WO1999020339A1

WO1999020339A1 - Muscle stimulating device and method for diagnosing and treating a breathing disorder

Info

Publication number: WO1999020339A1
Application number: PCT/US1998/021864
Authority: WO
Inventors: Douglas M. Mechlenburg; Roger Paul Gaumond
Original assignee: Respironics, Inc.; The Penn State Research Foundation
Priority date: 1997-10-17
Filing date: 1998-10-15
Publication date: 1999-04-29
Also published as: US6770022B2; US7367935B2; US20010018547A1; US20040193003A1; AU1093099A; CA2306918C; CA2306918A1

Abstract

This invention is a device (30), a method for magnetic stimulation of muscles for the diagnosis, and relief of a breathing disorder, such as obstructive sleep apnea. Magnetic stimulation is used to stimulate muscles which serve to stabilize the upper airway of an individual whose nocturnal apneic events are related to diminished muscle tone. A sensor (38) monitors a physiologic characteristic of the patient, a coil (56) is energized to stimulate the appropriate muscles associated with the upper airway, a power supply provides power for energizing the coil (56), and a control system (32) controls the application of power to the coil (56) based on the output of the sensor (38). Diagnosis of obstructive sleep apnea is accomplished by measuring the subject's compliance in the presence, and absence of the magnetic stimulation of the upper airway muscles. The smaller the difference between these two compliance levels, the more likely that patient suffers from obstructive sleep apnea.

Description

MUSCLE STIMULATING DEVICE AND METHOD FOR DIAGNOSING AND TREATING A BREATHING DISORDER

BACKGROUND OF THE INVENTION

1. Field of the Invention The present invention pertains to an apparatus and method for

noninvasive stimulation of muscles in the upper airway to diagnose and/or treat a

breathing disorder, such as obstructive sleep apnea. In particular, the present

invention pertains to a magnetic stimulation device and a method of using the device

to apply pulsed magnetic fields to the muscles in the neck area of a patient to induce

tension in such muscles, thereby relieving the obstructive sleep apnea caused by a

relaxation of such muscles. By measuring an awake patient's compliance in the presence and absence of the magnetic stimulation, the likelihood that the patient

suffers from obstructive sleep apnea can be determined.

2. Description of the Related Art Obstructive sleep apnea (OSA) is a condition in which sleep is

repeatedly interrupted by an inability to breathe due to an obstructed upper airway

segment. Those afflicted with OSA experience sleep fragmentation and complete or

nearly complete cessation of ventilation intermittently during sleep with potentially severe degrees of oxyhemoglobin desaturation. These symptoms may be translated clinically into extreme daytime sleepiness, cardiac arrhythmias, pulmonary-artery

hypertension, congestive heart failure and/or cognitive dysfunction. Other

consequences of OSA include right ventricular dysfunction, carbon dioxide retention during wakefulness, as well as during sleep, and continuous reduced arterial oxygen tension. Hypersomnolent sleep apnea patients may be at risk for excessive mortality

from these factors as well as by an elevated risk for accidents while driving and/or operating potentially dangerous equipment.

Studies of the mechanism of collapse of the airway suggest that during

some stages of sleep, there is a general relaxation of the muscles which stabilize the

upper airway segment. This general relaxation of the muscles is believed to be a

factor contributing to OSA.

Existing therapeutic remedies for treating OSA include the surgical

removal of deformed, loose or swollen structures in the upper airway. It is also

known to apply positive air pressure at the mouth and/or nose of the patient to "splint" the airway, thereby maintaining an open passage to the lungs. In addition,

pharmacologic solutions have also been pursued.

Neither of these therapies is successful in all cases. Surgical relief is

invasive, introduces a potential for surgical complications and is appropriate in only a

small percentage of cases. On the other hand, the nasal mask needed to apply a positive air pressure is not tolerated by some OSA patients. Pharmacological therapy

has been, in general, less than satisfactory, and side effects are frequent.

It is also known to treat OSA by electrically stimulating the

musculature in the neck area associated with the upper airway. One such method of

electrically stimulating the muscles in the upper airway area of a patient involves

placing an electrode in direct contact with a surface of the patient and passing a current through the surface tissues of the patient contacting the electrode. For

example, an intraoral appliance has been developed that applies electrical currents to

the tongue, causing it to contract, thereby helping to clear the airway. Another known

appliance applies electrical stimulation to the exterior surface of the patient's neck below the chin to induce contraction of the upper airway muscles.

Electrical stimulation using surface mounted electrodes creates

relatively large current densities at the site of the electrodes. Because these current

densities are disposed at the surface of the patient, which also contains a relatively

large number of nerve endings, such electrical stimulation devices can cause

unpleasant or painful sensations, possibly arousing the user from sleep.

It is also known to apply electrical stimulation to the muscles of the

upper airway via electrodes implanted in the patient. Subcutaneous electrodes have

the benefit of being positioned adjacent to the muscle or nerve to be stimulated to

focus the electrical energy on that muscle/nerve while reducing the amount of

collateral tissues effected by the high current densities near the electrode. There are

also typically fewer nerve endings deep within the patient than at the surface. Thus,

electrical stimulation using implanted electrodes reduces the likelihood that the electrical stimulation will induce an unpleasant or painful sensation in the patient.

However, electrical muscle stimulation utilizing implanted electrodes requires surgical intervention, the permanent presence of foreign materials within the patient's

neck tissue, and at least one electrical connection protruding from the patient. Consequently, there is a potential for infection or irritation at the surgical site and at

the site where the electrode protrudes through the surface of the patient.

SUMMARY OF THE INVENTION

Accordingly, it is an object of the present invention to provide a device for stimulating the muscles in the upper airway area for the treatment of OSA that

does not suffer from the disadvantages associated with the above-described

conventional OSA treatments. This object is achieved by providing a non-invasive

device for magnetically stimulating the muscles that stabilize the upper airway to

cause them to contract. Because the stimulation is via magnetic induction, which is

capable of stimulation of deep muscular structures, the present invention does not

generate large currents at the skin. Therefore, it is less painful than surface electrode

electrical stimulation devices.

The muscle stimulator for applying a magnetic field to at least one

muscle or muscle group associated with an upper airway in a patient experiencing obstructive sleep apnea to induce tension in that muscle or muscle group to relieve the

obstructive sleep apnea includes a plurality of loops of electrical wire and a power

supply that selectively provides electrical power to the plurality of loops. Applying power to the loops produces the magnetic field used to stimulate the targeted muscles.

A sensor monitors a condition of the patient associated with the obstructive sleep apnea, such as the snoring sounds produced by the patient or the patient's respiration,

to determine when to initiate stimulation and how to change the intensity of the stimulation, if necessary, during the therapy process. A control unit receives signals

output by the sensor and controls the application of electrical power from the power

supply to the plurality of loops of electrical wire. A positioning appliance secures the

plurality of loops of electrical wire to the patient at a position relative to the targeted

muscle or muscle group such that the magnetic field produced by applying electrical power to the plurality of loops of electrical wire induces tension in that muscle or

muscle group to relieve the obstructive sleep apnea.

It is a further object of the present invention to minimize the heat

experienced by the patient as a result of using the magnetic stimulator. To that end, the present invention includes an insulating material between the patient's skin and

the coil. In addition, the temperature of the coil is monitored by a temperature sensor

and the power to the coil is controlled based on the temperature of the coil so that

excessive heat is not generated in the coil. Also, portions of the coil are maintained as

far from the patient as possible while still permitting the magnetic stimulator to

provide its therapeutic effect.

It is a still further object of the present invention to control the application of magnetic energy to the patient based on the condition of the patient. To

achieve this object, sensors are provided to monitor the condition of the patient. For

example, sensors are used to determine whether the patient is snoring and/or experiencing an apneic event. If so, the coil is energized to treat the OSA.

Energizing the coil can also be synchronized with the patient's respiration so that

stimulation begins within a predetermined window during the patient's respiratory cycle, such as at the onset of inspiration or at a period offset therefrom. Also, the

present invention contemplates using the conditions of the patient, such as the

presence of snoring, an apneic event and/or the respiratory patterns of the patient, to

regulate the intensity of the magnetic stimulation. For example, the more prevalent

the apneic events, the greater the level of stimulation. Conversely, a reduced number of apneic events results in a reduced level of stimulation. In this manner, only the

necessary level of magnetic energy is applied to the patient.

It is a further object of the present invention to provide a method of

using the device discussed above to apply a magnetic field to at least one muscle group associated with an upper airway of a patient experiencing obstructive sleep

apnea to induce tension in that muscle group to treat the obstructive sleep apnea.

It is yet another object of the present invention to provide a system and

method for diagnosing whether a patient is likely to suffer from OSA. This object is

achieved by providing a system that measures a compliance of the patient to obtain a first compliance level, applies a magnetic field to at least one muscle group associated

with an upper airway of the patient, measures the compliance while applying the

magnetic field to obtain a second compliance level, and compares the first compliance

level to the second compliance level. The smaller the difference between the first and second compliance levels, the more likely the subject suffers from obstructive sleep apnea.

