US20080109045A1 - Selective nerve fiber stimulation for treating conditions - Google Patents

Abstract

Apparatus for treating a heart condition of a subject is provided, including an electrode device, which is adapted to be coupled to a vagus nerve of the subject. A control unit is adapted to drive the electrode device to apply to the vagus nerve a stimulating current, which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the vagus nerve. The control unit is also adapted to drive the electrode device to apply to the vagus nerve an inhibiting current, which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS
• The present patent application is a continuation-in-part of PCT Patent Application PCT/IL02/00068, filed Jan. 23, 2002, entitled, “Treatment of disorders by unidirectional nerve stimulation,” which is a continuation-in-part of U.S. patent application Ser. No. 09/944,913, filed Aug. 31, 2001, entitled, “Treatment of disorders by unidirectional nerve stimulation.” The '068 application and the '913 application are assigned to the assignee of the present patent application and are incorporated herein by reference.
• This application is related to a US patent application to Gross et al., filed on even date, entitled, “Electrode assembly for nerve control,” which is assigned to the assignee of the present patent application and is incorporated herein by reference.
• This application claims the benefit of U.S. Provisional Patent Application 60/383,157 to Ayal et al., filed May 23, 2002, entitled, “Inverse recruitment for autonomic nerve systems,” which is assigned to the assignee of the present patent application and is incorporated herein by reference.
FIELD OF THE INVENTION
• The present invention relates generally to treating patients by application of electrical signals to a selected nerve or nerve bundle, and specifically to methods and apparatus for stimulating the vagus nerve for treating heart conditions.
BACKGROUND OF THE INVENTION
• The use of nerve stimulation for treating and controlling a variety of medical, psychiatric, and neurological disorders has seen significant growth over the last several decades, including for treatment of heart conditions. In particular, stimulation of the vagus nerve (the tenth cranial nerve, and part of the parasympathetic nervous system) has been the subject of considerable research. The vagus nerve is composed of somatic and visceral afferents (inward conducting nerve fibers, which convey impulses toward the brain) and efferents (outward conducting nerve fibers, which convey impulses to an effector to regulate activity such as muscle contraction or glandular secretion).
• The rate of the heart is restrained in part by parasympathetic stimulation from the right and left vagus nerves. When the vagus nerves fail to properly stimulate the heart, various arrhythmias may result, including tachycardia and atrial fibrillation. By artificially stimulating the vagus nerves, it is possible to slow the heart, allowing the heart to more completely relax and the ventricles to experience increased filling. With larger diastolic volumes, the heart may beat more efficiently because it may expend less energy to overcome the myocardial viscosity and elastic forces of the heart with each beat.
• Stimulation of the vagus nerve has been proposed as a method for treating various heart conditions, including heart failure and atrial fibrillation. Heart failure is a cardiac condition characterized by a deficiency in the ability of the heart to pump blood throughout the body and/or to prevent blood from backing up in the lungs. Customary treatment of heart failure includes medication and lifestyle changes. It is often desirable to lower the heart rates of patients suffering from faster than normal heart rates. The effectiveness of beta blockers in treating heart disease is attributed in part to their heart-rate-lowering effect.
• Bilgutay et al., in “Vagal tuning: a new concept in the treatment of supraventricular arrhythmias, angina pectoris, and heart failure,” J. Thoracic Cardiovas. Surg. 56(1):71-82, July, 1968, which is incorporated herein by reference, studied the use of a permanently-implanted device with electrodes to stimulate the right vagus nerve for treatment of supraventricular arrhythmias, angina pectoris, and heart failure. Experiments were conducted to determine amplitudes, frequencies, wave shapes and pulse lengths of the stimulating current to achieve slowing of the heart rate. The authors additionally studied an external device, triggered by the R-wave of the electrocardiogram (ECG) of the subject to provide stimulation only upon an achievement of a certain heart rate. They found that when a pulsatile current with a frequency of ten pulses per second and 0.2 milliseconds pulse duration was applied to the vagus nerve, the heart rate could be decreased to half the resting rate while still preserving sinus rhythm. Low amplitude vagal stimulation was employed to control induced tachycardias and ectopic beats.
• PCT Patent Publication WO 01/26729 to Terry et al., which is incorporated herein by reference, describes techniques to increase cardiac output in patients suffering from heart failure. An implanted neurostimulator stimulates the vagus nerve in order to decrease the heart rate towards a target rate within the normal range. The vagal stimulation frequency is described as being automatically adjusted until the heart rate of the patient reaches the target rate. An activity sensor detects physical activity of the patient and adjusts the frequency of the stimulating pulses accordingly in order to elevate the heart rate during periods of physical activity.
• The effect of vagal stimulation on heart rate and other aspects of heart function, including the relationship between the timing of vagal stimulation within the cardiac cycle and the induced effect on heart rate, has been studied in animals. For example, Zhang Y et al., in “Optimal ventricular rate slowing during atrial fibrillation by feedback AV nodal-selective vagal stimulation,” Am J Physiol Heart Circ Physiol 282:H1102-H1110 (2002), describe the application of selective vagal stimulation by varying the nerve stimulation intensity, in order to achieve graded slowing of heart rate. This article is incorporated herein by reference.
• The following articles and book, which are incorporated herein by reference, may be of interest:
• Levy M N et al., in “Parasympathetic Control of the Heart”,Nervous Control of Vascular Function, Randall W C ed., Oxford University Press (1984)
• Armour J A et al. eds.,Neurocardiology, Oxford University Press (1994)
• Perez M G et al., “Effect of stimulating non-myelinated vagal axon on atrio-ventricular conduction and left ventricular function in anaesthetized rabbits,” Auton Neurosco 86 (2001)
• Jones, J F X et al., “Heart rate responses to selective stimulation of cardiac vagal C fibres in anaesthetized cats, rats and rabbits,” J Physiol 489 (Pt 1):203-14 (1995)
• Wallick D W et al., “Effects of ouabain and vagal stimulation on heart rate in the dog,” Cardiovasc. Res., 18(2):75-9 (1984)
• Martin P J et al., “Phasic effects of repetitive vagal stimulation on atrial contraction,” Circ. Res. 52(6):657-63 (1983)
• Wallick D W et al., “Effects of repetitive bursts of vagal activity on atrioventricular junctional rate in dogs,” 237(3):H275-81 (1979)
• A number of patents describe techniques for treating arrhythmias and/or ischemia by, at least in part, stimulating the vagus nerve. Arrhythmias in which the heart rate is too fast include fibrillation, flutter and tachycardia. Arrhythmia in which the heart rate is too slow is known as bradyarrhythmia. U.S. Pat. No. 5,700,282 to Zabara, which is incorporated herein by reference, describes techniques for stabilizing the heart rhythm of a patient by detecting arrhythmias and then electronically stimulating the vagus and cardiac sympathetic nerves of the patient. The stimulation of vagus efferents directly causes the heart rate to slow down, while the stimulation of cardiac sympathetic nerve efferents causes the heart rate to quicken. Simultaneously, afferents from vagus and/or cardiac sympathetic nerves induce the brain to employ the brain's natural mechanisms of heart rhythm control.
• U.S. Pat. No. 5,330,507 to Schwartz, which is incorporated herein by reference, describes a cardiac pacemaker for preventing or interrupting tachyarrhythmias and for applying pacing therapies to maintain the heart rhythm of a patient within acceptable limits. The device automatically stimulates the right or left vagal nerves as well as the heart tissue in a concerted fashion dependent upon need. Continuous and/or phasic electrical pulses are applied. Phasic pulses are applied in a specific relationship with the R-wave of the ECG of the patient.
• European Patent Application EP 0 688 577 to Holmstrom et al., which is incorporated herein by reference, describes a device to treat atrial tachyarrhythmia by detecting arrhythmia and stimulating a parasympathetic nerve that innervates the heart, such as the vagus nerve.
• U.S. Pat. Nos. 5,690,681 and 5,916,239 to Geddes et al., which are incorporated herein by reference, describe closed-loop, variable-frequency, vagal-stimulation apparatus for control of ventricular rate during atrial fibrillation. The apparatus stimulates the left vagus nerve, and automatically and continuously adjusts the vagal stimulation frequency as a function of the difference between actual and desired ventricular excitation rates. In an alternative embodiment, the apparatus automatically adjusts the vagal stimulation frequency as a function of the difference between ventricular excitation rate and arterial pulse rate in order to eliminate or minimize pulse deficit.
• U.S. Pat. No. 5,203,326 to Collins, which is incorporated herein by reference, describes a pacemaker which detects a cardiac abnormality and responds with electrical stimulation of the heart combined with vagal nerve stimulation. The vagal stimulation frequency is progressively increased in one-minute intervals, and, for the pulse delivery rate selected, the heart rate is described as being slowed to a desired, stable level by increasing the pulse current.
• U.S. Pat. No. 5,199,428 to Obel et al., which is incorporated herein by reference, describes a cardiac pacemaker for detecting and treating myocardial ischemia. The device automatically stimulates the vagal nervous system as well as the heart tissue in a concerted fashion in order to decrease cardiac workload and thereby protect the myocardium.
