Patent Application
20240198100
This invention relates generally to the field of spinal cord stimulation for improving respiratory function.
Thousands of patients annually in the United States suffer from respiratory insufficiency or failure, which may be caused by a wide range of conditions such as disease or injury. For example, acute respiratory distress syndrome (ARDS) is a potentially fatal form of respiratory failure that affects approximately 200,000 patients annually in the United States, resulting in nearly 75,000 deaths per year. Approximately 10% of intensive care unit (ICU) admissions are ARDS patients globally, representing more than 3 million patients annually. The best method of dealing with such respiratory failure is invasive mechanical ventilation (e.g., ventilation via an endotracheal tube or tracheostomy with breaths delivered by a mechanical ventilator) to augment deficiencies in oxygenation. However, while largely effective, mechanical ventilation can be a source of significant complication and is not sufficient for avoiding morbidity and mortality. Importantly, under prolonged intubation, patients typically experience ventilator-induced diaphragm dysfunction and/or other atrophy of respiratory musculature that has been measurable within 1-2 days of start of mechanical ventilation. This loss of respiratory function prevents expeditious weaning and removal from mechanical ventilation, which increases ventilation-associated complications and reduces quality of life. Furthermore, prolonged intubation occupies limited hospital resources, thereby limiting access to care, which can be devastating during times of great need for mechanical ventilation equipment, as evidenced by the recent COVID-19 pandemic.
Generally, in some variations, a method for conditioning respiratory muscles in a patient may include administering a stimulation signal to one or more of a cervical, thoracic, and lumbar spinal cord of the patient, where the stimulation signal is effective to augment and/or sustain the activation of one or more respiratory muscles in the patient, thereby maintaining strength of the one or more respiratory muscles. In some variations, the spinal cord stimulation may be combined with a cortical stimulation relevant to one or more respiratory muscles. In some variations, the method may include detecting an inspiratory phase of the patient from one or more sensors and administering the stimulation signal during the detected inspiratory phase. In some variations, the method may further include detecting an expiratory phase of the patient from one or more sensors and ceasing the administration of the stimulation signal during the detected expiratory phase. The thoracic spinal cord stimulation may be configured to activate the one or more respiratory muscles by activating motor neurons at a segmental spinal cord level. In some variations, the stimulation signal may be administered to a dorsal column of the thoracic spinal cord. In some variations, the method may include administering a second stimulation signal to a cervical spinal cord region of the patient, where the second stimulation signal is effective to activate respiratory drive in the patient. In some variations, the method may include administering a third stimulation signal to a lumbar spinal cord region of the patient, where the third stimulation signal is effective to activate respiratory drive in the patient.
In some variations, a system for conditioning muscles may include a controller configured to detect an inspiratory phase of the patient based on a sensor signal from one or more sensors, and a stimulator configured to administer a stimulation signal to one or more of a cervical, thoracic, and lumbar spinal cord of the patient during the detected inspiratory phase. The stimulation signal may be effective to activate one or more respiratory muscles in the patient during the inspiratory phase, thereby maintaining strength of the one or more respiratory muscles. In some variations, the spinal cord stimulation may be combined with a cortical stimulation relevant to one or more respiratory muscles. In some variations, the system may include a second stimulator configured to administer a second stimulation signal to a cervical spinal cord of the patient, where the second stimulation signal is effective to activate respiratory drive in the patient. In some variations, the system may include a third stimulator configured to administer a third stimulation signal to a lumbar spinal cord region of the patient, where the third stimulation signal is effective to activate respiratory drive in the patient.
Non limiting examples of various aspects and variations of the invention are described herein and illustrated in the accompanying drawings.
Described herein are methods and systems for spinal cord stimulation for conditioning respiratory muscles, such as to prevent, delay, or treat respiratory muscle atrophy in patients. The spinal cord stimulation may, for example, be administered to patients who are on mechanical ventilation (e.g., acute, chronic), in order to help prevent respiratory muscle atrophy in such patients. Mechanical ventilation may unload (e.g., decrease the force muscles need to generate ventilation) respiratory muscles and lead to muscle atrophy as force generation by muscles at least maintains muscle mass. After intubation and initiation of mechanical ventilation, many patients need large amounts of sedation to tolerate low tidal volume (lung protective) ventilation. The need for sedation (e.g., opioids, propofol) often suppresses the patient's own respiratory muscle activity (e.g., reduces respiratory drive, paralyzes respiratory muscles), which may lead to rapid onset of diaphragm atrophy, which in turn can cause or contribute to delayed weaning and delayed liberation from mechanical ventilation because of respiratory muscle weakness. However, patients on mechanical ventilation who are administered spinal cord stimulation such as that described herein may benefit from maintained or strengthened respiratory muscles, which may reduce time of mechanical ventilation and/or reduce ventilator-associated complications. For example, spinal cord stimulation (e.g., CPG) may induce respiratory activity (with ensemble of respiratory muscles activated including upper airway muscles such as genioglossus, hypoglossal, etc.) when there is no activity and increase frequency of respiration when there is existing respiratory activity. Furthermore, the methods and systems described herein may condition respiratory muscles to expedite the process of weaning from the mechanical ventilation, which reduces patient dependence on and/or reduces duration of mechanical ventilation. In turn, this increases availability of treatment of more patients with mechanical ventilation thereby improving access to care and maximizing valuable hospital resources.
Although in some variations the spinal cord stimulation may be administered to patients who are intubated on a mechanical ventilator or similar assistive equipment as described above, the spinal cord stimulation may be administered to patients in other settings. For example, in some variations, spinal cord stimulation such as that described herein may be administered to a patient who is not intubated on a mechanical ventilator, and the spinal cord stimulation may be administered to delay or prevent the need for mechanical ventilation. In some variations, spinal cord stimulation such as that described herein may be administered to a hospitalized patient to reduce or prevent skeletal and/or respiratory muscle atrophy due to bedrest, or to a patient in an ICU setting to reduce or prevent skeletal and/or respiratory muscle atrophy due to bedrest and/or mechanical ventilation. In some variations, patients in rehabilitation (e.g., at hospital, at home) may receive spinal cord stimulation such as that described herein, to reduce or prevent skeletal and/or respiratory muscle atrophy, promote muscle recovery, and/or the like. As another example, in some variations, spinal cord stimulation such as that described herein may be administered to a patient on venovenous extracorporeal membrane oxygenation (vv ECMO) where the respiratory muscles are not active due to lack of respiratory drive (pCO2). In some variations, ECMO may serve as a bridge therapy for patients with severe heart and respiratory failure prior to and following surgery (e.g., lung transplant). For example, respiratory muscles may be severely atrophied after a lung transplant and may benefit from spinal cord stimulation as described herein.
The methods and system described herein may be used to treat any suitable patient, such as patient having a respiratory insufficiency or failure (e.g., any condition that requires acute or chronic mechanical ventilation, where respiratory muscles are not active). For example, the respiratory insufficiency may be caused at least in part by respiratory distress syndrome (ARDS, COVID ARDS), ECMO (e.g., vv ECMO), ventilator-induced diaphragm dysfunction, critical illness myopathy, chronic obstructive pulmonary disease (COPD), stroke, spinal cord injury, heart failure, trauma, pneumonia, sepsis, aging, a neurodegenerative disorder (e.g., associated with Parkinson's disease, Alzheimer's disease, Huntington's disease, amyotrophic lateral sclerosis (ALS), congenital central hypoventilation syndrome (CCHS), primary lateral sclerosis (PLS), dystonia, cerebral palsy, Guillain Barre Syndrome, chronic inflammatory polyneuropathy, etc.), or any combination thereof.
In some variations, a method for conditioning respiratory muscles may include administering a stimulation signal to a cervical spinal cord, a thoracic spinal cord, and/or a lumbar spinal cord of a patient, where the stimulation signal is effective to augment and/or sustain the activation of respiratory muscles in the patient, thereby maintaining and/or improving strength of the respiratory muscles. The stimulation may be configured to activate motor neurons, nerve roots and/or interneurons at targeted spinal cord levels for respiratory muscles to prevent muscle atrophy. For example, the stimulation may function to activate local neural circuits that elicit segmental motor responses in intercostal muscles and/or diaphragm. Such stimulation may include subthreshold stimulation (i.e., stimulation that does not reach the necessary threshold for firing and thus does not directly trigger an action potential) and supratheshold stimulation.
