Patent Grant
RE48024
The inventions described herein relate to devices, systems and associated methods for treating sleeping disorders. More particularly, the inventions described herein relate to devices, systems and methods for treating obstructive sleep apnea.
Obstructive sleep apnea (OSA) is highly prevalent, affecting one in five adults in the United States. One in fifteen adults has moderate to severe OSA requiring treatment. Untreated OSA results in reduced quality of life measures and increased risk of disease including hypertension, stroke, heart disease, etc.
Continuous positive airway pressure (CPAP) is a standard treatment for OSA. While CPAP is non-invasive and highly effective, it is not well tolerated by patients. Patient compliance for CPAP is often reported to be between 40% and 60%.
Surgical treatment options for OSA are available too. However, they tend to be highly invasive (result in structural changes), irreversible, and have poor and/or inconsistent efficacy. Even the more effective surgical procedures are undesirable because they usually require multiple invasive and irreversible operations, they may alter a patient's appearance (e.g., maxillo-mandibulary advancement), and/or they may be socially stigmatic (e.g., tracheostomy).
U.S. Pat. No. 4,830,008 to Meer proposes hypoglossal nerve stimulation as an alternative treatment for OSA. An example of an implanted hypoglossal nerve stimulator for OSA treatment is the Inspire™ technology developed by Medtronic, Inc. (Fridely, Minn.). The Inspire device is not FDA approved and is not for commercial sale. The Inspire device includes an implanted neurostimulator, an implanted nerve cuff electrode connected to the neurostimulator by a lead, and an implanted intra-thoracic pressure sensor for respiratory feedback and stimulus trigger. The Inspire device was shown to be efficacious (approximately 75% response rate as defined by a 50% or more reduction in RDI and a post RDI of ≤20) in an eight patient human clinical study, the results of which were published by Schwartz et al. and Eisele et al. However, both authors reported that only three of eight patients remained free from device malfunction, thus demonstrating the need for improvements.
To address this and other unmet needs, the present invention provides, in exemplary non-limiting embodiments, devices, systems and methods for nerve stimulation for OSA therapy as described in the following detailed description.
It is to be understood that both the foregoing summary and the following detailed description are exemplary. Together with the following detailed description, the drawings illustrate exemplary embodiments and serve to explain certain principles. In the drawings:
The following detailed description should be read with reference to the drawings in which similar elements in different drawings are numbered the same. The drawings, which are not necessarily to scale, depict illustrative embodiments and are not intended to limit the scope of the invention.
Description of Fully Implanted Neurostimulator System
With reference to
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Generally, electrical stimulus is delivered by the INS 50 via the stimulation lead 60 to a nerve innervating a muscle controlling upper airway patency to mitigate obstruction thereof. To reduce nerve and muscle fatigue, the stimulus may be delivered for only a portion of the respiratory cycle, such as during inspiration which corresponds to negative pressure in the upper airway. Stimulation may be thus triggered as a function of respiration as detected by respiration sensing lead 70 in a closed-loop feedback system. By way of example, the stimulus may be triggered to turn on at the end of expiration (or at the beginning of inspiration), and triggered to turn off at the beginning of expiration (or at the end of inspiration). Triggering the stimulus as a function of expiration improves capture of the entire inspiratory phase, including a brief pre-inspiratory phase of about 300 milliseconds, thus more closely mimicking normal activation of upper airway dilator muscles. Over-stimulation may cause nerve and/or muscle fatigue, but a 40% to 50% duty cycle may be safely tolerated, thus enabling limited over-stimulation. As an alternative, stimulus may be delivered independent of actual respiration wherein the stimulus duty cycle is set for an average inspiratory duration at a frequency approximately equal to an average respiratory cycle.
Stimulus may be delivered to one or more of a variety of nerve sites to activate one muscle or muscle groups controlling patency of the upper airway. For example, stimulation of the genioglossus muscle via the hypoglossal nerve moves or otherwise stiffens the anterior portion of the upper airway, thereby decreasing the critical pressure at which the upper airway collapses during inspiration and reducing the likelihood of an apnea or hypopnea event occurring during sleep. Because the systems described herein work at the level of the tongue, it may be desirable to combine this therapy with a therapy (e.g., UPPP or palatal implant) that work at the level of the soft palate, thus increasing efficacy for a broader range of patients.
With reference back to
The patient controller 40 may comprise control circuitry and associated user interface to allow the patient to control the system via a wireless telemetry link while at home, for example. The patient controller 40 may include a power switch 42 to turn the system on and slowly ramp up when the patient goes to sleep at night, and turn it off when the patient wakes in the morning. A snooze switch 44 may be used to temporarily put the INS 50 in standby mode during which electrical stimulus is paused for a preprogrammed period of time to allow the patient to temporarily wake, after which the INS 50 turns back on and ramps up to the desired stimulus level. A display 46 may be provided to indicate the status of the INS 50 (e.g., on, off or standby), to indicate satisfactory wireless telemetry link to the INS 50, to indicate remaining battery life of the INS 50, to indicate normal operation of the INS 50, and/or to indicate the need for patient action etc. Display 46 may be configured to be a dash-board-like display, and may be any suitable display available to those of ordinary skill in the art, such as, for example, an LED or LCD display. Furthermore, information may be communicated to the patient controller 40 for display purposes by any suitable means known to those of ordinary skill in the art. For example, communication of information may be achieved through inductively coupled or radio frequency telemetry. The patient controller 40 may also have programmability to adjust stimulus parameters (e.g., amplitude) within a pre-set range determined by the physician in order to improve efficacy and/or to reduce sensory perception, for example. Optionally, the patient controller 40 may be configured to function as the programming wand 34 of the physician programmer 30.
Furthermore, the patient controller 40 may be provided with one or more mechanisms for improving patient compliance. For example, patient controller 40 may be provided with a time-keeping mechanism having the capabilities of a conventional alarm clock. In certain embodiments, controller 40 may be programmed by the user and/or the physician to alert the user when action, such as, for example, turning the system 10 on or off, is required by the user. Controller 40 may be configured to alert the user by any suitable means known in the art. For example, controller 40 may emit an audible alarm at programmed time intervals. In other embodiments, the patient controller 40 may be used to monitor a patient. For example, the patient controller 40 may be programmed to periodically send reports of patient actions, patient compliance, system status, etc., to a clinician or caregiver via a telephone or computer network.
With reference to
With reference to
The INS 50 may comprise a conventional implanted neurostimulator design used in neurostimulation applications, such as those available from Texcel (US), CCC (Uruguay) and NeuroTECH (Belgium), but modified for the present clinical application in terms of stimulation signal parameters, respiratory signal processing, trigger algorithm, patient control, physician programming, etc. The INS may contain a microprocessor and memory for storing and processing data and algorithms. Algorithms may be in the form of software and/or firmware, for example. One of several different embodiments of the neurostimulator may be implemented. For example, the neurostimulator may be an internal/implanted neurostimulator (INS) powered by a long-life primary battery or rechargeable battery, or an external neurostimulator (ENS) wirelessly linked (e.g., inductive) to an implanted receiver unit connected to the leads. The INS (or the receiver, unit of the ENS) may be implanted and optionally anchored in a number of different locations including a subcutaneous pocket in the pectoral region, the dorsal neck region, or cranial region behind the ear, for example.
The INS 50 may include any suitable circuitry and programming in accordance with the principles of the present disclosure. In one embodiment, INS 50 may include an activity sensor (not shown) for sensing the activity of a patient, including the amount of activity of the patient. The activity sensor may detect motion of a patient by any suitable means available to those of ordinary skill in the art. For example, a patient's motion may be detected by, for example, using an internal accelerometer and/or measuring the impedance of the patient's torso with, for example, the built-in respiration sensor discussed below, and/or measuring a tissue pressure on the surface of the implanted INS 50.
The data corresponding to a patient's detected motion may be stored, evaluated, and utilized in any of a number of various ways. In one embodiment, data corresponding to a patient's motion may be used to determine whether a patient is sleeping or awake. For example, when a patient's activity level falls below a predetermined threshold, it may be assumed that the patient is sleeping. Conversely, when the patient's activity level rises above the pre-determined threshold, it may be assumed that the patient is awake. The activity sensor therefore may be used to facilitate selectively applying treatment when the patient is detected to be sleeping and/or inhibiting treatment when the patient is detected to be awake. Alternatively, data corresponding to a patient's motion may be evaluated over a long period of time, such as, for example, the first few months of treatment, for indications of improvement in a patient's quality of life. It is contemplated that increases in a patient's average level of daily activity will correspond to successful treatment of OSA. This, in turn, may correspond to improvements in the patient's quality of life.
Moreover, the INS 50 may include a long-life battery (not shown) which requires periodic replacement after years of service. Alternatively, the INS may include a rechargeable power source such as a rechargeable battery or super capacitor that is used instead of the long-life battery. To facilitate recharging, the INS may include a receiver coil inductively linked to a transmitter coil that is connected to a recharging unit powered by a larger battery or line power. Because the patient is stationary while sleeping, recharging may be scheduled to occur sometime during sleep to eliminate the need to carry the recharging unit during daily activities. The transmitter coil and the receiver coil may be arranged coaxially in parallel planes to maximize energy transfer efficiency, and may be held in proximity to each other by a patch, garment, or other means as described with reference to the external neurostimulator embodiments. Other examples of neurostimulator designs will be described in more detail hereinafter.
With reference to
With continued reference to
The various embodiments of stimulation leads, for example, stimulation lead 60, disclosed herein may be fabricated by any suitable means known to those having ordinary skill in the art, and may be made from any suitable material. For example, the discussed sigmoid shape of the tubular jacket of lead body 62 may be formed by first extruding silicone in a semi-cured or semi cross-linked state. Next, the semi cross-linked extruded tubular jacket may be placed in a sigmoid mold and then allowed to become fully cross-linked. In particular, the semi cross-linked extruded tubular jacket may be placed in an oven and heated to convert the semi cross-linked silicone of the extruded tubular jacket to fully cross-linked silicone. Additionally, a lumen within the tubular jacket may be created along a longitudinal axis of the tubular jacket by any suitable means.
Furthermore, in accordance with the principles of the present disclosure, it is contemplated that one or more of the various embodiments of stimulation leads disclosed herein may be implanted in or near highly mobile portions of the body. For example, embodiments of the disclosed stimulation leads may be implanted in the ventral neck, for example, along a path between the clavicle and mandible of a patient. Additionally, although mastication, deglutition, and speech may result in mechanical loading on an implanted stimulation lead, it has been found that gross movement of the head and neck may create high mechanical stresses in the conductors of the lead body, lead jacket, and the junction between the conductor wires and the anchor points, such as, for example, the electrodes. Accordingly, it may be desirable to configure the various embodiments of stimulation leads to withstand certain predetermined amounts of fatigue and/or stresses, which may result from mechanical loading on a lead body due to gross movements of a patient's neck and head.
In particular, research has revealed that approximately 98% of the population may experience a 38.5% elongation or less in the distance between the clavicle and angle of the mandible (e.g., adjacent a contemplated area of implantation for a stimulation lead in accordance with the principles of this disclosure). It has also been found that the angular range of motion of the cervical spine between adjacent vertebrae may be approximately 12 degrees, thereby flexing the lead through this angle with a bend radius assumed to be approximately 1.0 centimeter. See Augustus A. White III et al., Clinical Biomechanics of the Spine, pp. 84, 356, and 373 (1978). Furthermore, the frequency of gross head movement through the range of motion in the contemplated area of implantation has been estimated to be approximately 300,000 cycles per year, or on the average approximately 50 times per waking hour.