• A number of patents and articles describe other methods and devices for stimulating nerves to achieve a desired effect. Often these techniques include a design for an electrode or electrode cuff.
• U.S. Pat. Nos. 4,608,985 to Crish et al. and 4,649,936 to Ungar et al., which are incorporated herein by reference, describe electrode cuffs for selectively blocking orthodromic action potentials passing along a nerve trunk, in a manner intended to avoid causing nerve damage.
• PCT Patent Publication WO 01/10375 to Felsen et al., which is incorporated herein by reference, describes apparatus for modifying the electrical behavior of nervous tissue. Electrical energy is applied with an electrode to a nerve in order to selectively inhibit propagation of an action potential.
• U.S. Pat. No. 5,755,750 to Petruska et al., which is incorporated herein by reference, describes techniques for selectively blocking different size fibers of a nerve by applying direct electric current between an anode and a cathode that is larger than the anode. The current applied to the electrodes blocks nerve transmission, but, as described, does not activate the nerve fibers in either direction.
• The following articles, which are incorporated herein by reference, may be of interest:
• Ungar I J et al., “Generation of unidirectionally propagating action potentials using a monopolar electrode cuff,” Annals of Biomedical Engineering, 14:437-450 (1986)
• Sweeney J D et al., “An asymmetric two electrode cuff for generation of unidirectionally propagated action potentials,” IEEE Transactions on Biomedical Engineering, vol. BME-33(6) (1986)
• Sweeney J D et al., “A nerve cuff technique for selective excitation of peripheral nerve trunk regions,” IEEE Transactions on Biomedical Engineering, 37(7) (1990)
• Naples G G et al., “A spiral nerve cuff electrode for peripheral nerve stimulation,” by IEEE Transactions on Biomedical Engineering, 35(11) (1988)
• van den Honert C et al., “Generation of unidirectionally propagated action potentials in a peripheral nerve by brief stimuli,” Science, 206:1311-1312 (1979)
• van den Honert C et al., “A technique for collision block of peripheral nerve: Single stimulus analysis,” MP-11, IEEE Trans. Biomed. Eng. 28:373-378 (1981)
• van den Honert C et al., “A technique for collision block of peripheral nerve: Frequency dependence,” MP-12, IEEE Trans. Biomed. Eng. 28:379-382 (1981)
• Rijkhoff N J et al., “Acute animal studies on the use of anodal block to reduce urethral resistance in sacral root stimulation,” IEEE Transactions on Rehabilitation Engineering, 2(2):92 (1994)
• Mushahwar V K et al., “Muscle recruitment through electrical stimulation of the lumbo-sacral spinal cord,” IEEE Trans Rehabil Eng, 8(1):22-9 (2000)
• Deurloo K E et al., “Transverse tripolar stimulation of peripheral nerve: a modelling study of spatial selectivity,” Med Biol Eng Comput, 36(1):66-74 (1998)
• Tarver W B et al., “Clinical experience with a helical bipolar stimulating lead,” Pace, Vol. 15, October, Part II (1992)
• In physiological muscle contraction, nerve fibers are recruited in the order of increasing size, from smaller-diameter fibers to progressively larger-diameter fibers. In contrast, artificial electrical stimulation of nerves using standard techniques recruits fibers in a larger- to smaller-diameter order, because larger-diameter fibers have a lower excitation threshold. This unnatural recruitment order causes muscle fatigue and poor force gradation. Techniques have been explored to mimic the natural order of recruitment when performing artificial stimulation of nerves to stimulate muscles.
• Fitzpatrick et al., in “A nerve cuff design for the selective activation and blocking of myelinated nerve fibers,” Ann. Conf. of the IEEE Eng. in Medicine and Biology Soc, 13(2), 906 (1991), which is incorporated herein by reference, describe a tripolar electrode used for muscle control. The electrode includes a central cathode flanked on its opposite sides by two anodes. The central cathode generates action potentials in the motor nerve fiber by cathodic stimulation. One of the anodes produces a complete anodal block in one direction so that the action potential produced by the cathode is unidirectional. The other anode produces a selective anodal block to permit passage of the action potential in the opposite direction through selected motor nerve fibers to produce the desired muscle stimulation or suppression.
• The following articles, which are incorporated herein by reference, may be of interest:
• Rijkhoff N J et al., “Orderly recruitment of motoneurons in an acute rabbit model,” Ann. Conf. of the IEEE Eng., Medicine and Biology Soc., 20(5):2564 (1998)
• Rijkhoff N J et al., “Selective stimulation of small diameter nerve fibers in a mixed bundle,” Proceedings of the Annual Project Meeting Sensations/Neuros and Mid-Term Review Meeting on the TMR-Network Neuros, Apr. 21-23, 1999, pp. 20-21 (1999)
• Baratta R et al., “Orderly stimulation of skeletal muscle motor units with tripolar nerve cuff electrode,” IEEE Transactions on Biomedical Engineering, 36(8):836-43 (1989)
• The following articles, which are incorporated herein by reference, describe techniques using point electrodes to selectively excite peripheral nerve fibers:
• Grill W M et al., “Inversion of the current-distance relationship by transient depolarization,” IEEE Trans Biomed Eng, 44(1):1-9 (1997)
• Goodall E V et al., “Position-selective activation of peripheral nerve fibers with a cuff electrode,” IEEE Trans Biomed Eng, 43(8):851-6 (1996)
• Veraart C et al., “Selective control of muscle activation with a multipolar nerve cuff electrode,” IEEE Trans Biomed Eng, 40(7):640-53 (1993)
SUMMARY OF THE INVENTION
• It is an object of some aspects of the present invention to provide apparatus and methods for treating and controlling a medical condition by application of electrical signals to a selected nerve or nerve bundle.
• It is also an object of some aspects of the present invention to provide apparatus and methods for treating and controlling a medical condition by application of electrical signals to a selected nerve or nerve bundle while minimizing adverse side effects.
• It is a further object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart conditions by application of electrical signals to the vagus nerve, while minimizing adverse side effects.
• It is still a further object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart failure by reducing the heart rate and/or cardiac contractility.
• It is yet a further object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart failure by slowing the heart rate without inducing excessive variability in the induced heart rate.
• It is an additional object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart arrhythmias, such as fibrillation, atrial fibrillation or tachycardia, by slowing and/or stabilizing the heart rate, and/or reducing cardiac contractility.
• It is yet an additional object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart arrhythmias without inducing excessive variability in the induced heart rate.
• It is still an additional object of some aspects of the present invention to provide apparatus and methods for treating and controlling heart conditions without the systemic side effects sometimes caused by pharmaceutical treatments of heart conditions.
• In preferred embodiments of the present invention, apparatus for treating a heart condition comprises a multipolar electrode device that is applied to a portion of a vagus nerve that innervates the heart of a patient. Typically, the system is configured to treat heart failure and/or heart arrhythmia, such as atrial fibrillation or tachycardia. A control unit preferably drives the electrode device to (i) apply signals to induce the propagation of efferent action potentials towards the heart, and (ii) suppress artificially-induced afferent action potentials towards the brain, in order to minimize any unintended side effect of the signal application.
• When inducing efferent action potentials towards the heart, the control unit preferably drives the electrode device to selectively recruit nerve fibers beginning with smaller-diameter fibers, and to recruit progressively larger-diameter fibers as the desired stimulation level increases. Preferably, in order to achieve this smaller-to-larger diameter fiber recruitment order, the control unit stimulates fibers essentially of all diameters using cathodic current from a central cathode, while simultaneously inhibiting fibers in a larger-to-smaller diameter order using anodal current (“efferent anodal current”) from a set of one or more anodes placed between the central cathode and the edge of the electrode device closer to the heart (“the efferent anode set”). The amount of parasympathetic stimulation delivered to the heart is preferably increased by decreasing the number of fibers affected by the efferent anodal current, in a smaller-to-larger diameter order, e.g., by decreasing the amplitude or frequency of the efferent anodal current applied to the nerve.
• The control unit preferably suppresses afferent action potentials induced by the cathodic current by inhibiting essentially all or a large fraction of fibers using anodal current (“afferent anodal current”) from a second set of one or more anodes (the “afferent anode set”). The afferent anode set is preferably placed between the central cathode and the edge of the electrode device closer to the brain (the “afferent edge”), to block essentially all fibers from conveying signals in the direction of the brain during application of the afferent anodal current.
• In some preferred embodiments of the present invention, the efferent anode set comprises a plurality of anodes. Application of the efferent anodal current in appropriate ratios from the plurality of anodes in these embodiments generally minimizes the “virtual cathode effect,” whereby application of too large an anodal current creates a virtual cathode, which stimulates rather than blocks fibers. When such techniques are not used, the virtual cathode effect generally hinders blocking of smaller-diameter fibers, because a relatively large anodal current is typically necessary to block such fibers, and this same large anodal current induces the virtual cathode effect. Likewise, the afferent anode set preferably comprises a plurality of anodes in order to minimize the virtual cathode effect in the direction of the brain.
