US20090149904A1

US20090149904A1 - Lv unipolar sensing or pacing vector

Info

Publication number: US20090149904A1
Application number: US12/327,567
Authority: US
Inventors: David L. Perschbacher; James O. Gilkerson; Nicholas J. Stessman
Original assignee: Cardiac Pacemakers Inc
Current assignee: Cardiac Pacemakers Inc
Priority date: 2007-12-11
Filing date: 2008-12-03
Publication date: 2009-06-11
Also published as: JP5174185B2; JP2011505965A; WO2009075820A1; US8886308B2; US20120150254A1; EP2227291B1; US8126551B2; US20090149907A1; EP2227291A1; WO2009075749A1

Abstract

An implantable medical device configured to deliver a defibrillation energy to a heart can sense a left ventricular activation using information received from a unipolar sensing or pacing vector defined between a left ventricle and an internal thoracic location external to a heart.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit under 35 U.S.C. 119(e) of U.S. Provisional Application No. 61/007,067, filed on Dec. 11, 2007, and of U.S. Provisional Application No. 61/007,634, filed on Dec. 13, 2007, each of which are hereby incorporated by reference in their entirety.

TECHNICAL FIELD

This invention relates to the field of medical devices, and more specifically to LV unipolar pacing and sensing.

BACKGROUND

Cardiac rhythm or function management devices can include implantable devices to help maintain heart rhythm or function. Cardiac rhythm or function management devices can include pacers, defibrillators, cardioverters, cardiac resynchronization therapy (CRT), or various combinations of these or other devices. In various examples, cardiac rhythm or function management devices can sense intrinsic heart contractions, deliver pacing pulses to evoke responsive heart contractions, or deliver a shock to interrupt certain arrhythmias. In certain examples, one or more of these functions can help improve a patient's heart rhythm or can help coordinate a spatial nature of a heart contraction, either of which can improve cardiac output of blood to help meet the patient's metabolic need for such cardiac output.