Thus, it may be desirable to design a lead body that is capable of withstanding, among other things, the stresses imparted by the above-noted head and neck movements for an extended amount of time, such as, for example, ten years. In particular, in order to design a lead body that may remain functional for the exemplary ten year implanted life, it may be desirable to configure the lead bodies disclosed herein to withstand at least the above noted elongation and ranges of motion. For example, since implanted lead bodies are likely to be elongated by at least 38.5%, it may be desirable to design lead bodies to withstand being elongated by a predetermined distance Y, such as, for example, approximately 40% (+/−2%) from an initial unstressed state, for a minimum of 3.0 million cycles without failure, as depicted in
With reference to
With continued reference to
With this arrangement, the anode electrodes 90A and 90B are connected to a common conductor 68A imbedded in the body 80, and the cathode electrode 90C is connected to an independent conductor 68B extending from the lateral side 82 to the medial side 84 and imbedded in the body 80. By using the conductors 68 to make connections within the body 80 of the cuff 64, fatigue stresses are imposed on the conductors rather than the electrode contacts 90A, 90B and 90C.
With additional reference to
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With continued reference to
System 10 may also include a plurality of diagnostic mechanisms (e.g., circuitry and/or programming) for monitoring and/or determining the functionality of certain components, such as, for example, stimulation lead 60. In particular, system 10 may include one or more switching circuits (not shown) that facilitate connection of the respiratory/trans-thoracic impedance sensing circuits of the present disclosure (discussed in greater detail below) to stimulation lead 60 for measuring the impedance of lead 60. In some embodiments, the impedance sensing circuit may be connected to each electrode pair. In other embodiments, the impedance sensing circuit may be connected between the case of the implanted INS 50 and each conductor 68 within the lead 60. While those having ordinary skill in the art will readily recognize that any suitable impedance sensing method may be utilized to monitor and/or determine the functionality of lead 60, the respiratory/trans-thoracic impedance sensing circuit of the present disclosure may be preferred, since this circuit may be capable of identifying small changes in impedance rather than the large changes detectable by standard methods.
As alluded to above, sensing the impedance of lead 60 may provide for monitoring and/or determining the functionality of lead 60. Specifically, sensing the impedance of lead 60 may facilitate diagnosing and distinguishing between differing types of failures of lead 60. In particular, research has revealed that changes in the impedance of lead 60 may be indicative of certain types of failures, including, but not limited to, corrosion, high contact resistance, breakage, and/or shorting. For example, a broken wire inside the lead could be identified by an excessively high lead impedance value. Corrosion of an electrode with its resultant decrease in effective electrode surface area could be identified by a smaller increase in impedance of that electrode. Similarly, an abnormally low value could correspond with a short between conductors in the lead, or an abrasion of the lead body that exposed a conductor to the tissue. Measuring from the case of the INS to each electrode allows independent identification of the integrity of each wire/electrode in the lead. In addition, sensing the impedance of lead 60 may facilitate periodic, automated adjustment of stimulation pulse amplitude so as to maintain constant current, energy, and/or charge delivery using a simpler voltage mode delivery circuit. Such automated adjustment may facilitate ensuring safety and effectiveness by consistently delivering the prescribed current, energy, or charge in the presence of tissue/electrode impedance variations. By consistently controlling the delivery of only the minimally required energy necessary for stimulation of the nerve, the stimulation amplitude may be programmed closer to the actual stimulation threshold rather than programming a wide margin to ensure continued effectiveness. This enhances safety and reduces power consumption. Moreover, sensing the impedance of lead 60 may allow monitoring of certain system dynamics, such as, for example, doses actually delivered to a patient.
Description of Implant Procedure
With reference to
With continued reference to
With reference to
The implant procedure may be performed with the patient under general anesthesia in a hospital setting on an out-patient basis. Alternatively, local anesthesia (at the surgical access sites and along the subcutaneous tunnels) may be used together with a sedative in a surgical center or physician office setting. As a further alternative, a facial nerve block may be employed. After a post-surgical healing period of about several weeks, the patient may return for a polysomnographic (PSG) test or sleep study at a sleep center for programming the system and titrating the therapy. A trialing period may be employed prior to full implantation wherein the hypoglossal nerve or the genioglossus muscle is stimulated with fine wire electrodes in a sleep study and the efficacy of delivering stimulus to the hypoglossal nerve or directly to the genioglossus muscle is observed and measured by reduction in apnea hypopnea index, for example.
Other nerve target sites are described elsewhere herein and may be accessed by similar surgical access techniques. As an alternative to surgical dissection, less invasive approaches such as percutaneous or laparoscopic access techniques may be utilized, making use of associated tools such as tubular sheaths, trocars, etc.
Description of Alternative Stimulation Target Sites
With reference to
Airway dilator muscles and associated nerves suitable for activation include are described in the following text and associated drawings. The dilator naris muscle functions to widen the anterior nasal aperture (i.e., flares nostrils) and is innervated by the buccal branch of the facial nerve (cranial nerve VII). The tensor veli palatine muscle functions to stiffen the soft palate and is innervated by the medial (or internal) pterygoid branch of the mandibular nerve MN. The genioglossus muscle is an extrinsic pharyngeal muscle connecting the base of the tongue to the chin and functions to protrude the tongue. The genioglossus muscle is typically innervated by a distal or medial branch (or braches) of the right and left hypoglossal nerve. The geniohyoid muscle connects the hyoid bone to the chin and the sternohyoid muscle attaches the hyoid bone to the sternum. The geniohyoid muscle functions to pull the hyoid bone anterosuperiorly, the sternohyoid muscle functions to pull hyoid bone inferiorly, and collectively (i.e., co-activation) they function to pull the hyoid bone anteriorly. The geniohyoid muscle is innervated by the hypoglossal nerve, and the sternohyoid muscle is innervated by the ansa cervicalis nerve.
By way of example, a nerve electrode may be attached to a specific branch of the hypoglossal nerve innervating the genioglossus muscle (tongue protruder), or may be attached to a more proximal portion (e.g., trunk) of the hypoglossal nerve in which a specific fascicle innervating the genioglossus muscle is targeted by steering the stimulus using an electrode array. Activating the genioglossus muscle causes the tongue to protrude thus increasing the size of anterior aspect of the upper airway or otherwise resisting collapse during inspiration.
As an alternative to activation of any or a combination of the airway dilator muscles, co-activation of airway dilator and airway restrictor or retruder muscles may be used to stiffen the airway and maintain patency. By way of example, a nerve electrode may be attached to specific branches of the hypoglossal nerve innervating the genioglossus muscle (tongue protruder), in addition to the hyoglossus and styloglossus muscles (tongue retruders), or may be attached to a more proximal portion (e.g., trunk) of the hypoglossal nerve in which specific fascicles innervating the genioglossus, hyoglossus and styloglossus muscles are targeted by steering the stimulus using an electrode array. Activating the hyoglossus and styloglossus muscles causes the tongue to retract, and when co-activated with the genioglossus, causes the tongue to stiffen thus supporting the anterior aspect of the upper airway and resisting collapse during inspiration. Because the tongue retruder muscles may overbear the tongue protruder muscle under equal co-activation, unbalanced co-activation may be desired. Thus, a greater stimulus (e.g., longer stimulation period, larger stimulation amplitude, higher stimulation frequency, etc.) or an earlier initiated stimulus may be delivered to the portion(s) of the hypoglossal nerve innervating the genioglossus muscle than to the portion(s) of the hypoglossal nerve innervating the hyoglossus and styloglossus muscles.
With continued reference to
Site A is a distal or medial branch of the hypoglossal nerve proximal of a branch innervating the genioglossus muscle and distal of a branch innervating the geniohyoid muscle. Site B is a more proximal portion of the hypoglossal nerve proximal of the branches innervating the genioglossus muscle and the geniohyoid muscle, and distal of the branches innervating the hyoglossus muscle and the styloglossus muscle. Site C is a medial branch of the hypoglossal nerve proximal of a branch innervating the geniohyoid muscle and distal of branches innervating the hyoglossus muscle and the styloglossus muscle. Site D is a branch of the ansa cervicalis nerve distal of the nerve root and innervating the sternohyoid. Site E is a very proximal portion (trunk) of the hypoglossal nerve proximal of the branches innervating the genioglossus, hyoglossus and styloglossus muscles.
Activating site B involves implanting an electrode on a hypoglossal nerve proximal of the branches innervating the genioglossus muscle and the geniohyoid muscle, and distal of the branches innervating the hyoglossus muscle and the styloglossus muscle.
Co-activating sites A+C involves implanting a first electrode on a hypoglossal nerve proximal of a branch innervating the genioglossus muscle and distal of a branch innervating the geniohyoid muscle, and implanting a second electrode on the hypoglossal nerve proximal of a branch innervating the geniohyoid muscle and distal of branches innervating the hyoglossus muscle and the styloglossus muscle.
Co-activating sites A+C+D involves implanting a first electrode on a hypoglossal nerve proximal of a branch innervating the genioglossus muscle and distal of a branch innervating the geniohyoid muscle; implanting a second electrode on the hypoglossal nerve proximal of a branch innervating the geniohyoid muscle and distal of branches innervating the hyoglossus muscle and the styloglossus muscle; and implanting a third electrode on a branch of an ansa cervicalis nerve distal of the nerve root and innervating the sternohyoid.
Co-activating sites B+D involves implanting a first electrode on a hypoglossal nerve proximal of branches innervating the genioglossus muscle and the geniohyoid muscle, and distal of branches innervating the hyoglossus muscle and the styloglossus muscle; and implanting a second electrode on a branch of an ansa cervicalis nerve distal of the nerve root and innervating the sternohyoid.
Co-activating sites C+D involves implanting a first electrode on a hypoglossal nerve proximal of a branch innervating the geniohyoid muscle, and distal of branches innervating the hyoglossus muscle and the styloglossus muscle and implanting a second electrode on a branch of an ansa cervicalis nerve distal of the nerve root and innervating the sternohyoid.
Activating site E involves implanting an electrode on a hypoglossal nerve proximal of the branches innervating the genioglossus, hyoglossus and styloglossus muscles; and selectively activating (e.g., by field steering) the genioglossus muscle before or more than the hyoglossus and styloglossus muscles.
With reference now to
Another possible nerve stimulation site may include the superior laryngeal nerve SLN. The superior laryngeal nerve SLN descends posterior and medial from the internal carotid artery and divides into the internal laryngeal nerve ILN and external laryngeal nerve ELN. While the external laryngeal nerve ELN descends behind the sternohyoid with the superior thyroid artery, the internal laryngeal nerve ILN descends near the superior laryngeal artery. The internal laryngeal nerve ILN contains sensory (afferent) fibers that are connected to receptors in the larynx. Some of these receptors include, but are not limited to, mechanoreceptors which detect pressure changes in a patient's upper airway associated with its collapse and institute a physiological response to re-open the patient's upper airway. Therefore, stimulation of specific afferent fibers inside the ILN nerve may result in triggering a reflex response that causes upper airway dilation by activating several muscles groups.
As discussed below, the superior laryngeal nerve SLN, in addition to being a sensory nerve, is also a motor nerve. Therefore, it is contemplated that one or more of the fiber selective stimulation means described in greater detail below may be utilized to facilitate only stimulating the sensory or afferent fibers of the nerve.
Description of Alternative Nerve Electrodes
Any of the alternative nerve electrode designs described hereinafter may be employed in the systems described herein, with modifications to position, orientation, arrangement, integration, etc. made as dictated by the particular embodiment employed. Examples of other nerve electrode designs are described in U.S. Pat. No. 5,531,778, to Maschino et al., U.S. Pat. No. 4,979,511 to Terry, Jr., and U.S. Pat. No. 4,573,481 to Bullara, the entire disclosures of which are incorporated herein by reference.
With reference to the following figures, various alternative electrode designs for use in the systems described above are schematically illustrated. In each of the embodiments, by way of example, not limitation, the lead body and electrode cuff may comprise the same or similar materials formed in the same or similar manner as described previously. For example, the lead body may comprise a polymeric jacket formed of silicone, polyurethane, or a co-extrusion thereof. The jacket may contain insulated wire conductors made from BSW or solid wire comprising MP35N, MP35N with Ag core, stainless steel or Tantalum, among others. The lead body may be sigmoid shaped to accommodate neck and mandibular movement. Also, a guarded cathode tri-polar electrode arrangement (e.g., anode-cathode-anode) may be used, with the electrodes made of 90/10 or 80/20 PtIr alloy with silicone or polyurethane backing.
