Obstructive sleep apnea treatment devices, systems and methods

Abstract

In one embodiment, a method for maintaining patency of an upper airway of a patient to treat obstructive sleep apnea may include delivering an electrical stimulation to a portion of a superior laryngeal nerve via a nerve cuff when the nerve cuff is adjacent an external surface of the superior laryngeal nerve, the nerve cuff having a plurality of electrodes, wherein the nerve cuff is configured to be connected to an electrical stimulator via a stimulation lead.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This
V_pk,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.

$\Delta V_{\mathrm{pk},0\mathrm{th}}=\frac{1}{2n}\Sigma \left(\Delta V_{\mathrm{pk},i}\right)$
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 ΔV_pk,0th, ΔV_pk,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.

$\Delta V_{\mathrm{pk},1\mathrm{st}}=\Sigma \left(i*\Delta V_{\mathrm{pk},i}\right)\mathrm{for}-n\le i<n$ $\mathrm{DEN}=\Sigma \left(i^2\right)\mathrm{for}-n\le i\le n$ $\mathrm{Correction}=\Delta V_{\mathrm{pk},0\mathrm{th}}\left(\frac{\mathrm{DEN}}{\Delta V_{\mathrm{pk},1\mathrm{st}}}\right)$
Additionally, an estimated peak time after correction may be determined as follows:
t′_pk,0=t_pk,0+Correction

With regards to step 4702e, a peak curvature estimate for inversion detection can be obtained from one of the statistics, ΔV_pk,1st, calculated for peak correction. Maximum peaks are sharper than minimum peaks and so typically have higher values of ΔV_pk,1st. One means of determining if a signal is inverted would be to compare the values of ΔV_pk,1st for a series of maximum peaks to a series of minimum peaks.

With renewed reference to FIG. 47A, prediction sub-routine 4703 may include predicting the time between sequentially identified peaks with either a parametric option or a non-parametric option. The parametric option makes a prediction of the duration of the next respiratory period based on the average duration of recent respiratory cycles and the rate of change of the duration of recent respiratory cycles. The parametric option also takes advantage of the fact that data points are collected at equal increments of time which simplifies the linear regression calculation. The parametric option may be defined as follows:
Δt_i=t_i−t_i−1

Zeroth order estimate of next peak.

$\Delta t_{0,0\mathrm{th}}=1/h·\Sigma \left(\Delta t_i\right),\mathrm{for}1\le i\le n$

where n is the number of past respiration cycles used

First Order Estimate

$\Delta t_{0,1\mathrm{st}}=\Sigma \left(i-\left(\frac{n+1}{2}\right)*\Delta t_i\right),\mathrm{for}1\le i\le n$ $\mathrm{DEN}1=\Sigma \left({\left(i-\left(\frac{n+1}{2}\right)\right)}^2\right),\mathrm{for}1\le i\le n$

Predicted Interval Length for Current Respiration Cycle

$\Delta t_{0,\mathrm{pred}}=\Delta t_{0,0\mathrm{th}}+\left(\frac{\Delta t_{0,1\mathrm{st}}}{\mathrm{DEN}1}\right)·\left(\frac{n+1}{2}\right)$

Next Predicted Offset at
t_0,pred=t_i+Δt_0,pred

Begin therapy delivery at:
t_therapy=t₁+(1−DC)*Δt_0,pred, where DC may be the allowable duty cycle for therapy delivery.

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:
Δt_i=t_i−t_i−1

Zeroth Order Estimate
Δt_0,oth=½ median{Δt_i+Δt_j, i+∈₀≤j≤1, . . . , n}

Where ∈₀ is optimally 0, 1, 2 or 3

First Order Estimate

$S_{\mathrm{ij}}=\frac{\Delta t_j-\Delta t_i}{j-i}1\le i+{\in }_1<j\le n$

where ∈₁ is optimally 0, 1, 2, or 3
Δt_0,1st=median{S_ij, 1≤i≤∈₁<j≤n}

Predicted Interval Length for Current Respiration cycle

$\Delta t_{0,\mathrm{pred}}=\Delta t_{0,0\mathrm{th}}+\Delta t_{0,1\mathrm{st}}·\left(\frac{n+1}{2}\right)$

Next Predicted Offset
t_0,pred=t₁+Δt_0,pred

Begin Therapy Delivery at
t_therapy=t₁+(1−DC))*Δt_0,pred, where DC may be the allowable duty cycle for therapy delivery.

Stimulation may then commence at the calculated t_therapy.