Overview

In certain examples, a left ventricular activation can be sensed using an implantable medical device configured to deliver a defibrillation energy to a heart. In an example, the left ventricular activation can be sensed using information received from a unipolar sensing or pacing vector defined between a left ventricle and an internal thoracic location external to a heart.
In Example 1, a system configured for sensing a left ventricular activation while avoiding oversensing a right ventricular activation or avoiding sensing a cardiac event other than a left ventricular activation includes an implantable medical device and a processor. The implantable medical device can be include a first sensing channel configured to receive information from a left ventricle, and a second sensing channel configured to receive information from an internal thoracic location external to a heart, wherein the implantable medical device is configured to deliver a defibrillation energy to the heart. The processor can be configured to receive information from the first and second sensing channels, wherein the left ventricle and the internal thoracic location external to the heart define a unipolar sensing or pacing vector, and wherein the processor is configured to sense a left ventricular activation using the received information from the first and second sensing channels.
In Example 2, the first sensing channel of Example 1 is optionally configured to electrically couple the left ventricle to the processor, and the second sensing channel is configured to electrically couple the internal thoracic location external to the heart to the processor.
In Example 3, the implantable medical device of any one or more of Examples 1-2 is optionally configured to deliver the defibrillation energy to the heart using the sensed left ventricular activation.
In Example 4, the processor of any one or more of Examples 1-3 is optionally configured to inhibit energy delivery to the left ventricle using the sensed left ventricular activation.
In Example 5, the implantable medical device of any one or more of Examples 1-4 optionally includes a housing, wherein at least a portion of the housing includes a conductor, and wherein the housing is configured to receive information from the internal thoracic location external to the heart.
In Example 6, the system of any one or more of Examples 1-5 optionally includes a lead coupled to the first sensing channel, wherein the lead includes an electrode configured to be coupled to and receive information from the left ventricle.
In Example 7, the unipolar sensing or pacing vector of any one or more of Examples 1-6 is optionally defined only between the left ventricle and the internal thoracic location external to the heart.
In Example 8, the implantable medical device of any one or more of Examples 1-7 is optionally configured to provide a stimulation energy to the heart using the unipolar sensing or pacing vector.
In Example 9, a method for sensing a left ventricular activation while avoiding oversensing a right ventricular activation or avoiding sensing a cardiac event other than a left ventricular activation includes receiving information from a left ventricle and an internal thoracic location external to a heart using an implantable medical device, wherein the left ventricle and the internal thoracic location external to the heart define a unipolar sensing or pacing vector, sensing a left ventricular activation using the received information to avoid oversensing a right ventricular activation or to avoid sensing a cardiac event other than a left ventricular activation, and wherein the implantable medical device is configured to deliver a defibrillation energy to the heart.
In Example 10, the method of Example 9 optionally includes delivering the defibrillation energy to the heart using the sensed left ventricular activation.
In Example 11, the method of any one or more of Examples 9-10 optionally includes inhibiting energy delivery to the left ventricle using the sensed left ventricular activation.
In Example 12, the receiving the information from the internal thoracic location external to the heart of any one or more of Examples 9-11 optionally includes receiving information from a housing can electrode.
In Example 13, the receiving the information from left ventricle of any one or more of Examples 9-12 optionally includes receiving information from an electrode located proximate to the left ventricle.
In Example 14, the method of any one or more of Examples 9-13 optionally includes providing a stimulation energy to the heart using the unipolar sensing or pacing vector.
In Example 15, the method of any one or more of Examples 9-14 optionally includes providing an implantable medical device including a housing can electrode, a first lead including a proximal defibrillation coil electrode and a distal defibrillation coil electrode coupled to the implantable medical device, and a second lead including a distal pacing or sensing electrode coupled to the implantable medical device, wherein the housing can electrode is electrically uncoupled from the proximal defibrillation coil electrode, using the first lead such that the proximal defibrillation coil is located in the right atrium or the superior vena cava and the distal defibrillation coil electrode is located in the right ventricle, using the second lead such that the distal pacing or sensing electrode is located in the coronary vasculature proximate to the left ventricle, and unipolarly sensing a left ventricular activation between the distal pacing or sensing electrode and the housing can electrode.
In Example 16, the method of any one or more of Examples 9-15 optionally includes delivering a defibrillation shock between the housing can electrode, the proximal defibrillation coil electrode, and the distal defibrillation coil electrode, wherein the housing can electrode is electrically coupled to the proximal defibrillation coil electrode.
In Example 17, an apparatus includes an implantable medical device including a housing can electrode, a proximal defibrillation coil electrode operatively coupled to the implantable medical device, and a distal pacing or sensing electrode operatively coupled to the implantable medical device, wherein the housing can electrode is electrically uncoupled from the proximal defibrillation coil electrode such that unipolar sensing is performed between the distal pacing or sensing electrode and the housing can electrode.
In Example 18, the proximal defibrillation coil electrode of Example 17 is optionally disposed along a first lead, and wherein the distal pacing or sensing electrode of Example 17 is optionally disposed on a second lead.
In Example 19, the first lead of any one or more of Examples 17-18 is optionally configured such that the proximal defibrillation coil is implantable within the right atrium or the superior vena cava, and wherein the second lead is configured such that the distal pacing or sensing electrode is implantable within the coronary vasculature.
In Example 20, the unipolar sensing of any one or more of Examples 17-19 is optionally performed between only distal pacing or sensing electrode and the housing can electrode.
This overview is intended to provide an overview of subject matter of the present patent application. It is not intended to provide an exclusive or exhaustive explanation of the invention. The detailed description is included to provide further information about the present patent application.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings, which are not necessarily drawn to scale, like numerals may describe similar components in different views. Like numerals having different letter suffixes may represent different instances of similar components. The drawings illustrate generally, by way of example, but not by way of limitation, various embodiments discussed in the present document.

FIGS. 1, 2, and 5 illustrate generally examples of systems or portions of a system for delivering cardiac therapy.

FIG. 3 illustrates generally an example of a state diagram illustrating switching between a normal AV delay, a first extended AV delay, and a second extended AV delay.

FIG. 4 illustrates generally an example of a timing diagram illustrating a relationship between a maximum tracking rate (MTR) (or upper rate limit (URL)), a post ventricular atrial refractory period (PVARP), and an AV delay.