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Arms 1602 may be secured around a nerve (not shown) by any suitable means. For example, it is contemplated that arms 1602 may be elastic in nature, so as to gently grasp the nerve on its deep (contralateral) side. Alternatively, arms 1602 may be actively secured about a nerve by, for example, suturing an end portion of arms 1602 to, e.g., a portion of lateral side 1601. In embodiments where arms 1602 may be actively secured about a nerve, arms 1602 may be provided with a safety mechanism (not shown) that permits nerve cuff electrode 1600 to become disengaged from a nerve it is secured about upon the application of a predetermined amount of force. This predetermined force will be established at a level that is below that which can cause damage to the nerve.
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Compliant sheet wrap 2002 may be provided with any of a number of means that allow sheet wrap 2002 to expand, in order to accommodate nerve swelling and/or over tightening. For example, in one embodiment, sheet wrap 2002 may be provided with a plurality of radially and/or longitudinally distributed fenestrations (not shown). In other embodiments, sheet wrap 2002 may be provided with a plurality of undulations 2002a, such as, for example, sigmoid undulations, which may allow for expansion of sheet wrap 2002.
With reference now to
Description of Alternative Implant Procedure for the Stimulation Lead
With reference to
A method of implanting lead 230 may generally comprise accessing a proximal extent of the nerve by minimal surgical dissection and retraction of the mylohyoid muscle as shown in
A less invasive method of implanting a paddle-shaped lead 230 is shown in
With reference to
Description of Stimulation Lead Anchoring Alternatives
With reference to
By way of example, not limitation, and as shown in
The tether 264 may be formed from a sigmoid length of braided permanent suture coated with an elastomer (such as silicone or polyurethane) to maintain the sigmoid shape when in the unloaded state. The tether 264 may also be made from a monofilament suture thermoformed or molded into a sigmoid shape. The distal end of the tether 264 may be attached to the fibrous loop using a suture 266 or staple or other secure means. Note that the tether 264 may be made from a biodegradable suture that will remain in place only during healing.
Also by way of example, not limitation, an alternative is shown in
As alluded to above, stimulation lead 60 may comprise a number of differing design embodiments. One such embodiment has been discussed above with respect to
Lead body portion 2664 may be made more flexible than lead body portion 2663 by any of a variety of ways. For example, lead body portion 2664 may be made from a material having differing flexibility. Alternatively, the diameters of the braided stranded wires (BSW) and/or wire insulation that make up the lead body portion 2664 may be reduced when possible.
With continuing reference to
Anchor 2665 may include any suitable configuration known in the art. For example, anchor 2665 may include a substantially flat body portion 2666. Body portion 2666 may be configured to be secured to tissue, such as, for example, tissue proximate a treatment site, by any suitable means available in the art. For example, body portion 2666 may be provided with openings 2667 to facilitate, for example, suturing anchor 2665 to nearby tissue. Anchor 2665 can thereby isolate stress (tension) to one portion of lead body 2662, and particularly portion 2663, caused by gross head and neck movement.
Description of Field Steering Alternatives
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Nerves like the hypoglossal nerve or superior laryngeal nerve typically include a plurality of fibers having relatively larger diameters and a plurality of fibers having relatively smaller diameters. In the case of single function nerves, such as, for example, the hypoglossal nerve HGN, all of the nerve fibers may either be sensory or motor in function. However, in the case of multi-function nerves, such as, for example, the superior laryngeal nerve SLN, the fibers having relatively larger diameters are typically motor (efferent) fibers, and the fibers having relatively smaller diameters are typically sensory (afferent) fibers. Accordingly, there may be a need to selectively stimulate the differing diameter fibers in a nerve.
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Electrode contacts 2702-2704 may be disposed on nerve cuff 2701 in any suitable configuration to achieve the desired effect. For example, electrode contacts 2702-2704 may be disposed on inner surface 2701b. As depicted in
In use, electrode 2700 may be implanted upon a nerve in accordance with the principles of this disclosure. Electrode 2700 may be oriented on the nerve it is implanted on in any suitable manner, such as, for example, according to the direction of intended stimulation. Thus, in circumstances where it may be desired to stimulate efferent (motor) fibers of a nerve, such as, for example, the superior laryngeal nerve SLN, while avoiding stimulation to afferent (sensory) fibers of the nerve, the electrode 2700 may be oriented on the nerve in a manner such that anode electrode contact 2702 is located distally of cathode electrode contact 2703, with distal and proximal designations based on the relative location of the electrode contact on the nerve. Alternatively, in circumstances where it may be desired to stimulate afferent fibers of a nerve while avoiding stimulation of efferent fibers of the nerve, the electrode 2700 may be oriented on the nerve in a manner such that anode electrode contact 2702 is located proximally of cathode electrode contact 2703.
With reference now to
Electrode contacts 2753 may be connected to an implanted neurostimulator (INS), such as, for example, INS 50, in accordance with the present disclosure. The INS may be programmed to select any of electrode contacts 2753a-2753e for nerve stimulation. For example, in circumstances where it may be desired to stimulate the smaller diameter fibers of a nerve, it is contemplated that all electrode contacts 2753a-2753e may be selected for nerve stimulation, since closely spaced electrode contacts typically affect smaller diameter fibers (e.g., afferent or sensory fibers). In these circumstances, electrode contacts 2753a, 2753c, and 2753e may function as anode electrode contacts and electrode contacts 2753b and 2753d may function as cathode electrode contacts. In circumstances where it may be desired to stimulate the larger diameter fibers of a nerve, it is contemplated that only electrode contacts 2753a, 2753c, and 2753e may be selected for nerve stimulation, since loosely spaced electrode contacts typically affect larger diameter fibers (e.g., efferent or motor fibers). In these circumstances, electrode contacts 2753a and 2753e may function as anode electrode contacts, and 2753c may function as a cathode electrode contact.
Alternatively, electrode 2750 may be utilized to reduce muscle fatigue when implanted on single function nerves, such as, for example, the hypoglossal nerve. In such circumstances, muscle fatigue may be reduced by alternatively switching between using loosely spaced electrode contacts 2753a, 2753c, and 2753e, to stimulate large diameter fibers, and closely spaced electrode contacts 2753a-2753e, to stimulate small diameter fibers.
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Since the small diameter fibers of a nerve are typically stimulated by low charge densities and large diameter fibers of the nerve are typically stimulated by high charge densities, portions 2763a and 2763b may be sequentially utilized to alternate between stimulating the small and large diameter fibers of a nerve. In other words, in use, a stimulation pulse may be first delivered to portion 2763a to stimulate the small diameter fibers of a nerve. A subsequent stimulation pulse may be then delivered to portion 2763b to stimulate the large diameter fibers of a nerve. It is contemplated that alternating between stimulating the small and large diameter fibers of a nerve may facilitate reducing muscle fatigue while also ensuring sufficient muscle mass is stimulated to maintain the necessary contraction and force generation to successfully treat OSA.
Turning now to
Each of portions 2783a and 2783b may be configured to be substantially similar in conductance despite their differing surface areas. For example, portion 2783a may be made of a first material having a relatively lower conductance, while portion 2783b may be made of a second material having a relatively higher conductance. Thus, when subjected to the same stimulation pulse (e.g., a slow rising, small amplitude pulse having a relatively long duration of approximately 0.2 to 0.35 milliseconds), portion 2783a may have a higher charge density than portion 2783b because of its relatively smaller surface area than portion 2783b. Similarly, when subjected to the same stimulation pulse, portion 2783b may have a lower charge density than portion 2783a because of its relatively larger surface area than portion 2783a. Accordingly, because of the differing charge densities, portion 2783a may be adapted to stimulate large diameter fibers of a nerve, and portion 2783b may be adapted to stimulate small diameter fibers of the nerve.
In use, a stimulation pulse may be first delivered to portion 2783a to stimulate the large diameter fibers of a nerve. A subsequent stimulation pulse may be then delivered to portion 2783b to stimulate the small diameter fibers of the nerve. It is contemplated that alternating between stimulating the small and large diameter fibers of a nerve may facilitate muscle fatigue while also ensuring that sufficient muscle mass is stimulated to maintain the necessary contraction and force generation to successfully treat OSA.
In certain embodiments, such as when nerve cuff electrodes 2760 and 2780 are implanted on a multi-function nerve (e.g., the superior laryngeal nerve SLN), it is contemplated that portions 2763a/2763b and portions 2783a/2783b may be utilized to selectively stimulate either the afferent or efferent fibers of the nerve.
With reference now to
Nerve cuff electrode 2790 may be configured to selectively stimulate both small diameter fibers contained in fascicle 2777a and large diameter fibers contained in fascicle 2777b of nerve 2792. For example, as shown in
Description of Respiration Sensing Lead Anchoring Alternatives
With reference to the following figures, various additional or alternative anchoring features for the respiration sensing lead 70 are schematically illustrated. Anchoring the respiration sensing lead 70 reduces motion artifact in the respiration signal and stabilizes the bio-impedance vector relative to the anatomy.
In each of the embodiments, by way of example, not limitation, the respiration sensing lead 70 includes a lead body 70 with a proximal connector and a plurality of distal respiration sensors 74 comprising ring electrodes for sensing bio-impedance. The lead body 72 of the respiration sensing lead 70 may include a jacket cover containing a plurality of conductors 78, one for each ring electrode 74 requiring independent control. Generally, the impedance electrodes 74 may comprise current emitting electrodes and voltage sensing electrodes for detecting respiration by changes in bio-impedance.
With reference to
With reference to
With reference to
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With reference to
With reference to
Other fixation embodiments may be used as well. For example, the fixation element may engage the muscle fascia and adjacent subcutaneous tissues or may be embedded therein. To this end, the electrodes may alternatively comprise intramuscular electrodes such as barbs or helical screws.
Description of Respiration Sensing Electrode Alternatives
A description of the various alternatives in number, spacing, anatomical location and function of the impedance electrodes follows. Generally, in each of the following embodiments, the respiration sensing lead includes a lead body and a plurality of respiration sensors comprising ring electrodes for sensing bio-impedance. The lead body may include a plurality of insulated conductors disposed therein, with one conductor provided for each ring electrode requiring independent connection and/or control. The impedance electrodes may comprise current emitting electrodes and voltage sensing electrodes for detecting respiration by changes in bio-impedance.
With reference to
With reference to
With reference to
In addition to the cylindrical electrodes shown, other electrode configurations are possible as well. For example, the electrodes may be bi-directional with one planar electrode surface separated from another planar electrode surface by insulative material. Alternatively or in combination, circular hoop electrodes may be placed concentrically on a planar insulative surface. To mitigate edge effects, each electrode may comprise a center primary electrode with two secondary side electrodes separated by resistive elements and arranged in series. An alternative is to have each primary current-carrying electrode connected by a resistive element to a single secondary side electrode. The conductive housing of the INS 50 may serve as an current-carrying electrode or voltage-sensing electrode. Alternatively or in addition, an electrode may be mounted to the housing of the INS 50.
Because bio-impedance has both a real and imaginary component, it is possible to measure the bio-Z phase as well as magnitude. It may be preferable to extract both magnitude and phase information from the bio-Z measurement because the movement of the lung-diaphragm-liver interface causes a significant change in the phase angle of the measured impedance. This may be valuable because motion artifacts of other tissue have less impact on the bio-Z phase angle than they do on the bio-Z magnitude. This means the bio-Z phase angle is a relatively robust measure of diaphragm movement even during motion artifacts.
An example of a bio-Z signal source is a modulated constant-current pulse train. The modulation may be such that it does not interfere with the stimulation signal. For example, if the stimulation signal is 30 Hz, the bio-Z signal source signal may be modulated at 30 Hz or a sub-multiple of 30 Hz such that bio-Z and stimulation do not occur simultaneously. The pulses in the pulse train may have a pulse width between 1 uS to 1 mS, such as 100 uS. The pulses may be separated by a period of time roughly equal to the pulse width (i.e., on-time of the pulses). The number of pulses in a train may be determined by a trade-off between signal-to-noise and power consumption. For example, no more than 10 pulses may be necessary in any given pulse train. The magnitude of current delivered during the pulse on-time may be between 10 uA and 500 uA, such as 50 uA.