With reference to FIG. 48, a self adjusting predictive algorithm may be implemented in the following manner.

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.

FIG. 49 is a table of some (not all) examples of waveform fiducials which can be extracted from each respiratory cycle waveform. For each fiducial there is a magnitude value and a time of occurrence. Each waveform has a set of fiducials associated with it. As a result, fiducials may be stored in the device memory for any reasonable number of past respiratory cycles. The values from past respiratory cycles which are stored in device memory are referred to as Historical Fiducial Variables.

The graphs illustrated in FIG. 50 are examples of fiducials marked on bio-Z waveforms. The first of the three graphs illustrate the bio-impedance signal after it has been filtered and cleared of cardiac and motion artifacts. The first graph will be referred to as the primary signal. The second graph is the first derivative of the primary signal and the third graph is the second derivative of the primary signal. Each graph also displays a square wave signal which is derived from airflow pressure. The square wave is low during inspiration. The falling edge of the square wave is onset of inspiration.

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 FIG. 50, the upper peak of the bio-Z waveform “A” approximately corresponds to the onset of expiration “O.” A dependent variable t_T−PK is created to represent the period of time between the positive peak of the primary signal for the current cycle, t·Vmax(n), indicated by “A_n” on the graph, and onset of inspiration for the next cycle, t·onset(n+1), indicated by “T” on the graph. The variable t_T−PK may be defined as:
t_T−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:

t_T−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 1^st 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:
T_pred=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 T_est:
T_est≈t·Vmax(n)+k0+k1*Δt·pk(n)

Thus, the predictive trigger time T_pred may be determined by adding t_T−PK to the time of the most recent peak (PK) of the bio-Z signal, where:
t_T−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 FIG. 50A, there is depicted an exemplary respiratory waveform 5500 for two complete respiratory cycles A and B. In analyzing exemplary waveform 5500, it may be determined that peaks M of the waveform 5500 may indicate onset of the expiratory phases of respiration cycles A and B. Furthermore, it may be discovered that peaks M occur at regular intervals of approximately 3-4 seconds. Thus, it may be relatively easy to predict the occurrence of subsequent peaks M, and consequently, the onset of expiration for future respiratory cycles.

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 FIG. 50B, there is depicted an exemplary stimulation pulse waveform 5000 that may be emitted from an INS in accordance with the principles of the present disclosure. Typically, exemplary stimulation pulse waveform 5000 may include a square wave pulse train having one or more square wave pulses 5001 of approximately 1 to 3 volts in amplitude, a duration of approximately 100 ms, and a frequency of approximately 30 Hz, assuming a 1000 ohm impedance at the electrodes and a constant current or voltage.

In some embodiments, exemplary stimulation pulse waveform 5000 may include a bi-phasic charge balanced waveform square pulses 5001 and 5002, as depicted in FIG. 50B. Square pulse 5002 may be included in waveform 5000 to, among other things, promote efficient stimulation and/or mitigate electrode corrosion. However, square pulse 5002 may be excluded from waveform 5000 as desired. Furthermore, although the depicted exemplary waveform 5000 includes square pulse 5002 that exactly balances the stimulation wave pulse 5001, in certain circumstances, square pulse 5002 may not exactly balance the stimulation wave pulse 5001, and may not be a square pulse.

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 FIG. 50B) may serve to saturate the large diameter fibers of the nerve so as to allow the stimulation pulse 5001 to only affect (e.g., stimulate) the smaller diameter fibers of the nerve. In circumstances where a nerve (e.g., the hypoglossal nerve) may be stimulated for extended periods of time, a pre-stimulation pulse 5004 may be selectively introduced to waveform 5000, so as to permit selective switching between stimulating the large and small diameter fibers of the nerve, in order to reduce muscle fatigue. Similarly, in situations where OSA may be treated by stimulating the superior laryngeal nerve to open the upper airway through a reflex mechanism, the presence of pre-stimulation pulse 5004 may serve to saturate the larger diameter efferent fibers so as to allow the stimulation pulse 5001 to only affect the smaller diameter afferent fibers of the nerve.

Description of External (Partially Implanted) System

With reference to FIGS. 51A and 51B, an example of an external neurostimulator system inductively coupled to an internal/implanted receiver is shown schematically. The system includes internal/implanted components comprising a receiver coil 910, a stimulator lead 60 (including lead body 62, proximal connector and distal nerve electrode 64). Any of the stimulation lead designs and external sensor designs described in more detail herein may be employed in this generically illustrated system, with modifications to position, orientation, arrangement, integration, etc. made as dictated by the particular embodiment employed. The system also includes external components comprising a transmit coil 912 (inductively linked to receiver coil 910 when in use), an external neurostimulator or external pulse generator 920 (ENS or EPG), and one or more external respiratory sensors 916/918.