• Preferably, parasympathetic stimulation of the vagus nerve is applied responsive to one or more sensed physiological parameters or other parameters, such as heart rate, electrocardiogram (ECG), blood pressure, indicators of cardiac contractility, cardiac output, norepinephrine concentration, or motion of the patient.
• Preferably, stimulation is applied in a closed-loop system in order to achieve and maintain a desired heart rate responsive to one or more such sensed parameters.
• In some preferred embodiments of the present invention, vagal stimulation is applied in a series of pulses. The application of the series of pulses in each cardiac cycle preferably commences after a variable delay after a detected R-wave, P-wave, or other feature of an ECG. The delay is preferably calculated in real time using a function, the inputs of which include one or more pre-programmed but updateable constants and one or more sensed parameters, such as the R-R interval between cardiac cycles and/or the P-R interval. Alternatively or additionally, a lookup table of delays is used to determine in real time the appropriate delay for each application of pulses, based on the one or more sensed parameters.
• Advantageously, the techniques described herein generally enable relatively fine control of the level of stimulation of the vagus nerve, by imitating the natural physiological smaller-to-larger diameter recruitment order of nerve fibers. This recruitment order allows improved and more natural control over the heart rate. Such fine control is particularly advantageous when applied in a closed-loop system, wherein such control results in smaller changes in heart rate and lower latencies in the control loop, which generally contribute to greater loop stability and reduced loop stabilization time. The use of a variable delay prior to application of pulses generally reduces the beat-to-beat variability of the heart rate sometimes experienced when using techniques having a constant ECG-based delay before application of pulses.
• “Vagus nerve,” and derivatives thereof, as used in the specification and the claims, is to be understood to include portions of the left vagus nerve, the right vagus nerve, and branches of the vagus nerve such as the superior cardiac nerve. Similarly, stimulation of the vagus nerve is described herein by way of illustration and not limitation, and it is to be understood that stimulation of other autonomic nerves, including nerves in the epicardial fat pads, for treatment of heart conditions or other conditions, is also included within the scope of the present invention.
• “Heart failure,” as used in the specification and the claims, is to be understood to include all forms of heart failure, including ischemic heart failure, non-ischemic heart failure, and diastolic heart failure.
• There is therefore provided, in accordance with a preferred embodiment of the present invention, apparatus for treating a heart condition of a subject, including:
• an electrode device, adapted to be coupled to a vagus nerve of the subject; and
• a control unit, adapted to:
• drive the electrode device to apply to the vagus nerve a stimulating current, which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the vagus nerve, and
• drive the electrode device to apply to the vagus nerve an inhibiting current, which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.
• Preferably, the therapeutic direction is an efferent therapeutic direction towards a heart of the subject. Alternatively or additionally, the therapeutic direction is an afferent therapeutic direction towards a brain of the subject.
• In a preferred embodiment, the control unit increases a number of action potentials traveling in the therapeutic direction by decreasing an amplitude of the applied inhibiting current, and/or decreases a number of action potentials traveling in the therapeutic direction by increasing an amplitude of the applied inhibiting current.
• In a preferred embodiment, the heart condition includes heart failure and/or cardiac arrhythmia, and the apparatus is adapted to treat the heart condition.
• Optionally, the apparatus includes an override, adapted to be used by the subject so as to influence the application by the electrode device of the stimulating and inhibiting currents.
• In a preferred embodiment, the apparatus includes a pacemaker, and the control unit is adapted to drive the pacemaker to apply pacing pulses to a heart of the subject. Alternatively, the apparatus includes an implantable cardioverter defibrillator (ICD), and the control unit is adapted to drive the ICD to apply energy to a heart of the subject.
• Preferably, the control unit is adapted to drive the electrode device to apply the stimulating current and/or the inhibiting current in a series of pulses.
• In a preferred embodiment, the control unit receives an electrical signal from the electrode device, and drives the electrode device to regulate the stimulating and/or inhibiting current responsive to the electrical signal.
• Preferably, the electrode device includes a cathode, adapted to apply the stimulating current, and a primary set of anodes, which applies the inhibiting current. Most preferably, the primary set of anodes includes a primary anode and a secondary anode, disposed so that the primary anode is located between the secondary anode and the cathode, and the secondary anode applies a current with an amplitude less than about one half an amplitude of a current applied by the primary anode.
• Preferably, the control unit is adapted to drive the electrode device to apply the stimulating current so as to regulate a heart rate of the subject. Most preferably, the control unit is adapted to drive the electrode device to regulate an amplitude of the stimulating current so as to regulate the heart rate of the subject.
• Alternatively or additionally, the control unit drives the electrode device to apply the inhibiting current so as to regulate a heart rate of the subject. In this case, the control unit preferably drives the electrode device to regulate an amplitude of the inhibiting current so as to regulate the heart rate of the subject.
• Preferably, the control unit is adapted to drive the electrode device to apply the stimulating and inhibiting currents in a series of pulses. Most preferably, the control unit:
• • drives the electrode device to apply the stimulating and inhibiting currents in a series of about one to 20 pulses,
  • configures the pulses to have a duration of between about one and three milliseconds, and/or
  • drives the electrode device to apply the stimulating and inhibiting currents in the series of pulses over a period of between about one and about 200 milliseconds.
• Preferably, the control unit drives the electrode device to apply the stimulating and inhibiting currents in the series of pulses so as to regulate a heart rate of the subject. Most preferably, the control unit regulates the number of pulses in the series of pulses so as to regulate the heart rate of the subject. Optionally, the control unit regulates a duration of each pulse so as to regulate the heart rate of the subject. Optionally, the control unit varies a length of a period of application of the series of pulses so as to regulate the heart rate of the subject.
• In a preferred embodiment, the control unit drives the electrode device to apply to the vagus nerve a second inhibiting current, which is capable of inhibiting device-induced action potentials traveling in a non-therapeutic direction opposite the therapeutic direction in the first and second sets of nerve fibers.
• Preferably, the control unit to drives the electrode device to apply the second inhibiting current to the vagus nerve at a primary and a secondary location, the primary location located between the secondary location and an application location of the stimulating current, and to apply at the secondary location a current with an amplitude less than about one half an amplitude of a current applied at the primary location.
• In a preferred embodiment, the apparatus includes a sensor unit, and the control unit is adapted to receive at least one sensed parameter from the sensor unit, and to drive the electrode device to apply the stimulating and inhibiting currents responsive to the at least one sensed parameter.
• Preferably, the control unit is adapted to determine a target heart rate of the subject responsive to the at least one sensed parameter, and the control unit is adapted to drive the electrode device to apply the stimulating and inhibiting currents so as to adjust a heart rate of the subject towards the target heart rate.
• The sensor unit may include one or more of the following sensors, in which case the control unit receives the at least one sensed parameter from the following one or more sensors:
• • a blood pressure sensor,
  • a left ventricular pressure (LVP) sensor,
  • an accelerometer (in which case, the at least one sensed parameter includes motion of the subject),
  • a detector of norepinephrine concentration in the subject, and/or
  • an impedance cardiography sensor.
• Alternatively or additionally, the at least one sensed parameter includes an indicator of decreased cardiac contractility, an indicator of cardiac output, and/or an indicator of a time derivative of a LVP, and the control unit receives the indicator.
• In a preferred embodiment, the sensor unit includes an electrocardiogram (ECG) monitor, the at least one sensed parameter includes an ECG value, and the control unit receives the at least one sensed parameter from the ECG monitor.
• Preferably, the at least one sensed parameter includes an ECG reading indicative of a presence of arrhythmia, and the control unit is adapted to receive the at least one sensed parameter from the ECG monitor. Optionally, the at least one sensed parameter includes an indication of a heart rate of the subject, and the control unit is adapted to receive the indication of the heart rate. Further optionally, the at least one sensed parameter includes indications of a plurality of heart rates of the subject at a respective plurality of points in time, and the control unit is adapted to receive the at least one sensed parameter and to determine a measure of variability of heart rate responsive thereto.