DETAILED DESCRIPTION

Generally, dual chamber pacing includes pacing where energy is delivered to both the atrium and the ventricle. The atrioventricular (AV) delay interval, as used herein, refers to the interval between an atrial event (e.g., an atrial pace or an atrial sense, usually the right atrium) and a first ventricular pace to one of the ventricles (e.g., a right ventricle). The AV delay interval can be the same or different depending upon whether it is initiated by an atrial sense or an atrial pace (e.g., in atrial tracking mode or AV sequential pacing mode, respectively). Bi-ventricular pacing includes pacing both the left ventricle and the right ventricle. The biventricular offset (BVO) interval, as used herein, refers to the interval between the first ventricular pace and a second ventricular pace to the other ventricle (e.g., the left ventricle) during the same cardiac cycle. One approach to bi-ventricular pacing includes specifying an AV delay interval and a BVO interval. Another approach to bi-ventricular pacing includes specifying a separate AV delay interval for each ventricle, which can be designated as AVDR for the right ventricle and AVDL for the left ventricle. Generally, for subjects having intact or normally functioning AV conduction pathways, the later-paced ventricle will be paced, if at all, close to the time at which that ventricle is intrinsically activated, such as to achieve an optimal or desired preloading. In subjects having normal AV conduction, the optimal or desired AVD and BVO intervals can be related to both the intrinsic atrioventricular interval and the amount of pre-excitation time needed for one ventricle relative to the other (e.g., the extent of the ventricular conduction deficit).
Generally, a cardiac rhythm or function management device can be configured to sense or detect one or more type of cardiac arrhythmia, such as an atrial or ventricular fibrillation or tachycardia. In certain examples, using shocking electrodes in one or more configurations, an implantable medical device can be configured to deliver a defibrillation energy configured to depolarize a critical mass of a heart, terminate the cardiac arrhythmia, and allow a normal sinus rhythm to be reestablished.
In certain examples, the implantable medical device can include an implantable defibrillator, or an implantable pacemaker or other cardiac rhythm or unction management device having a defibrillation backup or other defibrillation energy delivery mode.
FIG. 1 illustrates generally an example of a system 100 for delivering cardiac therapy. In an example, the system 100 can include an implantable medical device (IMD) 5 having a processor 50, a right ventricular sensing channel 10, a right ventricular pacing channel 20, a left ventricular sensing channel 30, a left ventricular pacing channel 40, and an atrial sensing channel 60. The atrial sensing channel 60 can include at least one of a right atrial sensing channel or a left atrial sensing channel. In other examples, the IMD 5 can include a combination of at least one of the a right ventricular sensing channel 10, the right ventricular pacing channel 20, the left ventricular sensing channel 30, the left ventricular pacing channel 40, or the atrial sensing channel 60.
In certain examples, the right ventricular sensing channel 10 can include a sense amplifier 11, the left ventricular sensing channel 30 can include a sense amplifier 31, the right ventricle pacing channel 20 can include a pulse generator 21, the left ventricular pacing channel 40 can include a pulse generator 41, and the atrial sensing channel 60 can include a sense amplifier 61. In other examples, the right ventricular sensing channel 10 or the right ventricular pacing channel 20 can be coupled to an electrode 16 disposed on a lead 15 or elsewhere, the left ventricular sensing channel 30 or the left ventricular pacing channels 40 can be coupled to an electrode 36 disposed on a lead 35 or elsewhere, or the atrial sensing channel 60 can be coupled to an electrode 66 disposed on a lead 65 or elsewhere.
In certain examples, the lead 15 can be configured to electrically couple the sense amplifier 11 or the pulse generator 21 to the electrode 16, which can be configured to be located in a right ventricle, such as in the septal region, the free wall region, or another region of the right ventricle. Similarly, the lead 35 can be configured to electrically couple the sense amplifier 31 or the pulse generator 41 to the electrode 36, which can be configured to be located in, on, or near a left ventricle, such as in the septal region, the free wall region, or another region of the left ventricle or in the coronary vasculature. Further, the lead 65 can be configured to electrically couple the sense amplifier 61 to the electrode 66, which can be configured to be located in at least one of a right atrium or a left atrium of the subject 101.
In certain examples, the implantable medical device 5 can include one or more other pacing or sensing channels, such as an internal thoracic pacing or sensing channel configured to couple the processor 50 to an internal thoracic location external to the heart (e.g., through one or more leads, electrodes, pulse generators, or sense amplifiers). In an example, the internal thoracic pacing or sensing channel can be configured to send or receive information to or from a housing can electrode, located on the exterior housing of an implantable medical device located in the internal thoracic location external to the heart.
In the example of FIG. 1, the processor 50 can be an implantable component, an external component, or a combination or permutation of an implantable processor and an external processor. In an example, if at least a portion of the processor 50 includes an external processor, then the processor 50 can be configured to be communicatively coupled (such as via telemetry, RF, or other communication protocol) with the remaining implantable components (such as the sense amplifier 11, 31, the pulse generator 21, 41, the lead 15, 35, or the electrode 16, 36). In an example, the implantable processor can be configured to have reduced or minimal functionality or power consumption. In certain examples, it can be advantageous for the processor 50 to include an external processor for computing complex operations, such as to compute an AV delay interval. In other examples, the external processor can include an external device that can be either local or remote. In an example, the processor 50 can include a microcontroller, a microprocessor, a logic circuit, or other processor.
FIG. 2 illustrates generally an example of a portion of a system 200 including an IMD 5 configured to be implanted in a subject 101. The system 200 can include at least one of a local programmer 70 or a remote programmer 75. Both the local programmer 70 and the remote programmer 75 are external components. In an example, the local programmer 70 can include a hand-held programmer or other programmer capable of being positioned in communication proximity to the processor 50. The proximity range between the processor 50 and the local programmer 70 can vary depending upon the type of data communication and is bound by the physical constraints of the communication type. In an example, the remote programmer 75 can include any programmer configured to communicate with the IMD 5 either directly or indirectly (such as through another device, e.g., a router, the local programmer 70, etc.). In various examples, the remote programmer 75 can be configured to communicate with or store information from a plurality of implanted or external devices, and the remote programmer 75 can be configured to be located a long distance from the subject 1.
In an example, the local programmer 70 or the remote programmer 75 can be configured to send information to or receive information from the IMD 5. The information can include programming information, subject data, device data, or other instructions, alerts, or other information. Further, the local programmer 70 or the remote programmer 75 can be configured to communicate the sent or received information to a user or physician, such as by sending an alert via email of the status of the subject 1 or the system components.

