems is typically 12Hz – 20Hz, leaving little room for temporal summation.

One aspect that separates neuroprostheses from typical neuromodulation devices or even pacemakers is that users are given direct control over when and how the stimulation is delivered. This is because the stimulation produces a motor activity that must be incorporated into the individual’s daily routine. Figure 2 shows some of the different control methods used for implanted neuroprostheses. For some systems, such as those for cough or bladder function, the user activates a switch that triggers the function. A preprogrammed stimulation pattern is then delivered to the target nerves/muscles to produce the desired effect. For other systems, particularly for upper and lower extremity function, the control systems are much more incorporated into the patterning of the stimulation. For these systems, real-time adjustments to the stimulation are necessary – such as step-to-step adjustments or smooth control of grasp opening and closing. A key goal in these systems is to develop a control method and algorithm that is as natural and unobtrusive as possible. “Natural” in this context means that as the user volitionally attempts to make the desired movement and the control system properly interprets the intention and then delivers the appropriate stimulation pattern to accomplish the desired movement. In practice, however, it is rarely possible to interpret an individual’s intended movement with a high degree of accuracy. Therefore control systems usually require a period of training in order to gain proficiency in the use of the system.

Figure 2.

Methods of user control of neuroprosthetic systems. a) Control of grasp and release can be achieved using myoelectric control. Shown is the placement of a bipolar myoelectric signal recording electrode placed on the wrist extensor. Inset shows electrode skirt sutured to muscle epimysium. Leads are routed subcutaneously to implanted controller. b) Finger-mounted switch used to control standing and stepping functions for implanted neuroprostheses. Switches are mounted on a ring and used to initiate and terminate desired stimulation patterns. c) Diaphragm pacing control system, worn by the user but generally controlled by caregiver. Stimulation intensity and breathing rate can be adjusted as necessary. d) External control device for implanted bladder/bowel control system. The user depressed one of three pre-programmed patterns, depending on the desired function.

Implanted Grasp and Reach Neuroprostheses

Hand and arm control is the most highly desired function for people with spinal cord injury at the cervical level [Anderson, 2004]. Electrical stimulation of the paralyzed muscles of the hand and arm can be used to provide grasp and reach for individuals with cervical SCI. A key aspect of these upper extremity neuroprostheses is that the user requires real-time control over the movements of the arm and hand so that these movements can be incorporated into intentional functional tasks [Scott and Haugland, 2001]. This control is derived from the user’s remaining voluntary function, and can include joint movement, myoelectric signals, and direct brain control through a brain-computer interface (BCI).

Upper extremity neuroprostheses are often combined with other surgical interventions such as tendon transfers and nerve transfers [Keith et al., 1996; Kilgore et al., 2018]. Tendon transfers involve disconnecting the tendon insertion of a muscle under voluntary control and connecting it to the tendon of a paralyzed muscle so that contraction of the donor muscle results in movement that was previously paralyzed. Tendon transfers have been used quite extensively for restoration of pinch and elbow extension in cervical SCI [Keith and Peljovich, 2012]. The criteria is that the patient have a transferrable muscle available as the donor. Common transfers can provide elbow extension, wrist extension, thumb flexion, and finger flexion. These functions can be combined with the electrically-stimulated function obtained from a neuroprosthesis.

Recently, the use of nerve transfers has begun to be studied in SCI [Van Zyl et al., 2019]. In this case, a donor nerve is selected and crossed to a nerve that innervates a paralyzed muscle that one wishes to have under voluntary control. The transferred nerve grows down the paralyzed nerve tract and reinnervates the target muscles. Recovery of function typically requires 6–12 months. Nerve transfers usually need to be performed within six months of injury in order to utilize a viable nerve tract for regrowth.