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 FIGS. 51C-51G, alternative embodiments of an external neurostimulator system inductively coupled to an internal/implanted receiver are schematically shown. These embodiments are similar to the external embodiment described above, with a few exceptions. In these embodiments, the receiver coil 910 is implanted in a positioned proximate the implanted stimulation lead body 62 and nerve electrode 64. The receiver coil 910 may be positioned in a subcutaneous pocket on the platysma muscle under the mandible, with the lead body 62 tunneling a short distance to the nerve electrode 64 attached to the hypoglossal nerve. Also in these embodiments, the respiratory sensor(s) 916/918 may be integrated into the ENS 920 and attached to a conventional respiratory belt 922 to measure respiratory effort about the abdomen and/or chest. An external cable 914 connects the ENS 920 to the transmitter coil 912.

In the embodiment of FIG. 51D, the transmitter coil 912 is carried by an adhesive patch 924 that may be placed on the skin adjacent the receiver coil 910 under the mandible. In the embodiment of FIG. 51E, the transmitter coil 912 is carried by an under-chin strap 926 worn by the patient to maintain the position of the transmitter coil 912 adjacent the receiver coil 910 under the mandible. In the embodiment of FIG. 51F, the receiver coil 910 may be positioned in a subcutaneous pocket on the platysma muscle in the neck, with the lead body 122 tunneling a slightly greater distance. The transmitter coil 912 may be carried by a neck strap 928 worn by the patient to maintain the position of the transmitter coil 912 adjacent the receiver coil 910 in the neck.

With reference to FIGS. 51G-51K, additional alternative embodiments of an external neurostimulator system inductively coupled to an internal/implanted receiver are schematically shown. These embodiments are similar to the external embodiment described above, with a few exceptions. As above, the receiver coil 910 may be positioned in a subcutaneous pocket on the platysma muscle under the mandible, with the lead body 62 tunneling a short distance to the nerve electrode 64 attached to the hypoglossal nerve. However, in these embodiments, the ENS 920 (not shown) may be located remote from the patient such as on the night stand or headboard adjacent the bed. The ENS 920 may be connected via a cable 930 to a large transmitter coil 912 that is inductively coupled to the receiver coil 910. The respiratory sensor 916 may comprise a conventional respiratory belt 922 sensor to measure respiratory effort about the abdomen and/or chest, and sensor signals may be wirelessly transmitted to the remote ENS 920. As compared to other embodiments described above, the transmitter coil 912 is not carried by the patient, but rather resides in a proximate carrier such as a bed pillow, under a mattress, on a headboard, or in a neck pillow, for example. Because the transmitter coil 912 is not as proximate the receiver coil as in the embodiments described above, the transmitter coil may be driven by a high powered oscillator capable of generating large electromagnetic fields.

As shown in FIG. 51H, the transmitter coil 912 may be disposed in a bed pillow 934. As shown in FIG. 51I, the transmitter coil 912 may comprise a series of overlapping coils disposed in a bed pillow 934 that are simultaneously driven or selectively driven to maximize energy transfer efficiency as a function of changes in body position of the patient corresponding to changes in position of the receiver coil 910. This overlapping transmitter coil arrangement may also be applied to other embodiments such as those described previously wherein the transmitter coil is carried by an article donned by the patient. In FIG. 51J, two or more transmitter coils 912 are carried by orthogonal plates 936 arranged as shown to create orthogonal electromagnetic fields, thereby increasing energy transfer efficiency to compensate for movement of the patient corresponding to changes in position of the receiver coil 910. FIG. 51J also illustrates a non-contact respiratory sensor 916 arrangement as utilized for detecting sudden infant death syndrome (SIDS). As shown in FIG. 51K, two orthogonal transmitter coils 912 are located on each side of a neck pillow 938, which is particularly beneficial for bilateral stimulation wherein a receiver coil 910 may be located on either side of the neck.