One or more strategies may be used to help prevent muscle atrophy. For example, the cervical spinal cord, thoracic spinal cord, and/or lumbar spinal cord stimulation may result in segmental activation of respiratory muscles to condition the respiratory muscles, without interfering with mechanical ventilation (if present) (e.g., the activation of neuro-respiratory substrates specific to diaphragm muscles). As another example, the cervical spinal cord, thoracic spinal cord, and/or lumbar spinal cord stimulation may result in activation of a wide array of respiratory muscles through medullary respiratory central pattern generation (CPG) (e.g., more global, CPG-dependent respiratory muscle activation).
The spinal cord stimulation may be administered to any spinal cord region. For example, in some variations the method may include administering stimulation to a thoracic spinal cord region selected from the group consisting of T7-T7, T7-T8, T7-T9, T8-T8, T8-T9, T9-T9, and T1-11. These thoracic spinal cord regions are associated with segmental activation of respiratory muscles including intercostal (e.g., external intercostal muscle) and diaphragm muscles. Generally, in some variations, the thoracic spinal cord stimulation signal may have a stimulation frequency of at least about 20 Hz, between about 20 Hz and about 100 Hz, between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, or between about 1 Hz and about 5 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz. Stimulation frequencies of up to about 5 Hz may correspond to segmental stimulation while higher frequencies may access CPG activity regardless of stimulation site. In some variations, segmental stimulation at the respiratory musculature motor pool may be configured to condition muscles at supramotor threshold stimulation. In some variations, the stimulation described herein may be administered during an inspiratory phase.
Additionally or alternatively, the spinal cord stimulation may be administered to a suitable cervical spinal cord region. For example, in some variations the method may include administering stimulation to a cervical spinal cord region selected from the group consisting of C1-C1, C1-C2, C1-C3, C1-C4, C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, C4-C4, C3, C4, C5. These cervical spinal cord regions are also associated with segmental activation of respiratory muscles including intercostal and a primary inspiratory muscle (e.g., diaphragm muscles). Generally, in some variations, the cervical spinal cord stimulation signal may have a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, or of at least about 20 Hz, between about 20 Hz and about 100 Hz, or between about 1 Hz and about 5 Hz. In some variations, the cervical spinal cord stimulation has a stimulation frequency of about 30 Hz. In some variations, the method may include administering stimulation to a cervical spinal cord region at C3/4 at a frequency of at least about 20 Hz. In some variations, the cervical spinal cord stimulation may be similar to that described below with respect to CPG activation. For example, the cervical spinal cord stimulation may be administered for muscle conditioning and/or CPG activation. In some variations, the stimulation described herein may be administered during an inspiratory phase.
Additionally or alternatively, the spinal cord stimulation may be administered to a suitable lumbar spinal cord region. For example, in some variations the method may include administering stimulation to a lumbar spinal cord region selected from the group consisting of L1-L2, L3-L4, and L4-L5. Generally, in some variations, the lumbar spinal cord stimulation signal may have a stimulation frequency of at least about 20 Hz, between about 20 Hz and about 100 Hz, between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, or between about 1 Hz and about 5 Hz.
In some variations of the method, two or more stimulation signals may be administered to a spinal cord region at slightly offset frequencies in a temporal interference (TI) stimulation scheme (e.g., interferential stimulation). For example, cervical, thoracic, and/or lumbar spinal cord stimulation may be performed using two stimulation waveforms that are offset by a frequency difference ranging between about 1 Hz and about 10 Hz, between about 1 Hz and about 5 Hz, or between about 1 Hz and about 2 Hz (e.g., 1 Hz, 2 Hz, 3 Hz, 4 Hz, 5 Hz, 6 Hz, 7 Hz, 8 Hz, 9 Hz, or 10 Hz difference in frequency between the two waveforms). For example, thoracic spinal cord stimulation for conditioning respiratory muscles and/or avoiding respiratory muscle atrophy may be administered by two separate stimulation sources (e.g., electrodes) providing stimulation at 1 Hz and 2 Hz, respectively. As another example, cervical spinal cord stimulation for conditioning respiratory muscles and/or avoiding respiratory muscle atrophy may be administered by two separate stimulation sources (e.g., electrodes) providing stimulation at 30 Hz and 31 Hz (or 5000 Hz and 5001 Hz), respectively. The offset frequencies may induce an interferential stimulation pattern at a predetermined frequency (e.g., about 1 Hz). Without being bound by any particular theory, it is believed that TI stimulation may activate neurons via the offset or beat frequency of the two waveforms, and with reduced stimulation of overlying anatomy not of interest. In some variations, TI stimulation may be applied for transcutaneous spinal stimulation and/or spinal stimulation using needle electrodes. In some variations, the two or more stimulation signals may have a stimulation frequency as described herein of at least about 20 Hz, between about 20 Hz and about 100 Hz, between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, or between about 1 Hz and about 5 Hz.
In some variations of the method, two or more stimulation signals may be administered to a spinal cord region with a first stimulation signal (e.g., monophasic signal, biphasic signal) having a first frequency and an overlapping second stimulation signal having a second frequency higher than the first frequency. For example, cervical, thoracic, and/or lumbar spinal cord stimulation may be performed using two overlapping stimulation waveforms with a first stimulation signal having a frequency between about 0.5 Hz and about 100 Hz, and a second stimulation signal having a frequency between about 5 kHz and about 10 kHz. In some variations, the stimulation may be monopolar or bipolar, and may further comprise an amplitude of between about 0.5 mA and about 200 mA, and a pulse duration of between about 0.5 ms and about 3.0 ms. In some variations, the first stimulation signal may comprise a frequency of at least about 20 Hz, or between about 20 Hz and about 100 Hz, or between about 1 Hz and about 50 Hz, or between about 0.5 Hz and about 30 Hz, or between about 0.5 Hz and about 10 Hz, or between about 0.5 Hz and about 5 Hz. In some variations, the stimulation signal amplitude may range from about 30 mA, or about 40 mA, or about 50 mA, or about 60 mA, or about 70 mA, or about 80 mA up to about 200 mA, or up to about 200 mA, or up to about 150 mA.
In some variations, the method may include combining the cervical spinal cord stimulation, the thoracic spinal cord stimulation, and/or lumbar spinal cord stimulation as described herein with a cortical stimulation relevant to one or more respiratory muscles. The cortical stimulation signal may, for example, help enhance synaptic plasticity in those neural circuits relevant to function of those respiratory muscle(s). For example, in some variations the method may include combining the cervical, thoracic, and/or lumbar spinal cord stimulation described herein with cortical stimulation for the diaphragm muscle, in order to help improve or maintain diaphragm function. The cortical stimulation may be applied to the motor cortex, and the accompanying cervical, thoracic and/or lumbar spinal cord stimulation may be timed to arrive at the cervical, thoracic, and/or lumbar synapses, respectively, substantially simultaneously with (at a predetermined interval after) the cortical stimulation pulse(s) arrive at the cervical, thoracic, and/or lumbar synapses. That is, cortical stimulation to activate affected muscle can be induced to be temporally coincident with spinal stimulation such that a first stimulus administered to a cortical motor neuron arrives at a spinal motor neuron at about the same time as a second stimulus for spinal stimulation arrives at the spinal motor neuron. In some variations, the location of cortical stimulation may be based on (e.g., titrated and adjusted to) a pre-motor or motor cortex homunculus (e.g., cortical representation of associated muscles including the diaphragm).
In some variations, spinal cord associative plasticity may be used to increase volitional motor output. For example, transcranial magnetic stimulation administered in combination with cervical stimulation may increase the force of one or more target muscles. In some variations, cervical transcutaneous spinal cord stimulation pulses administered at subthreshold intensity in combination with magnetic pulses administered over the motor cortex at suprathreshold intensity may be configured to temporally converge in the cervical spinal cord to enhance a hand response. For example, single pairs of cortical-spinal stimulation where a cortical pulse reached the cervical spinal cord up to about 5 milliseconds prior to a spinal pulse enhanced a hand response.