The first commercially available implanted neuroprosthesis to provide significant gains in hand and arm function for individuals with tetraplegia was the Freehand System. The Freehand ® neuroprosthesis utilized an eight-channel receiver-stimulator (IRS-8), eight epimysial or intramuscular electrodes, leads, and connectors [Keith et al., 1989]. Electrodes were surgically placed on or in the paralyzed muscles of the forearm and hand, and an inductive link provided the communication and power to the implanted pulse generator. Figure 3 shows the steps for implantation of intramuscular electrodes. The external components of the neuroprosthesis were an external control unit, a transmitting coil, and an external shoulder position transducer. The external control unit performed the signal processing of the control inputs and generated the output signal delivered to the implant. Two grasp patterns were provided for functional activities: lateral pinch and palmar prehension [Kilgore, et al., 1989]. Control of grasp opening and closing was achieved through graded elevation of the user’s contralateral shoulder [Johnson and Peckham, 1990]. The Freehand system was transferred to industry (NeuroControl Corp.), and was implemented successfully in over 220 patients [Peckham et al., 2001; Pancrazio et al., 2006]. Premarket approval (PMA) from the FDA was received in 1997, and over 40 sites internationally were trained in its deployment.

Figure 3.

Implantation of an intramuscular electrode in the dorsal intrinsic muscles of the hand. a) After probe with sheath has been used to verify stimulated response, the probe is removed and the electrode inserted into the sheath until it protrudes from the sheath and anchors in the muscle. b) Close-up showing electrode about to be inserted into sheath. The electrode is delivered on a shuttle that can be used to push the electrode down the sheath. c) Electrode and shuttle are fully inserted into the sheath. d) Shuttle is removed, leaving electrode in the muscle. e) Sheath is removed. f) Electrode lead is tunneled subcutaneously to the implanted stimulator using a polymer tunneler. Suction is connected to one end of the tunneler and saline is squirted into the other end to draw the electrode lead through the tunneler.

The functional impact of the Freehand System was high. The neuroprosthesis produced increased pinch force in every recipient, and there was a significant increase in the ability to manipulate objects of different size and weight [Wuolle et al., 1994; Peckham, et al., 2001]. The independence provided by the neuroprosthesis was directly compared to the maximum independence that could be provided by any other means, e.g. orthotics or tendon transfers. With the neuroprosthesis, 100% of the participants (n= 28) had greater independence in at least one task, and 78% were more independent using the neuroprosthesis in at least three tasks. All participants preferred to use the neuroprosthesis for at least one task and 96% preferred to use the neuroprosthesis for at least three tasks [Peckham et al., 2001]. More than 90% of the participants were satisfied with the neuroprosthesis [Stroh Wuolle et al., 1999].

The team that originally developed the Freehand System subsequently developed a second generation system referred to as the implanted stimulator-telemeter (IST-12) [Smith et al., 1998]. The functional specifications for the second generation neuroprosthesis were developed based on interviews with neuroprosthesis users and clinicians. The IST-12 System was a myoelectrically-controlled neuroprosthesis providing control of grasp, forearm pronation and elbow extension for individuals who are paralyzed with cervical level spinal cord injury. A key feature of this system was the implantation of both the control and the stimulation source, which reduced the external components by 50% compared to the Freehand System. The IST-12 consisted of twelve stimulation channels and two channels of myoelectric signal recording acquisition.

Twelve subjects were implanted with the IST-12 device, including three with systems for restoring movement in both hands [Kilgore et al., 2008; Kilgore et al., 2018]. Subjects were able to successfully use the myoelectric signal from their wrist extensor for proportional control of grasp opening and closing. Subjects also demonstrated the ability to generate myoelectric signals from trapezius, platysma, deltoid, and biceps muscles. The use of myoelectric control in neuroprostheses allowed considerable flexibility in the control algorithms, enabling them to be tailored to each individual subject. The study results indicated that every subject improved significantly in pinch force strength and in the ability to manipulate objects [Kilgore et al., 2018]. The ability to perform activities of daily living was assessed for 13 arms in ten subjects. Every subject demonstrated improvement in at least two activities, with one subject demonstrating improvement in 11 of 12 activities tested and another subject demonstrating improvement in 9 of 9 activities tested. All thirteen arms in the ten subjects showed improved function in eating with a fork and 12/13 showed improvement in writing with a pen. Other tasks in which subjects showed improvement included: office tasks, using a cell phone, getting money out of a wallet, and embroidery.