Extended AV Delay

FIG. 3 illustrates generally an example of a state diagram 300 illustrating switching between a first AV delay 305, a first extended AV delay 310, and a second extended AV delay 315. Pacing a heart using the first extended AV delay 310 or the second AV extended delay 315 can allow the heart to regain intrinsic control of ventricular activations below the first extended AV delay 310 or the second extended AV delay 315. In certain examples, the first AV delay 305 can include a fixed interval, e.g., an AV delay interval established by a clinician or a device using physiological data of the subject. In certain examples, the first AV delay 305 can include a dynamic interval, e.g., an AV delay interval established, updated, or otherwise modulated using physiological data from the subject 1.
In certain examples, the first AV delay 305 can be calculated as an optimal AV delay, such as disclosed in the commonly assigned Ding et al. U.S. Pat. No. 7,013,176 entitled, “METHOD AND APPARATUS FOR SETTING PACING PARAMETERS IN CARDIAC RESYNCHRONIZATION THERAPY,” (herein “the Ding et al. '176 patent”) the commonly assigned Ding et al. U.S. Pat. No. 7,203,540 entitled, “METHOD AND SYSTEM FOR SETTING CARDIAC RESYNCHRONIZATION THERAPY PARAMETERS,” (herein “the Ding et al. '540 patent”) or the commonly assigned Ding et al. U.S. Pat. No. 7,123,960 entitled, “METHOD AND SYSTEM FOR DELIVERING CARDIAC RESYNCHRONIZATION THERAPY WITH VARIABLE ATRIO-VENTRICULAR DELAY,” (herein “the Ding et al. '960 patent”) the disclosures of which are each incorporated by reference in their entirety, including their disclosure of computing an optimal AV delay interval. In other examples, other techniques of calculating the first AV delay interval can be used.
In the example of FIG. 3, the first extended AV delay 310 and the second extended AV delay 315 can include fixed values. In an example, the first extended AV delay 310 or the second extended AV delay 315 can be established by a clinician. In various examples, the first extended AV delay 310 can be established as the same value or a different value as the second extended AV delay 315. The present inventors have recognized, among other things, that a fixed-value extended AV delay interval can provide a simple, low power, well-defined, recognizable extended AV delay interval (e.g., in contrast to a dynamic extended AV delay). In certain examples, the extended AV delay interval can be fixed at a value that would violate certain conditions placed on other non-fixed-value AV delay calculations. For example, a clinician may not recognize a value or an occurrence of an extended AV delay interval that is established as a function of a normal AV delay interval. Moreover, establishing the extended AV delay interval as a function of the normal AV delay interval requires processing power, and the resulting extended AV delay interval can be bound by certain conditions. However, by fixing the first extended AV delay 310 or the second extended AV interval 315, the clinician can more easily recognize an occurrence of an extended AV delay interval at the fixed value. In certain examples, the fixed-value extended AV delay interval can be established using less processing power. The fixed-value extended AV delay interval can also be permitted to violate certain constraints that are sometimes imposed on variable-value extended AV delay intervals. In an example, the clinician can specify the fixed-value of the first extended AV delay 310 or the second extended AV delay 315 such that one or both intervals can exceed the normal boundary established by the MTR and the post ventricular atrial refractory period (PVARP), the relationship of which shown in FIG. 4.
In an example, the first AV delay 305 transitions to the extended AV delay 310 after a first condition 306 is satisfied, such as after the occurrence of a cardiac cycles. The a cardiac cycles can include a fixed, pre-determined, or otherwise established number of cardiac cycles, e.g., 32 cardiac cycles, 64 cardiac cycles, etc. Establishing a regular fixed entry condition to the first extended AV delay 310, such as every a cardiac cycles or one or more other regular conditions (e.g., a specified time interval, etc.), can allow for a regular chance to cease ventricular pacing and allow the heart to regain intrinsic control of ventricular activations. Other entry conditions into an extended AV delay can include the occurrence of one or more intrinsic activations occurring within the first AV delay 305, which can establish irregular or infrequent chances to cease ventricular pacing and allow for the heart to regain intrinsic control of ventricular activations. Using the regular fixed entry condition (e.g., a cardiac cycles) can provide for a more regularly engaged or more robust transition from the first AV delay 305 to the first extended AV delay 310. In certain examples, the first condition 306 can include the occurrence of consecutive intrinsic activations, or the first condition 306 can include the occurrence of non-consecutive intrinsic activations in a specified number of cardiac cycles (e.g., 2 intrinsic activations in three cardiac cycles, etc.).