Moreover, stimulation may be administered bilaterally to bilateral muscles or unilaterally to affect a contralateral muscle. In some variations, stimulation may be coordinated to muscle contraction, in the case of autonomic function, such as respiratory function, such that stimulation is active during inspiration. In some variations, cortical stimulation may be administered alone or in combination with spinal stimulation to condition one or more muscles and/or prevent muscle atrophy.
In some variations, cortical stimulation may be configured to activate respiratory muscles through descending inputs to condition one or more muscles through one or more of activation of the CPG, direct or indirect activation of spinal motor neurons (e.g., activation by direct cortical or lumbar to spinal motor neuron pathways or through the respiratory CPG regardless of the site of stimulation; these pathways exist in parallel). In some variations, activation of the CPG may be configured to activate (and strengthen) respiratory muscles with innervation connected through the CPG in proportion to the strength of CPG stimulation. Moreover, direct spinal motor activation may comprise a locally dispersed pattern of stimulation (e.g., thoracic stimulation at T8 may activate motor neurons at T6-12 with a bell-shaped curve of descending activation from the spinal motor neuron activation peak).
In some variations, the spinal cord stimulation may be timed to arrive at the relevant set of synapses at an interval ranging between about 0 ms and about 10 ms after the cortical stimulation pulses arrive at the same. Such an interval may, for example, be about 1 ms, about 2 ms, about 3 ms, about 4 ms, about 5 ms, about 6 ms, about 7 ms, about 8 ms, about 9 ms, or about 10 ms after the arrival of the cortical stimulation pulses. For example, a controller such as the controller 210 described in more detail herein may be configured control a timing of cortical-spinal stimulation as described herein.
The cortical stimulation may be applied transcranially, and may include transcutaneous electrical stimulation, percutaneous electrical stimulation, and/or magnetic stimulation as described in further detail below.
Stimulation of the cervical, thoracic, and/or lumbar spinal cord regions may be performed using a dorsal and/or ventral approach. For example, in some variations, at least one stimulation signal may be administered to a dorsal column of the cervical, thoracic, and/or lumbar spinal cord. A dorsal approach may, for example, be easily accessible and less likely to interfere with other medical equipment such as that associated with a mechanical ventilator.
In some variations, stimulation signals may be administered in a combined dorsal and ventral approach. For example, in a variation in which transcutaneous, percutaneous, or epidural electrical stimulation is administered to a target stimulation location for respiratory muscle conditioning, one or more electrodes may be placed on a posterior region of the patient and one or more electrodes may positioned on an anterior region of the patient. For example, cervical spinal cord transcutaneous, percutaneous, or epidural electrical stimulation for respiratory muscle conditioning may be administered using a posteroanterior configuration in which at least one electrode (e.g., cathode) is positioned over upper thoracic spinous processes, and at least one electrode (e.g., anode) is positioned over an anterior surface of the cervical region of the patient. It is thought, for example, that this posteroanterior electrode configuration may elicit muscle responses across multiple cervical myotomes through sensory afferent and motor efferent circuit activation, where lower stimulation intensities may primarily activate sensor afferent circuits, and higher stimulation intensities may primarily activate motor efferent circuits.
In some variations, a method for conditioning respiratory muscles of a patient may include administering a stimulation signal comprising two alternating pulses of opposite polarities separated by a predetermined delay to form a delayed biphasic pulse waveform. In some variations, the predetermined delay may be up to about 1 μs, between about 1 μs and about 1 μs, between about 1 μs and about 100 μs, or between about 100 μs and about 500 μs. For example, the delayed pulses may comprise a first frequency biphasic carrier pulse (e.g., about 10 kHz) and a second frequency (e.g., about 30 Hz) burst pulse, each pulse having a pulse width of about 1 ms. In some variations, the delayed pulses of the stimulation signal may be applied using transcutaneous electrical spinal cord neuromodulation (TESCoN) (e.g., an adhesive electrode between C3-C4, C5-C6, or T1-T2 serving as the cathode and two adhesive electrodes over bilateral shoulders as the anode.
In some variations, the method may include administering the stimulation signal during one or more treatment sessions. A treatment session may have a duration that ranges, for example, between about 5 minutes and about 30 minutes, between about 5 minutes and about 25 minutes, between about 5 minutes and about 20 minutes, between about 5 minutes and about 15 minutes, between about 10 minutes and about 30 minutes, between about 10 minutes and about 25 minutes, or about 15 minutes.
The patient may undergo multiple treatment sessions, such as periodically at any suitable frequency. For example, the method may include administering the stimulation signal in a treatment session every hour, every 90 minutes, every 2 hours, every 3 hours, or every 5 hours. The repeated treatment sessions may each have the same duration, or they may have different durations. The treatment sessions may be repeated as long as needed to maintain and/or improve respiratory muscle strength. For example, in variations in which the patient is sedated or unconscious and intubated on mechanical ventilation, the treatment sessions may be repeated until the patient regains consciousness. As another example, in variations in which the patient is on bed rest or in rehabilitation, the treatment sessions may be repeated until the patient is no longer on bed rest, or may be repeated throughout a rehabilitation therapy session for multiple rehabilitation therapy sessions until the patient is sufficiently rehabilitated.
In an exemplary variation, a method for conditioning respiratory muscles of a patient includes administering a stimulation signal to a thoracic spinal cord region of the patient in a treatment session every hour, where each treatment session has a duration of about 15 minutes. In variations in which the method is performed on a patient that is sedated, the treatment sessions may be repeated until the patient regains consciousness.
The spinal cord stimulation may be administered in a suitable non-invasive manner or invasive manner. For example, in some variations the stimulation signal may be administered transcutaneously, percutaneously, or epidurally. In some variations, the spinal cord stimulation may be electrical or magnetic.
In some variations, a method of conditioning respiratory muscles may include administering a transcutaneous electrical stimulation signal to a cervical spinal cord region, thoracic spinal cord region and/or lumbar spinal cord region, as described above. The transcutaneous electrical stimulation may, for example, be administered via one or more surface electrodes.
The transcutaneous electrical stimulation signal may have a suitable frequency and amplitude to evoke a motor response of the targeted respiratory muscles (e.g., intercostal muscles, diaphragm). In some variations, the method may include administering to a thoracic spinal cord region a transcutaneous electrical stimulation signal having a stimulation frequency of between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, between about 1 Hz and about 5 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz. Additionally or alternatively, in some variations, the method may include administering to a cervical spinal cord region or a lumbar spinal cord region a transcutaneous electrical stimulation signal having a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the cervical spinal cord or lumbar spinal cord stimulation has a stimulation frequency of about 30 Hz.
Additionally or alternatively, the method may include administering a transcutaneous electrical stimulation signal having an amplitude of between about 5 mA to about 300 mA, or between about 5 mA to about 250 mA, or between about 5 mA to about 200 mA, between about 5 mA to about 150 mA, or between about 5 mA to about 100 mA, or between about 5 mA to about 80 mA, or between about 5 mA to about 60 mA, or between about 5 mA to about 50 mA.
In some variations, the transcutaneous electrical stimulation signal may be superimposed on a high frequency carrier signal. The high frequency carrier signal may, for example, range between about 3 kHz and up to about 30 kHz, or up to about 20 kHz, or up to about 15 kHz. In certain embodiments the carrier signal is about 10 kHz. In some variations, the carrier frequency amplitude may range from about 30 mA, or about 40 mA, or about 50 mA, or about 60 mA, or about 70 mA, or about 80 mA up to about 300 mA, or up to about 200 mA, or up to about 150 mA.
In some variations, a method of conditioning respiratory muscles may include administering a percutaneous electrical stimulation signal to a cervical spinal cord region, a thoracic spinal cord region and/or a lumbar spinal cord region, as described above. The percutaneous stimulation may, for example, be administered via one or more needle electrodes.