• In a preferred embodiment, the sensor unit is adapted to sense an initiation physiological parameter and a termination physiological parameter of the subject, and the control unit is adapted to drive the electrode device to apply the stimulating and inhibiting currents to the vagus nerve after a delay, to initiate the delay responsive to the sensing of the initiation physiological parameter, and to set a length of the delay responsive to the termination physiological parameter.
• Preferably, the control unit is adapted to determine a target heart rate of the subject responsive to the at least one sensed parameter, and the control unit is adapted to set the delay so as to adjust the heart rate towards the target heart rate.
• Optionally, the termination physiological parameter includes an atrioventricular (AV) delay of the subject, and the control unit is adapted to set the length of the delay responsive to the AV delay.
• Preferably, the sensor unit includes an electrocardiogram (ECG) monitor, and the initiation physiological parameter includes a P-wave or R-wave of a cardiac cycle of the subject, and wherein the control unit is adapted to initiate the delay responsive to the sensing of the P-wave or R-wave, as the case may be. Preferably, the termination physiological parameter includes a difference in time between two features of an ECG signal recorded by the ECG monitor, such as an R-R interval between a sensing of an R-wave of a first cardiac cycle of the subject and a sensing of an R-wave of a next cardiac cycle of the subject, or a P-R interval between a sensing of a P-wave of a cardiac cycle of the subject and a sensing of an R-wave of the cardiac cycle, and the control unit sets the length of the delay responsive to the termination physiological parameter.
• There is further provided, in accordance with a preferred embodiment of the present invention, apparatus for treating a heart condition of a subject, including:
• a cathode, adapted to apply to a vagus nerve of the subject a stimulating current which is capable of inducing action potentials in the vagus nerve; and
• a primary and a secondary anode, adapted to be disposed so that the primary anode is located between the secondary anode and the cathode, and adapted to apply to the vagus nerve respective primary and secondary inhibiting currents which are capable of inhibiting action potentials in the vagus nerve.
• Preferably, the primary and secondary anodes are adapted to be placed between about 0.5 and about 2.0 millimeters apart from one another. Further preferably, the secondary anode is adapted to apply the secondary inhibiting current with an amplitude equal to between about 2 and about 5 milliamps. Still further preferably, the secondary anode is adapted to apply the secondary inhibiting current with an amplitude less than about one half an amplitude of the primary inhibiting current applied by the primary anode.
• In a preferred embodiment, the primary anode, the secondary anode, and/or the cathode includes a ring electrode adapted to apply a generally uniform current around a circumference of the vagus nerve. Alternatively or additionally, the primary anode, the secondary anode, and/or the cathode includes a plurality of discrete primary anodes, adapted to be disposed at respective positions around an axis of the vagus nerve.
• Optionally, the apparatus includes a tertiary anode, adapted to be disposed such that the secondary anode is between the tertiary anode and the primary anode.
• Preferably, the electrode device includes an efferent edge, and the cathode is adapted to be disposed closer than the anodes to the efferent edge of the electrode device.
• Preferably, the cathode and/or the anodes are adapted to apply the stimulating current so as to regulate a heart rate of the subject.
• Optionally, the cathode includes a plurality of discrete cathodes, adapted to be disposed at respective positions around an axis of the vagus nerve, so as to selectively stimulate nerve fibers of the vagus nerve responsive to the positions of the nerve fibers in the vagus nerve.
• Optionally, the apparatus includes a set of one or more blocking anodes, adapted to be disposed such that the cathode is between the set of blocking anodes and the primary anode, and adapted to apply to the vagus nerve a current which is capable of inhibiting action potentials propagating in the vagus nerve in a direction from the cathode towards the set of blocking anodes.
• Preferably, the set of blocking anodes includes a first anode and a second anode, adapted to be disposed such that the first anode is located between the second anode and the cathode, and wherein the second anode is adapted to apply a current with an amplitude less than about one half an amplitude of a current applied by the first anode.
• Preferably, the electrode device includes an afferent edge, wherein the cathode is adapted to be disposed closer than the anodes to the afferent edge of the electrode device.
• Preferably, the apparatus includes a cuff, and an electrically-insulating element coupled to an inner portion of the cuff, and the primary anode and the cathode are adapted to be mounted in the cuff and separated from one another by the insulating element. Preferably, the primary and secondary anodes and the cathode are recessed in the cuff so as not to be in direct contact with the vagus nerve.
• Preferably, the apparatus includes a control unit, adapted to drive the cathode and the anodes to apply the respective currents to the vagus nerve, so as to treat the subject.
• Preferably, the cathode is adapted to apply the stimulating current and the anodes are adapted to apply the inhibiting current so as to regulate a heart rate of the subject. Optionally, the cathode is adapted to vary an amplitude of the applied stimulating current and the anodes are adapted to vary an amplitude of the applied inhibiting current so as to regulate a heart rate of the subject.
• There is still further provided, in accordance with a preferred embodiment of the present invention, apparatus for treating a heart condition of a subject, including:
• an electrode device, adapted to be coupled to a vagus nerve of the subject;
• a sensor unit, adapted to sense an initiation physiological parameter and a termination physiological parameter of the subject; and
• a control unit, adapted to:
• drive the electrode device to apply to the vagus nerve, after a delay, a current which is capable of inducing action potentials that propagate in the vagus nerve,
• initiate the delay responsive to the sensing of the initiation physiological parameter, and
• set a length of the delay responsive to the termination physiological parameter.
• Optionally, the sensor unit includes a single sensor, adapted to sense the initiation physiological parameter and the termination physiological parameter.
• The termination physiological parameter may include an atrioventricular (AV) delay of the subject, a respiration parameter of the subject, and the control unit is adapted to set the length of the delay responsive to the termination physiological parameter.
• Preferably, the control unit is adapted to:
• drive the electrode device to apply to the vagus nerve a stimulating current, which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the vagus nerve, and
• drive the electrode device to apply to the vagus nerve an inhibiting current, which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.
• Optionally, the termination physiological parameter includes a blood pressure of the subject, and wherein the control unit is adapted to set the length of the delay responsive to the blood pressure.
• Preferably, the sensor unit is adapted to sense a rate-setting parameter of the subject, wherein the rate-setting parameter includes a blood pressure of the subject, and wherein the control unit is adapted to receive the rate-setting parameter from the sensor unit and to drive the electrode device to apply the current responsive to the rate-setting parameter.
• Optionally, the rate-setting parameter includes the initiation physiological parameter and/or the termination physiological parameter, and the control unit is adapted to drive the electrode device to apply the current responsive to the initiation physiological parameter so as to regulate the heart rate of the subject.
• Preferably, the control unit is adapted to set the length of the delay so as to adjust the heart rate towards the target heart rate. Optionally, the control unit is adapted to access a lookup table of delays, and to set the length of the delay using the lookup table and responsive to the initiation and termination physiological parameters.
• Preferably, the initiation physiological parameter includes a P-wave, R-wave, Q-wave, S-wave, or T-wave of a cardiac cycle of the subject, and wherein the control unit is adapted to initiate the delay responsive to the sensing of the cardiac wave.
• Preferably, the termination physiological parameter includes a difference in time between two features of an ECG signal recorded by the ECG monitor, and the control unit is adapted to set the length of the delay responsive to the difference in time between the two features. The termination physiological parameter may include an R-R interval between a sensing of an R-wave of a first cardiac cycle of the subject and a sensing of an R-wave of a next cardiac cycle of the subject, and wherein the control unit is adapted to set the length of the delay responsive to the R-R interval. Alternatively or additionally, the termination physiological parameter includes an average of R-R intervals sensed for a number of cardiac cycles, and wherein the control unit is adapted to set the length of the delay responsive to the average of the R-R intervals.
• Alternatively, the termination physiological parameter includes a P-R interval between a sensing of a P-wave of a cardiac cycle of the subject and a sensing of an R-wave of the cardiac cycle, and wherein the control unit is adapted to set the length of the delay responsive to the P-R interval. Alternatively or additionally, the termination physiological parameter includes an average of P-R intervals sensed for a number of cardiac cycles, and wherein the control unit is adapted to set the length of the delay responsive to the average of the P-R intervals.
• There is also provided, in accordance with a preferred embodiment of the present invention, apparatus for treating a condition of a subject, including:
• an electrode device, adapted to be coupled to an autonomic nerve of the subject; and