In certain examples, the first extended AV delay 310 can transition back to the first AV delay 305 or transition to the second extended AV delay 315. In an example, the first extended AV delay 310 can transition back to first AV delay 305 after a third condition 311 is satisfied, such as b ventricular paces in the first extended AV delay 310. The b ventricular paces can include a fixed, pre-determined, or otherwise established number of ventricular paces, e.g., 4, 8, 16, etc. In certain examples, the b ventricular paces can include consecutive ventricular paces. However, in other examples, the b ventricular paces can include non-consecutive ventricular paces, for example, to provide a more robust exit condition. The ventricular paces can include sensed ventricular paces. In this example, the third condition 311 can include a number of b ventricular paces higher than 1, and in certain examples, a significant amount of ventricular paces higher than 1 (e.g., 4, 8, 16, etc.). In an example, the third condition 311 can allow for the heart to incrementally regain intrinsic control by a more robust exit criteria from the first extended AV delay 310, for example, as opposed to requiring consecutive ventricular senses to enter or remain at an extended AV delay.
In another example, the first extended AV delay 310 can transition to the second extended AV delay 315 after a second condition 312 is satisfied, such as a ventricular sensed activation. The ventricular sensed activation can include a specified number of ventricular sensed activations (e.g., one or more consecutive or non-consecutive ventricular sensed activations) occurring before the b ventricular paces is satisfied. In certain examples, because the b ventricular paces can include a number of ventricular paces higher than 1, and because the b ventricular paces can be non-consecutive, the second condition 312 can provide a more robust entry criteria to the second extended AV delay 315, for example, as opposed to requiring consecutive ventricular senses to enter the second extended AV delay 315.
The entry condition for the transition from the first extended AV delay 310 to the first AV delay 305 can be more stringent than for the transition from the second extended AV delay 315 to the first AV delay 305. This can encourage a tendency to remain in the second extended AV delay 315, which, in turn, can allow the heart more opportunity to intrinsically control the ventricular activations. In an example, the second extended AV delay 315 can transition to the first AV delay 305 after a fourth condition 316 is satisfied, such as the occurrence of c ventricular paces in d cardiac cycles. The c ventricular paces in d cardiac cycles can include a fixed, predetermined, or otherwise established number of ventricular paces out of a fixed, predetermined, or otherwise established number of cardiac cycles (d), e.g., 2 ventricular paces out of the last 10 cardiac cycles (2 ventricular paces/10 cardiac cycles, etc.). In certain examples, the c ventricular paces can include consecutive ventricular paces. However, in other examples, the c ventricular paces can include non-consecutive ventricular paces, for example, to provide a more robust exit condition. Like above with respect to the second condition 312 and the third condition 311, in certain examples, the fourth condition 316 can provide a more robust exit criteria from the second extended AV delay 315 to the first AV delay 305, for example, by not requiring consecutive ventricular senses or paces.