The use of implanted neuroprostheses for individuals with high tetraplegia (C4 or higher) has been rare [Memberg et al., 2014], although implanted intracortical arrays have been used with surface [Bouton et al., 2016] or percutaneous [Ajiboye et al., 2017] stimulation systems. Two high tetraplegic individuals were implanted with dual IST-12 systems for shoulder, arm and hand function using myoelectric control from the shoulder or neck [Memberg et al., 2014]. Each individual was able to perform at least two activities of daily living using the neuroprostheses, whereas they were completely dependent without the neuroprosthesis. Difficulties included significant denervation in the deltoid and biceps muscles and developing control algorithms that were easy to learn and use.

Implanted Neuroprostheses for Exercise, Standing and Stepping

Both cervical and thoracic SCI result in paralysis of the torso and pelvis that can lead to unhealthy and non-functional seated postures which may be one of the primary contributing factors to chronic health problems in wheelchair users [Sinnot et al., 2000]. Following SCI, lack of voluntary or reflexive control of the paralyzed trunk and hip musculature compromises seated posture and balance, significantly limiting independent performance of activities of daily living (ADLs) and contributing to secondary health complications such as pressure ulcers, pathological posterior pelvic tilt and pathological vertebral alignment, and even leading to secondary health complications such as reduced respiratory capacity. Stiffening the paralyzed trunk and hip extensors with continuous electrical stimulation has a multitude of benefits: it can correct kyphotic seated postures, normalize lateral vertebral alignment, improve ventilation and respiratory volumes, and alter interface pressures. It can also expand bimanual workspace, statically stabilize the torso, increase the forces that can be exerted on objects with the upper extremities, return users to erect sitting from a fully forward-flexed posture, and improve manual wheelchair propulsion efficiency at comfortable speeds [Triolo et al., 2013a; Triolo et al., 2013b].

The inability to stand or step is another limitation that significantly limits the performance of individuals with many activities of daily living (ADL) such as washing dishes at a counter, reaching items on high shelves, or essential transfers between surfaces of varying heights. For individuals with thoracic-level SCI, stimulated contractions of the lower extremity muscles can enable standing and stepping, facilitate independent transfers, increase personal mobility and improve general health and quality of life after complete paralysis, as well as significantly enhance walking performance after incomplete injuries [Triolo et al., 2012; Triolo et al., 2018].

Since the long paraspinal muscles (longissimus, iliocostalis, and spinalis) are segmentally innervated, they can only be partially activated with single channel stimulation. Therefore, stimulation of the L1-L2 or T12-L1 spinal roots with intramuscular electrodes results in activation of multiple lumbar segments of the erector spinae muscles to provide trunk extension. Carefully placed intramuscular electrodes at the T11-L2 spinal roots can also activate the iliopsoas, quadratus lumborum, rectus abdominus, obliques and other core trunk muscles [Triolo et al., 2000; Marsolais and Kobetic, 1986]. Bilateral activation of the lumbar erector spinae with intramuscular electrodes inserted at these locations can reduce the posterior pelvic tilt, restore a more normal lumbar curve, and shift the workspace of seated neuroprosthesis users forward and upward. Figure 4 shows the implantation procedure for electrodes inserted in the lumbar paraspinal muscles. Stabilizing the lumbar spine with stimulation of the paraspinal muscles can allow heavier objects to be manipulated greater distances from the body, and improve stable seated posture [Davis et al., 2001a; Davis et al., 2001b; Kukke and Triolo, 2004].

Figure 4.

Surgical placement of electrodes in the erector spinae muscles under fluoroscopic guidance. a) Probes are inserted directly into the target muscles. Probes are insulated stainless steel with exposed tips, allowing for stimulation to be applied to the tip. b) C-arm fluoroscopy is used to visualize the tip of the probes in relation to the vertebrae. c) Electrical stimulation is applied to the probe to observe muscle response. d) Once the desired location has been achieved, the electrode is inserted via a sheath into the target muscle.