The percutaneous electrical stimulation signal may have a suitable frequency and amplitude to evoke a motor response of the targeted respiratory muscles (e.g., intercostal muscles, diaphragm). In some variations, the method may include administering to a thoracic spinal cord region a percutaneous electrical stimulation signal having a stimulation frequency of between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, between about 1 Hz and about 5 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz. Additionally or alternatively, in some variations, the method may include administering to a cervical spinal cord region or a lumbar spinal cord region a percutaneous electrical stimulation signal having a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the cervical spinal cord or lumbar spinal cord stimulation has a stimulation frequency of about 30 Hz.
Additionally or alternatively, the method may include administering a percutaneous electrical stimulation signal having an amplitude of between about 5 mA to about 300 mA, or between about 5 mA to about 250 mA, or between about 5 mA to about 200 mA, between about 5 mA to about 150 mA, or between about 5 mA to about 100 mA, or between about 5 mA to about 80 mA, or between about 5 mA to about 60 mA, or between about 5 mA to about 50 mA.
In some variations, the percutaneous electrical stimulation signal may be superimposed on a high frequency carrier signal. The high frequency carrier signal may, for example, range between about 3 kHz and up to about 30 kHz, or up to about 20 kHz, or up to about 15 kHz. In certain embodiments the carrier signal is about 10 kHz. In some variations, the carrier frequency amplitude may range from about 30 mA, or about 40 mA, or about 50 mA, or about 60 mA, or about 70 mA, or about 80 mA up to about 300 mA, or up to about 200 mA, or up to about 150 mA.
In some variations, a method of conditioning respiratory muscles may include administering an epidural electrical stimulation signal to a cervical spinal region, a thoracic spinal cord region and/or a lumbar spinal cord region, as described above. The epidural stimulation may, for example, be administered via one or more implanted electrodes placed at an epidural site.
The epidural stimulation signal may have a suitable frequency to evoke a motor response of the targeted respiratory muscles (e.g., intercostal muscles, diaphragm). In some variations, the method may include administering to a thoracic spinal cord region an epidural stimulation signal having a stimulation frequency of between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, between about 1 Hz and about 5 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz. Additionally or alternatively, in some variations, the method may include administering to a cervical spinal cord region or a lumbar spinal cord region an epidural electrical stimulation signal having a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the cervical spinal cord or lumbar spinal cord stimulation has a stimulation frequency of about 30 Hz.
Additionally or alternatively, the method may include administering an epidural stimulation signal having an amplitude of between about 5 mA to about 300 mA, or between about 5 mA to about 250 mA, or between about 5 mA to about 200 mA, between about 5 mA to about 150 mA, or between about 5 mA to about 100 mA, or between about 5 mA to about 80 mA, or between about 5 mA to about 60 mA, or between about 5 mA to about 50 mA.
In some variations, a method of conditioning respiratory muscles may include administering a stimulation signal, induced by a magnetic signal, to a cervical spinal region, a thoracic spinal cord region, and/or a lumbar spinal cord region, as described above. The magnetic signal may, for example, be administered via one or more magnetic coils (e.g., magnetic wand).
The stimulation signal induced by a magnetic signal may have a suitable frequency to evoke a motor response of the targeted respiratory muscles (e.g., intercostal muscles, diaphragm). In some variations, the method may include administering to a thoracic spinal cord region a stimulation signal having a stimulation frequency of between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, between about 1 Hz and about 5 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz. Additionally or alternatively, in some variations, the method may include administering to a cervical spinal cord region or a lumbar spinal cord region a stimulation signal having a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the cervical spinal cord or lumbar spinal cord stimulation has a stimulation frequency of about 30 Hz.
In some variations, the stimulation is administered by producing a magnetic field strength of up to about 10 tesla, up to about 8 tesla, up to about 6 tesla, up to about 5 tesla, up to about 4 tesla, up to about 3 tesla, up to about 2 tesla, or up to about 1 tesla.
The stimulation signal may have a suitable frequency and amplitude to evoke a motor response of the targeted respiratory muscles (e.g., intercostal muscles, diaphragm). In some variations, the method may include administering a stimulation signal having a stimulation frequency of between about 1 Hz and about 50 Hz, between about 1 Hz and about 30 Hz, between about 1 Hz and about 10 Hz, or between about 1 Hz and about 5 Hz. In some variations, the stimulation frequency is about 1 Hz or about 2 Hz.
Respiration involves a complex network of circuits that is involved in central pattern generation (CPG) that spans the brainstem and cervical spinal cord to generate a respiratory rhythm. In some variations, the method may additionally or alternatively include activating the respiratory network to activate respiratory drive by administering stimulation to a cervical spinal cord region of the patient.
Accordingly, in some variations, the method for conditioning respiratory muscles may include administering a second stimulation signal to a cervical spinal cord of the patient, where the second stimulation signal is effective to activate a respiratory drive in the patient. The second stimulation signal may, for example, activate rostrally-directed sensor input to brainstem respiratory circuits that in turn increase widespread activation of respiratory muscles. The second stimulation signal to the cervical spinal cord may, for example, be administered simultaneously with a stimulation signal to the thoracic spinal cord and/or lumbar spinal cord as described above. Together, the cervical, thoracic, and/or lumbar spinal cord stimulation may be performed to more effectively condition the respiratory muscles (e.g., to expedite ventilator weaning).
Similarly, in some variations, the method for conditioning respiratory muscles may include administering a third stimulation signal to a lumbar spinal cord of the patient, where the third stimulation signal is effective to activate a respiratory drive in the patient. The second stimulation signal may, for example, activate rostrally-directed sensor input to brainstem respiratory circuits that in turn increase widespread activation of respiratory muscles. The third stimulation signal to the lumbar spinal cord may, for example, be administered simultaneously with a stimulation signal to the thoracic spinal cord and/or cervical spinal cord as described above. Together, the cervical, thoracic, and/or lumbar spinal cord stimulation may be performed to more effectively condition the respiratory muscles (e.g., to expedite ventilator weaning or where the respiratory muscles are not active due to vv ECMO).
In some variations, administering the third stimulation signal may be performed during the detected inspiratory phase. In some variations, the third stimulation signal may be administered to a region selected from the group consisting of L1-L2, L3-L4, and L4-L5.
The cervical spinal cord stimulation may, in some variations, be similar to that described in U.S. Patent Pub. No. 2018/0185642 entitled “Accessing Spinal Network to Enable Respiratory Function” and/or U.S. Patent Pub. No. 20190381313 entitled “Accessing Spinal Network to Enable Respiratory Function”, each of which is incorporated herein in its entirety by this reference. For example, in some variations, the cervical spinal cord stimulation may be administered to a region selected from the group consisting of C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, and C4-C4. Furthermore, the cervical spinal cord stimulation signal may have a stimulation frequency ranging from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, at least about 20 Hz, or between about 20 Hz and about 100 Hz. In some variations, the cervical spinal cord stimulation has a stimulation frequency of about 30 Hz.
Like the thoracic and lumbar spinal cord stimulation described above, the cervical spinal cord stimulation may be in the form of transcutaneous electrical stimulation, percutaneous electrical stimulation, epidural stimulation, and/or stimulation induced by a magnetic signal.
In some variations, the spinal cord stimulation may be administered in a temporally coordinated manner with respiratory activity. For example, to properly condition the respiratory muscles, the method may include stimulating one or more regions of the cervical, thoracic, and/or lumbar spinal cord in phase with an inspiratory phase of the patients. Accordingly, in some variations, as shown in
Similar to that described above, the thoracic and/or lumbar stimulation signal may be effective to augment and/or sustain the activation of one or more respiratory muscles in the patient during the inspiratory phases, thereby maintaining strength of the one or more respiratory muscles. Additionally or alternatively, the cervical stimulation signal may be effective to activate a respiratory drive in the patient. The stimulation signal(s) administered in response to the detected inspiratory phase may be similar to any of the stimulation signals described above.