With reference to FIGS. 51L (front view) and 51M (rear view), external respiratory effort sensors 916/918 are schematically shown incorporated into a stretchable garment 945 donned by the patient. The sensors 916/918 generally include one or more inductive transducers and an electronics module 942. The inductive transducers may comprise one or more shaped (e.g., zig-zag or sinusoidal) stranded wires to accommodate stretching and may be carried by (e.g., sewn into) the garment 945 to extend around the patient's abdomen and chest, for example. As the patient breathes, the patient's chest and/or abdomen expands and contracts, thus changing the cross-sectional area of the shape (i.e., hoop) formed by the wire resulting in changes in inductance. The electronics module may include an oscillator (LC) circuit with the inductive transducer (L) comprising a part of the circuit. Changes in frequency of the oscillator correspond to changes in inductance of the shaped wires which correlate to respiratory effort. The electronics module may be integrated with an ENS (not shown) or connected to an ENS via a wired or wireless link for triggering stimulus as described previously.

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 FIGS. 52A-52G a specific embodiment utilizing an external neurostimulator system inductively coupled to an internal/implanted receiver is schematically shown. With initial reference to FIG. 52A, the illustrated hypoglossal nerve stimulator includes several major components, namely: an implantable electronics unit that derives power from an external power source; a stimulation delivery lead that is anchored to the nerve or adjacent to the nerve and provides electrical connection between the electronics unit and the nerve, an external (non-implanted) power transmitting device that is inductively coupled with the implant to convey a powering signal and control signals; a power source for the external device that is either small and integrated into the body-worn coil and transmitter or is wired to the transmitter and transmit induction coil and can be powered by primary or secondary batteries or can be line powered; and a respiratory sensor such as those described previously.

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 FIGS. 52B-52E, the waveform generation logic may be used to modulate the carrier in such a way that narrow gaps in the carrier correspond to narrow stimulation pulses. When stimulator pulses are not needed, interruptions to the carrier are stopped but the carrier is maintained to ensure that power is immediately available within the stimulator upon demand. Presence or absence of electrical nerve stimulation is based on respiration or surrogates thereof. The transmitted signal may comprise a carrier of about 1.8 MHz. To control the implanted electronics unit to generate individual nerve stimulation pulses, the carrier signal is interrupted. The duration of the interruption is about equal to the duration of the output stimulation pulse. The stimulation pulses may be about 110 microseconds in duration and are repeated at a rate of approximately 33 per second. In addition, multiple pulses can be transmitted to logic within the implant to control stimulation pulse amplitude, pulse width, polarity, frequency and structure if needed. Further, onset and removal of stimulation can be graded to manage patient discomfort from abruptness. Grading may comprise pulse width control, signal amplitude control or a combination thereof.

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 electromyographical 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 FIG. 52F may be used for the implanted electronics unit. There are five main subsystems within the design: a receive coil, a power rectifier, a signal rectifier, an output switch and an output regulator. The signal from the inductive link is received by L1 which is resonated in combination with C1 and is delivered to both the power and signal rectifiers. Good coupling consistent with low transmitter coil drive occurs when the transmit coil diameter is equal to the receive coil diameter. When coil sizes are matched, coupling degrades quickly when the coil separation is about one coil diameter. A large transmit coil diameter will reduce the criticality of small coil spacing and coil-to-coil coaxial alignment for maximum signal transfer at the cost of requiring more input drive power.

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 FIG. 52G and includes a capacitive coupling between the ground side of the stimulator and tissue interface in addition to a shunt from the active electrode to circuit ground for re-zeroing the output coupling capacitor when an output pulse is not being actively delivered.

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 FIG. 53, a non-invasive oral appliance 530 may be worn by the patient during a sleep study that can directly measure the protrusion force of the tongue as a basis for patient selection. The oral appliance 530 may include a displacement probe 532 for measuring tongue movement protrusion force by deflection (D). The oral appliance 530 may also include a force sensor 534 for measuring the force (F) applied by protrusion of the tongue. The sensors in the displacement probe 532 and the force sensor 534 may be connected to measurement apparatus by wires 536.

FIG. 54 illustrates another example of a non-invasive oral appliance 540 that may be worn by the patient during a sleep study to directly measure the protrusion force of the tongue as a basis for patient selection. The oral appliance 540 includes a displacement sensor 542 for measuring tongue movement and a force sensor for measuring tongue protrusion force. The displacement sensor and the force sensor may be connected to measurement apparatus by wires 546.

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 FIG. 55, an oral appliance 550 includes a pair of small needle intramuscular electrodes 552 that extend into the genioglossus. The electrodes 552 are carried by flexible wires 554 and may be coupled to an external pulse generator (not shown) by wires 556. The electrodes 552 may be supported by a drug (e.g., anesthetic) eluting polymeric member 558.