These and other objects, features and characteristics of the present invention, as well as the methods of operation and functions of the related elements of structure and the combination of parts and economies of manufacture, will become more apparent upon consideration of the following description and the appended

claims with reference to the accompanying drawings, all of which form a part of this

specification, wherein like reference numerals designate corresponding parts in the

various figures. It is to be expressly understood, however, that the drawings are for

the purpose of illustration and description only and are not intended as a definition of

the limits of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

Fig. 1 is a perspective view of a magnetic stimulator according to the

principles of the present invention;

Fig. 2 is a side view of a person wearing the collar illustrated in Fig. 1 ; Fig. 3 is another side view, partially in section, showing in greater

detail the collar of Fig. 1 positioned on the patient;

Fig. 4 is a plan view of a first embodiment of the coil disposed in the

collar portion of the magnetic stimulator;

Fig. 5 is a front view illustrating the superposition of the coil

illustrated in Fig. 4 with respect to the neck of the patient;

Fig. 6 is a side view of the coil structure illustrated in Fig. 4 showing

the positioning of the coil relative to the patient's neck; Figs. 7A, 7B and 7C illustrate a second, third and fourth embodiment,

respectively, for the coil in the collar portion of the magnetic stimulator; Figs. 8A and 8B illustrate a fifth embodiment for the coil in the collar;

Fig. 9 illustrates an alternative embodiment for the collar;

Fig. 10 is a schematic diagram of the magnetic stimulator illustrated in

Fig. 1; Fig. 11 is a flowchart illustrating a process carried by the magnetic

stimulator in achieving its therapeutic effect;

Fig. 12 is a side view of the coil, a portion of the patient's neck, and a

miniature intramuscular stimulator according to another embodiment of the present invention;

Fig. 13 is a schematic diagram of the miniature intramuscular stimulator adapted for use with the magnetic stimulator of the present invention; and

Fig. 14 is a schematic diagram of a system for diagnosing whether a

patient is likely to suffer from OSA using the magnetic stimulator.

DETAILED DESCRIPTION OF THE PRESENTLY PREFERRED EMBODIMENTS OF THE INVENTION

Fig. 1 illustrates a first embodiment of a magnetic stimulator 30 according to the principles of the present invention. Magnetic stimulator 30 includes

a control unit 32 and a collar 34 coupled to control unit 32 via a flexible cable 36.

Collar 34 attaches to the patient's neck, as shown in Fig. 2, such that a portion 35 of

collar 34 containing at least one magnetic field generating coil is disposed directly

under the patient's chin 37. Control unit 32 receives signals from at least one sensor, such as sensor 38, which is connected to control unit 32 via a cable 39. Control unit 32 energizes the coil in collar 34 to produce a time varying electrical current that

creates a changing magnetic field, whose rapidly increasing flux, in turn, creates a

spacially varying electric field having a gradient that is maximized at specific muscles

and/or muscle nerves in the upper airway. In short, the changing magnetic field

produced by energizing the coil with a time varying current, such as a pulse train, induces tension in the muscles pulling the obstructing tissue from the patient's

airway, thereby relieving the obstructive sleep apnea.

In the embodiment illustrated in Fig. 1 , power is provided to control

unit 32 from an external power supply. It is to be understood, however, that batteries

or other internal power storage devices can be provided in place of, or in addition to, the external power source to energize the coil in collar 34, sensor 38, and/or the

components within control unit 32.

In the illustrated embodiment, control unit 32 includes manually

operable actuating mechanisms 33, such as buttons, dials, knobs or switches, for

performing functions such as activating and deactivating the unit, setting the ranges for the output field strength and/or duration, setting threshold values, setting operating modes, and conducting diagnostic routines on the magnetic stimulator. The present

invention also contemplates that one control unit can be used in conjunction with a

plurality of sensors, a plurality of collars, and/or a plurality of collar-sensor

combinations. If one control unit is being used in conjunction with a plurality of

sensors, a plurality of collars, and/or a plurality of collar-sensor combinations, that control unit would include additional input/output interfaces 31a for connecting the

additional sensors, collars, and or collar-sensor combinations thereto.

The control unit can also be configured with any appropriate input/output interface for exchanging data between the control unit and an external

source. For example, one or more interfaces 31b can be provided for accessing,

modifying, or downloading data stored in the control unit. Such data exchange

interfaces can include, but are not limited to, an RS-232 port, modem, coaxial, optical

fiber, rf, infrared, ultrasonic, or other interfaces that permit data exchange between the

control unit and the external device. For example, data can be provided to the control

unit using manual input devices, such as knobs, switches, buttons, and/or keypads

coupled to or integral with the control unit. Data can also be provided to, modified or

extracted from the control unit using an external computer that communicates with

the control unit using an appropriate interface.

In the illustrated embodiment, control unit 32 and collar 34 include

warning devices, such as an audio indicator 41a and a visual indicator 41b, that

inform the user, or a person monitoring the user, of the condition of the patient and/or

magnetic stimulator 30. For example, an audio or visual warning can be generated if the patient has stopped breathing for a predetermined period of time, has begun or has stopped snoring, and/or has removed or put on the collar. Of course, an appropriate

sensor or plurality of sensors for sensing such conditions must be provided.

As noted above, the present invention also contemplates providing

warning signals indicative of the status of the magnetic stimulator. For example, an audio or visual warning signal can be generated if the coil in the collar exceeds a

predetermined temperature, if the power provided to the control unit, the sensors, or

the collar has been shut off, falls below a predetermined level or exceeds a predetermined level, if the sensors or the coil are not working, have become disconnected or fail to communicate with the control unit, and/or if there is a short in

the coil, sensors and/or control unit.

In addition to or in place of the relatively simple audio/visual warning

indicators 41a and 41b, other warning devices can be provided. For example, control

unit 32 can include circuitry for notifying a remotely located third party of the existence of the condition causing the warning, using, for example, signals

communicated via telephone lines. Furthermore, the warning signals, as well as other

signals indicative of the condition of the patient and/or the magnetic stimulator that

do not constitute a warning, can be provided to a display device (not shown) such as a monitor or LED. Such a display system may be particularly beneficial in a sleep lab

setting where a single control unit is being used to monitor and magnetically stimulate

a plurality of patients under the supervision of a sleep lab technician.

It is to be further understood, that the collar, control unit and sensors

need not be separate elements. For example, as discussed in greater detail below, the sensor can be disposed on the collar so that the collar-sensor combination functions as a unit. In addition, the control unit can also be provided on the collar so that most of the components of the magnetic stimulation system, i.e., the sensors, coil, and control

unit are contained in one assembly that is worn by the patient. Depending on the power requirements, the power supply can also be provided in that assembly, further

minimizing the number of components that the patient has to be concerned with when

using the magnetic stimulator.

As shown in Fig. 3, which is a schematic illustration of the muscles

associated with the upper airway, the muscles targeted for stimulation are the

geniohyoid muscle 40 under the chin 37, the left and right stemohyoid muscles 42, the

left and right thyrohyoid muscles 44, and the left and right stemothyroid muscles 46.

The stemothyroid, stemohyoid and thyrohyoid muscles are arrayed in pairs on either

side of the trachea mid-line. However, for ease of illustration, only one of each of

these muscles is illustrated in Fig. 3, which also shows the respective attachments of

these muscles to the sternum 48, mandible 50, thyroid cartilage 52 and hyoid arch 54.

These muscles have been identified by the present inventors as being

particularly relevant to the onset and prevention of OSA because, when contracted,

these muscles brace the hyoid arch and increase tension in the tissue surrounding the

upper airway, thereby preventing obstruction of the airway. It has been discovered

that during sleep, in some patients, the relaxation of these muscles decreases the hyoid

arch support and the support of the tissue surrounding the upper airway to an extent

sufficient to result in obstruction of the upper airway, thereby causing those patients

to suffer from OSA. The present invention avoids this consequence by magnetically

stimulating the geniohyoid, stemothyroid, stemohyoid and thyrohyoid muscles so that

they provide the proper level of support even while the patient is asleep. It is to be understood that while the geniohyoid, stemothyroid,

stemohyoid and thyrohyoid muscles are the primary muscles that the present

invention contemplates stimulating, this invention is not limited to stimulation of

these particular muscles. Other muscles or muscle groups, instead of or in addition to

these muscles, can be targeted for stimulation. For example, the genioglossus, the

stylohyoid muscle and hyoglossus muscle attaching to the rostral surface of the hyoid

cartilage, and the omohyoid muscle, which attaches below the hyoid cartilage, are

possible targets for stimulation, so long as any such stimulation furthers the goal of

supporting the tissues surrounding the upper airway to reduce and/or minimize the

occurrence of OSA.