• a control unit, adapted to:
• drive the electrode device to apply to the nerve a stimulating current, which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the nerve, and
• drive the electrode device to apply to the nerve an inhibiting current, which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.
• Preferably, the autonomic nerve includes one or more of the following:
• a lacrimal nerve,
• a salivary nerve,
• a vagus nerve,
• a pelvic splanchnic nerve,
• a sympathetic nerve,
• and the control unit is adapted to drive the electrode device to apply the stimulating and inhibiting currents to the nerve.
• Preferably, the control unit is adapted to drive the electrode device to apply the stimulating and inhibiting currents to the nerve so as to affect behavior of one of the following, so as to treat the condition:
• a lung of the subject,
• a stomach of the subject,
• a pancreas of the subject,
• a small intestine of the subject,
• a liver of the subject,
• a spleen of the subject,
• a kidney of the subject,
• a bladder of the subject,
• a rectum of the subject,
• a large intestine of the subject,
• a reproductive organ of the subject, and/or
• an adrenal gland of the subject.
• There is additionally provided, in accordance with a preferred embodiment of the present invention, apparatus for treating a condition of a subject, including:
• a cathode, adapted to apply to an autonomic nerve of the subject a stimulating current which is capable of inducing action potentials in the nerve; and
• a primary and a secondary anode, adapted to be disposed so that the primary anode is located between the secondary anode and the cathode, and adapted to apply to the nerve respective primary and secondary inhibiting currents which are capable of inhibiting action potentials in the nerve.
• There is yet additionally provided, in accordance with a preferred embodiment of the present invention, a method for treating a heart condition of a subject, including:
• applying, to a vagus nerve of the subject, a stimulating current which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the vagus nerve; and
• applying to the vagus nerve an inhibiting current which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.
• There is still additionally provided, in accordance with a preferred embodiment of the present invention, a method for treating a heart condition of a subject, including:
• applying, to a vagus nerve of the subject, at a stimulation location, a stimulating current which is capable of inducing action potentials in the vagus nerve, so as to treat the subject; and
• applying to the vagus nerve at a primary and a secondary location, the primary location located between the secondary location and the stimulation location, an inhibiting current which is capable of inhibiting action potentials in the vagus nerve.
• There is further provided, in accordance with a preferred embodiment of the present invention, a method for treating a heart condition of a subject, including:
• sensing an initiation physiological parameter and a termination physiological parameter of the subject;
• setting a length of a delay period responsive to the termination physiological parameter;
• initiating the delay period responsive to the initiation parameter; and
• upon completion of the delay period, applying, to a vagus nerve of the subject, a current which is capable of inducing action potentials that propagate in the vagus nerve.
• There is still further provided, in accordance with a preferred embodiment of the present invention, a method for treating a condition of a subject, including:
• applying, to an autonomic nerve of the subject, a stimulating current which is capable of inducing action potentials in a therapeutic direction in a first set and a second set of nerve fibers of the nerve; and
• applying to the nerve an inhibiting current which is capable of inhibiting the induced action potentials traveling in the therapeutic direction in the second set of nerve fibers, the nerve fibers in the second set having generally larger diameters than the nerve fibers in the first set.
• There is also provided, in accordance with a preferred embodiment of the present invention, a method for treating a condition of a subject, including:
• applying, to an autonomic nerve of the subject, at a stimulation location, a stimulating current which is capable of inducing action potentials in the nerve, so as to treat the subject; and
• applying to the nerve at a primary and a secondary location, the primary location located between the secondary location and the stimulation location, an inhibiting current which is capable of inhibiting action potentials in the nerve.
• The present invention will be more fully understood from the following detailed description of a preferred embodiment thereof, taken together with the drawings, in which:
BRIEF DESCRIPTION OF THE DRAWINGS
• FIG. 1 is a block diagram that schematically illustrates a vagal stimulation system applied to a vagus nerve of a patient, in accordance with a preferred embodiment of the present invention;
• FIG. 2A is a simplified cross-sectional illustration of a multipolar electrode device applied to a vagus nerve, in accordance with a preferred embodiment of the present invention;
• FIG. 2B is a simplified perspective illustration of the electrode device ofFIG. 2A;
• FIG. 3 is a simplified perspective illustration of a multipolar point electrode device applied to a vagus nerve, in accordance with a preferred embodiment of the present invention;
• FIG. 4 is a conceptual illustration of the application of current to a vagus nerve, in accordance with a preferred embodiment of the present invention; and
• FIG. 5 is a simplified illustration of an electrocardiogram (ECG) recording and of example timelines showing the timing of the application of a series of stimulation pulses, in accordance with a preferred embodiment of the present invention.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
• FIG. 1 is a block diagram that schematically illustrates avagal stimulation system18 comprising amultipolar electrode device40, in accordance with a preferred embodiment of the present invention.Electrode device40 is applied to a portion of avagus nerve36 that innervates aheart30 of a patient. Typically,system18 is utilized for treating a heart condition such as heart failure and/or cardiac arrhythmia.Vagal stimulation system18 further comprises an implanted orexternal control unit20, which typically communicates withelectrode device40 over a set of leads42.Control unit20 driveselectrode device40 to (i) apply signals to induce the propagation of efferent nerve impulses towardsheart30, and (ii) suppress artificially-induced afferent nerve impulses towards abrain34 of the patient, in order to minimize unintended side effects of the signal application. The efferent nerve pulses invagus nerve36 are induced byelectrode device40 in order to regulate the heart rate of the patient.
• For some applications,control unit20 is adapted to receive feedback from one or more of the electrodes inelectrode device40, and to regulate the signals applied to the electrode device responsive thereto. For example,control unit20 may analyze latencies of various peaks in a compound action potential (CAP) signal recorded by the electrodes, in order to determine a relative proportion of stimulated larger fibers (having faster conduction velocities) to smaller fibers (having slower conduction velocities). Alternatively or additionally,control unit20 analyzes an area of the CAP, in order to determine an overall effect of the stimulation. Preferably, a relationship is determined between the effect on heart rate and the recorded CAP area and/or CAP latencies, and this relationship is used by the control unit to modulate the steps described in (i) and (ii) above. In a preferred embodiment, the feedback is received by electrodes other than those used to apply signals to the nerve.
• Control unit20 is preferably adapted to receive and analyze one or more sensed physiological parameters or other parameters of the patient, such as heart rate, electrocardiogram (ECG), blood pressure, indicators of decreased cardiac contractility, cardiac output, norepinephrine concentration, or motion of the patient. In order to receive these sensed parameters,control unit20 may comprise, for example, anECG monitor24, connected to a site on the patient's body such as aheart30, and/or the control unit may comprise anaccelerometer22 for detecting motion of the patient. Alternatively, ECG monitor24 and/oraccelerometer22 comprise separate implanted devices placed external to controlunit20, and, optionally, external to the patient's body. Alternatively or additionally,control unit20 receives signals from one or morephysiological sensors26, such as blood pressure sensors.Sensors26 are preferably implanted in the patient, for example in aleft ventricle32 ofheart30. In a preferred embodiment,control unit20 comprises or is coupled to an implanteddevice25 for monitoring and correcting the heart rate, such as an implantable cardioverter defibrillator (ICD) or a pacemaker (e.g., a bi-ventricular or standard pacemaker). For example, implanteddevice25 may be incorporated into a control loop executed bycontrol unit20, in order to increase the heart rate when the heart rate for any reason is too low.
• FIG. 2A is a simplified cross-sectional illustration of a generally-cylindrical electrode device40 applied tovagus nerve36, in accordance with a preferred embodiment of the present invention.Electrode device40 comprises acentral cathode46 for applying a negative current (“cathodic current”) in order to stimulatevagus nerve36, as described below.Electrode device40 additionally comprises a set of one or more anodes44 (44a,44b, herein: “efferent anode set44”), placed betweencathode46 and the edge ofelectrode device40 closer to heart30 (the “efferent edge”). Efferent anode set44 applies a positive current (“efferent anodal current”) tovagus nerve36, for blocking action potential conduction invagus nerve36 induced by the cathodic current, as described below. Preferably,electrode device40 comprises an additional set of one or more anodes45 (45a,45b, herein: “afferent anode set45”), placed betweencathode46 and the edge ofelectrode device40 closer tobrain34. Afferent anode set45 applies a positive current (“afferent anodal current”) tovagus nerve36, in order to block propagation of action potentials in the direction of the brain during application of the cathodic current.