FIG. 4 illustrates generally an example of a timing diagram 400 illustrating a relationship between a maximum tracking rate (MTR) (or upper rate limit (URL)), a post ventricular atrial refractory period (PVARP), and an AV delay. The MTR is a maximum pacing rate determined by a clinician or calculated using physiological data of the subject 1. The PVARP is an interval following a ventricular event during which atrial-like events (e.g., retrograde P waves, far-field R waves, premature atrial contractions, etc.) are ignored for the purposes of beginning an AV delay. The timing diagram 400 includes a MTR beginning with a ventricular event and ending with a ventricular pace. The ventricular event can include a ventricular pace or a ventricular sensed activation. If a ventricular sensed activation does not occur following a ventricular event of the previous cardiac cycle during a pre-set or otherwise established interval, such as the MTR, then the ventricle is paced. Thus, absent a ventricular sensed activation, the MTR is the time between a ventricular event of a first cardiac cycle and a ventricular pace of a second cardiac cycle. Generally, the AV delay (e.g., the first AV delay 305 or the extended AV delay 310, 315) is constrained by the relationship between the MTR and the PVARP (e.g., AV≦MTR−PVARP).
In an example, the first AV delay 305 adheres to this relationship. However, in other examples, a clinician can violate this relationship by fixing the first extended AV delay 310 or the second extended AV delay 315 to be beyond the given relationship.
LV Unipolar Sensing or Pacing Vector In an example, an AV delay can be calculated using an intrinsic atrioventricular interval AVR (the interval between an intrinsic atrial activation and an intrinsic right ventricular activation) or an intrinsic atrioventricular interval AVL, (the interval between an intrinsic atrial activation and an intrinsic left ventricular activation), such as is disclosed in the above-incorporated Ding et al.'176 patent, the above-incorporated Ding et al. '540 patent, or the above-incorporated Ding et al. '960 patent.
In certain examples, the intrinsic atrial activation can be sensed using the electrode 66 coupled to the atrial sensing channel 60 of the IMD 5, the intrinsic left ventricular activation can be sensed using the electrode 36 coupled to the LV sensing channel 30 of the IMD 5, or the intrinsic right ventricular activation can be sensed using the electrode 16 coupled to the RV sensing channel 10 of the IMD 5. In an example, the processor 50 can be configured to compute the AVR or the AVL using at least one of the sensed intrinsic atrial activation, the sensed intrinsic right ventricular activation, or the sensed intrinsic left ventricular activation.
FIG. 5 illustrates generally an example of portions of a system 500 including an IMD 5, an RV lead 15, an LV lead 35, an atrial lead 65, and a heart 555. The IMD 5 can include a housing 506 (or CAN), and a header 507. In an example, at least a portion of the exterior of the housing 506 can include an electrode, herein referred to as the housing can electrode.
The RV lead 15 can include a first electrode 16 a configured to be located in the superior vena cava 575 of the heart 555, and a second electrode 16 b, a third electrode 16 b, and a fourth electrode 16 d configured to be located in the right ventricle 560 of the heart 555. In an example, one or more electrodes, such as the first electrode 16 a or the second electrode 16 b, can include a shocking coil electrode configured to deliver a high energy shock (e.g., 0.1 Joule or greater, etc.) to the heart. In certain examples, the first electrode 16 a can include a proximal defibrillation coil electrode and the second electrode 16 b can include a distal defibrillation coil electrode.
The LV lead 35 can include a fifth electrode 36 a and a sixth electrode 36 b configured to be located in, on, or near the left ventricle 565 of the heart 555, such as within the coronary vasculature. In an example, the sixth electrode 36 b can include a distal pacing or sensing electrode. The atrial lead 65 can include a seventh electrode 66 a and an eighth electrode 66 b configured to be located in the right atrium 570 of the heart 555. In certain examples, the housing can electrode can be electrically coupled to at least one other electrode (e.g., the first electrode 16 a), or the housing can electrode can be electrically isolated from other electrodes and capable of independent control. Further, in certain examples, the first electrode 16 a through the eighth electrode 66 b can include at least one of a coil-type electrode, a ring-type electrode, or a tip electrode.