As shown in Fig. 3, when properly worn by the patient, collar 34

positions a coil 56 in an overlying relationship with the geniohyoid, stemothyroid,

stemohyoid and thyrohyoid muscles so that the magnetic field generated by passing a

current through coil 56 is specifically targeted on these muscles and/or on the nerves

controlling the contraction of these muscles. Collar 34 encircles the patient's neck

and is made from a comfortable, semi-flexible material. Collar 34 must be flexible

enough to be fitted on and comfortably worn by the patient. However, it must be rigid

enough to maintain coil 56 in an appropriate position relative to the targeted muscles

so that at a localized concentration of the magnetic field occurs at these muscles even

if the patient moves during sleep. The collar is also preferably made from a heat

insulating material so that heat generated by the current passing through the coil is

prevented from reaching the patient. To further achieve this goal, an additional thermo-insulating material or layers of such material can be provided between coil 56 and the inside surface of collar 34.

It is to be understood that the present invention is not limited to the

illustrated configuration of the collar. Quite the contrary, the present invention

contemplates any positioning device that locates and maintains the coil in an

appropriate position to stimulate the targeted muscles while minimizing heat transfer

to the patient. For example, the present invention contemplates that coil 56 can be

attached to the patient using an adhesive, for example, without the need for a collar.

In which case, an insulating material can be provided between the coil and the patient

that is also attached to the patient using any suitable method, such as adhesive.

In one embodiment of the present invention, magnetic stimulator 30 is

dynamically controlled so that stimulation is only applied to the patient's upper

airway muscles as required in order to counteract the occurrence of OSA. For this

reason, sensors, such as sensor 38 in Fig. 1, are provided to detect the onset of OSA

by monitoring characteristics of the patient indicative of this event. It is to be understood, however, that other characteristics of a patient that may or may not relate

to the onset of OSA, such as body temperature, can be monitored by the sensors and

the control unit of this invention to provide more general information on the condition

of the patient, which may be useful in determining the condition of the patient

throughout the stimulation process. This information may be particularly useful in the

sleep lab situation or hospital. Another patient characteristic that can be monitored is

the blood gas levels, such as the oxygen and/or CO₂ levels. Blood gas information can be used to monitor the effectiveness of the stimulation or to control the activation

and or deactivation of such stimulation.

In one embodiment of the present invention, sensor 38 is an acoustic

sensor that is positioned near or on the patient to sense the onset of inspiration-

induced upper airway collapse, which manifests in the form of snoring sounds emitted

by the patient. Such snoring sounds are typically produced by the unstable airway

vibrating during inspiration, and the occurrence of a snore and its increase in

prominence in successive breaths can indicate the onset of an apneic event. The

increase in snore intensity on successive inspirations warns of the impending need for

magnetic stimulation on a subsequent inspiration. Thus, detecting the occurrence of a

snore and controlling the stimulator based thereon is an effective method for

dynamically controlling stimulation so that it is only applied to the patient as

necessary to counteract the occurrence of OSA.

In another embodiment of the present invention, one or more sensors

are provided to detect the respiratory patterns of the patient. This can be

accomplished, for example, by monitoring the airflow in the patient's airway and/or

the expansion and contraction of the chest, thorax and or abdomen. The magnetic

stimulator can be activated during a specific window in the patient's respiratory cycle,

such as at the onset of inspiration or at a period offset therefrom, to prevent or threat

OSA. The present invention also contemplates monitoring the patient's EMG activity

and stimulating the patient based thereon. In the embodiment illustrated in Fig. 1, sensor 38 is a separate

component from collar 34. As such, it must be separately mounted on the patient.

This configuration is advantageous in that it permits one or more sensors to be located at various spaced apart locations on the patient unrelated to the other elements of the magnetic stimulator, such as the collar, for monitoring the same or different

conditions of the patient from various anatomical locations. For example, the

patient's heart rate can be monitored from sensors located on the front and back of the

patient's torso.

It has been determined through clinical testing that the sound

frequencies that correspond to upper airway narrowing are in the range of 20-250 Hz.

To optimize the detection of upper airway sounds in this bandwidth, it is preferable to

locate an acoustic sensor on the external surface of the patient's throat. In the

embodiment illustrated in Fig. 3, an acoustic sensor 58 is fixed at the inside surface of

collar 34 so that sensor 58 is positioned at the external surface of the patient's throat

when collar 34 is worn by the patient. This configuration also enables both the coil

and the sensor to be properly mounted on the patient by merely donning collar 34, thereby avoiding the need to place the collar and sensor on the patient separately.

Sensor 58 is coupled to control unit 32 via wiring 60 and transmits a signal indicative

of the sounds generated in the patient's upper airways to the control unit. While the sensor described above detects throat vibration using an acoustic sensor, it is to be understood that other sensors capable of detecting the onset

of an upper airway event are within the scope of the present invention. Examples of other suitable sensors include airflow sensors, pressure sensors, an electromyogram

(EMG) as a measure of muscular effort, and fiber-optic vibration sensors. Such

sensors can be operatively coupled to the collar, the control unit or can be wireless. Furthermore, while only one patient condition monitoring sensor is illustrated in

collar 34 of Fig. 3, other sensors in addition to or in place of sensor 58 can be

provided at the same locations or at other locations than that illustrated in Fig. 3. For

example, an acoustic sensor may be provided on an exposed surface of collar 34

instead of or in addition to audio sensor 58. Also, a pressure sensor and/or an EMG

sensor, separate from collar 34, may be fixed to the patient for monitoring inspiration

or muscle effort, respectively. The data from the combination of sensors can be

compared and analyzed together to detect more accurately the onset of an upper

airway event that is indicative of the occurrence of OSA.

Collar 34 in Fig. 3 also includes a second sensor 62 in the form of a

thermistor probe to monitor the temperature of coil 56. Sensor 62 enables the control

unit to prevent electrical energy from being provided to coil 56 in the event the heat generated by energizing the coil exceeds a predetermined threshold. Sensor 62 is

connected to the control unit via electrical wiring 64 within the collar. Electrical

wiring 60 and 64, as well as the electrical wiring providing power to coil 56, can be provided in the same flexible tube 36 so that only one cable and one interface are

needed between the collar and the control unit.

In the embodiment illustrated in Fig. 3, cable 36 connects coil 56 to a

power supply. It is to be understood, however, that other methods of providing power to coil 56 are contemplated by the present invention. For example, collar 34 can

contain an internal power supply for energizing coil 56, thus eliminating the need for

a dedicated power supply line between the control unit and the coil. Such a

configuration requires a communication link between the control unit and the power

supply system in the collar so that activation, deactivation and energy levels provided

to the coil can be controlled. Such a communication link can be hardwired or

wireless.

It is to be further understood that the data link between the control unit

and sensors 58 and 62 can be hardwired, as shown in Fig. 3, or wireless, so long as

data is transmitted by the sensors to the control unit. Wireless communication, which

can be rf, infrared, or ultrasonic, for example, requires that a power supply be

provided on collar 34 for powering sensors 58 and 62. Furthermore, data can be sent

from sensors 58 and 62 automatically, for example at regular timed intervals, or upon

a request from the control unit. This latter technique, however, requires that sensors

58 and 62 have the ability to receive and process commands from the control unit and

that the control unit have the ability to transmit and process these commands and the

associated responses.

Details of a first embodiment of coil 56 and the general position of coil

56 relative to the patient are discussed below with reference to Figs. 4-6. As shown in

Fig. 4, coil 56 includes a plurality of adjacently located loops, identified 1, 2, 3, and 4.

Loops 1-4 each have one or more turns, and the entire coil is wound from a

continuous length of electrical wire, such as copper or silver, so that only one pair of terminals 73 are needed to energize all four loops. An electrical insulation separates each turn in each loop from the other turns in that loop. Each loop can be configured

so that the wires in each turn of that loop lie in the same plane, as shown in Fig. 4.

However, other configurations for the wires in the loops are possible. For example,

the turns in a loop can be stacked one on another, or twisted or braided together.

The structure of coil 56 and the direction of current flow through the

loops, as shown by the arrows in Fig. 4, is selected to optimize the magnetic field

intensity at certain locations relative to coil 56. In particular, increased magnetic field

intensities are created in an area below coil 56 corresponding to areas A, B, C, and D

between adjacent loops at which currents summate. In other words, an area of increased magnetic field strength is created in an area below the coil where two loops are adjacent one another and where the currents flow through these adjacent loops in

the same direction. In Fig. 4, the currents in loops 1 and 2 at area A are flowing in the

same direction, e.g., downward relative to the top of this diagram. Thus, there is an

area of increased magnetic field strength in a region below coil 56, i.e., in a direction

toward the page, corresponding to area A. This increased magnetic field strength is

caused by a summation of magnetic fields generated by loops 1 and 2. Similar areas

of increased magnetic fields are created at areas corresponding to areas B, C, and D. In the embodiment illustrated in Fig. 4, four areas of increased

magnetic field strength are created in order to target the stimulating effect provided by

the present invention at four regions of the patient's neck. These regions correspond

to the locations of the geniohyoid 40, stemothyroid 46, stemohyoid 42 and thyrohyoid 44 muscles. See Fig. 5. By providing the specific configuration for coil 56, the

present invention stimulates only muscles deemed to be particularly suited to maintaining an unobstructed airway.