• Cathodes46 and anode sets44 and45 (collectively, “electrodes”) are preferably mounted in an electrically-insulatingcuff48 and separated from one another by insulating elements such asprotrusions49 of the cuff. Preferably, the width of the electrodes is between about 0.5 and about 1 millimeter, or is equal to approximately one-half the radius of the vagus nerve. Further preferably, in order to achieve generally uniform field distributions of the currents generated by the electrodes, the electrodes are recessed so as not to come in direct contact withvagus nerve36. Most preferably, the distance between the electrodes and the axis of the vagus nerve is between about 1.5 and 4 millimeters, and is greater than the closest distance from the ends of the protrusions to the axis of the vagus nerve. Preferably,protrusions49 are relatively short (as shown). Most preferably, the distance between the ends ofprotrusions49 and the center of the vagus nerve is between about 1.5 and 3 millimeters. (Generally, the radius of the vagus nerve is between about 1 and 2 millimeters.)
• Alternatively, for some applications,protrusions49 are longer and/or the electrodes are placed closer to the vagus nerve in order to reduce the energy consumption ofelectrode device40.
• In a preferred embodiment of the present invention, efferent anode set44 comprises a plurality of anodes44, typically twoanodes44aand44b, spaced approximately 0.5 to 2.0 millimeters apart. Application of the efferent anodal current in appropriate ratios from a plurality of anodes generally minimizes the “virtual cathode effect,” whereby application of too large an anodal current stimulates rather than blocks fibers. In a preferred embodiment,anode44aapplies a current with an amplitude equal to about 2 to about 5 milliamps (typically one-third) of the amplitude of the current applied byanode44b. When such techniques are not used, the virtual cathode effect generally hinders blocking of smaller-diameter fibers, as described below, because a relatively large anodal current is generally necessary to block such fibers.
• Anode44ais preferably positioned incuff48 to apply current at the location onvagus nerve36 where the virtual cathode effect is maximally generated byanode44b. For applications in which the blocking current throughanode44bis expected to vary substantially, efferent anode set44 preferably comprises a plurality of virtual-cathode-inhibitinganodes44a, one or more of which is activated at any time based on the expected magnitude and location of the virtual cathode effect.
• Likewise, afferent anode set45 preferably comprises a plurality of anodes45, typically twoanodes45aand45b, in order to minimize the virtual cathode effect in the direction of the brain. In certain electrode configurations,cathode46 comprises a plurality of cathodes in order to minimize the “virtual anode effect,” which is analogous to the virtual cathode effect.
• As appropriate, techniques described herein are practiced in conjunction with methods and apparatus described in the above-cited US patent application to Gross et al., filed on even date with the present patent application, entitled, “Electrode assembly for nerve control,” which is assigned to the assignee of the present patent application and is incorporated herein by reference. Alternatively or additionally, techniques described herein are practiced in conjunction with methods and apparatus described in U.S. Provisional Patent Application 60/383,157 to Ayal et al., filed May 23, 2002, entitled, “Inverse recruitment for autonomic nerve systems,” which is assigned to the assignee of the present patent application and is incorporated herein by reference.
• FIG. 2B is a simplified perspective illustration ofelectrode device40. When applied tovagus nerve36,electrode device40 preferably encompasses the nerve. As described,control unit20 typically driveselectrode device40 to (i) apply signals tovagus nerve36 in order to induce the propagation of efferent action potentials towardsheart30, and (ii) suppress artificially-induced afferent action potentials towardsbrain34. The electrodes preferably comprise ring electrodes adapted to apply a generally uniform current around the circumference of the nerve, as best shown inFIG. 2B.
• FIG. 3 is a simplified perspective illustration of a multipolarpoint electrode device140 applied tovagus nerve36, in accordance with a preferred embodiment of the present invention. In this embodiment,anodes144aand144band acathode146 preferably comprise point electrodes (typically 2 to 100), fixed to an insulatingcuff148 and arranged aroundvagus nerve36 so as to selectively stimulate nerve fibers according to their positions inside the nerve. In this case, techniques described in the above-cited articles by Grill et al., Goodall et al., and/or Veraart et al. are preferably used. The point electrodes preferably have a surface area between about 0.01 mm2 and 1 mm2. In some applications, the point electrodes are in contact withvagus nerve36, as shown, while in other applications the point electrodes are recessed incuff148, so as not to come in direct contact withvagus nerve36, similar to the recessed ring electrode arrangement described above with reference toFIG. 2A. For some applications, one or more of the electrodes, such ascathode146 oranode144a, comprise a ring electrode, as described with reference toFIG. 2B, such thatelectrode device140 comprises both ring electrode(s) and point electrodes. Additionally,electrode device40 optionally comprises an afferent anode set (positioned likeanodes45aand45binFIG. 2A), the anodes of which comprise point electrodes and/or ring electrodes.
• Alternatively, ordinary, non-cuff electrodes are used, such as when the electrodes are placed on the epicardial fat pads instead of on the vagus nerve.
• FIG. 4 is a conceptual illustration of the application of current tovagus nerve36 in order to achieve smaller-to-larger diameter fiber recruitment, in accordance with a preferred embodiment of the present invention. When inducing efferent action potentials towardsheart30,control unit20 driveselectrode device40 to selectively recruit nerve fibers beginning with smaller-diameter fibers and to progressively recruit larger-diameter fibers as the desired stimulation level increases. This smaller-to-larger diameter recruitment order mimics the body's natural order of recruitment.
• Preferably, in order to achieve this recruitment order, the control unit stimulates fibers essentially of all diameters using cathodic current fromcathode46, while simultaneously inhibiting fibers in a larger-to-smaller diameter order using efferent anodal current from efferent anode set44. For example,FIG. 4 illustrates the recruitment of a single,smallest nerve fiber56, without the recruitment of anylarger fibers50,52 and54. The depolarizations generated bycathode46 stimulate all of the nerve fibers shown, producing action potentials in both directions along all the nerve fibers. Efferent anode set44 generates a hyperpolarization effect sufficiently strong to block only the threelargest nerve fibers50,52 and54, but notfiber56. This blocking order of larger-to-smaller diameter fibers is achieved because larger nerve fibers are inhibited by weaker anodal currents than are smaller nerve fibers. Stronger anodal currents inhibit progressively smaller nerve fibers. When the action potentials induced bycathode46 inlarger fibers50,52 and54 reach the hyperpolarized region in the larger fibers adjacent to efferent anode set44, these action potentials are blocked. On the other hand, the action potentials induced bycathode46 insmallest fiber56 are not blocked, and continue traveling unimpeded towardheart30.Anode pole44ais shown generating less current thananode pole44bin order to minimize the virtual cathode effect in the direction of the heart, as described above.
• When desired, in order to increase the parasympathetic stimulation delivered to the heart, the number of fibers not blocked is progressively increased by decreasing the amplitude of the current applied by efferent anode set44. The action potentials induced bycathode46 in the fibers now not blocked travel unimpeded towards the heart. As a result, the parasympathetic stimulation delivered to the heart is progressively increased in a smaller-to-larger diameter fiber order, mimicking the body's natural method of increasing stimulation. In addition, for any given number of fibers stimulated (and not blocked), the amount of stimulation delivered to the heart can be increased by increasing the amplitude and/or frequency of the current applied tovagus nerve36.
• In order to suppress artificially-induced afferent action potentials from traveling towards the brain in response to the cathodic stimulation,control unit20 preferably driveselectrode device40 to inhibitfibers50,52,54 and56 using afferent anodal current from afferent anode set45. When the afferent-directed action potentials induced bycathode46 in all of the fibers reach the hyperpolarized region in all of the fibers adjacent to afferent anode set45, the action potentials are blocked. Blocking these afferent action potentials generally minimizes any unintended side effects, such as undesired or counterproductive feedback to the brain, that might be caused by these action potentials.Anode45bis shown generating less current thananode45ain order to minimize the virtual cathode effect in the direction of the brain, as described above.
• In a preferred embodiment of the present invention, stimulation of the vagus nerve is applied responsive to one or more sensed parameters.Control unit20 is preferably configured to commence or halt stimulation, or to vary the amount and/or timing of stimulation in order to achieve a desired target heart rate, typically based on configuration values and on parameters including one or more of the following:
• • Heart rate—the control unit can be configured to driveelectrode device40 to stimulate the vagus nerve only when the heart rate exceeds a certain value.
  • ECG readings—the control unit can be configured to driveelectrode device40 to stimulate the vagus nerve based on certain ECG readings, such as readings indicative of designated forms of arrhythmia. Additionally, ECG readings are preferably used for achieving a desire heart rate, as described below with reference toFIG. 5.