Alternatively, with reference to FIG. 56, an oral appliance 560 includes a cathode electrode 562 guarded by two anode electrodes 564 carried by a soft extension 565 that extends under the tongue. The surface electrodes 562 and 564 contact the floor of the mouth under the tongue to indirectly stimulate the genioglossus. The electrodes 562 and 564 may be coupled to an external pulse generator (not shown) by wires 566. The extension 565 may incorporate holes 568 through which a drug (e.g., anesthetic) may be eluted.

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 FIGS. 57A and 57B. In this embodiment, the tool 570 includes a first shaft 571 with a distal half-cuff 573. Tool 570 further includes a second shaft 575 with a proximal movable collar 574 and a distal half-cuff 575. Stimulating tool 570 includes multiple electrodes 572 on half-cuff 573 and/or half-cuff 575 that may be arranged in an array or matrix as shown in FIG. 57C, which is a view taken along line A-A in FIG. 57B. The half-cuffs 573 and 575 may be longitudinally separated for placement about a nerve and subsequently closed such that the half-cuffs 573 and 575 gently grasp the nerve. The electrodes 575 may be sequenced through a series of electrode/field shape combinations to optimize (lower) the critical opening pressure, airway caliber, tongue protrusion force or other acute indicia of therapeutic efficacy.

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 FIGS. 58A-58B, there is depicted a tool 5800 for temporarily expanding a nerve cuff electrode in accordance with the principles of the present disclosure. Tool 5800 may include a substantially scissor-like configuration having a first element 5801 and a second element 5802 pivotably secured together by a suitable fastener, such as, for example, pivot pin 5803, acting as a fulcrum. Elements 5801 and 5802 may be substantially similar to each other or may differ as necessary. In the depicted embodiment, elements 5801 and 5802 may include levers having distal effecting portions 5804, 5805 and proximal actuating portions 5806, 5807.

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 FIGS. 58A-58B, hook-like projections 5804a, 5805a may be configured to be disposed in differing parallel planes, such that projections 5804a, 5805a may be spaced (offset) horizontally from one another. In use, distal effecting portions 5804, 5805 may be opened and closed as proximal actuating portions 5806, 5807 may be rotated about pivot pin 5803.

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.

Claims

1. A method of maintaining patency of an upper airway of a patient to treat obstructive sleep apnea, the method comprising:

sensing a biological parameter indicative of respiration, wherein the biological parameter includes impedance;

analyzing the biological parameter to identify onsets of expiration;

calculating a respiratory period from the onsets of expiration;

predicting an onset of a future expiratory phase; and

beginning stimulation of a nerve a fraction of the calculated respiratory period before the onset of the future expiratory phase, and continuing stimulation of the nerve during an entire inspiratory phase, wherein the method is performed without identifying an onset of the inspiratory phase.

2. The method of claim 1, wherein the nerve is an internal branch of a superior laryngeal nerve.

3. The method of claim 1, further comprising:

implanting an impedance sensor within the patient, wherein the impedance sensor is coupled to an electrical stimulator by a sensing lead.

4. The method of claim 1, wherein beginning stimulation of the nerve includes delivering electrical stimulation to one of a hypoglossal nerve and a glossopharyngeal nerve.

5. The method of claim 4, further comprising delivering stimulation to a portion of a superior laryngeal nerve concurrently with the stimulation delivered to the one of a hypoglossal nerve and a glossopharyngeal nerve.

6. The method of claim 1, further comprising: steering an electrical field of a nerve cuff to stimulate only afferent fibers of the nerve.

7. The method of claim 1, wherein the step of beginning stimulation of a nerve includes delivering stimulation to only afferent fibers of an internal branch of a superior laryngeal nerve.

8. The method of claim 1, wherein the stimulation is delivered via a nerve cuff connected to an electrical stimulator via a stimulation lead including a portion having a serpentine configuration.

9. The method of claim 8, wherein the stimulation lead includes a portion configured to be secured to a body structure other than a nerve.

10. The method of claim 8, wherein the nerve cuff includes a plurality of electrodes in direct contact with the nerve.

11. The method of claim 1, further comprising:

an electrode sensor for wherein the step of sensing the biological parameter, wherein the electrode sensor is performed via an electrode sensor coupled to sensing circuitry of an electrical stimulator,

wherein stimulation of the nerve includes delivering an electrical stimulation to a glossopharyngeal nerve via a nerve cuff having a plurality of electrodes, wherein the nerve cuff is connected to-the to the electrical stimulator by a stimulation lead, and wherein a portion of the stimulation lead is configured to elongate in response to movement by the patient.