Recipients of an implanted neuroprosthesis with epimysial and intramuscular electrodes that continuously activated the vasti, gluteals, hamstrings and lumbar erector spinae exhibited mean standing times of 10 minutes, and maintained the usage patterns and functional abilities for up to 17 years post-rehabilitation with their systems [Triolo et al., 2012; Triolo et al., 2018]. This is sufficient for facilitating transfers to high surfaces, performing swing-to gait for short distances in wheelchair inaccessible environments and participating in other social, work and personal activities. Some implant recipients in a Phase II clinical trial of the system were able to stand for more than 20 minutes, and all were able to release one hand from a walker or assistive device to reach objects overhead. Long term use of neuroprostheses for standing was safe and effective and had no adverse physiological effects. Stepping of up to 100m has also been achieved after paralysis with simple pre-programmed patterns of open-loop stimulation delivered from the surface electrodes or via 8- and 16-channel implanted pulse generators [Triolo et al., 2018].

Implanted Neuroprostheses for Respiratory Function

Spinal cord injury at C4 or higher can result in full or partial paralysis of the diaphragm, making the individual dependent on mechanical ventilation for breathing function. Side effects of mechanical ventilation include respiratory tract infections, difficulty with speech, as well as the practical issues of physical discomfort and limited mobility. Diaphragm pacing is a significant improvement over mechanical ventilation systems. Electrically-stimulated pacing reduces or eliminates these effects, providing a more natural form of breathing.

Neuroprostheses for respiration can be produced via stimulation of the phrenic nerve bilaterally. A number of implanted diaphragm pacing systems were commercialized [Avery, Medimplant, Atrotech]. These systems use an electrode placed around the phrenic nerve, connected to an implanted stimulator that drives breathing at a constant rate [Glenn et al., 1988; Khong et al., 2010; Romero et al., 2012]. Proper function requires that the phrenic nerve be intact without significant lower motor neuron damage, and this is a key screening criterion. Phrenic nerve electrodes are typically placed through a thoracic approach. Longitudinal studies demonstrate that these electrodes, when properly placed, do not damage the phrenic nerve [Glenn et al., 1986; Elefteriades et al., 2002].

The stimulated respiratory rate is typically 8–14 breaths/minute [Le Pimpec-Barthes et al., 2016]. Tidal volume can be adjusted by altering the stimulation frequency, but should not exceed 20Hz. It is important to note that diaphragm pacing requires a period of training before the individual achieves full-time ventilatory support using electrical pacing. Specifically, it is necessary to build diaphragm strength and fatigue resistance in order to achieve adequate ventilation using electrical stimulation. In general, users first achieve stimulated ventilation during the day and continue to use mechanical ventilation at night. With weeks of regular use, many users can wean entirely off of mechanical ventilation.

The outcomes show that diaphragm pacing has significant advantages over mechanical ventilation. Pimpec-Barthes [2016] reported effective stimulation was achieved in 82% - 90% of cases. Phrenic pacing has successfully been used for as long as 21 years [Khong et al., 2010]. Respiratory tract infections may be significantly reduced and complication are low.

It is also possible to activate the diaphragm via electrodes placed in the diaphragm itself [DiMarco et al., 2005; Onders et al., 2009]. Intramuscular electrodes are used in this case, with leads extending percutaneously to an external stimulator. This approach has the advantage of being minimally invasive, particularly relative to the surgical risks of placement of electrodes on the phrenic nerve.

Respiratory muscles are partially paralyzed in many cervical level injuries because the respiratory muscles of the chest are innervated by spinal roots in the thoracic cord. Even when the diaphragm is spared, breathing is compromised due to the lack of major inspiratory and expiratory intercostal muscles. Abdominal muscles also play a role in expiration. Therefore, in particular, cough is weak and thus it can be difficult for individuals to clear their airway.