  • Blood pressure—the control unit can be configured to regulate the current applied byelectrode device40 to the vagus nerve when blood pressure exceeds a certain threshold or falls below a certain threshold.
  • Indicators of decreased cardiac contractility—these indicators include left ventricular pressure (LVP). When LVP and/or d(LVP)/dt exceeds a certain threshold or falls below a certain threshold,control unit20 can driveelectrode device40 to regulate the current applied byelectrode device40 to the vagus nerve.
  • Motion of the patient—the control unit can be configured to interpret motion of the patient as an indicator of increased exertion by the patient, and appropriately reduce parasympathetic stimulation of the heart in order to allow the heart to naturally increase its rate.
  • Heart rate variability—the control unit can be configured to driveelectrode device40 to stimulate the vagus nerve based on heart rate variability, which is preferably calculated based on certain ECG readings.
  • Norepinephrine concentration—the control unit can be configured to driveelectrode device40 to stimulate the vagus nerve based on norepinephrine concentration.
  • Cardiac output—the control unit can be configured to driveelectrode device40 to stimulate the vagus nerve based on cardiac output, which is preferably determined using impedance cardiography.
• The parameters and behaviors included in this list are for illustrative purposes only, and other possible parameters and/or behaviors will readily present themselves to those skilled in the art, having read the disclosure of the present patent application.
• In embodiments of the present invention in whichvagal stimulation system18 comprises implanteddevice25 for monitoring and correcting the heart rate,control unit20 preferably uses measured parameters received fromdevice25 as additional inputs for determining the level and/or type of stimulation to apply.Control unit20 preferably coordinates its behavior with the behavior ofdevice25.Control unit20 anddevice25 preferablyshare sensors26 in order to avoid redundancy in the combined system.
• Optionally,vagal stimulation system18 comprises a patient override, such as a switch that can be activated by the patient using an external magnet. The override preferably can be used by the patient to activate vagal stimulation, for example in the event of arrhythmia apparently undetected by the system, or to deactivate vagal stimulation, for example in the event of apparently undetected physical exertion.
• FIG. 5 is a simplified illustration of anECG recording70 andexample timelines72 and76 showing the timing of the application of a series ofstimulation pulses74, in accordance with a preferred embodiment of the present invention. Stimulation is preferably applied tovagus nerve36 in a closed-loop system in order to achieve and maintain the desired target heart rate, determined as described above. Precise graded slowing of the heart beat is preferably achieved by varying the number of nerve fibers stimulated, in a smaller-to-larger diameter order, and/or the intensity of vagus nerve stimulation. Stimulation with blocking, as described herein, is preferably applied during each cardiac cycle in a series ofpulses74, preferably containing between about 1 and about 20 pulses, each of about 1-3 milliseconds duration, over a period of about 1-200 milliseconds. Advantageously, such short pulse durations generally do not substantially block or interfere with the natural efferent or afferent action potentials traveling along the vagus nerve. Additionally, the number of pulses and/or their duration is sometimes varied in order to facilitate achievement of precise graded slowing of the heart beat.
• To apply the closed-loop system, preferably the target heart rate is expressed as a ventricular R-R interval (shown as the interval between R₁and R₂inFIG. 5). The actual R-R interval is measured in real time and compared with the target R-R interval. The difference between the two intervals is defined as a control error.Control unit20 calculates the change in stimulation necessary to move the actual R-R towards the target R-R, and driveselectrode device40 to apply the new calculated stimulation. Intermittently, e.g., every 1, 10, or 100 beats, measured R-R intervals or average R-R intervals are evaluated, and stimulation of the vagus nerve is modified accordingly.
• The delay before applyingpulse series74 in each cardiac cycle influences the R-R interval achieved at any given level of stimulation. This delay can be measured from a number of sensed physiological parameters (“initiation physiological parameters”), including sensed points in the cardiac cycle, including P-, Q-, R-, S- and T-waves. Preferably the delay is measured from the P-wave, which indicates atrial contraction. Alternatively, the delay is measured from the R-wave, particularly when the P-wave is not easily detected.Timeline A72 andTimeline B76 show the delays, Δt_Rand Δt_Pmeasured from R and P, respectively.
• When a closed-loop system is used with a constant Δt, a desired target R-R interval can be achieved, but a substantial R-R interval variability on a beat-to-beat basis often occurs, as described in Zhang Y et al., cited above. The techniques described herein, by varying Δt in real time (that is, using Δt as a controlled parameter), rather than using a constant Δt, generally substantially reduce this R-R interval variability.
• Preferably, Δt from either R or P is calculated in real time using a function, the inputs of which include one or more numeric parameters and one or more ECG values or other physiological values (“termination physiological parameters”) measured in real time. The termination physiological parameters determine how long the delay Δt will continue beforepulse series74 is begun. The values of the numeric parameters and which physiological inputs to use are preferably determined during a calibration procedure, as described below, or may be based on the particular heart condition and/or medical history of the patient being treated.
• For example, Δt may be measured from R or P, as shown intimeline A72 andtimeline B76, respectively, and the function may take the form of:
  Δ^t=C+K*f(R-Rinterval,P-Rinterval),
  wherein C and K are constants optimized to minimize R-R interval variability, and the R-R interval and/or P-R interval are inputs to the function. Alternatively or additionally, the function includes as inputs other ECG values and/or sensed physiological parameters, such as atrioventricular (AV) delay, blood pressure, or respiration. For some applications, the function includes other types of linear and non-linear relationships, such as exponentials or differentials.
• Typically, the function uses the R-R or P-R interval, or other sensed parameters, that were measured in the previous cardiac cycle, in order to maximize responsiveness of the function to real-time changes in heart rate. Alternatively, the interval or other sensed parameters are calculated as a running average of intervals or parameters measured during a certain number of previous heart cycles, in order to smooth the variability of Δt from beat to beat.
• In a preferred embodiment, Δt is obtained in real time from a lookup table, the inputs to which include one or more ECG or other physiological values. The lookup table is typically either populated during a calibration procedure, or with fixed values for a particular heart condition.
• To facilitate the above process, a calibration procedure is preferably performed. This procedure is typically performed by a physician for an individual patient prior to or soon after installation ofvagal stimulation system18, or, alternatively or additionally, by or on behalf of the manufacturer of the system prior to its sale. During calibration for an individual patient, the physician preferably determines suitable parameters for real-time determination of Δt by recording ECGs of the patient under different levels of heart stress while applying stimulation with a range of values of Δt.
• In a preferred embodiment,vagal stimulation system18 is further configured to apply stimulation responsive to pre-set time parameters, such as intermittently, constantly, or based on the time of day.
• Optionally, the stimulation applied byvagal stimulation system18 is applied in conjunction with or separately from stimulation of sympathetic nerves innervating the heart. Such sympathetic stimulation can be applied using techniques of smaller-to-larger diameter fiber recruitment, as described herein, or other nerve stimulation techniques known in the art.
• Alternatively or additionally, the techniques of smaller-to-larger diameter fiber recruitment and Δt control are applied in conjunction with methods and apparatus described in one or more of the patents, patent applications, articles and books cited herein.
• Although preferred embodiments of the present invention are described herein with respect to treating heart conditions, it is to be understood that the scope of the present invention includes utilizing the techniques described herein to controllably stimulate the vagus nerve to facilitate other treatments, e.g., to treat depression, epilepsy, spasticity, obesity, syncope, brain disorders, gastrointestinal tract disorders, renal disorders, pancreatic disorders, or lung disorders. In particular, the techniques described herein may be performed in combination with other techniques, which are well known in the art or which are described in the references cited herein, that stimulate the vagus nerve in order to achieve a desired therapeutic end.
• For some applications, techniques described herein are used to apply controlled stimulation to one or more of the following: the lacrimal nerve, the salivary nerve, the vagus nerve, the pelvic splanchnic nerve, or one or more sympathetic or parasympathetic autonomic nerves. Such controlled stimulation may be used, for example, to regulate or treat a condition of the lung, heart, stomach, pancreas, small intestine, liver, spleen, kidney, bladder, rectum, large intestine, reproductive organs, or adrenal gland.
• It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described hereinabove. Rather, the scope of the present invention includes both combinations and subcombinations of the various features described hereinabove, as well as variations and modifications thereof that are not in the prior art, which would occur to persons skilled in the art upon reading the foregoing description.