The inspiratory phase of the patient may be detected based one or more sensor signals, in that the sensor signal(s) may provide feedback in the closed-loop stimulation method to indicate inspiration, expiration, and/or other respiration activity of the patient. For example, sensor signals from a sensor configured to detect chest wall expansion or other movement and provide a sensor signal indicating the same. As described in further detail below, examples of such sensors include a device attachable to the patient and measures thoracic impedance or rib cage movement (e.g., inductance band, strain gauge band, accelerometer) of the patient. Accordingly, the cervical and/or thoracic spinal cord stimulation may be administered in phase with the inspiratory phase detected based on one or more such sensor signals.
In variations in which the patient is on mechanical ventilation, the cervical, thoracic, and/or lumbar spinal cord stimulation administered to the patient may be coordinated with mechanical ventilation. As further described below, an output signal from the mechanical ventilator indicating ventilation cycle or phase may be provided and analyzed to determine timing of the induced inspiratory phase of the patient. Accordingly, the cervical, thoracic, and/or lumbar spinal cord stimulation may be administered in phase with mechanical ventilator activity.
For example,
As shown in
Furthermore, the system 200 may include suitable circuitry elements (not pictured) for providing power to the electronic components of the system 200, allowing for network connectivity (e.g., data communication), and/or other suitable elements. At least a portion of the system 200 may, in some variations, be implantable. In variations in which at least a portion of the system 200 is implanted, the system 200 may include wireless power transfer elements such as antennas or coils for providing wireless power to implanted electronics (e.g., via inductive coupling, radiative coupling, etc.), or a wired power transfer via conductive connection. In some variations, the system 200 may include a power storage element such as a battery or capacitor. In some variations, the system 200 may comprise a mechanical ventilator configured for one or more of invasive and non-invasive ventilation of a patient.
In various embodiments, the controller 210 functions to modulate stimulation pulses to be administered to the patient through the stimulator(s) 230. For example, the controller 210 may regulate the stimulation parameters produced by the stimulator(s) 230, and/or control on/off timing of the stimulation provided by the stimulator(s) 230. The controller 210 may be separate from the stimulator(s) 230, or may be integrated with one or more of the stimulator(s) 230. The controller 210 may include or be operably coupled to one or more memory devices storing instructions to control the stimulation signal(s), and may include one or more processors for performing analysis (e.g., analyzing sensor signals), determining instructions to send to the stimulator for signal generation, determining timing of such instructions, and/or the like.
As described above, the controller 210 may be communicatively coupled to one or more sensors 240, such as to receive one or more sensor signals indicating respiratory activity. The controller 210 may receive such sensor signals, analyze the sensor signals to determine inspiration phase, expiration phase, and/or other suitable features of the patient's respiratory activity, and control the ramping up/ramping down of the stimulation signal(s) and/or modulate stimulation parameters as described above. In some variations, stimulation by the stimulator 230 may be modulated based on a measured respiratory phase of the patient monitored by one or more sensors 240.
In some variations, the system 200 may include one or more sensors 240 configured to provide sensor signals indicative of respiratory activity. For example, the system 200 may include one or more sensors configured to detect chest wall expansion or other chest movement. Various sensor technologies may be suitable for detecting chest wall expansion or other chest movement. For example, rib cage movement can be measured with an inductance or strain gauge band placed around the rib cage (e.g., immediately below the axillae). In some variations, the one or more sensors may be part of an inductance band, in which chest expansion can be determined by changes in the inductance of the band induced by stretching of the band. Similarly, in some variations, the one or more sensors may be part of a strain gauge band, in which changes in resistance/conductance of the strain gauges produced by band expansion/contraction can readily be measured using methods known to those of skill in the art. As another example, chest wall expansion and/or movement can be monitored with a sensor measuring thoracic impedance. In some variations, respiratory phase may be estimated with a sensor measuring one or more of airway flow and end tidal CO2.
Additionally or alternatively, a sensor 240 may include an accelerometer attached to the surface of the body (e.g., with a wearable band or other garment, with adhesive, etc.), while in other variations, the accelerometer can be implanted within the body. The signal from the accelerometer may be analyzed to determine respiratory activity by, for example, mapping movement and/or timing of chest wall movements.
In various embodiments, the system 200 may include one or more stimulators 230 configured to administer stimulation to a spinal cord region. Each stimulator 230 may include a pulse generator and one or more stimulation elements configured to administer stimulation in accordance with pulses generated by the pulse generator. The pulse generator and one or more stimulation elements may be housed together or may be housed separately (and connected to each other by a lead, for example).
In some variations, the stimulation elements of a stimulator 230 may be configured to provide transcutaneous electrical stimulation. The stimulator 230 may, for example, include one or more surface electrodes applicable to skin of the patient proximate the target spinal cord location (e.g., thoracic spinal cord, cervical spinal cord, lumbar spinal cord, etc.). In some variations, the one or more surface electrodes may be adhesive so as to be removably attached to the skin. Alternatively, in some variations, the stimulation elements for providing transcutaneous electrical stimulation may include one or more surface electrodes on a housing (e.g., handheld device, wearable device, etc.) that may be held against or secured to the patient such that the surface electrodes contact the skin.
In some variations, the stimulation elements of a stimulator 230 may be configured to provide percutaneous electrical stimulation. The stimulator 230 may, for example, include one or more needle electrodes that may be inserted at one or more target stimulation locations. For example, a percutaneous lead may include two or more spaced electrodes (e.g., equally or unequally spaced electrodes), that are placed above the dura layer (e.g., through the use of a Touhy-like needle). For insertion, the Touhy-like needle can be passed through the skin, between desired vertebrae, to open above the dura layer.
In some variations, the stimulation elements of a stimulator 230 may be configured to provide epidural stimulation. The stimulator 230 may, for example, include an implanted electrode array. In some variations, the implanted electrode array may be a high density electrode array prepared using suitable microfabrication techniques to place numerous electrodes in an array configuration on a flexible substrate. The electrode arrays may include one or more biocompatible metals (e.g., gold, platinum, chromium, titanium, iridium, tungsten, and/or oxides and/or allow thereof) disposed on a flexible material. Examples of suitable flexible materials include parylene A, parylene C, parylene AM, parylene F, parylene N, parylene D, silicon, and other flexible substrate materials, or combinations thereof. The implanted electrode array may be implanted using any of a number of methods (e.g., a laminectomy procedure), such as those known to those of skill in the art. For example, in some embodiments, electrical energy is delivered through electrodes positioned external to the dura layer surrounding the spinal cord. Stimulation on the surface of the cord (subdurally) is also contemplated, for example, stimulation may be applied to the dorsal columns as well as to the dorsal root entry zone.
In some variations, implanted electrodes can also be provided with an implantable controller 210 and/or an implantable power source. The implantable controller 210 may be programmed/reprogrammed by use of an external device (e.g., using a handheld device that communicates with the control circuitry through the skin). The programming can be repeated as often as necessary.
In some variations, the electrodes for electrical stimulation (transcutaneous, percutaneous, epidural) may be operably linked to the controller 210 that permits selection of electrode(s) to activate/stimulate and/or that controls frequency, and/or pulse width, and/or amplitude of stimulation. In some variations, the electrode selection, frequency, amplitude, and pulse width may be independently selectable, e.g., at different times, different electrodes can be selected. At any time, different electrodes can provide different stimulation frequencies and/or amplitudes. In some variations, different electrodes or all electrodes can be operated in a monopolar mode and/or a bipolar mode, using constant current or constant voltage delivery of the stimulation.
In some variations, the stimulation elements of a stimulator 230 may be configured to provide stimulation induced by a magnetic signal. The stimulator 230 may, for example, include one or more elements configured to generate a magnetic field that induces current at the spinal cord region of interest. In some variations, effective nerve stimulation may be achieved with a current transient of about 108 A/s. In certain variations this current is obtained by switching the current through an electronic switching component (e.g., a thyristor or an insulated gate bipolar transistor (IGBT)).