A clinical trial using lower thoracic spinal cord stimulation (SCS) to restore an effective cough system was conducted in 12 tetraplegic subjects [DiMarco et al. 2009a, DiMarco et al. 2009b]. A fully implantable electrical stimulation system was surgically placed in each subject. Partial hemi-laminotomies were used to place single-disc electrodes in the dorsal epidural space at the T9, T11 and L1 spinal levels. A radiofrequency receiver (Finetech Medical) was also positioned in a subcutaneous pocket over the anterior chest. Electrode wires were tunneled subcutaneously and connected to the radiofrequency receiver. Stimulation was applied via an external antenna by activating a small portable external stimulus controller box powered by a rechargeable battery to each electrode lead alone and in combination. Nine patients were followed for a minimum of 12 months and demonstrated that supramaximal SCS generates large positive airway pressures and high peak airflow rates during stimulation at each electrode lead. Maximum airway pressures and peak airflow rates were achieved with combined stimulation of any 2 leads. At total lung capacity, mean maximum airway pressure generation and peak airflow rates were 130 ± 30 cmH2O and 8.6 ± 1.8 L/s, respectively. Importantly, repetitive stimulation every 30 sec for 30 min did not result in the development of fatigue as pressure generation remained unchanged [DiMarco et al. 2009a]. SCS was performed at home 2–3 times/day on a chronic basis, and also as needed for secretion management. The degree of difficulty in raising secretions improved markedly and the need for alternative methods of secretion removal were virtually eliminated. Subject life quality related to respiratory care also improved with subjects reporting greater control of their breathing problems. The incidence of pneumonia fell significantly from 1.7 ± 0.5 to 0.2 ± 0.1 events/subject year (p<0.01) and mean level of trained caregiver support related to secretion management decreased from 16.9 ± 7.9 to 2.9 ± 1.2 times/week. Subject mobility also increased significantly as many individuals no longer had to travel with trained caregivers and/or with any apparatus for suctioning. Importantly, there were no instances of bowel or bladder leakage. These preliminary results strongly suggest that the SCS cough system facilitates secretion management, reduces the need for caregiver support and reduces the incidence of respiratory tract infection. Application of this system may also reduce overall health care costs as reduce the morbidity and mortality associated with respiratory complications in subjects with SCI. The SCS cough system therefore may become an important clinical tool in the respiratory management of subjects with spinal cord injury. A further study evaluated a less invasive techniques for electrode installation using a wire (or “linear”) electrode [DiMarco et al., 2018]. This electrode can be inserted through the vertebral foramen or inter-vertebral space eliminating the need for multiple laminotomies.

Implanted Neuroprostheses for Bladder and Bowel Function

The goal of electrical stimulation of the urinary system is to restore on-command micturition and then continence at all other times. Of all body functions desired by the combination populations of tetraplegia and paraplegia, this is the highest priority need in SCI [Anderson, 2004]. It is important not only for the personal and social implications, but poor bladder management has medical implications. These include inducing autonomic dysreflexia, and bladder infections, which create significant health risks. The alternative means for bladder management provide for external collection of urine with indwelling catheters of various forms. Necessarily, these are not very desirable, and create health risks of their own.

Sacral root stimulation can be used to activate bladder, bowel and sexual function [Brindley, 1994]. A U.S. study of the sacral anterior root stimulator (SARS) showed that the majority of patients utilized the system routinely for producing micturition 4–6 times per day. In a study of twenty subjects who received this system, the average post-void residual volume with the stimulator was 22 ± 14 ml and the median number of urine infections decreased from 7 to 1 per year [Creasey et al., 2001], which substantially reduces the use of antibiotics. Eighteen of these 20 subjects became catheter-free. The abolition of detrusor hyper-reflexia by posterior rhizotomy allowed patients to discontinue anticholinergic medications, which in turn reduced constipation and other side effects such as a dry mouth, blurred vision and drowsiness. Continence was achieved in over 85% of patients, but this is largely attributable to the abolition of detrusor hyper-reflexia and increase in bladder compliance which follow posterior sacral rhizotomy. Interviews by a life care plan analyst with patients between six months and six years after implantation and rhizotomy indicated a six-fold reduction in the costs of bladder and bowel care, predicting that savings in bladder and bowel care would equal the cost of purchasing and implanting the stimulator after about five years, and thereafter be expected to result in progressive savings to the health care payer [Creasey and Dahlberg, 2001].

The SARS system can also have a positive impact on bowel management. Most users report a reduction in constipation and reduced need for laxatives and stool softeners. Some users are able to defecate by a pattern of intermittent stimulation similar to that used for micturition but with longer intervals between bursts of stimulation to allow passage of stool. In the Cleveland series the time spent on bowel emptying was reduced by 75% [Creasey et al., 2001].