Other wave forms of bio-Z source signal may be used, including, without limitation, pulse, pulse train, bi-phasic pulse, bi-phasic pulse train, sinusoidal, sinusoidal w/ramping, square wave, and square w/ramping. The bio-Z source signal may be constant current or non-constant current, such as a voltage source, for example. If a non-constant current source is used, the delivered current may be monitored to calculate the impedance value. The current-carrying electrodes may have a single current source, a split-current source (one current source split between two or more current-carrying electrodes), or a current mirror source (one current source that maintains set current levels to two or more current-carrying electrodes). Different characteristics of the sensed signal may be measured including, without limitation, magnitude, phase shift of sensed voltage relative to the current source signal, and multi-frequency magnitude and/or phase shift of the sensed signal. Multi-frequency information may be obtained by applying multiple signal sources at different frequencies or a single signal source which contains two or more frequency components. One example of a single multi-frequency source signal is a square wave current pulse. The resultant voltage waveform would contain the same frequency components as the square wave current pulse which would allow extraction of Bio-Z data for more than a single frequency.
With reference to
A variety of different bio-Z vector orientations relative to the anatomy may be employed. Generally, bio-Z vectors for monitoring respiration may be located on the thorax. However, bio-Z electrodes located in the head and neck may also be used to define respiratory bio-Z vectors. By way of example, not limitation, the bio-Z vector may be arranged transthoracically (e.g., bilaterally across the thorax), anteriorly on the thorax (e.g., bilaterally across the thoracic mid-line), across the lung-diaphragm-liver interface, perpendicular to intercostal muscles, between adjacent ribs, etc. A single bio-Z vector may be used, or multiple independent vectors may be used, potentially necessitating multiple sensing leads. One or more bio-Z sub-vectors within a given bio-Z vector may be used as well.
With reference to
There are several short bio-Z vectors which provide excellent signals correlated to diaphragmatic movement. In general, these vectors have at least one end at or near the lower edge of the ribcage. The short diaphragmatic bio-Z vectors have been successfully used in canines in vector lengths ranging from approximately less than ½ inch to a few inches in length.
By way of example, not limitation, the following bio-Z vectors may be effective for monitoring respiration and/or for measuring artifacts for subsequent removal of the artifact from the respiration signal. Vector C-G is across the upper left and upper right lobes of the lungs, and provides a good signal of ribcage expansion with moderate cardiac artifact. Vector D-F is a short-path version of C-G that provides a good respiratory signature largely correlated with ribcage expansion, with less cardiac artifact than C-G, but may be sensitive to movement of arms due to location on pectoral muscles. Vector C-D is a short-path ipsilateral vector of the upper right lung that may be sensitive to arm movement but has less cardiac artifact. Vector B-H is a transverse vector of the thoracic cavity that captures the bulk of the lungs and diaphragm movement. Vector B-H, however, may be relatively less susceptible to changes in body position, and may still provide a generally good signal when the patient changes positions. In certain circumstances, the signal produced by vector B-H may have a less than desired signal to noise ratio. However, it is contemplated that generally available methods of signal processing in accordance with the present disclosure may be utilized the improve signal to noise ratio of the signal produced by Vector B-H. Vector A-E is an ipsilateral vector across the lung-diaphragm-liver interface. Because the liver is higher in conductivity and has a different impedance phase angle than the lung, vector A-E1 yields a good signal on both bio-Z magnitude and phase with limited cardiac artifact. Vector B-K is an ipsilateral vector across the lung-diaphragm-liver interface that is substantially between a common set of ribs with a current path that is mostly perpendicular to the intercostal muscles. Because resistivity of muscle is much higher perpendicular to the muscle direction than parallel, vector B-K reduces current-shunting through the muscle which otherwise detracts from the signal of the lung-diaphragm-liver interface. Vector A-K is an ipsilateral vector across the lung-diaphragm-liver interface similar to vector A-E1 but is more sensitive to movement of the lung-diaphragm-liver interface than to changes in resistivity of the lung-diaphragm-liver interface due to inspired air volume and is thus a good indicator of diaphragm movement. Vector B-E1 is a vector across the middle and lower right lung and is good for detecting diaphragm movement with little cardiac artifact. Vector C-E1 is a vector across the upper and middle right lung and is also good for detecting diaphragm movement with little cardiac artifact. Vector D-E1 is a vector across the upper right lung with little cardiac artifact. Vector A-D is an ipsilateral across a substantial portion of the right lung and diaphragm with little cardiac artifact, but may be susceptible to motion artifact due to arm movement. Vector E1-E2 is a vector across the heart and provides a good cardiac signal that may be used for removing cardiac artifact from a respiratory signal. Vector E2-J is a vector across the lung-diaphragm-stomach interface that provides a good measure of diaphragm movement using bio-Z phase vs. magnitude because the stomach has almost no capacitive component and generally low conductivity. Vector L-M is a trans-diaphragm vector that is generally across the lung-diaphragm-liver interface with little cardiac artifact. Vector L-M may be relatively less susceptible to body position and movement and may yield a good signal even if the patient is laying on the side of the sensing lead. In embodiments where the signal produced by vector L-M has a less than desired signal to noise ratio, it is contemplated that generally available methods of signal processing may be utilized to improve the signal to noise ratio of the signal produced by vector L-M.
Electrodes placed at any of the above-noted locations may include, but are not limited to, combination electrodes, such as, for example, electrodes capable of both providing a current charge and sensing a voltage.
With reference to
With specific reference to
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With reference to
In some embodiments, it is contemplated that several short, intermediate, and long distance vectors may be continually sampled, even if a desirable signal is being received from a short distance vector, in order to identify secondary vector signals that may be utilized if the currently utilized vector signal fails for any reason. However, fully processing the data from signals generated by all of the vectors may require complex sensing circuitry and processing of detection algorithms that may utilize undesirable amounts of battery power. Therefore, it may be desirable to only monitor selected characteristics of the secondary vector signals. With specific reference to
In particular, method 3850 may include feeding the signals from all available vectors into a plurality of channel selection switches 3851. The signals may be then analyzed for relevant fiducials by the respiratory impedance sensing circuit 3853. Once relevant fiducials have been discriminated, it may be possible to identify the best vector signal for respiration signal analysis. The fiducials of the remaining vectors may be then stored in circular buffer memory 3854 (as noted above) to facilitate switching to a secondary vector signal if the primary signal is no longer suitable for respiration detection.
The periodic monitoring (or interleaving) of secondary vector signals may facilitate faster switching to those vector signals when necessary. In particular, it is contemplated that when a decision to switch to a secondary vector signal is made (i.e., when the primary signals degrades to a point where it is no loner desirable for detecting respiration), the saved data (e.g., relevant fiducials) may be used to “seed” a signal analysis algorithm with recently collected data, so as to promote faster vector switching by eliminating the need to wait for collection of sufficient data for the secondary vector signal. In other words, because select information of a secondary signal is available before the signal is actually used for respiration detection, analysis of the secondary signal for, among other things, respiration detection may begin slightly faster than it would have if no data was available.
Furthermore, in certain embodiments, additional impedance sensors may be used as backup sensors to the sensor generating the primary vector signal. In these embodiments, data from the secondary sensors may be also analyzed to identify and save relevant fiducials in the memory. This stored information may be used to provide supplemental or alternate information to facilitate identifying appropriate respiratory timing, when switching vector signals becomes necessary as a result of primary signal degradation.
The respiratory bio-Z signal is partly due to the resistivity change which occurs when air infuses lung tissue, partly due to the relative movement of electrodes as the rib cage expands, and partly due to the displacement of other body fluids, tissue and organs as the lungs move along with the ribcage and diaphragm. As described above, each vector measures certain of these changes to different extents. It may be desirable, therefore, to combine vectors which have complementary information or even redundant information to improve the respiratory information of the bio-Z signal. To this end, multiple vectors may be used. For example, one vector may be used to sense changes in the lung-diaphragm-liver interface and a second vector may be used to detect changes (e.g., expansion, contraction) of the lung(s). Examples of the former include A-K, B-K, A-E1, B-E1, and A-B. Examples of the later include D-F, B-D, C-G, D-E1, and C-E1. Note that some vector combinations which share a common vector endpoint such as A-E1, D-E1 and B-E1, B-D may use a common electrode which would simplify the respiratory sensing lead or leads.
An advantage of using the lung-diaphragm-liver interface vector is that it provides a robust signal indicative of the movement of the diaphragm throughout the respiratory cycle. The liver is almost two times more electrically conductive than lung tissue so a relatively large bio-Z signal can be obtained by monitoring the movement of the lung-diaphragm-liver interface. Because the liver functions to filter all the blood in the body, the liver is nearly completely infused with blood. This helps to dampen out the cardiac artifact associated with the pulsatile flow of the circulatory system. Another advantage of this location is that vectors can be selected which avoid significant current path through the heart or major arteries which will help reduce cardiac artifact.
It is worth noting that diaphragm movement is not necessarily synchronous with inspiration or expiration. Diaphragm movement typically causes and therefore precedes inspiration and expiration. Respiratory mechanics do allow for paradoxical motion of the ribcage and diaphragm, so diaphragm movement is not necessarily coincident with inspiration. During REM sleep, the diaphragm is the dominant respiratory driver and paradoxical motion of the ribs and diaphragm can be problematic, especially if movement of the ribcage is being relied upon as an inspiratory indicator. Monitoring the diaphragm for pre-inspiratory movement becomes especially valuable under these circumstances. Bio-Z monitoring of the diaphragm can be used as a more sophisticated indicator of impending inspiration rather than the antiquated approach of desperately trying to identify and respond to inspiration in pseudo-real time based on sensors which are responding to characteristics of inspiration.
For purposes of monitoring respiration, it is desirable to minimize shunting of the electrical current through tissues which are not of interest. Shunting may result in at least two problems: reduced signal from the lungs; and increased chance of artifacts from the shunted current path. Skeletal muscle has non-isotropic conductivity. The muscle's transverse resistivity (1600 ohm-cm) is more than 5 times its longitudinal resistivity (300 ohm-cm). In order to minimize the adverse effect of shunting current, it is desirable to select bio-Z sensing vectors which are perpendicular to muscle structure if possible. One such example is to locate two or more electrodes of a bio-Z sensing array substantially aligned with the ribs because the intercostal muscles are substantially perpendicular to the ribs.
Description of Respiration Signal Processing
With reference to
With continued reference to
As noted above, the present disclosure contemplates conditioning sensed bio-impedance into a useable trigger signal for stimulation. However, one exemplary limitation to using sensed bio-impedance may be the body's nominal impedance. In practice, a sensed bio-impedance signal may be obtained by applying a suitable, known current through one portion of a tissue of interest and measuring the voltage potential across the same tissue. This measurement technique is illustrated in
Turning now to
In use, the impedance Z1 of exemplary bridge 3900 may be closely matched to the expected impedance of a patient's body Zbody, the impedance Z2 matched to impedance Z3, and the voltage potential across voltage measuring device 3902 may be measured. It is contemplated that if impedances Z1-Z3 are closely matched to Zbody, the measured voltage potential across voltage measuring device 3902 will be predominantly due to respiratory impedance changes and the voltage signal due to the body's nominal impedance will be largely removed. Further, it is contemplated that the voltage changes measured at 3902 due to respiratory impedance changes will have an amplitude that is approximately ½ of the amplitude of the voltage changes, measured with the above-noted direct-measurement technique, assuming the same currently flow through the body. The removal of the voltage signal due to the body's nominal impedance while retaining ½ of the voltage signal amplitude due to changes in respiratory impedance, may facilitate detecting the small impedance changes associated with respiration by improving the resolution of those changes.