In the embodiment of the present invention illustrated in Fig. 3, in which sensors 58 and 62 are provided on or in collar 34, it is desirable to locate these

sensors in an area where the magnetic field intensity is at a minimum. Such an area is

identified as area E in Fig. 4 and corresponds to a position between adjacent loops 2

and 3 where the current in each loop are flowing in opposite directions.

While Figs. 4-5 suggest that loops 1-4 lie in the same plane, other configurations for loops 1-4 are contemplated by the present invention. For example, as shown in Fig. 6, it is desirable to orient loops 2 and 3 in separate planes so that the

area of increased magnetic field strength created at the area between loops 1 and 2

and between loops 2 and 4 is targeted toward geniohyoid muscle 40 when the collar is

positioned on the patient. Similarly, the area of increased magnetic field strength

created at the area between loops 1 and 3 and between loops 3 and 4 is targeted toward the stemothyroid 46, stemohyoid 42 and thyrohyoid 44 muscles. Thus, loop 2

and the upper portions of loops 1 and 4 adjacent to loop 2 are generally parallel the

surface of the neck under the patient's chin 37, while loop 3 and the lower portions of

loops 1 and 4 adjacent to loop 3 are generally parallel to the portion 72 of the patient's

neck between chin 37 and the sternum when the collar is worn by the patient. Please

note that Fig. 6 does not illustrate portions of the collar, other than coil 56, for ease of illustration. Because energizing coil 56 tends to cause heating of the coil, it is also

desirable to position portions 74 and 76 of loops 1 and 4, respectively, which are not

adjacent loops 2 and 3, as far as possible from the surface of the patient. Increasing the distance from portions 74 and 76 of loops 1 and 4 to the surface of the patient maximizes the thermal protection afforded by the collar, so that as little heat as possible is transferred to the patient. In addition, locating portions 74 and 76 of loops

1 and 4 as far as possible from the patient's skin minimizes the possibility of

unwanted stimulation of nerves, such as the phrenic nerve, which contracts the

diaphragm, and the vagus nerve, which depresses the patient's heart rate, by the

magnetic fields generated by the coil. The configuration of the coil concentrates the

magnetic fields in the areas shown in Fig. 4. At all other areas, the field strength is

minimized so that the only significant stimulation takes place at the targeted

locations.

A second embodiment for the coil used in the collar according to the

principles of the present invention is shown in Fig. 7 A. In this embodiment, six generally similar loops 82, 84, 86, 88, 90 and 92 define coil 80 with a current passing

therethrough as indicated by the arrows. In the illustrated embodiment, loops 82, 84, 86, 88, 90 and 92 have the same number of turns and are wound from a continuous

electrical wire. Because the loops in coil 80 are connected in series, a single pair of

terminals 94 are all that is required to energize the coil. The coil configuration

illustrated in Fig. 7A provides generally the same magnetic field pattern as the coil configuration illustrated in Figs. 4-6. Namely, four magnetic field concentrations of generally uniform magnitudes are provided generally at areas A, B, C and D when a

current is provided to terminal 94.

As noted above, the plurality of loops in coil 56 of Fig. 4 and in coil 80 of Fig. 7A are defined from a continuous wire so that only one pair of leads is

connected to the power supply. The same current flows through each loop. It is to be

understood, however, that it is not necessary for each loop in the overall coil to be

connected to any other loop. For example, in an alternative embodiment of the

present invention illustrated in Fig. 7B, coil 81 is defined by six loops separated into

two groups of loops 83a-83c and 85a-85c, wherein each group of loops is made from

a continuous length of wire and is energized by an independent power supply.

As with the previous embodiments, four areas of increased magnetic

field concentrations A-D are created by energizing loops 83a-83c and 85a-85c. Loops

83a, 83b and 83c have a common terminal 87, and loops 85a, 85b and 85c have a

common terminal 89. As noted above, terminals 87 and 89 can be connected to separate power supplies, i.e., driven by separate currents, so that each group of loops

is energized independently of the other, both in terms of timing and magnitude.

Alternatively, terminals 87 and 89 can be connected together so that each group of

loops receives the same current. This third embodiment of the coil simplifies the manufacture of the coil by enabling each group of loops to be made individually and

combined to define the coil, thereby avoiding the relatively complicated winding

pattern required to manufacture the coil illustrated in Figs. 4 and 7A. Fig. 7C illustrates a fourth embodiment in which each loop 93a-93f in

coil 91 is independent of the other loops in that coil so that each loop 93a-93f has its

own terminal 95a-95f, respectively. Because each loop is capable of being energized

individually, this configuration maximizes the variety of pattems of increased areas of magnetic stimulation that can be created by coil 91 , the intensity of the stimulation at

each area, and the timing at which these areas are stimulated, all of which is done

under the control of the control unit.

It is to be understood that each loop need not have the same number of

turns or be energized at the same voltage/current or at the same time as the other

loops or other groups of loops. Instead, the desired magnetic field pattern can be

selected by adjusting these parameters so that specific muscles are targeted for

stimulation and are stimulated at a specified timing. For example, if there is an area

that should be stimulated with a larger intensity than the other areas, the number of

turns in the loops associated with that area can be increased, with the current level

being kept constant, or the current level to the loops associated with that area can be increased, with the current levels provided to the other loops remaining unchanged. If

there is an area that is to be stimulated before the other areas, current can be provided

to the loops or group of loops associated with that area prior to being provided to the other loops. If groups of loops are provided, rather than individual loops, the groups

of loops can be powered at different levels by associated power supplies, have

numbers of turns that are different from other groups of loops, and/or configurations

that are different from other groups of loops, and be energized at timings different from the other groups of loops to achieve a variety of magnetic field intensities, pattems and timings.

For example, the coil stmcture in Fig. 4 can be modified so that loops

1 and 4 are energized together and so that loops 2 and 3 are energized independently of one another. This configuration permits loops 1 , 2 and 4 to be energized as a group

to stimulate areas A and B. Similarly loops 1, 3, and 4 can be energized as a group to

stimulate areas C and D. Also, the timing at which each areas A-D are stimulated can

be synchronized or independent so that one area or more areas are stimulated at the

same time, at an offset time period or at different times than the other areas.

It can be appreciated that a wide variety of loop configurations,

activation combinations or pattems, activation timings and stimulation intensities can

be provided so that a single coil structure, such as those shown in Figs. 4-7C, can provide many different magnetic field pattems. The different magnetic field pattems

can be created by independently modulating the electrical current magnitude, phase,

and duration, in each loop or groups of loops in the coil. The control unit is used to

set the energizing pattem, magnitude and timing for the coil so that selected loops are

activated at selected power levels at appropriate times to produce a particular magnetic field pattem with a particular stimulation intensity at selected portions of that pattem. Ideally, the magnetic field pattem, stimulation intensities and stimulation

timing targets the muscles in the patient that maximize the OSA treatment capabilities

of the present invention. A fifth embodiment of the coil is shown in Figs. 8A-8B. In this embodiment, coil 106 is defined by three adjacent loops 108, 110 and 112 with the current flowing therethrough as illustrated by the arrows. This configuration provides

two areas 1 14 and 116 of concentrated magnetic stimulation. However, this

configuration is more compact than the coil configurations of the previous

embodiments. As shown in Fig. 8B, ends 118 and 120 of outer loops 108 and 1 12 are spaced apart from a surface 122 of the patient to minimize heat transfer to the patient

and prevent the magnetic fields from stimulating the phrenic and/or vagus nerves.

As with the previous embodiments, the loops shown in Figs. 8 A and

8B can be wound as a group of individually so that each loop is independent of the

other loops. Also, the loops can be energized together from a common source, in

groups, or individually and can be energized at the same or different power levels and at the same time or at different times depending on the desired magnetic field pattem.

Fig. 8C illustrates a sixth embodiment for the coil. Coil 111 in this figure is similar to the coil configuration shown in Figs. 4-6 except that one of the

large loops have been deleted, leaving a three-loop coil with two areas 113 of field strength summation. This coil configuration is advantageous in that is reduces the

coil resistance and inductance as compared to the coil of Figs. 4-6.

It is to be understood that loop shapes, other than those shown in Figs.

4, 7A-7C and 8A-8C are contemplated by the present invention. For example, one or

more of the loops in the same coil can be circular, elliptical, square, triangular, or

rectangular. Also, the present invention contemplates providing more than one coil in the collar. Each such coil can have an overall shape, loop configuration, power supply, and activation pattem (including activation timings and intensity) that differs

from the other coils in the collar.