Claims (10)

1.-322. (canceled)

323. A method comprising:

driving a current into a nerve of a subject that modulates an aspect of sexual functioning of the subject;

configuring the current in a first mode so as to facilitate engorgement of erectile tissue of the subject; and

configuring the current in a second mode, different from the first mode, so as to facilitate an orgasmic response by the subject.

324. The method according toclaim 323, wherein the nerve includes a pelvic nerve, and wherein driving the current comprises driving the current into the pelvic nerve.

325. The method according toclaim 323, wherein driving the current comprises driving the current into a nerve of a male subject.

326. The method according toclaim 323, wherein driving the current comprises driving the current into a nerve of a female subject.

327. The method according toclaim 323, wherein driving the current comprises driving the current into a parasympathetic nerve of the subject.

328. The method according toclaim 323, wherein driving the current comprises driving the current into a sympathetic nerve of the subject.

329. A method comprising:

driving a first current into a parasympathetic nerve of the subject;

configuring the first current to induce action potentials that facilitate engorgement of erectile tissue of the subject;

driving a second current into a sympathetic nerve of the subject; and

configuring the second current to induce action potentials that facilitate an orgasmic response by the subject.

330. A method comprising:

driving a current into a sympathetic nerve of subject; and

configuring the current to induce action potentials that propagate in the nerve towards a central nervous system (CNS) of the subject, and collide with and inhibit natural action potentials propagating away from the CNS, which natural action potentials would otherwise inhibit engorgement of erectile tissue of the subject.

331. A method according toclaim 330, wherein driving the current comprises driving a first current, and comprising:

driving a second current into a parasympathetic nerve of the subject; and

configuring the current to induce action potentials that travel towards the CNS and collide with and inhibit natural action potentials propagating away from the CNS, which natural action potentials would otherwise inhibit an orgasmic response by the subject.

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