In some variations, a magnetic stimulator may include a high current pulse generator producing discharge currents (e.g., 5,000 amps or more) and a stimulating coil producing magnetic pulses (e.g., with field strengths up to 4, 6, 8, or even 10 tesla) and with a pulse duration typically ranging from about 100 μs to 1 ms or more, depending on the stimulator type. The stimulating coils may, in some variations, include one or more well-insulated copper windings, together with temperature sensors and safety switches. A voltage (power) source (e.g., a battery) may charge a capacitor or other power storage element via charging circuitry under the control of control circuitry (e.g., a microprocessor) that accepts information such as the capacitor voltage, power set by the user, and various safety interlocks within the equipment to ensure proper operation, and the capacitor may then connected to the coil via an electronic switching component when the stimulus is to be applied. The control circuitry may be operated via a controller interface that can receive user input and/or sensor signal(s) and adjust stimulus parameters in response.
When activated, the discharge current flows through the coils inducing a magnetic flux. It is the rate of change of the magnetic field that causes the electrical current within tissue to be generated, and therefore a fast discharge time is important to stimulator efficiency. Accordingly, an electrical current is generated within the tissue, and that it is the electrical current that causes the depolarization of the cell membrane and thus the stimulation of the target nerve.
Since the magnetic field strength falls off with the square of the distance from the stimulating coil, the stimulus strength is at its highest close to the coil surface. The stimulation characteristics of the magnetic pulse, such as depth of penetration, strength and accuracy, depend on the rise time, peak electrical energy transferred to the coil and the spatial distribution of the field. The rise time and peak coil energy are governed by the electrical characteristics of the magnetic stimulator and stimulating coil, whereas the spatial distribution of the induced electric field depends on the coil geometry and the anatomy of the region of induced current flow.
As described above, in various embodiments the system 200 may include multiple stimulators (or multiple stimulating elements). For example, the system 200 may include a first stimulator configured to administer thoracic spinal cord stimulation, a second stimulator configured to administer cervical spinal cord stimulation, and a third stimulator configured to administer lumbar spinal cord stimulation. In some variations with multiple stimulators, the first, second, and/or third stimulators may be substantially identical in construction (e.g., having same modality, such as both stimulators providing transcutaneous electrical stimulation, percutaneous electrical stimulation, epidural stimulation, or magnetic stimulation). Alternatively, in some variations with multiple stimulators, the first, second, and/or third stimulators may be different (e.g., having different stimulation modalities). Furthermore, it should be understood that the system 200 may include any suitable number of stimulators, such as one, two, three, four, five, or more stimulators.
Somatostatin (SST) and neurokinin-1 receptors (NK1R) in the cervical spinal cord are involved in gating afferent inputs and may be associated with the generation of respiratory pattern (i.e., respiratory drive) in the brainstem (see Example 3 below). Glutamate may be a helpful excitatory neurotransmitter for improving the mechanism for SST+/NK1R+ neurons in the cervical spinal cord.
Accordingly, to further enhance respiratory function (e.g., enhance CPG for respiratory drive, improve combined enhancement of respiratory function in a patient some variations, the spinal cord stimulation methods described herein may be used in conjunction with one or more pharmacological agents, such as glutamatergic agents.
These agents can be administered alone or in conjunction with spinal cord stimulation as described herein. For example, glutamatergic agents may be administered in conjunction with transcutaneous electrical stimulation, percutaneous electrical stimulation, epidural electrical stimulation, and/or magnetic stimulation of the cervical spinal cord and/or thoracic spinal cord, as described herein. This combined approach can help to put the spinal cord in an optimal physiological state for activating and/or improving respiratory drive, and/or otherwise enhancing respiratory function (e.g., for conditioning respiratory muscles as described herein).
In some variations, glutamatergic agent(s) may be administered systemically, though additionally or alternatively, glutamatergic agent(s) may be administered locally (e.g., to particular regions of the spinal cord, such as the cervical spinal cord). Glutamatergic agent(s) can be administered or delivered by injection (e.g., subcutaneously, intravenously, intramuscularly), orally, rectally, inhaled, or in any suitable manner.
The following examples are offered to illustrate, but not to limit the claimed invention.
Opioid overdose suppresses brainstem respiratory circuits and may result in death. We tested the hypothesis that exogenous stimulation of the cervical spine could activate respiratory centers in the ventral medulla and increase ventilation in humans. To determine if neuromodulation can reverse opioid-induced respiratory depression (OIRD), we used a commercially available electrode approved for intraoperative monitoring to apply epidural electrical stimulation (EES) dorsally at cervical spinal levels C2 to C7 in 17 anesthetized human subjects whose respiration was suppressed following administration of the synthetic opioid analgesic remifentanil. One subject was only tested in the control, no-stimulation condition. We administered two doses of remifentanil to the tested subjects: a low dose, which was 0.01-0.03 mcg/kg/min, and a high dose, which was 0.03-0.1 mcg/kg/min. Low-dose remifentanil partially suppressed respiration. High-dose remifentanil induced respiratory depression that led to apnea.
We defined spontaneous, voluntary breathing in subjects as the ON-State, whereas complete inhibition of spontaneous respiratory activity (remifentanil-induced apnea) was defined as the OFF-State. We tested seventeen subjects in ON-State and eight of them were tested in both ON- and OFF-States. EMG recordings measured the extent to which EES affected respiratory muscle activity. We assessed two frequencies of constant current, monopolar EES applied to seven locations in subjects in ON- and OFF-States to determine optimal stimulation parameters (
5 Hz EES was found to increase respiratory frequency and 30 Hz EES was found to increase amplitude of respiration in patients with voluntary respiration. Among the subjects tested in the ON-State (
EES stimulation at 5 Hz at cervical spinal segments C5, C6, and C7 increased respiratory frequency compared to control values (C5, p=0.0356; C6, p=0.0061; and C7, p=0.0092), but did not significantly increase tidal volume or decrease ΔPETCO2 (
The stimulation intensity of EES was below the motor activation threshold. Deltoid muscle EMG activity did not respond to 5- or 30 Hz EES at any cervical level tested in ON-State subjects, including the C5-C6 levels where the motor neurons that innervate the deltoid muscles reside. We observed genioglossal EMG activation in 73% of the tests that elicited a respiratory response, from which we infer that EES activated the hypoglossal nuclei in the brainstem. Moreover, the genioglosssal EMG activity was coordinated with EMG activation of the diaphragm and intercostal muscles and preceded activation of these ‘pump muscles’, as it typically does during eupnea. These observations indicate that motor neuron pacing was not the root cause of the responses that we measured, but rather that EES of the dorsal cervical spine activated neurons that augmented activity of the endogenous respiratory control system within the brainstem, which in turn increased the respiratory frequency or magnitude of respiratory muscle activation.
30 Hz stimulation induced sustained respiratory responses when voluntary respiration was depressed by high-dose remifentanil. Eight out of the seventeen subjects were tested in the OFF-State in the absence of any voluntary respiration (
Although 5 Hz stimulation in OFF-State subjects marginally decreased PETCO2 after stimulation, it failed to induce meaningful respiratory activity (
Cervical EES reset the respiratory cycle. A further analysis of the inspiratory onset in the ON-State indicated that cervical EES reset the respiratory cycle, which was evaluated using a phase transition analysis of the respiratory cycle (
Accordingly, we studied the capability of EES to modulate the rhythmic respiratory pattern itself in a setting where communication with the effector motor neurons in the ventral spine were intact, but the activity of the respiratory rhythm/pattern generator was suppressed. We observed that 30 Hz EES at C3/4 augmented the minute tidal volume in patients who were breathing spontaneously and induced cyclic respiratory activity in patients with apnea after remifentanil administration. The effect of the EES persisted after the EES stopped, suggesting that EES of the dorsal cervical spine elicited short-term potentiation of the respiratory pattern generator, which decayed within 60-90 seconds after EES ceased. The cervical spinal cord circuit may be regarded as the effector of respiratory muscle activation downstream from the more rostral, ponto-medullary network generating rhythmic respiratory activity. We observed that cervical EES not only augmented the amplitude of the respiration but also actively modulated the frequency of respiratory oscillations. Five Hz stimulation at C5 to C7 regions increased the respiratory frequency and often induced phase shifting of the respiratory cycle at the onset of EES; whereas 30 Hz stimulation increased the tidal volume during EES at the C4 level. Dual effects of dorsal cervical EES at different locations of the spine suggest that different sets of cervical neurons or axons of passage expressed different frequency-dependent patterns of activation, and that the different sets of activated neurons or axons communicate with different parts of the respiratory central pattern generator that control respiratory frequency (likely more rostral ponto-medullary elements of the respiratory pattern generating network) and tidal volume (likely more ventral medullary elements of the respiratory central pattern generator or spinal phrenic motor neurons).