Fig. 9 illustrates a second embodiment for the collar. In this embodiment, collar 124 includes a cutout portion 126 in the area of the collar

underlying the patient's chin. Cutout potion 126 provides a cavity that receives the

chin and/or jaw when the collar is positioned on the patient so that the collar is

comfortable to the patient.

While collar 34 in Fig. 1 and collar 124 in Fig. 9 are both illustrated as

having a generally circular shape with a uniform height and thickness around the

circumference (except for the chin cutout in Fig. 9), it is to be understood that other variations in the stmcture of the collar are contemplated by the present invention. For

example, the height and thickness of the collar can be reduced at the back of the

patient's neck because this portion of the collar does not directly support the coil in

the collar. In addition, the collar can be made from a continuous piece of material that slips over the patient's head with an elastic portion to ensure that the collar remains properly positioned on the patient. Altematively, the collar can be a strip of

material having ends that selectively secure to one another to attach the collar about

the patient's neck. In which case, any conventional fastening device, such as snaps,

clasps, hooks, a zipper, a button or VELCRO , can be used to attach the ends of the

collar to one another. It is important that the collar be properly positioned on the patient. To that end, collar 124 in Fig. 9 includes markings 128 on an exposed surface thereof to

assist in properly positioning the collar on the patient. In the illustrated embodiment, collar 124 includes an arrow 128 that indicates the central axis of the coil configuration, such as central axis 130 in Fig. 8 A, which is the axis of symmetry for

the coil configuration. To properly position the coil relative to the muscles to be

stimulated, the user aligns arrow 128 directly below the chin along the centerline of

the face. It is to be understood that other indicia or indexing markings or mechanisms

can be employed to position the collar on the neck at the proper location. For

example, markings on the collar could be provided on the portions of the collar that

overlie the carotid arteries when the collar is positioned on the patient. The location

of the carotid arteries are relatively easy to locate, either by the user or another person

applying the collar and, thus, are useful in positioning the collar merely by aligning

the carotid artery markings on the collar with the patient's carotid arteries. Fig. 10 is a schematic diagram of magnetic stimulator 30. In the illustrated embodiment, collar 34 includes a snore sensor 130, such as sensor 58 of

Fig. 3, and circuitry for amplifying and filtering the analog signal output by the

sensor. Filtering is done to eliminate extraneous noise from the signal output from the snore sensor. The amplified and filtered snore sensor signal is provided to sample

and hold sensor 132, A/D converter 134 and microprocessor 136 in control unit 32.

Microprocessor 136 controls the operation of a coil drive circuit 140, which provides

energy to coil 142 in collar 34. Memory 138 stores threshold data, data provided from microprocessor 136, and programs carried out by the microprocessor. Power from a power supply 144 is provided to coil drive circuit 140 through an over current

protection circuit 146. Power supply 144 can be any suitable power supply that is capable of providing sufficient power to coil 142. Coil drive circuit 146 can be any

suitable circuit for energizing coil 142, such as a selectively dischargeable

capacitance. Over current protection circuit 146 can be any suitable circuit that limits

the amount of energy (voltage/current) that can be provided to coil 142 for safety purposes.

The energy limiting function of over current protection circuit 146 is

separate from the energy level setting function of microprocessor 136. More

specifically, over current protection circuit 146 ensures that the patient is never

stimulated at a level that is above that appropriate for that patient, even if the

maximum stimulation intensity level is set by the user. Preferably, the maximum

current permitted by over protection circuit 146 is set in advanced based on the characteristics of the patient using the stimulator.

One embodiment of the operation of magnetic stimulator 30 is discussed below with reference to Fig. 11, which is a flowchart illustrating a process

carried by the magnetic stimulator in achieving its therapeutic effect. More specifically, the process illustrated in Fig. 11 is repeatedly conducted under the

control of the microprocessor once the magnetic stimulator is activated. In step S30,

the airway sound vibrations are detected using an appropriate transducer that is in

communication with the patient's airway, such as audio snore sensor 58 of Fig. 3. These sound vibrations are output by the transducer as an electrical signal, which is

bandpass filtered, amplified and converted from an analog to a digital signal S in step S32. Filtering is performed to eliminate noise in the signal output from the sensor,

and amplification is performed to adjust the signal level to a level suitable for the

components receiving that signal. Signal S is provided to microprocessor 136.

In step S34, the magnitude of signal S is compared to a threshold

magnitude S_TH, which is a predetermined minimum noise threshold. Threshold

magnitude S_TH is preferably determined and set so in advance so that it is specific to the patient using the magnetic stimulator. If signal S does not exceed S_TH, the signal

output by the transducer is considered to not correspond to a snore and the process

returns to step S30. If signal S exceeds S_TH, the signal is considered to correspond to

a snore sound and is integrated in step S36 to determine its duration So and energy level S_E, which are stored in memory 138.

In step S38, duration and energy level thresholds D_TH and E_TH,

respectively, are set. These thresholds can have fixed values that are determined and

set in advance, preferably based on the condition of the patient, or they can have values that vary during the operation of the stimulator. For example, the magnitude

of duration and energy level thresholds D_TH and E_TH can be set based on the recent history of snore sounds. During an intense snoring period, the energy level thresholds

D_TH and E_TH can be increased so that lower amplitude snore sounds. On the other

hand, these threshold values can be decreased, thereby increasing the sensitivity of the stimulator, if apnea events are detected or if the intensity (magnitude and/or duration) of the snore sounds diminish.

In a preferred embodiment of the present invention, an average of a

predetermined number of previous signals corresponding to snore sounds are used to

set thresholds D_TO and E_TH- For example, the duration and energy level of the past ten snore sound signals, eliminating the maximum and minimum values, can be averaged

to set these thresholds. It is to be understood, however, that other techniques can be

used to average the previous snore sounds signals to set D_TH and E_TH-

In steps S40 and S42, the duration S_ of the snore sound signal is

compared to duration threshold D_TH, and the energy level S_E of the snore sound signal is compared to energy level threshold E_TH- If either of these thresholds are not met, the process returns to step S30, meaning that the snoring sound does not qualify as an

apneic event. If, however, both of these thresholds are met, the snore sound signal is

considered to qualify to an apneic event and the process continues to step S44.

In step S44, microprocessor determines if more than 30 seconds have

elapsed since the last snore sound signal S qualifying as an apneic event. If it has

been 30 seconds or less since the last snore sound signal S qualifying as an apneic event, a counter in microprocessor 136 is incremented in step S46. Thus, the counter

is incremented if the upper airway sound producing a sound signal that qualifies as an apneic event is detected at or within 30 seconds of a previous sound signal also

qualifying as an apneic event. If more than 30 seconds have elapsed, this counter is

reset in step S48 and the process returns to step 30. In step S50, the microprocessor determines if the counter has reached

three. If not, the process returns to step S30. If so, the microprocessor determines, in

step S52, if more than 60 seconds have elapsed since the previous stimulation. If only

60 or less seconds have elapsed since the previous stimulation, the process returns to

step S30. If, however, more than 60 seconds have elapsed, the stimulation level is set

by the microprocessor in step S54 and the microprocessor causes coil drive circuit

140 to apply energy to the coil to stimulate the patient at the set stimulation level.

The initial stimulation level is typically set in advance by a qualified

physician. However, an input device, such as dial or keypad, on or operatively

coupled to the control unit can be used to adjust this level. Preferably, a lockout mechanism is provided to prevent the user from adjusting the intensity level beyond that specified by the physician. For example, the control unit can be preprogrammed,

prior to being provided to the user, to not accept or apply any stimulation levels above

a predetermined level. Thus providing a further safeguard against excessive

stimulation.

The present invention also contemplates modifying the intensity of the magnetic stimulation as necessary during the stimulation therapy. This is done in step S56 following the application of the magnetic stimulation using a feedback system.

For example, as additional upper airway sounds qualify as snore sounds or further

qualify as an apneic events, the intensity of the magnetic stimulation can be increased, preferably incrementally, to further stabilize the airway. The incremental amount of

each increase can be fixed or variable, and each increase need not be by the same amount. The amount of the incremental increase is typically established in advance or

it can be set based on the conditions of the patient, such as the snoring activity. In a preferred embodiment of the present invention, steps S30 through S50 are repeated, and if the counter has reached three in step S50, the stimulation level is increased by a predetermined amount.

The stimulation level can also be decreased if the number of upper

airway sounds qualifying as snore sounds or further qualifying as apneic events

decreases following the onset of stimulation. In this manner, only the stimulation

intensities necessary to treat the apneic events are applied to the patient, thereby

conserving power and minimizing use of the magnetic stimulator.