In other embodiments, the body's nominal impedance may be removed or reduced from a sensed signal by, for example, introducing a nominal offset removal module 3921 into an impedance measuring circuit 3920 of the present disclosure, as depicted in
Turning now to
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With reference to
The step of removing specific noise artifacts 374 may be performed in a number of different ways. However, before signal processing 374, both cardiac and motion noise artifact may be mitigated. For example, both cardiac and motion noise artifact may be mitigated prior to signal processing 374 by selection of bio-Z vectors that are less susceptible to noise (motion and/or cardiac) as described previously. In addition, motion artifact may be mitigated before signal processing 374 by minimizing movement of the sensing lead and electrodes relative to the body using anchoring techniques described elsewhere herein. Furthermore, motion artifact may be mitigated prior to signal processing 374 by minimizing relative movement between the current-carrying electrodes and the voltage-sensing electrodes, such as by using combined current-carrying and voltage-sensing electrodes.
After cardiac and motion artifact has been mitigated using the pre-signal processing techniques described above, both cardiac and motion artifact may be removed by signal processing 374.
For example, the signal processing step 374 may involve the use of a low pass filter (e.g., less than 1 Hz) to remove cardiac frequency noise components which typically occur at 0.5 to 2.0 Hz, whereas resting respiration frequency typically occurs below 1.0 Hz.
Alternatively, the signal processing step 374 may involve the use of a band pass or high pass filter (e.g., greater than 1 Hz) to obtain a cardiac sync signal to enable removal of the cardiac noise from the bio-Z signal in real time using an adaptive filter, for example. Adaptive filters enable removal of noise from a signal in real time, and an example of an adaptive filter is illustrated in
Another signal processing technique to remove cardiac noise is to combine signals from two or more bio-Z vectors wherein respiration is the predominate signal with some cardiac noise. This may also be used to reduce motion artifact and other asynchronous noise. Each of the two or more signals from different bio-Z vectors may be weighted prior to combining them into a resultant signal Vw(i). If it is assumed that (a) the respiratory bio-impedance is the largest component in each measured vector, (b) the non-respiratory signal components in one vector are substantially independent of the non-respiratory components in the other vector, and (c) the ratio of the non-respiratory component to the respiratory components in one vector is substantially equal to the same ratio in the other vector, then a simple weighting scheme may be used wherein each signal is divided by it's historic peak-to-peak magnitude and the results are added. For example, if MA=historical average peak-to-peak magnitude of signal from vector A, MB=historical average peak-to-peak magnitude of signal from vector B, VA(i)=data point (i) from vector A, VB(i)=data point (i) from vector B, then the resultant signal VW(i) (i.e., weighted average of A & B for data point (i)) may be expressed as VW(i)=VA(i)/MA+VB(i)/MB.
Yet another signal processing technique for removing cardiac noise is to subtract a first signal that is predominantly respiration from a second signal that is predominantly cardiac. For example, the first signal may be from a predominantly respiratory bio-Z vector (e.g., vector B-H) with some cardiac noise, and the second signal may be from a predominantly cardiac bio-Z vector (e.g., vector E1-E2) with some respiration signal. Each of the two signals from the different bio-Z vectors may be weighted prior to subtracting them. The appropriate weighting may be determined, for example, by calculating the power density spectra in the range of 2-4 Hz for a range of weighted differences across at least several respiratory cycles A minimum will occur in the power density spectra for the weighted averages which are sufficiently optimal.
Motion artifact may be removed by signal processing 374 as well. Motion artifact may be identified and rejected using signal processing techniques such as monitoring voltage magnitude, testing the correlation of magnitude and phase, and/or testing correlation at two or more frequencies. Motion artifacts may cause a large change in measured bio-impedance. A typical feature of motion artifacts is that the voltage swings are much larger than respiration. Another feature is that the voltage changes are highly erratic. Using these characteristics, which will be described in more detail below, motion artifact may be removed from the respiration signal.
The step of extracting waveforms indicative of respiration and other events 374 may be better explained with reference to
The step of extracting 374 waveform data indicative of an awake period 422 vs. a sleep period 424 from a bio-Z signal 420 may be explained in more detail with reference to
The CV may be calculated as follows:
Generally, if the CV is greater than 0.20 over a one minute period then person is awake. Also generally, if the CV is less than 0.20 over a one-minute period then person is asleep. These events may be flagged for the step of fiducial extraction 378 wherein data (e.g., event duration, CV, PP range, PPmin, PPmax, etc.) may be time stamped and stored with an event identifier. If CV is greater than 1.00 over a 20 second period then body movement is affecting the bio-Z signal. By way of example, not limitation, if body movement is detected, then (a) stimulation may be delivered in an open loop fashion (e.g., based on historical respiratory data); (b) stimulation may be delivered constantly the same or lower level; or (c) stimulation may be turned off during the period of movement. The selected stimulation response to detected movement may be preset by the physician programmer or by the patient control device. Other stimulation responses may be employed as will be described hereinafter.
In each of
A typical indication of hypopnea (HYP) and apnea (OSA, CSA) events is a recurrent event followed by a recovery. The period (T) of each event (where PP oscillates between PPmax and PPmin and back to PPmax) may be about 15 to 120 seconds, depending on the individual. The largest PP values observed during hypopneas and apneas are usually between 2 and 5 times larger than those observed during regular breathing 424 during sleep. The ratio of the PPmax to PPmin during recurrent hypopnea and apnea events is about 2 or more. During the event and recovery periods (excluding transitional events), PP values of adjacent respiratory cycles do not typically change abruptly and it is rare for the change in PP amplitude to be more than 50% of PPmax. One exception to this observation is that some people gasp 456, 466 (i.e., transitional event) as they recover from a CSA or OSA event.
The ratio of successive PP magnitudes during normal (non-event) sleep 424 is mostly random. The ratio of successive PP magnitudes during apnea and hypopnea events will tend to be a non-random sequence due to the oscillatory pattern of the PP values. Recurrent apneas and hypopneas may be diagnosed by applying a statistical test to the sequence of successive PP ratios.
The step of extracting 374 waveform data indicative of an hypopnea event 442 from a bio-Z signal 440 may be explained in more detail with reference to
The step of extracting 374 waveform data indicative of an OSA event 452 from a bio-Z signal 450 may be explained in more detail with reference to
The step of extracting 374 waveform data indicative of a CSA event 462 from a bio-Z signal 460 may be explained in more detail with reference to
With continued reference to
The step of extracting 374 waveform data indicative of sleep stage (e.g., rapid eye movement (REM) sleep vs. no-rapid eye movement (NREM) sleep) may be performed by comparing the phase difference between a first vector and a second vector wherein the first bio-Z vector is along the lung-diaphragm-liver interface (e.g., vector A-K or vector B-K) and the second bio-Z vector is about the lung(s). Examples of the first bio-Z vector include A-K, B-K, A-E1, B-E1, and A-B. Examples of the second bio-Z vector include D-F, B-D, C-G, D-E1, and C-E1. Note that some vector combinations which share a common vector endpoint such as A-E1, D-E1 and B-E1, B-D may use a common electrode and to simplify the respiratory sensing lead or leads. Typically, during NREM sleep, the two vectors are substantially in phase. During REM sleep, the diaphragm is the primary respiratory driver and a common consequence is paradoxical motion of the ribcage and diaphragm (i.e., the two vectors are substantially out of phase). This characteristic would allow for an effective monitor of a person's ability to reach REM sleep. Accordingly, REM and NREM sleep stages may be detected, identified, and flagged for the step of fiducial extraction 378 wherein characteristic data (e.g., event duration, phase, etc.) may be time stamped and stored with an event identifier.
An alternative method of detecting an OSA event is to make use of a split current electrode arrangement as shown in
Generally, the extracted 378 waveform and event data may be used for therapy tracking, for stimulus titration, and/or for closed loop therapy control. For example, data indicative of apneas and hypopneas (or other events) may be stored by the INS 50 and/or telemetered to the patient controlled 40. The data may be subsequently transmitted or downloaded to the physician programmer 30. The data may be used to determine therapeutic efficacy (e.g., apnea hypopnea index, amount of REM sleep, etc.) and/or to titrate stimulus parameters using the physician programmer 30. The data may also be used to control stimulus in a closed loop fashion by, for example, increasing stimulus intensity during periods of increased apnea and hypopnea occurrence or decreasing stimulus intensity during periods of decreased apnea and hypopnea occurrence (which may be observed if a muscle conditioning effect is seen with chronic use). Further, the data may be used to turn stimulus on (e.g., when apnea or hypopnea events start occurring or when motion artifact is absent) or to turn stimulus off (e.g., when no apnea or hypopnea events are occurring over a present time period or when motion artifact is predominant).
Description of Stimulus Trigger Algorithms
As mentioned previously with reference to
The system components 482 involved in implementing the algorithm may include the physician programmer (or patient controller), INS and associated device memory, and the respiratory sensor(s). The sensors and device memory are the sources of real-time data and historical fiducial data which the current algorithm uses to generate a stimulation trigger signal. The data 484 utilized in implementing the algorithm may include patient specific data derived from a sleep study (i.e., PSG data), data from titrating the system post implantation, and historic and real-time respiratory data including respiratory and event fiducials. The processes 486 utilized in implementing the algorithm may include providing a default algorithm pre-programmed in the INS, patient controller or physician programmer, modifying the default algorithm, and deriving a current algorithm used to generate a trigger signal 488.
More specifically, the processes 486 utilized in implementing a predictive trigger algorithm may involve several sub-steps. First, a default algorithm may be provided to predict onset of inspiration from fiducial data. Selecting an appropriate default algorithm may depend on identifying the simplest and most robust fiducial data subsets which allow effective prediction of onset. It also may depend on a reliable means of modifying the algorithm for optimal performance. Second, modification of the default algorithm may require a reference datum. The reference datum may be the estimated onset for past respiratory cycles. It is therefore useful to precisely estimate inspiratory onset for previous respiratory cycles from historical fiducial data. This estimation of inspiratory onset for previous respiratory cycles may be specific to person, sensor location, sleep stage, sleep position, or a variety of other factors. Third, the current algorithm may be derived from real-time and historical data to yield a stimulation trigger signal 488.
As alluded to above, a trigger algorithm, such as, for example, trigger algorithm 4700 depicted in
With reference now to
With reference to
With reference now to
As described above, a peak is declared for a given set of data points under consideration when a peak detection criteria is met. The declared peak itself may be used in further algorithm calculations or a more precise estimate of peak time and voltage may be calculated. The more precise estimates of peak time and voltage are referred to as the peak correction. With regard to step 4702a, peak correction may be calculated as follows:
ΔVpk,i=Vpk,i−Vpk,i−1 for −n≤i≤n
Vpk,0 is defined to be the declared peak for which a correction is being calculated. The difference in voltage between successive data points is calculated for a given number of data points, n, to either side of the declared peak.
The peak in signal ideally occurs when the rate of change of the signal is zero. Taking successive differences in measured voltage is an approximation to the rate of change of the signal. Linear regression is used on a range of successive differences to estimate the point in time when the rate of change is zero. Due to the fact that the data points are collected at equal increments of time, calculating the statistics ΔVpk,0th, ΔVpk,1st and DEN allows a simple calculation based on linear regression to estimate the point in time at which the rate of change of the signal is zero.
Additionally, an estimated peak time after correction may be determined as follows:
t′pk.0=tpk,0+Correction
With regards to step 4702e, a peak curvature estimate for inversion detection can be obtained from one of the statistics, ΔVpk,1st, calculated for peak correction. Maximum peaks are sharper than minimum peaks and so typically have higher values of ΔVpk,1st. One means of determining if a signal is inverted would be to compare the values of ΔVpk,1st for a series of maximum peaks to a series of minimum peaks.
With renewed reference to
Δti=ti−ti−1
Zeroth order estimate of next peak.