Bladder hyper-reflexia is a major problem that must be addressed in an effective neural prosthesis for bladder control. Stimulation of peripheral sensory pathways can access and influence the spinal neural circuits that control pelvic reflexes and function. Afferent-mediated neural prostheses take advantage of natural nervous system processes and are potentially less invasive than spinal-root based approaches such as the SARS system. This approach has the potential to provide more natural function than motor driven approaches, though it is more dependent on stimulation patterns and other inputs to the spinal circuits. One such approach uses genital nerve stimulation to achieve direct spinal level bladder inhibition [Lee et al., 2002; Lee et al., 2012]. This approach has primarily been used acutely, but it has also shown to improve urinary continence and bladder capacity in persons with SCI during short duration use. If longer term use is effective, then this approach may provide both a noninvasive and implanted option. Bladder inhibition via implanted electrodes on the pudendal nerve and sacral roots can also provide bladder inhibition in individuals with SCI [Bourbeau et al., 2017; Bourbeau et al., 2018].

Summary

The success of neuroprostheses in providing increased independence, when compared to all existing alternative strategies for this population, is nearly universal [Peckham and Kilgore, 2013; Ho et al., 2014]. Arguably, the most important indication of the success of these systems is user acceptance and level of satisfaction. The following paragraphs include spontaneous comments from various individuals who have sustained a spinal cord injury who are using implantable neuroprosthetic systems.

From a person with a C5 complete SCI who is an upper extremity neuroprosthesis user:

“I was very physical all of my life and worked as an assistant dog trainer, but after my SCI, I could not wash my face, comb my hair, write, or even drink a glass of juice. After I was implanted with the upper extremity neuroprosthesis I could write, comb my hair, apply lipstick, wash my face, drink a glass of juice, and I have returned to doing embroidery.”

From a person with C6 complete SCI who has a trunk and hand neuroprosthesis:

“To go for 21-plus years as a quadriplegic – no feeling, no ability to move – it’s scary sometimes. I turn my trunk system on, I feel rigid, I feel muscles below my injury line that I haven’t felt for a long time, and it feels good.”

From a person with C2 tetraplegia who uses a cough neuroprosthesis:

“I was a college student living independently of my family before my SCI. The injury was devastating, and I lost my freedom. I could not go anywhere without my nurse or mom, as when I had difficulty breathing I needed them to suction me. Following implantation of the cough system, I was able to go out with my friends without my mom or nurse and enjoy myself. …This system has opened up my life to my friends without being a burden to my mom or nursing staff.”

From a person who is a T9 paraplegic who uses a bladder stimulation neuroprosthesis:

“I had a [urinary tract infection] UTI every month for the first 10 months after SCI. Worse than that, I was afraid to go out because I was afraid I would have an accident. Once I got the bladder stimulation system, I could void when I wanted, I could leave my house without fear of an accident, and I have had only 4 infections in the last 6 years.”

From a person with a C6 complete SCI who is an upper extremity neuroprosthesis user:

“I’m a daily user and rely on it to enable me to work full-time with no support hours required during work hours.”

The cost-benefit of neuroprostheses has been studied for bladder and hand neuroprostheses. In the case of bladder neuroprostheses, the reduction in secondary health conditions, particularly urinary tract infections, resulted in an overall reduction in the cost of care which exceeded the cost of the implant and maintenance within a five years [Creasey & Dahlberg, 2001]. In the case of hand neuroprostheses, it was demonstrated that a reduction in attendant care time could offset the cost of the surgical procedure and system maintenance over the lifetime of the recipient [Creasey et al., 2000]. Further analysis of the costs-benefits of implanted neuroprostheses need to consider the impact of improved quality of life.

In summary, it is possible to utilize advanced implantable neuroprostheses to restore function for individuals with SCI. These systems have demonstrated use for more than two decades, indicating a high degree of utility, functional benefits and, in some cases, significant health benefits. The surgical installation methods are well-established and the technology has proven to be robust and safe. A key focus for the future is to make implanted neuroprostheses broadly available to the SCI population within existing and evolving health care delivery systems.