In a preferred embodiment of the present invention, if no apneic event

snore sounds are detected after 5 minutes after the onset of stimulation, the stimulation level is reduced by a first predetermined amount, which can either be fixed or variable. In a second embodiment of the present invention, steps S30 through

S 50 are repeated and if the counter does not reach three in step S50, the stimulation intensity is reduced by the first predetermined amount. In both of these embodiments,

the stimulation intensity can be further reduced by a second predetermined amount for

each consecutive time period, such as a 5 minute interval, during which no apneic events are detected until the stimulation level reaches zero. This second

predetermined amount can be the same as the first predetermined amount and can be

fixed or variable. Thereafter, the process returns to step S30. It is to be understood, that the time period during which further apneic

events are monitored to determine how to change (or cease) the stimulation level, if

necessary, can be a fixed or variable length of time. Also, the present invention contemplates simply ceasing stimulation after a predetermined period of time has elapsed during which a minimum number, e.g., zero, of apneic events are detected. It

is to be further understood that this same scenario for decreasing the intensity of the

magnetic stimulation can also be used to increase its intensity.

While the occurrence of an apneic event is detected in step S50 if the

counter reaches three, it is to be understood that other integer numbers of sounds

qualifying as a snore sound can be used as a benchmark for determining the

occurrence of an apneic event. For example, two or four snore sounds occurring

within a predetermined time period can be used to determine the occurrence of an

apneic event. Furthermore, the duration of this predetermined time period, which

corresponds to the 30 sec period in step S44, can be set in advance or it can be variable based on the monitored conditions of the patient.

Although the initiation, modification and termination of stimulation

can be conducted using the process discussed above, it is also possible to apply the

process discussed in U.S. Patent No. 5,203,343, the contents of which are incorporated herein by reference, to the magnetic stimulator. The process illustrated

in the '343 patent is intended for use with a positive airway pressure device to control

the initiation, modification and termination of the positive airway pressure. However,

the process taught by the '343 patent can be used in an analogous manner to control the magnetic stimulator. In which case, it is not the pressure level that is controlled,

but the intensity of the magnetic stimulation.

The initiation, modification and termination of stimulation can also be

performed based on the patient's respiratory cycle. For example, stimulation can be synchronized with the patient's inspiration so that stimulation begins at the same time

as inspiration. Altematively, stimulation can be initiated just prior to, i.e., not more

than one second before, or just after, i.e., not more than one second after, the initiation

of inspiration. This method obviates the need to determine the occurrence of snore

and/or an apneic event and attempts to eliminate such events before they occur.

In an exemplary embodiment of the present invention, stimulation

energy is provided to the patient by energizing the coil with a series of current pulses,

each pulse having a prescribed magnitude and duration. The magnitude of the pulses in the pulse train and/or the duty ratio can be set to determined the overall intensity of

the stimulation provided to the patient. For example, in a preferred embodiment, a

series of pulse trains, each having a pulse rate between 5-30 pulses/sec and lasting

between 1-3 seconds, is provided to the patient. Altematively, stimulation can be

provided in phase with the patient's inspiratory effort. This requires monitoring the inhalation and exhalation of the patient using any appropriate device and timing the

stimulation to coincide with the onset of inhalation. It is to be understood, however, that stimulation can be initiated at any period offset from the onset of inspiration so

that the initiation of stimulation either precedes or follows the onset of inspiration. Maximum magnitudes and pulse repetition rates can be set in advance to limit the overall stimulation that the patient receives. Typically, these magnitudes

and pulse repetition rates, as well as the duration of the pulse trains, threshold levels

and other variables discussed above are set by a doctor or other physician after

conducting an evaluation of the patient. Furthermore, the current pulses are optimized to reduce the energy dissipated in the coil. For example, the coil is

energized by a current emanating from charge stored on a low-loss capacitor, most of which charge is recaptured during the applied pulse.

Although not shown in the process illustrated in Fig. 11 , the overall

energy level provided to the coil can be ceased or reduced if the coil temperature exceeds a predetermined value. Conversely, the energy level can be increased so long

as the coil temperature remains within an acceptable range. This feature of the

present invention ensures that the patient's safety is not compromised while still

providing the maximum therapy to the patient.

The present invention further contemplates controlling the application,

changes in intensity, and cessation of stimulation based on other criteria. For

example, the present invention contemplates delaying the application of stimulation energy to the patient after the magnetic stimulation system has been activated, so that the patient has the opportunity to fall asleep prior to the start of the stimulation

therapy. This can be accomplished, for example, by causing a timer to be activated,

either manually or automatically upon activation of the stimulation system, and once the time counts out a predetermined time interval, initiating the stimulation therapy. This therapy delay feature can also be based on a conventional clock so that the user

can set the therapy to begin at any preselected time during the night. Similarly, the magnetic stimulation system of the present invention can cease application of the

stimulation after the passage of a selectable time period so that stimulation ceases

before the patient typically awakes, thereby preventing the user from being awaken by the stimulation therapy. This delay in turning off the stimulation therapy can be based on a time interval or based on a conventional clock.

The present invention also contemplates controlling the stimulation

energy applied to the patient in a variety of ways to maximize patient comfort. For

example, one embodiment of the present invention contemplates incrementally increasing the intensity of the stimulation energy being delivered to the patient following the actuation of the stimulation system. This increase can take place in

place of or after the delay period discussed above. Another embodiment of the

present invention contemplates incrementally decreasing the intensity of the

stimulation energy being delivered to the patient. This decrease can take place in

place of or before the delay in turning off the stimulation therapy discussed above.

The intensity of the stimulation can also be controlled based on the patient's sleep stages, assuming, of course, that the appropriate sensors and control systems are

provided to detect and classify the patient's sleep stages. The present invention further contemplates providing various methods

for interrupting the stimulation therapy. For example, a pause function that stops stimulation therapy can be initiated by the user either by manually actuating an input device, such as a button, on the control unit or remotely. The stimulation therapy can

also be interrupted automatically, if, for example, a malfunction is detected. Restart

of the stimulation therapy can begin automatically, after the elapse of a fixed or

selectable time period, for example, or by manually actuating the input device, i.e.,

again actuating the button or the remote control. Restart of the stimulation therapy

can begin at the stimulation energy levels existing prior to the pause, at the initial

energy level, or at some other preselected level. In addition, the delay function and/or

the incremental intensity functions can be instituted during the restart so that the user

again has the opportunity to fall asleep in the absence of any stimulation therapy.

The present invention also contemplates providing a safety feature in

which a maximum stimulation energy that can be provided to the patient is set. This can be accomplished via a control unit. This stimulation energy provided to the patient will not be exceed the set maximum regardless of the stimulation energy set

by the user on the control unit. It is preferable that the means by which the maximum

stimulation energy is set is secured so that it cannot be altered inadvertently, or tampered with. The use of a password that must be input in order to alter the

maximum setting is an example of such a security feature.

In still another embodiment of the present invention, the magnetic

stimulation system is provided with an automatic tum-on and/or an automatic tum-off

feature. This provides the advantages of simplifying the operation of the system and conserving power, for example. Sensors on the collar, for example, such as a temperature sensor or galvanic type sensor can detect when the appliance is disposed on the patient. The output of these sensors are used to control the actuation and

deactivation of the stimulation system of the application and cessation of the stimulation therapy.

With the growing popularity of managed healthcare, healthcare providers are becoming more concerned that the patients actually use the prescribed

therapy devices. To meet this concern, the present invention monitors patient

compliance by storing information regarding the used of magnetic stimulator, such as

the amount of time that the unit was tumed on and/or the amount of time that the coil

has been energized.

In one embodiment discussed above, the coil is only energized once an apneic event is detected. In another embodiment, the coil is energized in

synchronization with the patient's respiratory cycle. Thus, the present invention

makes it difficult for the patient to deceive the healthcare provider as to the actual

usage of the device, thereby providing a relatively reliable and accurate indication of

the actual usage of the magnetic stimulator.

Furthermore, because the stimulator is capable of communicating with

external devices using a modem, for example, patient compliance can be remotely

monitored by the healthcare provider with little or no patient involvement. This same

remote patient compliance monitoring feature also permits the healthcare provider to monitor the operating status of the stimulator, for example, by causing the device to

run a diagnostic routine and reports the results. Fig. 12 illustrates a further embodiment of the present invention. In this embodiment, the stmcture for the magnetic stimulator, including the coil and control unit are the same as in the previous embodiments. In this embodiment,

however, miniature implantable intramuscular stimulators 160 and 162 are provided

in or near the patient's muscles that are targeted for stimulation or near the nerves that contract such muscles. Because these devices are relatively small, they can be

implanted using a hypodermic, thereby minimizing the invasiveness of the

implantation surgery. Also, because these devices are not physically connected to any

other devices, they do not suffer the medical consequences associated with providing

an electrode permanently penetrating the patient's skin, as is the case with many conventional implanted electrodes.