Characterizing the distribution of cells with somatostatin (SST) and neurokinin-1 receptors (NK1R) in the cervical spinal cord may lead to better understanding of the mechanism of respiratory neuromodulation. Spinal SST+ and NK1R+ neurons are both involved in gating afferent inputs and SST+/NK1R+ neurons are associated with the generation of the respiratory pattern in the brainstem. We conducted an immunohistochemical analysis to identify the distribution of SST+ and NK1R+ neurons in the cervical spinal region in five human cadavers. Levels C3/4, C6, and C7 contained significantly high densities of SST and NK1R, double-positive neurons (
We investigated non-invasive neuromodulation of the respiratory spinal cord circuit, specifically with transcutaneous electrical stimulation (TES). This spinal neuromodulation has a substantial safety profile; there has been no TES-associated side-effects in combined >50,000 hours of treatment in more than 50 subjects.
As shown in
Furthermore,
Overall, TES of the spinal cord was shown to activate spinal cord motor neurons related to intercostal and diaphragm muscles (
A set of surface plots of phase and stimulation intensity of EES-induced respiratory responses were generated (not shown) for a set of timepoints including pre-stimulation baseline, intra-stimulation, immediately post-stimulation, 3 minutes post-stimulation, and 6 minutes post-stimulation. Furthermore, plots were generated with respect to changes of the tidal volume ratio in response to EES applied at L1L2, L3L4, and L5L6 spinal levels, changes of the frequency ratio in response to EES applied at L1L2, L3L4, and L5L6 spinal levels, changes of the minute ventilation ratio in response to EES applied at L1L2, L3L4, and L5L6 spinal levels. Stimulation was performed at 30 Hz. It should be noted that the L6 spinal level of a mouse is considered to correspond to the L5 spinal level of a human since humans do not have an L6 spinal level.
In
Various embodiments provided herein may include, but need not be limited to, one or more of the following:
Embodiment A1. A method for conditioning respiratory muscles in a patient, the method comprising:
Embodiment A2. The method of embodiment A1, wherein the stimulation signal activates the one or more respiratory muscles via activating motor neurons at a segmental spinal cord level.
Embodiment A3. The method of embodiment A1 or embodiment A2, wherein the stimulation signal is administered to a dorsal column of the thoracic spinal cord.
Embodiment A4. The method of any one of embodiments A1 to A3, wherein the stimulation signal is administered to a region selected from the group consisting of: C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, C4-C4, C3, C4, C5, C2-C7, T1, T1-T12, T7-T7, T7-T8, T7-T9, T8-T8, T8-T9, T9-T9, L1-L2, L3-L4, and L4-L5.
Embodiment A5. The method of any one of embodiments A1-A4, wherein the stimulation signal has a stimulation frequency of between about 20 Hz and 100 Hz.
Embodiment A6. The method of embodiment A5, wherein the stimulation signal has a stimulation frequency of between about 1 Hz and about 50 Hz.
Embodiment A7. The method of embodiment A6, wherein the stimulation signal has a stimulation frequency of between about 1 Hz and about 10 Hz.
Embodiment A8. The method of any one of embodiments A1-A7, wherein the stimulation signal is superimposed on a high frequency carrier signal.
Embodiment A9. The method of embodiment A8, wherein the high frequency carrier signal has a frequency of about 3 kHz, or about 5 kHz, or about 8 kHz up to about 30 kHz, or up to about 20 kHz, or up to about 15 kHz.
Embodiment A10. The method of embodiment A9, wherein the high frequency carrier signal has a frequency of about 10 kHz.
Embodiment A11. The method of any one of embodiments A1-A10, wherein the stimulation signal is an electrical stimulation signal.
Embodiment A12. The method of any one of embodiments A1-A11, wherein the stimulation signal has an amplitude of between about 5 mA to about 300 mA, or between about 5 mA to about 250 mA, or between about 5 mA to about 200 mA, between about 5 mA to about 150 mA, or between about 5 mA to about 100 mA, or between about 5 mA to about 80 mA, or between about 5 mA to about 60 mA, or between about 5 mA to about 50 mA.
Embodiment A13. The method of any one of embodiments A1-A11, wherein the stimulation signal is administered transcutaneously.
Embodiment A14. The method of any one of embodiments A1-A11, wherein the stimulation signal is delivered epidurally.
Embodiment A15. The method of any one of embodiments A1-A11, wherein the stimulation signal is delivered percutaneously.
Embodiment A16. The method of any one of embodiments A1-A11, wherein the stimulation signal is induced by a magnetic signal.
Embodiment A17. The method of any one of embodiments A1-A16, wherein the one or more respiratory muscles comprises intercostal muscles, a diaphragm, or both.
Embodiment A18. The method of any one of embodiments A1-A17, further comprising administering a second stimulation signal to a cervical spinal cord of the patient, wherein the second stimulation signal is effective to activate respiratory drive in the patient.
Embodiment A19. The method of embodiment A18, wherein administering the second stimulation signal is performed during the detected inspiratory phase.
Embodiment A20. The method of embodiment A18 or embodiment A19, wherein the second stimulation signal is administered to a region selected from the group consisting of C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, C4-C4, and C3, C4, C5.
Embodiment A21. The method of any one of embodiments A1-A20, further comprising administering a third stimulation signal to a lumbar spinal cord of the patient, wherein the third stimulation signal is effective to activate respiratory drive in the patient.
Embodiment A22. The method of embodiment A21, wherein administering the third stimulation signal is performed during the detected inspiratory phase.
Embodiment A23. The method of embodiment A21 or A22, wherein the third stimulation signal is administered to a region selected from the group consisting of L1-L2, L3-L4, and L4-L5.
Embodiment A24. The method of any one of embodiments A18-A20, wherein the second stimulation signal has a stimulation frequency from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, or between about 20 Hz and about 100 Hz.
Embodiment A25. The method of any one of embodiments A21-A23, wherein the third stimulation signal has a stimulation frequency from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, or between about 20 Hz and about 100 Hz.
Embodiment A26. The method of any one of embodiments A1-A25, further comprising detecting an expiratory phase of the patient, and ceasing administration of the stimulation signal during the detected expiratory phase.
Embodiment A27. The method of any one of embodiments A1-A26, wherein the stimulation signal is administered to prevent respiratory muscle atrophy in the patient.
Embodiment A28. The method of any one of embodiments A1-A26, wherein the stimulation signal is administered to treat respiratory muscle atrophy in the patient.
Embodiment A29. The method of any one of embodiments A1-A28, wherein the patient is intubated on a mechanical ventilator and the stimulation signal is administered to expedite ventilator weaning.
Embodiment A30. The method of any one of embodiments A1-A28, wherein the patient is not intubated on a mechanical ventilator and the stimulation signal is administered to delay or prevent the need for mechanical ventilation.
Embodiment A31. The method of any of embodiments A1-A30, wherein the patient has a respiratory insufficiency or failure.
Embodiment A32. The method of embodiment A29, wherein the respiratory insufficiency or failure is caused by any one or more of: acute respiratory distress syndrome (ARDS), ECMO, ventilator-induced diaphragm dysfunction, critical illness myopathy, chronic obstructive pulmonary disease (COPD), stroke, spinal cord injury, heart failure, trauma, pneumonia, sepsis, aging, and a neurodegenerative disorder.
Embodiment A33. The method of embodiment A32, wherein the neurodegenerative disorder is associated with a condition selected from the group consisting of: Parkinson's disease, Alzheimer's disease, Huntington's disease, amyotrophic lateral sclerosis (ALS), congenital central hypoventilation syndrome (CCHS), primary lateral sclerosis (PLS), dystonia, cerebral palsy, Guillain Barre Syndrome, and chronic inflammatory polyneuropathy.
Embodiment A34. The method of any one of embodiments A1-A33, further comprising administering a glutamatergic agent to the patient.