Δt0,0th=1/h·Σ(Δti), for 1≤i≤n
where n is the number of past respiration cycles used
First Order Estimate
Predicted Interval Length for Current Respiration Cycle
Next Predicted Offset at
t0,pred=t1+Δt0,pred
Begin therapy delivery at:
The non-parametric option is very similar to the parametric option in that it also estimates the duration of the next respiratory period based on the nominal duration of recent respiratory cycles and the rate of change of the duration of recent respiratory periods. The method is explained in more detail in “Nonparametric Statistic Method” by Hollander and Wolfe in sections related to the Theil statistic and the Hodges-Lehman, there disclose of which is incorporated herein by reference. The non-parametric prediction method may be defined as follows:
Δti=ti−ti−1
Zeroth Order Estimate
Δt0,oth=½median{Δti+Δtj,i+ϵ0≤j≤1, . . . , n}
Where ϵ0 is optimally 0, 1, 2 or 3
First Order Estimate
Predicted Interval Length for Current Respiration cycle
Next Predicted Offset
t0,pred=t1+Δt0,pred
Begin Therapy Delivery at
Stimulation may then commence at the calculated ttherapy.
With reference to
The Programmer block illustrates means by which PSG-derived data may be uploaded into the device.
The Sensors and Device Memory block includes the sources of real-time data and historical fiducial variables which the current algorithm uses to generate a stimulation trigger signal.
The Patient PSG Titration Data block includes conventional polysomnographic (PSG) data obtained in a sleep study. A self-adjusting predictive algorithm utilizes a reference datum to which the algorithm can be adjusted. Onset may be defined as onset of inspiration as measured by airflow or pressure sensor used in a sleep study, for example. Estimated Onset may be defined as an estimate of Onset calculated solely from information available from the device sensors and memory. To enable the predictive algorithm to be self-adjusting, either Onset or Estimated Onset data is used. During actual use, the implanted device will typically not have access to Onset as that would require output from an airflow sensor. The device then may rely on an estimate of Onset or Estimated Onset. The calibration of Estimated Onset to Onset may be based on PSG data collected during a sleep study. The calibration may be unique to a person and/or sleep stage and/or sleep position and/or respiratory pattern.
The Historical Fiducial Variables block represents the Historical Fiducial Variables (or data) which have been extracted from the bio-Z waveform and stored in the device memory. This block assumes that the raw sensor data has been processed and is either clean or has been flagged for cardiac, movement, apnea or other artifacts. Note that fiducial data includes fiducials, mathematical combinations of fiducials or a function of one or more fiducials such as a fuzzy logic decision matrix.
The Real-Time Data and Historical Fiducial Variables block incorporates all the information content of the Historical Fiducial Variables block and also includes real-time bio-Z data.
The Default Algorithm block represents one or more preset trigger algorithms pre-programmed into the INS or physician programmer. The default algorithm used at a specific point in time while delivering therapy may be selected from a library of pre-set algorithms. The selection of the algorithm can be made automatically by the INS based on: patient sleep position (position sensor), heart rate (detectable through the impedance measuring system) or respiration rate. Clinical evidence supports that the algorithm used to predict the onset of inspiration may be dependant on sleep position, sleep state or other detectable conditions of the patient.
The Modify Algorithm block represents the process of modifying the Default Algorithm based on historical data to yield the Current Algorithm. Once the calibration of Estimated Onset to Onset is resident in the device memory it can be used to calculate Estimated Onset for past respiratory cycles from Fiducial Variables. The variable used to represent the Estimated Onset will be TEST or TEST(i) where the “i” indicates the cycle number. Note that Estimated Onset is calculated for past respiratory cycles. This means that sensor fiducial variables which either proceed or follow each Onset event may be used to calculate the Estimated Onset.
The Current Algorithm block represents the process of using the Modified Default Algorithm to predict the next inspiratory onset (Predicted Onset). The Predicted Onset for the next respiratory cycle may be calculated from real-time data and historical fiducial variables. The calculation may be based on the Modified Default Algorithm. Modification of the Modified Default Algorithm to derive the Current Algorithm may be dependent on the calibration of Estimated Onset to Onset which was input from the physician programmer and may be based on comparison of real-time bio-Z data to data collected during a PSG titration study. The Current Algorithm may use historic and/or real-time sensor fiducial variables to predict the next onset of inspiration. This predicted onset of inspiration may be referred to as Predicted Onset. The variable used to represent Predicted Onset may be TPRED or TPRED(i) where the “i” indicates the respiratory cycle.
The Stimulation Trigger Signal block represents the Current Algorithm generating a trigger signal which the device uses to trigger stimulation to the hypoglossal nerve.
The graphs illustrated in
Due to the fact that it may be difficult to identify onset of inspiration in real-time from respiratory bio-impedance, a goal is to construct an algorithm which can reliably predict onset of inspiration “T” for the next respiratory cycle from information available from the current and/or previous cycles. A reliable, distinct and known reference point occurring prior to onset of inspiration, “T”, is “A”, the peak of the primary signal in the current cycle. As can be seen in
tT−PK=t.onset(n+1)−t.Vmax(n)
Note that t.Vmax could be replaced by any other suitable fiducial in defining a dependent variable for predicting onset.
A general model for a predictive algorithm may be of the following form:
tT−PK=f(fiducials extracted from current and/or previous cycles)
A less general model would be to use a function which is a linear combination of Fiducial Variables and Real-Time Data.
The following fiducials may be both highly statistically significant and practically significant in estimating T:
t.Vmax(n)=the time where positive peak occurs for the current cycle;
t.dV.in(n)=the time of most positive 1st derivative during inspiration for the current cycle; and
t.Vmax(n−1)=the time of positive peak for the previous cycle.
This model can be further simplified by combining the variables as follows:
Δt.pk(n)=t.Vmax(n)−t.Vmax(n−1)
Δt.in(n)=t.Vmax(n)−t.dV.in(n)
Either Δt.pk(n) or Δt.in(n) is a good predictor of Onset.
The following example uses Δt.pk(n). The time from a positive peak until the next inspiration onset can be estimated by:
Tpred=t.Vmax(n)+k0+k1*Δt.pk(n)
The coefficients k0 and k1 would be constantly modified by optimizing the following equation for recent historical respiratory cycles against Test:
Test=t.Vmax(n)+k0+k1*Δt.pk(n)
Thus, the predictive trigger time Tpred may be determined by adding tT−PK to the time of the most recent peak (PK) of the bio-Z signal, where:
tT−PK=k0+k1*Δt.pk(n)
The predictive equation we are proposing is based on the fact that the very most recent cycle times should be negatively weighted. Regression analysis supports this approach and indicates a negative weighting is appropriate for accurate prediction of onset. Thus, predicting onset is more effective if the most recent historical cycle time is incorporated into an algorithm with a negative coefficient.
As noted above, stimulation may be delivered for only a portion of the respiratory cycle, such as, for example, during inspiration. Additionally, it may be desirable to begin stimulation approximately 300 milliseconds before the onset of inspiration to more closely mimic normal activation of upper airway dilator muscles. However, predicting and/or measuring inspiration, in particular, the onset of inspiration, may be relatively challenging. Thus, since the onset of expiration may be relatively easy to measure and/or predict (as discussed in greater detail below) when an adequate measure of respiration is available, it is contemplated that stimulation may be triggered as a function of expiration onset.
Turning now to
Therefore, in order to deliver a stimulus to a patient in accordance with the principles of the present disclosure, the start of stimulation may be calculated by first predicting the time intervals between the start of expiration for subsequently occurring respiratory cycles. Next, in order to capture the entire inspiratory phase, including the brief pre-inspiratory phase of approximately 300 milliseconds, stimulation may be started at the time N that is prior to the next onset of expiration by approximately 30% to 50% of the time between subsequently occurring expiratory phases. Stimulating less than 30% or more than 50% prior to the next expiratory phase may result in an inadequate stimulation period and muscle fatigue, respectively.
In some embodiments, however, it is contemplated that an adequate measure of respiration may not be available, such as, for example, when a relied upon signal has failed. In these embodiments, it is contemplated that the implanted neurostimulator system may be configured to respond in one or more of the following three ways. First, the implanted neurostimulator may completely cease stimulation until an adequate signal is acquired. Second, the neurostimulator may deliver continuous simulation pulses of predetermined durations (e.g., up to 60 seconds) until an adequate signal is acquired; or if an adequate signal is not acquired in this time, the stimulation will be turned off. Third, the neurostimulator may continue to stimulate at the same or a fraction (e.g., one quarter) of the stimulation rate for the most recently measured respiratory cycle. That is to say, the neurostimulator may deliver stimulation pulses of relatively long durations at a frequency that is less than the frequency of stimulation utilized with an adequate measure of respiration. Alternatively, the neurostimulator may deliver stimulation pulses of relatively short durations at a frequency that is greater than the frequency used with an adequate measure of respiration.
Description of an Exemplary Stimulation Pulse
Turning now to
In some embodiments, exemplary stimulation pulse waveform 5000 may include a bi-phasic charge balanced waveform square pulses 5001 and 5002, as depicted in
In some embodiments, exemplary stimulation pulse waveform 5000 may include the delivery of a low amplitude (e.g., below the stimulation threshold), long duration, pre-stimulation pulse 5004. The pre-stimulation pulse 5004 may include any suitable low amplitude, long duration pulse, and may be provided approximately 0.5 ms before the delivery of a first stimulation pulse 5001.
Pre-stimulation pulse 5004 may facilitate selectively stimulating certain fibers of a nerve, such as, for example, the hypoglossal nerve or the superior laryngeal nerve. In particular, when stimulating the hypoglossal nerve, the presence of a pre-stimulation pulse, such as, for example, pulse 5004, before a stimulation pulse (e.g., the bi-phasic stimulation pulse 5001 depicted in
Description of External (Partially Implanted) System
With reference to
As illustrated, the receiver coil 910 is implanted in a subcutaneous pocket in the pectoral region and the stimulation lead body 62 is tunneled subcutaneously along the platysma in the neck region. The nerve electrode 64 is attached to the hypoglossal nerve in the submandibular region.
The transmitter coil 912 may be held in close proximity to the receiver coil 910 by any suitable means such as an adhesive patch, a belt or strap, or an article of clothing (e.g., shirt, vest, brazier, etc.) donned by the patient. For purposes of illustration, the transmitter coil 912 is shown carried by a t-shirt 915, which also serves to carry the ENS 920 and respiratory sensor(s) 916, 918. The ENS 920 may be positioned adjacent the waist or abdomen away from the ribs to avoid discomfort while sleeping. The respiratory sensor(s) 916, 918 may be positioned as a function of the parameter being measured, and in this embodiment, the sensors are positioned to measure abdominal and thoracic/chest expansion which are indicative of respiratory effort, a surrogate measure for respiration. The external components may be interconnected by cables 914 carried by the shirt or by wireless means. The shirt may incorporate recloseable pockets for the external components and the components may be disconnected from the cables such that the reusable components may be removed from the garment which may be disposed or washed.
The transmitting coil antenna 912 and the receiving coil antenna 910 may comprise air core wire coils with matched wind diameters, number of wire turns and wire gauge. The wire coils may be disposed in a disc-shaped hermetic enclosure comprising a material that does not attenuate the inductive link, such as a polymeric or ceramic material. The transmitting coil 912 and the receiving coil 910 may be arranged in a co-axial and parallel fashion for coupling efficiency, but are shown side-by-side for sake of illustration only.
Because power is supplied to the internal components via an inductive link, the internal components may be chronically implanted without the need for replacement of an implanted battery, which would otherwise require re-operation. Examples of inductively powered implantable stimulators are described in U.S. Pat. No. 6,609,031 to Law et al., U.S. Pat. No. 4,612,934 to Borkan, and U.S. Pat. No. 3,893,463 to Williams, the entire disclosures of which are incorporated herein by reference.
With reference to
In the embodiment of
With reference to
As shown in
With reference to
The garment 945 may include features to minimize movement artifact and accommodate various body shapes. For example, the garment 945 may be form-fitting and may be sleeveless (e.g., vest) to reduce sensor artifacts due to arm movement. Further, the garment 945 may be tailored to fit over the patient's hips with a bottom elastic band which helps pull the garment down and keep the sensors 916/918 in the proper location.
Description of a Specific External (Partially Implanted) Embodiment
With reference to
These components may be configured to provide immediate or delayed activation of respiration controlled stimulation. Initiation of the stimulation regimen may be by means of activation of an input switch. Visual confirmation can be by an LED that shows adequate signal coupling and that the system is operating and is or will be applying stimulation. As a means of controlling gentleness of stimulation onset and removal, either pulse width ramping of a constant amplitude stimulation signal can be commanded or amplitude of a constant pulse width stimulation signal or a combination thereof can be performed.