As shown in Fig. 13, intramuscular stimulators 160 and 162 include a

receiver coil 164 that communicates with coil 56 in the collar, high capacitance electrodes 166, and a decoding network 168. Receiver coil 164 and high capacitance

electrode 166 transfer the magnetic energy provided by the coil into electrical energy

that is applied directly to the muscle (or nerve) contacting the intramusculuar stimulator. This permits specific muscles to be targeted for stimulation, which is

especially beneficial in situations where the targeted muscle is recessed deeply beneath the patient's skin or is not easily distinguishable from non-target muscles of

nerves.

Decoding network 168 enables the control unit to distinguish and

control a selected intramuscular stimulator using, for example, an AM or FM signal. In this manner, intramuscular stimulator 160 can be controlled, for example, to stimulate the geniohyoid muscle without causing intramuscular stimulator 162 to

stimulate the stemohyoid muscle. Of course, other muscles can be target using other intramusculor stimulators and groups of muscles (or one muscle) can be stimulated

using a plurality of intramuscular or stimulators implanted into those muscles (or that

single muscle) all of which have the same identification for activation purposes. The

stimulation intensities and the timing at which the muscles are stimulated can be

varied in the same manner discussed above with respect to the many ways in which areas A-D can be stimulated. See Fig. 4. This is accomplished by selectively

actuating the intramuscular stimulators either independently of one another or in

synchronization and controlling the stimulation intensity level of each intramuscular

stimulator, all of which is done by the control unit.

The present invention also contemplates providing an implantable

passive probe that alters the magnetic field strength in the vicinity of the probe in

addition to or in place of the active probes discussed above. In a preferred embodiment of the present invention, the passive probe is a glass encapsulated strip of

material having a high magnetic permeability, typically about 0.5 mm in length and 2 mm long, and curved so that the strip can wrap, at least partially, around a nerve. Such a device having a high magnetic permeability reduces the magnetic field at its

exterior. Providing such a device near a nerve fiber enhances magnetic stimulation by

creating an increase in the gradient of the electric field along the nerve fiber. This electric field gradient is believed to be the mechanism by which the nerve fiber is stimulated.

From the forgoing, it can be appreciated that the present invention

increases the tension in the muscles that stabilize the upper airway to prevent its collapse. It is non-painful and more tolerable than skin/surface stimulation

techniques. The device is non-invasive, and, therefore, safer than systems that stimulate the musculature with implanted electrodes. For those patients for whom

electrical stimulation of the muscles stabilizing the upper airway is planned, magnetic

stimulation may be useful in establishing the efficacy of the planned treatment. In

this regard, the intensity of the magnetic stimulation applied by the qualified caregiver can be larger than that possible in the unit intended for home use. This enables the

caregiver to determine if electrical stimulation, either induced by the present

invention or using conventional implanted electrodes, will produce the desired

therapeutic benefit in that patient.

In the previous embodiments of the present invention, the magnetic

stimulating system is the sole means for treating the patient's breathing disorder. It is

to be understood, however, that the present invention contemplates using the magnetic stimulating system in conjunction with other techniques for treating breathing disorders. For example, one embodiment of the present invention

contemplates using the magnetic stimulating system in conjunction with conventional

electrical stimulation systems to target additional muscles or muscle groups for stimulation or supplement the stimulation provided by the electrode-based muscle

stimulator.

Another embodiment of the present invention contemplates using the

magnetic stimulating system in conjunction with a conventional pressure support

system that applies positive air pressure at the mouth and/or nose of the patient to

"splint" the airway. Even if magnetic stimulation the muscles of the airway does not

fully open the airway, it is believed that the induced muscle stimulation will reduce

the pressures necessary to be provided by the pressure support system in order to

splint the airway and treat the breathing disorder. It is well recognized that the

pressure needed to be provided to the patient by the pressure support device to treat the breathing disorder should be kept as low as possible.

The present invention contemplates that the magnetic stimulating

system of the present invention can be used in conjunction with most, if not all, conventional the pressure support systems. Such pressure support systems typically

include a pressure generator 172 that generates a gas flow, a conduit 173 that carries

the gas flow to the patient, and a patient interface device 174 that communicates the conduit with the patient's airway. See Fig. 14. Examples of pressure support devices

that are used in conventional pressure support systems include a CPAP (continuous

positive airway pressure) device, bi-level devices, which provide variable levels of pressure support during the patient's respiratory cycle, such as the Respironics

BiPAP^® devices, PAV^® devices and PPAP devices. Examples of suitable patient

interface devices include nasal masks, oral appliances, nasal/oral masks, full face masks, hoods, nasal cannulas, trachea tube, and any other device that communications

a gas flow with the patient's airway.

The present invention also contemplates using the magnetic stimulator

discussed above as a diagnosis device to assess the likelihood that a subject suffers from OSA. It has been clinically determined using standard electromyography

techniques that the muscle activity in the upper airway of awake patients suffering

from OSA is higher than in normal subjects. By measuring the compliance of the

subject in the awake state, both in the presence and in the absence of magnetic

stimulation, it is possible to determine whether that subject is likely to suffer from

OSA. Compliance is determined by measuring the change in the cross-sectional area, and hence the volume, of the patient's upper airway while different positive pressures

are applied to the upper airway by means of a standard continuous positive airway

pressure ("CPAP") device.

In patients likely to suffer from OSA, the difference in the measured

compliance with and without magnetic stimulation is less than the difference in the

measured compliance with and without magnetic stimulation in normal subjects. This

is so because patients likely to suffer from OSA tend to have abnormally high muscle

activity in their upper airway in the awake state. Thus, the application of magnetic

stimulation to the upper airway in the awake state has little effect in tensing the upper airway muscles, resulting in little change in compliance. In normal patients, however,

the application of magnetic stimulation to the upper airway generally has a more

significant impact on compliance because the magnetic stimulation tenses the otherwise relaxed upper airway muscles. Thus, by measuring compliance, first

without magnetic stimulation to the upper airway muscles and then with such

stimulation, it can be determined that the subject is likely to suffer from OSA if there is relatively little change in compliance under these two conditions.

Fig. 14 illustrates an example of a system 170 for diagnosing the likelihood that a subject suffers from OSA using the magnetic stimulator discussed

above. Diagnosis system 170 includes a CPAP device 172 for providing continuous

positive airway pressure to the patients airway via a nosemask 174 or other suitable

nose sealing member. Magnetic stimulator 30 induces tension in the subjects upper

airway muscles. An acoustic transducer 176 measures the subject's compliance, i.e.,

the change in the cross-sectional area, and hence the volume, of the patient's upper airway. It to be understood that other devices for measuring the subject's compliance,

such as through magnetic resonance imaging (MRI), are contemplated by the present

invention; An acoustic transducer is used for this purpose in the illustrated embodiment because of its relative simplicity, ease of use and low cost. In the

illustrated embodiment, CPAP device 172, acoustic transducer 176 and magnetic

stimulator 30 are all operated under the control of a computer 178. Also, a monitor

180 and keyboard 182 are coupled to computer 178.

System 170 diagnoses the likelihood that the subject suffers from

obstructive sleep apnea by first measuring the compliance of the subject to obtain a first compliance level using acoustic transducers 176. This is done in the absence of

magnetic stimulation. Next, a magnetic field is applied to at least one muscle group associated with an upper airway of the subject using magnetic stimulator 30. The compliance of the subject is measured while the magnetic field is being applied to

obtain a second compliance level. The first compliance level is compared to the second compliance level to determine the difference therebetween. The smaller the

difference between the first and second compliance levels, the more likely the subject

suffers from obstructive sleep apnea. In a preferred embodiment of the present invention, computer 178 makes this comparison and outputs an indication of the

likelihood that the subject suffers from OSA.

Although the invention has been described in detail for the purpose of

illustration based on what is currently considered to be the most practical and

preferred embodiments, it is to be understood that such detail is solely for that

purpose and that the invention is not limited to the disclosed embodiments, but on the contrary, is intended to cover modifications and equivalent arrangements that are

within the spirit and scope of the appended claims.

Claims

What is Claimed is:

1. A muscle stimulator adapted to apply a magnetic field to at least one muscle group associated with an upper airway of a patient having a breathing

disorder to induce tension in said muscle group to treat said breathing disorder, said muscle stimulator comprising:

a plurality of loops of electrical wire; a power supply that selectively provides electrical power to said

plurality of loops to produce said magnetic field;

a sensor adapted to monitor a physiological characteristic of a patient;

a control unit that receives signals output by said sensor and controls

application of said electrical power from said power supply to said plurality of loops of electrical wire based thereon; and

a positioning appliance adapted to secure said plurality of loops of

electrical wire to a patient at a position relative to said at least one muscle group such that said magnetic field produced by applying said electrical power to said plurality of

loops of electrical wire induces tension in said at least one muscle group to treat said breathing disorder.

2. The muscle stimulator of claim 1 , further comprising a temperature sensor disposed proximate to said plurality of loops of electrical wire to sense a temperature of said loops.

3. The muscle stimulator of claim 2, wherein said control unit

prevents application of electrical power to said plurality of loops of electrical wire

responsive to said temperature detected by said temperature sensor exceeding a predetermined threshold temperature.