Embodiment A35. A stimulator configured to administer the stimulation signal according to any one of embodiments A1-A34.
Embodiment B1. A system for conditioning muscles in a patient, the system comprising:
Embodiment B2. The system of embodiment B1, wherein the one or more sensors comprises a sensor configured to detect chest wall expansion.
Embodiment B3. The system of embodiment B1 or embodiment B2, wherein the one or more sensors comprises a sensor coupled to a mechanical ventilator treating the patient.
Embodiment B4. The system of any one of embodiments B1-B3, wherein the stimulation signal activates the one or more respiratory muscles via activating motor neurons at a segmental spinal cord level.
Embodiment B5. The system of any one of embodiments B1-B4, wherein the stimulation signal is administered to a dorsal column of the thoracic spinal cord.
Embodiment B6. The system of any one of embodiments B1-B5, wherein the stimulation signal is administered to a region selected from the group consisting of: C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, C4-C4, C3, C4, C5, C2-C7, T1, T1-T12, T7-T7, T7-T8, T7-T9, T8-T8, T8-T9, T9-T9, L1-L2, L3-L4, and L4-L5.
Embodiment B7. The system of any one of embodiments B1-B5, wherein the stimulation signal has a stimulation frequency of between about 1 Hz and 50 Hz.
Embodiment B8. The system of embodiment B7, wherein the stimulation signal has a stimulation frequency of between about 20 Hz and about 100 Hz.
Embodiment B9. The system of embodiment B8, wherein the stimulation signal has a stimulation frequency of between about 1 Hz and about 50 Hz.
Embodiment B10. The system of any one of embodiments B1-B9, wherein the stimulation signal is superimposed on a high frequency carrier signal.
Embodiment B11. The system of embodiment B10, wherein the high frequency carrier signal has a frequency of about 3 kHz, or about 5 kHz, or about 8 kHz up to about 30 kHz, or up to about 20 kHz, or up to about 15 kHz.
Embodiment B12. The method of embodiment B11, wherein the high frequency carrier signal has a frequency of about 10 kHz.
Embodiment B13. The system of any one of embodiments B1-B12, wherein the stimulator is an electrical stimulator.
Embodiment B14. The system of embodiment B13, wherein the stimulation signal has an amplitude of between about 5 mA to about 300 mA, or between about 5 mA to about 250 mA, or between about 5 mA to about 200 mA, between about 5 mA to about 150 mA, or between about 5 mA to about 100 mA, or between about 5 mA to about 80 mA, or between about 5 mA to about 60 mA, or between about 5 mA to about 50 mA.
Embodiment B15. The system of any one of embodiments B1-B14, wherein the stimulator is configured to administer transcutaneous stimulation.
Embodiment B16. The system of embodiment B15, wherein the stimulator comprises one or more adhesive stimulators.
Embodiment B17. The system of any one of embodiments B1-B14, wherein the stimulator is configured to administer epidural stimulation.
Embodiment B18. The system of any one of embodiments B1-B14, wherein the stimulator is configured to administer percutaneous stimulation.
Embodiment B19. The system of any one of embodiments B1-B12, wherein the stimulator is a magnetic stimulator.
Embodiment B20. The system of any one of embodiments B1-B19, further comprising a second stimulator configured to administer a second stimulation signal to a cervical spinal cord of the patient, wherein the second stimulation signal is effective to activate respiratory drive in the patient.
Embodiment B21. The system of embodiment B20, wherein the second stimulator is configured to administer the second stimulation signal during the detected inspiratory phase.
Embodiment B22. The system of embodiment B20 or embodiment B21, wherein the second stimulation signal is administered to a region selected from the group consisting of C2-C2, C2-C3, C2-C4, C3-C3, C3-C4, C4-C4, and C3, C4, C5.
Embodiment B23. The system of any one of embodiments B1-B22, further comprising a third stimulator configured to administer a third stimulation signal to a lumbar spinal cord region of the patient, where the third stimulation signal is effective to activate respiratory drive in the patient.
Embodiment B24. The system of embodiment B23, wherein the third stimulator is configured to administer the third stimulation signal during the detected inspiratory phase.
Embodiment B25. The method of claim B23 or B24, wherein the third stimulator is configured to administer the third stimulation signal to a region selected from the group consisting of L1-L2, L3-L4, and L4-L5.
Embodiment B26. The system of any one of embodiments B20-B22, wherein the second stimulation signal has a stimulation frequency from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, or between about 20 Hz and about 100 Hz.
Embodiment B27. The system of any one of embodiments B23-B25, wherein the third stimulation signal has a stimulation frequency from about 1 Hz, or from about 2 Hz, or from about 3 Hz, or from about 4 Hz, or from about 5 Hz, or from about 10 Hz, or from about 10 Hz, or from about 10 Hz, up to about 500 Hz, or up to about 400 Hz, or up to about 300 Hz, or up to about 200 Hz up to about 100 Hz, or up to about 90 Hz, or up to about 80 Hz, or up to about 60 Hz, or up to about 40 Hz, or from about 3 Hz or from about 5 Hz up to about 80 Hz, or from about 5 Hz to about 60 Hz, or up to about 30 Hz, or between about 20 Hz and about 100 Hz.
Embodiment B28. The system of any one of embodiments B1-B27, wherein the controller is further configured to detect an expiratory phase of the patient based on a second sensor signal from one or more sensors, and wherein the stimulator is configured to cease administration of the stimulation signal during the detected expiratory phase.
Embodiment B29. The system of any one of embodiments B1-B28, wherein the system is configured for use with a patient who is intubated on a mechanical ventilator and the stimulation signal is administered to expedite ventilator weaning.
Embodiment B30. The system of any one of embodiments B1-B28, wherein the system is configured for use with a patient who is not intubated on a mechanical ventilator and the stimulation signal is administered to delay or prevent the need for mechanical ventilation.
It is noted that the term “patient” used herein can refer to a human or to a non-human mammal under the care of a medical practitioner. However, the methods provided herein can be applied to subjects that are not under the control or care of a medical practitioner. Thus, the terms “subject”, “individual,” and “patient” may be used interchangeably and typically refer to a mammal, and in certain embodiments a human or a non-human primate. It will be recognized that while the methods are described herein with respect to use in humans, in certain embodiments they are also suitable for animal, e.g., veterinary use. Thus, certain illustrative subjects include, but are not limited to humans, non-human primates, canines, equines, felines, porcines, ungulates, lagomorphs, and the like. Certain embodiments contemplate the methods described herein for use with domesticated mammals (e.g., canine, feline, equine), laboratory mammals (e.g., mouse, rat, rabbit, hamster, guinea pig), and agricultural mammals (e.g., equine, bovine, porcine, ovine), and the like. The term “subject” does not require one to have any particular status with respect to a hospital, clinic, or research facility (e.g., as an admitted patient, a study participant, or the like). Thus, in various embodiments, the subject can be a human (e.g., adult male, adult female, adolescent male, adolescent female, male child, female child) under the care of a physician or other health worker in a hospital, psychiatric care facility, as an outpatient, or other, clinical context. In certain embodiments the subject may not be under the care a physician or health worker and, in certain embodiments, may self-prescribe and/or self-administer the methods provided herein.
The foregoing description, for purposes of explanation, used specific nomenclature to provide a thorough understanding of the invention. However, it will be apparent to one skilled in the art that specific details are not required in order to practice the invention. Thus, the foregoing descriptions of specific embodiments of the invention are presented for purposes of illustration and description. They are not intended to be exhaustive or to limit the invention to the precise forms disclosed; obviously, many modifications and variations are possible in view of the above teachings. The embodiments were chosen and described in order to explain the principles of the invention and its practical applications, they thereby enable others skilled in the art to utilize the invention and various embodiments with various modifications as are suited to the particular use contemplated. It is intended that the following claims and their equivalents define the scope of the invention.
This application claims priority to U.S. Provisional Patent Application No. 63/174,979 filed on Apr. 14, 2021, the entire contents of which are hereby incorporated by reference in its entirety.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US22/24673 | 4/13/2022 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 63174979 | Apr 2021 | US |