The electrical stimulation signal is delivered by the stimulation lead that is connected to the implanted nerve stimulator and attached to or in proximity of a nerve. The implanted electronics unit receives power through a magnetically coupled inductive link. The operating carrier frequency may be high enough to ensure that several cycles (at least 10) of the carrier comprise the output pulse. The operating frequency may be in a band of frequencies approved by governmental agencies for use with medical instruments operating at high transmitted radio frequency (RF) power (at least 100 milliwatts). For example, the operating frequency may be 1.8 MHz, but 13.56 MHz is also a good candidate since it is in the ISM (Industrial/Scientific/Medical) band. The non-implanted (external) transmitter device integrates respiration interface, waveform generation logic and transmit power driver to drive an induction coil. The power driver generates an oscillating signal that drives the transmitter induction coil and is designed to directly drive a coil of coil reactance that is high enough or can be resonated in combination with a capacitor. Power can come from a high internal voltage that is used to directly drive the transmit induction coil or power can come from a low voltage source applied to a tap point on the induction coil.
With reference to
An indicator (not shown) may be used to show when the transmitter is properly positioned over the implant. The indicator may be a part of the transmitter or by way of communication with the transmitter, or a part of related patient viewable equipment. Determination of proper position may be accomplished by monitoring the transmitter power output loading relative to the unloaded power level. Alternatively, the implant receive signal level transmitted back by a transmitter within the implant may be monitored to determine proper positioning. Or, the implant receive signal level that is communicated back to the transmitter by momentarily changing the loading properties presented to the transmitter, such a shorting out the receive coil may be monitored to determine proper positioning. Such communication may be by means of modulation such as pulse presence, pulse width, pulse-to-pulse interval, multi-pulse coding.
The transmitter may be powered by an internal primary power source that is used until it is exhausted, a rechargeable power source or a power source wired to a base unit. In the case of the wired base unit, power can be supplied by any combination of battery or line power.
The respiration interface may transduce sensed respiratory activity to an on-off control signal for the transmitter. Onset of stimulation may be approximately correlated slightly in advance of inspiration and lasts through the end of inspiration, or onset may be based on anticipation of the next respiration cycle from the prior respiration cycle or cycles. The respiration sensor may comprise any one or combination of devices capable of detecting inspiration. The following are examples: one or more chest straps; an impedance sensor; an electromiographical measurement of the muscles involved with respiration; a microphone that is worn or is in proximity to the patients' face; a flow sensor; a pressure sensor in combination with a mask to measure flow; and a temperature sensor to detect the difference between cool inspired air versus warmed expired air.
The circuit illustrated in
The power rectifier may comprise a voltage doubler design to take maximum advantage of lower signal levels when the transmit to receive coil spacing is large. The voltage doubler operates with an input AC voltage that swing negative (below ground potential) causes D1 to conduct and forces C2 to the maximum negative peak potential (minus a diode drop). As the input AC voltage swings away from maximum negative, the node of C2, D1, D2 moves from a diode drop below ground to a diode drop above ground, forward biasing diode D2. Further upswing of the input AC voltage causes charge accumulated on C2 to be transferred through D2 to C3 and to “pump up” the voltage on C3 on successive AC voltage cycles. To limit the voltage developed across C3 so that an over-voltage condition will not cause damage, and Zener diode, D3 shunts C3. Voltage limiting imposed by D3 also limits the output of the signal rectifier section. The power rectifier has a long time constant, compared to the signal rectifier section, of about 10 milliseconds.
The signal rectifier section may be similar in topology to the power rectifier except that time constants are much shorter—on the order of 10 microseconds—to respond with good fidelity to drop-outs in the transmitted signal. There is an output load of 100K (R1) that imposes a controlled discharge time constant. Output of the signal rectifier is used to switch Q1, in the output switching section, on and off.
The output switching section compares the potential of C3 to that across C5 by means of the Q1, Q2 combination. When there is a gap in the transmitted signal, the voltage across C5 falls very rapidly in comparison with C3. When the voltage difference between C5 and C3 is about 1.4 volts, Q1 and Q2 turn on. Q1 and Q2 in combination form a high gain amplifier stage that provides for rapid output switching time. R3 is intended to limit the drive current supplied to Q2, and R2 aids in discharging the base of Q2 to improve the turn-off time.
In the output regulator section, the available power rectifier voltage is usually limited by Zener diode D3. When the coil separation becomes suboptimal or too large the power rectifier output voltage will be come variable as will the switched voltage available at the collector of Q2. For proper nerve stimulation, it may be necessary to regulate the (either) high or variable available voltage to an appropriate level. An acceptable level is about 3 volts peak. A switched voltage is applied to Zener diode D6 through emitter follower Q3 and bias resistor R5. When the switched voltage rises to a level where D6 conducts and develops about 0.6 volts across R4 and the base-emitter junction of Q4, Q4 conducts. o Increased conduction of Q4 is used to remove bias from Q3 through negative feedback. Since the level of conduction of Q4 is a very sensitive function of base to emitter voltage, Q4 provides substantial amplification of small variations in D6 current flow and therefore bias voltage level. The overall result is to regulate the bias voltage applied to Zener diode D6. Output is taken from the junction of the emitter of Q3 and D6 since that point is well regulated by the combination of Zener diode breakdown voltage combined with the amplification provided by Q4. In addition to good voltage regulation a the junction of the emitter of Q3 and D6, the output is very tolerant of load current demand since the conductivity of Q3 will be changed by shifts in the operating point of Q4. Due to amplification by Q3 and Q4, the circuit can drive a range of load resistances. Tolerable load resistances above 1000 ohms and less than 200 ohms. The regulator has the advantage of delivering only the current needed to operate the load while consuming only moderate bias current. Further, bias current is only drawn during delivery of the stimulation pulse which drops to zero when no stimulation is delivered. As a comparison, a simple series resistance biased Zener diode requires enough excess current to deliver a stimulation pulse and still maintain adequate Zener bias. As a further comparison, conventional integrated circuit regulators, such as three terminal regulators are not designed to well regulate and respond quickly to short input pulses. Experiment shows that three-terminal regulators exhibit significant output overshoot and ramp-up time upon application of an input pulse. This can be addressed by applying a constant bias to a regulator circuit or even moving the regulator before the output switching stage but this will be at the cost of constant current drain and subsequently reduced range.
The implanted electronics unit may be used to manage the loss of control and power signals. With this design, more than enough stimulation power is stored in C3 to supply multiple delivered stimulation pulses. This design is intended to ensure that the voltage drop is minimal on any individual pulse. One of the consequences is that when signal is lost, the circuit treats the condition as a commanded delivery of stimulation and will apply a single, extended duration, energy pulse until the full stored capacity of C3 is empty. An alternative method may be to use an indirect control modulation to command delivery of a nerve stimulation pulse through logic and provide for a time-out that limits pulse duration.
To stimulate tissue, a modified output stage may be used to mitigate electrode corrosion and establish balanced charging. The output stage is illustrated in
Description of Alternative Screening Methods
Screening generally refers to selecting patients that will be responsive to the therapy, namely neurostimulation of the upper airway dilator nerves and/or muscles such as the hypoglossal nerve that innervates the genioglossus. Screening may be based on a number of different factors including level of obstruction and critical collapse pressure (Pcrit) of the upper airway, for example. Because stimulation of the hypoglossal nerve affects the genioglossus (base of tongue) as well as other muscles, OSA patients with obstruction at the level of the tongue base and OSA patients with obstruction at the level of the palate and tongue base (collectively patients with tongue base involvement) may be selected. Because stimulation of the hypoglossal nerve affects upper airway collapsibility, OSA patients with airways that have a low critical collapse pressure (e.g., Pcrit of less than about 5 cm water) may be selected. Pcrit may be measured using pressure transducers in the upper airway and measuring the pressure just prior to an apnea event (airway collapse). Alternatively, a surrogate for Pcrit such as CPAP pressure may be used. In this alternative, the lowest CPAP pressure at which apnea events are mitigated may correlate to Pcrit.
The critical collapse pressure (Pcrit) may be defined as the pressure at which the upper airway collapses and limits flow to a maximal level. Thus, Pcrit is a measure of airway collapsibility and depends on the stability of the walls defining the upper airway as well as the surrounding pressure. Pcrit may be more accurately defined as the pressure inside the upper airway at the onset of flow limitation when the upper airway collapses. Pcrit may be expressed as:
Pcrit=Pin−Pout
where
Pin=pressure inside the upper airway at the moment of airway collapse; and
Pout=pressure outside the upper airway (e.g., atmospheric pressure).
Other screening methods and tools may be employed as well. For example, screening may be accomplished through acute testing of tongue protruder muscle contraction using percutaneous fine wire electrodes inserted into the genioglossus muscle, delivering stimulus and measuring one or more of several variables including the amount of change in critical opening pressure, the amount of change in airway caliber, the displacement of the tongue base, and/or the retraction force of the tongue (as measured with a displacement and/or force gauge). For example, a device similar to a CPAP machine can be used to seal against the face (mask) and control inlet pressure down to where the tongue and upper airway collapse and occlude during inspiration. This measurement can be repeated while the patient is receiving stimulation of the geneoglossus muscle (or other muscles involved with the patency of the upper airway). Patients may be indicated for the stimulation therapy if the difference in critical pressure (stimulated vs. non-stimulated) is above a threshold level.
Similarly, a flexible optical scope may be used to observe the upper airway, having been inserted through the mask and nasal passage. The difference in upper airway caliber between stimulation and non-stimulation may be used as an inclusion criterion for the therapy. The measurement may be taken with the inlet air pressure to the patient established at a pre-determined level below atmospheric pressure to better assess the effectiveness of the stimulation therapy.
Another screening technique involves assessing the protrusion force of the tongue upon anterior displacement or movement of the tongue with and without stimulation while the patient is supine and (possibly) sedated or asleep. A minimum increase in protrusion force while under stimulation may be a basis for patient selection.
For example, with reference to
Oral appliances 530 and 540 could be worn during a sleep study and would measure the tongue protrusion force during (and just prior to) an apnea event when the protruder muscle tone is presumed to be inadequate to maintain upper airway patency. The protrusion force measured as the apnea is resolved by the patient will increase as the patient changes sleep state and the airway again becomes patent. The force difference may be used as a basis for patient selection.
Another screening technique involves the use of an oral appliance with sub-lingual surface electrodes contacting the base of the tongue or fine wire electrodes inserted into the genioglossus muscle to stimulate the tongue protruder muscle(s) synchronous with respiration during a sleep study. The oral appliance may be fitted with a drug delivery system (e.g., drug eluting coating, elastomeric pump, electronically controlled pump) for topical anesthesia to relieve the discomfort of the electrodes.
For example, with reference to
Alternatively, with reference to
Oral appliances 550 and 560 may be used during a sleep study and stimulation of the target tissue can be performed synchronous with respiration and while inlet airflow pressure can be modulated. The ability to prevent apneas/hypopneas can be directly determined. Also the critical opening pressure with and without stimulation can be determined. Alternatively or in addition, the intramuscular or surface electrodes may be used to measure genioglossus EMG activity, either with or without stimulation. On any of theses bases, patient selection may be made.
Patient selection may also be applied to the respiratory sensors to determine if the respiratory sensors will adequately detect respiration for triggering stimulation. For example, in the embodiment wherein bio-Z is used to detect respiration using an implanted lead 70, skin surface or shallow needle electrodes may be used prior to implantation to determine if the signal will be adequate. This method may also be sued to determine the preferred position of the electrodes (i.e., optimal bio-Z vector). This may be done while the patient is sleeping (i.e., during a sleep study) or while the patient is awake.