4. The muscle stimulator of claim 1, wherein said sensor is an audio

sensor disposed on said positioning appliance and adapted to detect snoring sounds

produced by said patient and to output a signal indicative thereof.

5. The muscle stimulator of claim 1, wherein said sensor detects a condition of a patient associated with respiration outputs a signal indicative thereof.

6. The muscle stimulator of claim 1, wherein said plurality of loops of

electrical wire are non-overlapping and are carried by said positioning appliance such

that a peripheral portion of each loop is adjacent a peripheral portion of another loop.

7. The muscle stimulator of claim 6, wherein each loop in said plurality of loops has more than one turn.

8. The muscle stimulator of claim 7, wherein each loop generally a same number of turns and all loops are energized from a common pair of terminals.

9. The muscle stimulator of claim 8, wherein said turns in each loop

are arranged in a spiral, such that turns distal from a common central axis in each loop

have a radius that is greater than turns proximate to said common central axis in that

same loop.

10. The muscle stimulator of claims 6, wherein an outer peripheral portion of at least one of said loops, which is not adjacent a peripheral portion of

another of said loops, is carried by said positioning appliance so as to be spaced

further apart from said patient than another portion of said at least one loop that is adjacent another one of said loops responsive to said positioning appliance attaching said plurality of loops to said patient, thereby minimizing an amount of heat produced

by said loops that reaches said patient.

11. The muscle stimulator of claim 6, wherein said plurality of loops

of electrical wire comprises four loops having a common terminal and configured such that applying electrical power to said common terminal produces four areas

where said magnetic fields are concentrated.

12. The muscle stimulator of claim 6, wherein said plurality of loops

of electrical wire comprises three loops configured such that applying electrical power to said three loops produces two areas where said magnetic fields are concentrated.

13. The muscle stimulator of claim 6, wherein said plurality of loops of electrical includes a first loop and a second loop, said first loop being independent

of said second loop so that that said first loop is capable of being energized independently of said second loop.

14. The muscle stimulator of claim 1 , further comprising a thermal

insulating material disposed between said plurality of loops from said patient.

15. The muscle stimulator of claim 1, wherein said positioning

appliance is a selectively attachable collar adapted to encircle a neck of said patient and to be worn by said patient such that said plurality of loops are positioned

proximate to said neck between a chin and a sternum.

16. The muscle stimulator of claim 15, wherein said collar includes

markings on an exposed surface thereof to assist in properly positioning said collar on

said patient.

17. The muscle stimulator of claim 1, wherein said control unit is operatively coupled to said positioning appliance and said sensor via a flexible cable

for hardwire transmission of signals between said control unit and said sensor and

said coil carried by said positioning appliance.

18. The muscle stimulator of claim 1, wherein said sensor is carried

by said positioning appliance such that properly positioning said positioning

appliance on said patient locates said loops in a position relative to said muscles to be

stimulated and also locates said sensor at an appropriate position on said patient for collecting relevant data.

19. The muscle stimulator of claim 1, wherein said control unit includes means for comparing said signal output by said sensor to a threshold value

indicative of an occurrence of an apneic event, said control unit causing said power

supply to supply electrical power to said plurality of loops of electrical wire

responsive to said signal exceeding said threshold value.

20. The muscle stimulator of claim 19, wherein said control unit

further includes means for monitoring a number of times said signal exceeds said

threshold values during a predetermined time interval, said control unit causing said power supply to provide said electrical energy to said plurality of loops responsive to

said number of times said signal exceeds said threshold values during said predetermined time interval being greater than a first predetermined number.

21. The muscle stimulator of claim 20, wherein said control unit

includes means for adjusting said threshold values.

22. The muscle stimulator of claim 1, wherein said control unit

includes means for adjusting an intensity of said magnetic field produced by said muscle stimulator and a duration that said magnetic field is applied to said patient.

23. The muscle stimulator of claim 22, wherein said means for adjusting said intensity of said magnetic field adjusts said magnitude responsive to

signals provided by said sensor.

24. The muscle stimulator of claim 1 , wherein said plurality of loops

of electrical wire are defined by a continuous electrical wire.

25. The muscle stimulator of claim 1, further comprising a warning system that provides a warning signal indicative of one of a condition of said patient

and a condition of said muscle stimulator.

26. The muscle stimulator of claim 1, further comprising an

implantable non-conductive member adapted to provide an electric field discontinuity to enhance excitability of a nerve proximate to said non-conductive member

responsive to application of said magnetic field.

27. The muscle stimulator of claim 1, further comprising a miniature

intramuscular stimulator adapted to be implanted in said patient, said miniature intramuscular stimulator transferring energy contained in said magnetic field

produced by said into electrical energy that is adapted to be applied directly to said patient at a site of said intramuscular stimulator.

28. The muscle stimulator of claim 27, wherein said intramuscular

stimulator includes a receiving coil adapted to receive signals from said coil, a

decoding network that enables said control unit to distinguish and control said

intramuscular stimulator independently of other intramuscular stimulators, and an

electrode for applying electrical energy to a portion of said patient contacting said

electrode, said electrical energy being derived from said magnetic field applied to said

intramuscular stimulator.

29. The muscle stimulator of claim 27, further comprising a first

intramuscular stimulator and a second intramuscular stimulator, wherein said control

unit is capable of actuating said first intramuscular stimulator independent of said

second intramuscular stimulator.

30. A muscle stimulator adapted to apply a magnetic field to at least

one muscle group associated with an upper airway of a patient having a breathing disorder to induce tension in said muscle group to treat said breathing disorder, said muscle stimulator comprising:

a plurality of loops of electrical wire;

means for supplying electrical power to said plurality of loops of electrical wire to produce said magnetic field;

means for monitoring a physiological characteristic of a patient;

means, receiving signals output by said first sensing means, for

controlling said electrical power provided to said plurality of loops based thereon; and

means for maintaining said plurality of loops of electrical wire at a position relative to a patient so as to direct said magnetic field produced by said

plurality of loops at said at least one muscle group to induce tension in said at least one muscle group to treat said breathing disorder.

31. A method of applying a magnetic field to at least one muscle

group associated with an upper airway of a patient having a breathing disorder induce

tension in said muscle group to treat said breathing disorder, said muscle stimulator

comprising: affixing a plurality of loops of electrical wire proximate to said at least

one muscle group; monitoring a physiological characteristic of a patient;

providing electrical power to said plurality of loops of electrical wire to produce said magnetic field based on said monitored physiological characteristic, thereby inducing tension in said at least one muscle group to treat said breathing disorder.

32. The method of applying a magnetic field according to claim 31, further comprising the steps:

generating a signal indicative of said physiological characteristic;

comparing said signal to a threshold value indicative of an occu╧Çence of breathing disorder; and

applying electrical power to said plurality of loops of electrical wire responsive to said signal exceeding said threshold value.

33. The method of applying a magnetic field according to claim 32,

further comprising the step of monitoring a number of times said signal exceeds said

threshold value during a predetermined time interval, and applying said electrical

energy to said plurality of loops responsive to said number of times said signal

exceeds said threshold values during said predetermined time interval being greater

than a first predetermined number.

34. The method of applying a magnetic field according to claim 33,

further comprising the step of adjusting said threshold values.

35. The method of applying a magnetic field according to claim 31, further comprising the step of adjusting an intensity of said magnetic field and a

duration that said magnetic field is applied to a patient.

36. The method of applying a magnetic field according to claim 31 ,

further comprising providing a non-conductive member proximate to a nerve in a

patient, said non-conductive member providing an electric field discontinuity to

enhance excitability of said nerve responsive to application of said magnetic field.

37. A system for diagnosing the likelihood that a subject suffers from

obstructive sleep apnea, comprising: a compliance measuring system adapted to measure a compliance level

of said subject; a magnetic stimulator adapted to magnetically stimulate at least one

muscle group associated with an upper airway of said subject;

means for causing said compliance measuring system to measure a

first compliance level of said subject in an absence of magnetic stimulation and to

measure a second compliance level of said subject while said magnetic stimulation is

being applied to said least one muscle group associated with said upper airway; and means for comparing said first compliance level to said second

compliance level to determine a difference therebetween, whereby the smaller said difference between said first and said second compliance level, the more likely said subject is likely to suffer from obstructive sleep apnea.

38. A method of diagnosing the likelihood that a subject suffers from obstructive sleep apnea, comprising the steps of:

measuring a compliance of said subject to obtain a first compliance

level;

applying a magnetic field to at least one muscle group associated with

an upper airway of said subject;

measuring said compliance of said subject while applying said

magnetic field to at least one muscle group associated with an upper airway to obtain a second compliance level; and

comparing said first compliance level to said second compliance level to determine a difference therebetween, whereby the smaller the difference between

said first and said second compliance level, the more likely said subject is likely to

suffer from obstructive sleep apnea.