12. The method of claim 11, wherein the stimulation lead further includes a portion configured to be secured to a body structure other than a nerve.

13. The method of claim 1, wherein the stimulation is delivered to the nerve via a nerve cuff connected to an electrical stimulator, the nerve cuff comprising:

a base member extending from a first side wall to a second side wall and having a top wall and a bottom wall;

a first member extending from the first side wall;

a second member extending from the second side wall; and

a third member having a first end fixedly engaged to the first side wall adjacent the first member, wherein the third member extends over the top wall of the base member, the second member extends over the top wall of the base member, and the first member, the second member, and the third member define a lumen.

14. The method of claim 13, wherein the third member is capable of transitioning between a first position, prior to positioning of the electrode cuff about a nerve, and a second position subsequent to the positioning of the electrode cuff about the nerve, wherein the third member is positioned a first distance above the top wall of the base member in the first position, and the third member is positioned a second distance smaller than the first distance above the top wall of the base member in the second position.

15. The method of claim 13, wherein the second member is capable of transitioning between a first position, prior to positioning of the electrode cuff about a nerve, and a second position subsequent to the positioning of the electrode cuff about the nerve, wherein the second member is positioned a first distance above the top wall of the base member in the first position, and the second member is positioned a second distance, greater than the first distance, above the top wall of the base member in the second position.

16. The method of claim 13, wherein the second member has a first thickness at a first end of the second member and a second thickness, less than the first thickness, at a second end.

17. A method of treating obstructive sleep apnea by innervating a mechanoreceptor within a patient's upper airway via stimulating a superior laryngeal nerve including both afferent and efferent fibers, the method comprising:

chronically implanting a nerve cuff adjacent a portion of a superior laryngeal nerve:;

sensing a biological parameter indicative of respiration, wherein the biological parameter includes impedance;

analyzing the sensed biological parameter to identify onsets of expiration;

calculating a respiratory period from the onsets of expiration;

predicting the onset of a future expiratory phase; and

beginning stimulation of the superior laryngeal nerve a fraction of the calculated respiratory period before the onset of the future expiratory phase, and continuing stimulation of the superior laryngeal nerve during an entire inspiratory phase, wherein the method is performed without identifying an onset of the inspiratory phase.

18. The method of claim 17, further comprising:

delivering an electrical stimulation to one of a hypoglossal nerve and a glossopharyngeal nerve simultaneously with the stimulation to the superior laryngeal nerve.

19. The method of claim 17, further comprising:

steering an electrical field of the nerve cuff to stimulate only the afferent fibers of an internal branch of the superior laryngeal nerve.

20. The method of claim 17, wherein the nerve cuff includes a plurality of electrodes in direct contact with a surface of the superior laryngeal nerve.

21. A method of treating obstructive sleep apnea, the method comprising:

chronically implanting a nerve cuff adjacent a portion of a superior laryngeal nerve;

sensing a biological parameter indicative of respiration, wherein the biological parameter includes impedance;

analyzing the biological parameter to identify onsets of expiration;

calculating a respiratory period from the onsets of expiration;

predicting an onset of a future expiratory phase; and

beginning stimulation of the superior laryngeal nerve a fraction of the calculated respiratory period before the onset of the future expiratory phase, and continuing stimulation of the superior laryngeal nerve during an entire inspiratory phase, wherein the method is performed without identifying an onset of the inspiratory phase.

22. A method of treating obstructive sleep apnea, the method comprising:

sensing a biological parameter indicative of respiration, wherein the biological parameter includes impedance;

analyzing the biological parameter to identify onsets of expiration;

calculating a respiratory period from the onsets of expiration;

predicting an onset of a future expiratory phase; and

beginning stimulation of a nerve a fraction of the calculated respiratory period before the onset of the future expiratory phase, and continuing stimulation of the nerve during an entire inspiratory phase, wherein the method is performed without identifying an onset of the inspiratory phase.

23. The method of claim 1, further comprising steering an electrical field of a nerve cuff to stimulate fibers of the nerve, wherein a majority of the stimulated fibers of the nerve comprises afferent fibers.

24. The method of claim 1, wherein beginning stimulation of the nerve includes delivering stimulation to fibers of an internal branch of a superior laryngeal nerve, and wherein a majority of the fibers to which stimulation is delivered comprises afferent fibers.

25. The method of claim 17, further comprising steering an electrical field of the nerve cuff to stimulate fibers of an internal branch of the superior laryngeal nerve, wherein a majority of the stimulated fibers of the nerve comprises afferent fibers.