Description of Alternative Intra-operative Tools
Intra-operatively, it may be desirable to determine the correct portion of the nerve to stimulate in order to activate the correct muscle(s) and implant the nerve cuff electrode accordingly. Determining the correct position may involve stimulating at different locations along the length or circumference of the nerve and observing the effect (e.g., tongue protrusion). In addition or in the alternative, and particularly in the case of field steering where multiple combinations of electrode contacts are possible, it may be desirable to determine optimal electrode or filed shape combinations.
An example of an intra-operative stimulating tool 570 is shown in
The tool 570 may be part of an intra-operative system including: (1) tool 570 or other tool with one or more stimulating electrodes that are designed to be easily handled by the surgeon during implant surgery; (2) an external pulse generator which triggers off of a respiration signal; (3) a feedback diagnostic device that can measure critical closing pressure intra-operatively; and (4) an algorithm (e.g., firmware or software in the programmer) that is design to automatically or manually sequence through a series of electrode configurations that will identify the best placement of electrode cuffs on the nerves and configuration of electrode polarity and amplitude settings. Information from the intra-operative system may greatly speed the process of identifying where to place the electrode cuff(s) on the hypoglossal nerve and what field steering may be optimal or necessary to provide efficacy.
In certain circumstances, such as, when treating a child or a small adult, it may be difficult to implant a nerve cuff electrode of the present disclosure about a nerve in a patient's body. Accordingly, it may be desirable to provide a tool capable of facilitating temporary expansion of a nerve cuff electrode of the present disclosure, so as to slip the nerve cuff electrode around a patient's nerve. Turning now to
Proximal actuating portions 5806, 5807 may be of any suitable length and may be connected to respective handles (not shown), which may be used to operate tool 5800. Alternatively, proximal actuating portions 5806, 5807 themselves may be used to operate tool 5800. Distal effecting portions 5804, 5805 may include any suitable configuration to achieve the desired effect. For example, each portion 5804, 5805 may include a substantially curved configuration. Additionally, a distal end of each portion 5804, 5805 may be provided with a fastening mechanism, such as, for example, hook-like projection 5804a, 5805a, for facilitating connection of tool 5800 to a nerve cuff electrode. As shown in
In embodiments where tool 5800 may be used to temporarily expand a nerve cuff electrode for implantation purposes, the nerve cuff electrode, e.g., nerve cuff electrode 5810, may be provided with one more geometric configurations for facilitation connection with tool 5800. In the depicted embodiment, nerve cuff electrode 5810 may be provided with extensions 5811, 5812 for facilitating connection with tool 5800. Each extension 5811, 5812 may be provided with openings 5811a, 5812a, respectively, for receiving hook-like projections 5804a, 5805a, so as to operably couple nerve cuff electrode 5811 with tool 5800.
Description of Miscellaneous Alternatives
The implanted neurostimulation system may be configured so that stimulation of the nerve is set at a relatively low level (i.e., low voltage amplitude, narrow pulse width, lower frequency) so as to maximize battery life of the INS and to minimize the chances that the electrical stimulation will cause arousal from sleep. If apneas/hypopneas are detected, then the electrical stimulation can be increased progressively until the apneas/hypopneas are no longer detected, up to a maximum pre-set stimulation level. This auto titration may automatically be reset to the low level after the patient is awakened and sits up (position detector) or manually reset using the patient controller. The stimulation level may be automatically reduced after a period of time has elapsed with no (or few) apneas/hypopneas detected.
The stimulation level (i.e., voltage amplitude, pulse width, frequency) may be adjusted based on changes in respiration rate. Respiration rate or patterns of rate change may be indicative of sleep state. A different power level based on sleep state may be used for minimal power consumption, minimal unwanted stimulation (sensory response), etc., while providing adequate efficacy.
The electrical field shape used to stimulate the target nerve can be changed while the system is proving therapy based on feedback indicating the presence (or lack) of apneas/hypopneas. The electrical field shape for an implanted system can be changed by adjusting the polarity, amplitude and other stimulation intensity parameters for each of the electrodes within the nerve stimulating cuff. An algorithm within the INS may change the currently operating electrical field shape if the presence of apneas/hypopneas is detected, and then wait a set period of time to determine if the new configuration was successful in mitigating the apneas/hypopneas before adjusting the field shape again. Additionally, the system may be designed to keep a log of the most successful stimulation patterns and when they were most likely to be effective. This may allow the system to “learn” which settings to be used during what part of the night, for example, or with specific breathing patterns or cardiac signal patterns or combinations thereof.
The proportion of stimulation intensity of two electrode cuffs used to stimulate a nerve can be modulated while the system is providing therapy based on feedback indicating the presence (or lack) of apneas/hypopneas. For example, one nerve stimulating electrode cuff may be place on the more proximal section of the hypoglossal nerve, while a second is placed more distally. The proximal cuff will be more likely to stimulate branches of the hypoglossal nerve going to muscles in the upper airway involved with tongue or hyoid retrusion while the more distal electrode cuff will more likely stimulate only the muscles involved with tongue/hyoid protrusion. Research suggests that to best maintain upper airway patency, stimulating both protrudes and retruders (in the right proportion) may be more effective that stimulating protruders alone. Software within the INS may change the currently operating proportion of electrical stimulation going to the distal electrode cuff in proportion to that going to the proximal cuff based on the presence of apneas/hypopneas detected. The system may then wait a set period of time to determine if the new configuration was successful in mitigating the apneas/hypopneas before adjusting the system again. Additionally, the system software may be designed to keep a log of the most successful stimulation proportion and when they were most likely to be effective. This may allow the system to “learn” which settings to be used during what part of the night, for example, or with specific breathing patterns or cardiac signal patterns or combinations thereof.
The system described above may modulate electrical stimulation intensity proportion based on electromyogram (EMG) feedback from the muscles in the upper airway being stimulated or others in the area. This feedback may be used to determine the correct proportion of stimulation between protruders and retruders. The correct ratio of EMG activity between retruders and protruders may be determined during a sleep study for an individual, may be determined to be a constant for a class of patients or may be “learned” my the implanted system by using the detection of apneas/hypopneas as feedback.
A library of electrical stimulation parameter settings can be programmed into the INS. These settings listed in the library may be selected by the patient manually using the patient programmer based on, for example: (1) direct patient perception of comfort during stimulation; (2) a log of the most successful settings compiled by the software in the INS (assumes apnea/hypopnea detection capability); (3) a sleep physician's or technician's assessment of the most effective stimulation as determined during a sleep study; and/or (4) a list of the most effective parameters produced for a particular class of patient or other.
The electrical stimulation parameters described above may be adjusted based on patient position as detected by a position sensor within the INS. The best setting for a given position may be determined by, for example: (1) a log of the most successful settings compiled or learned by the software in the INS (assumes apnea/hypopnea detection capability); (2) a sleep physician's or technician's assessment of the most effective stimulation as determined during a sleep study; and/or (3) a list of the most effective parameters produced for a particular class of patient or other.
To avoid fatigue using a normal duty cycle or to extend the time that the upper airway is opened through neurostimulation, different parts of the genioglossus muscle and/or different muscles involved with establishing patency of the upper airway can be alternately stimulated. For example, using two or more nerve or muscle electrode cuffs, the left and right side genioglossus muscles can be alternately stimulated, cutting the effective duty cycle on each muscle in half. In addition, different protruder muscles on the ipsilateral side such as the geniohyoid and the genioglossus muscle can be alternately stimulated to the same effect. This may also be accomplished through one electrode cuff using field steering methods that selectively stimulated the fascicles of the hypoglossal nerve going to one group of protruders alternating with stimulating the fascicles leading to a different protruder muscle group. This method may also be used to alternately stimulate one group of muscle fibers within the genioglossus muscle with the compliment of muscle fibers in the same muscle group.
To increase the ability of the upper airway to open during a (sensed) apnea/hypopnea through neurostimulation, different parts of the genioglossus muscle and/or different muscles involved with establishing patency of the upper airway can be simultaneously stimulated. For example, using two or more nerve or muscle electrode cuffs, the left and right side genioglossus muscles can be simultaneously stimulated, greatly increasing the protrusion forces. In addition, different protruder muscles on the ipsilateral side such as the geneohyoid and the genioglossus muscle can be simultaneously stimulated to the same effect. This may also be accomplished through one electrode cuff using field steering methods that selectively stimulated the fascicles of the hypoglossal nerve going to one group of protruders simultaneously with stimulating the fascicles leading to a different protruder muscle group. This may be achieved with one electrode cuff using field steering on a more proximal location on the hypoglossal nerve or two or more electrode cuffs, one on each branch going to a muscle involved with maintaining muscle patency.
A sensor inside the INS (or elsewhere in system implanted) may detect body position and automatically shut off stimulation when patient sits up or stands up. This will prevent unwanted stimulation when patient is no longer sleeping. The device may automatically restart the stimulation after the sensor indicates the patient is again horizontal, with or without a delay. The system may also be configured so that the stimulation can only be restarted using the patient controller, with, or without a delay.
The respiration signal using impedance and/or EMG/ENG are easily capable of determining heart rate. The stimulation may be interrupted or turned off when the heart rate falls outside out a pre-determined acceptable range. This may be an effective safety measure that will decrease the chance that hypoglossal nerve stimulation will interfere with mitigating physiological processes or interventional emergent medical procedures.
Respiration waveforms indicating apneas/hypopneas or of other clinical interest may be recorded and automatically telemetered to a bed-side receiver unit or patient programmer. Respiration waveforms indicating frequent apneas/hypopneas, abnormal breathing patterns, irregular heart rate/rhythm may be recorded and automatically telemetered to a bed-side deceiver unit or patient programmer causing an alarm to be issued (audible/visible). The INS status such as low battery or system malfunction may also trigger an alarm.
Electrical stimulation intensity could be ramped up for each respiration cycle by increasing amplitude or pulse width from 0 to a set point to prevent sudden tongue protrusion or sudden airway opening causing the patient to wake up. During inspiration, the system may deliver approximately 30 pulses per second for a length of time of one to one and one half seconds, totaling between about 30 and 45 pulses per respiration cycle. Prior to delivery of these 30 to 45 pulses, amplitude of each individual therapy pulse (in an added group of pulses) could be ramped up from 0 to a set point at a rate of <10% of the amplitude intended for the active duty cycle or 200 mS, whichever is less. The pulse width of each individual therapy pulse could be ramped up from 0 to a set point at a rate of <10% of the active duty cycle or 200 mS, whichever is less. Each of these ramp methods would require a predictive algorithm that would stimulate based on the previous inspiration cycle.
Nerves innervating muscles that are involved with inspiration, such as the hypoglossal nerve, have been shown to have greater electrical activity during apnea or hypopnea. This signal cannot be easily measured while simultaneously stimulating the same nerve. One method of stimulating and sensing using the same lead is to interleave a sensing period within the stimulation pulse bursts during the duty cycle. In other words, the sensing period may occur between pulses within the stimulation pulse train. This approach may be used with electrodes/leads that directly stimulate and alternately sense on a nerve involved with inspiration or on a muscle involved with inspiration or a combination of the two. The approach may allow sensing of apnea/hypopnea, as well as therapeutic stimulation.
From the foregoing, it will be apparent to those skilled in the art that the present invention provides, in exemplary non-limiting embodiments, devices and methods for nerve stimulation for OSA therapy. Further, those skilled in the art will recognize that the present invention may be manifested in a variety of forms other than the specific embodiments described and contemplated herein. Accordingly, departures in form and detail may be made without departing from the scope and spirit of the present invention as described in the appended claims.
This patent application is a reissue application of U.S. Pat. No. 8,417,343 B2, which issued on Apr. 9, 2013, from U.S. patent application Ser. No. 11/907,533, filed on Oct. 12, 2007, which claims the benefits of priority under 35 U.S.C. §§119 and 120 to U.S. Provisional Patent Application Nos. 60/851,386 and 60/918,257, filed on Oct. 13, 2006, and Mar. 14, 2007, respectively, the disclosures of which are expressly incorporated by reference herein. The entire contents of these provisional applications are incorporated herein by reference.This application is related to reissue application Ser. No. 14/693,836, filed on Apr. 22, 2015.
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| Child | 14681764 | US |