In certain examples, the RV lead 15 can be configured to electrically couple the IMD 5 to at least one of the right ventricle 560, the right atrium 570, or the superior vena cava 575 using at least one electrode (e.g., the first electrode 16 a, the second electrode 16 b, the third electrode 16 c, or the fourth electrode 16 d), the LV lead 35 can be configured to electrically couple the IMD 5 to the left ventricle 565 using at least one electrode (e.g., the fifth electrode 36 a or the sixth electrode 36 b), or the atrial lead 65 can be configured to electrically couple the IMD 5 to the right ventricle 570 using at least one electrode (e.g., the seventh electrode 66 a or the eighth electrode 66 b). In an example, at least one of the second electrode 16 b, the third electrode 16 c, or the fourth electrode 16, can be configured to be located in, on, or near a right apical region of the heart 555. In other examples, the fifth electrode 36 a or the sixth electrode 36 b can be configured to be located in, on, or near a left apical region of the heart 555 or a left ventricular free lateral wall of the heart 555.
In an example, the left ventricular activation can be sensed, such as to calculate an AV delay interval or other pacing interval or parameter, or for other desired purpose in cardiac function management, such as cardiac arrhythmia detection. The left ventricular activation can be sensed using a sensing vector defined by the particular electrodes used for performing the sensing. In certain examples, the sensing vector can include a bipolar sensing vector 580, the bipolar sensing vector 580 including a sensing vector between a left ventricular tip electrode, such as the sixth electrode 36 b, and a left ventricular ring electrode, such as the fifth electrode 36 a, or an extended bipolar sensing vector 581, the extended bipolar sensing vector 581 including a sensing vector between a left ventricular tip electrode, such as the sixth electrode 36 b, and a right ventricular distal electrode, such as the second electrode 16 b or the third electrode 16 c. However, the present inventors have recognized, among other things, that sensing the left ventricular activation using the bipolar sensing vector 580 or extended bipolar sensing vector 581 can potentially lead to oversensing the right ventricular activation, or more generally, sensing something other than the left ventricular activation. Moreover, the present inventors have recognized, among other things, that it can be difficult or impossible to determine if oversensing is occurring in various implantable systems (e.g., due to differences in available sensing vectors, etc.). Thus, to avoid the oversensing or the uncertainty of using the bipolar sensing vector 580 or the extended bipolar sensing vector 581, the left ventricular activation can be sensed using a unipolar sensing vector 582, the unipolar sensing vector 582 including a vector between a left ventricular electrode, such as the fifth electrode 36 a or the sixth electrode 36 b, and a housing can electrode. In other examples, the one or more other sensing vectors can be defined using one or more right atrial electrodes, one or more right ventricular electrodes, or one or more other electrodes, and a housing can electrode, creating a right atrium to housing can unipolar sensing vector, a right ventricle to housing can unipolar sensing vector, or one or more other unipolar sensing vectors.
In certain examples, a cardiac rhythm management device capable of delivering a defibrillation energy can include a shocking electrode, such as the first electrode 16 a, electrically tied or coupled to the housing can electrode. In this example, having the housing can electrode electrically tied or coupled to one or more other electrodes can eliminate the possibility of using the unipolar sensing vector 582 due to the added vector between the left ventricular electrode and the shocking electrode.
In an example, the IMD 5 can automatically switch to using the unipolar sensing vector 582 to detect, sense, measure, or calculate a left ventricular activation, e.g., to calculate the AV delay interval or other pacing intervals or parameters, or for other cardiac function management purpose, such as to avoid the oversensing or the uncertainty of using the bipolar sensing vector 580 or the extended bipolar sensing vector 581. However, when a defibrillation energy is desired, the IMD 5 can be configured to electrically or mechanically couple the first electrode 15 or one or more other electrode to the housing can electrode to deliver a defibrillation energy to the heart.
In other examples, a pacing or other stimulation energy can be delivered using the unipolar sensing vector 582 or one or more other unipolar sensing vectors (e.g., right ventricle to housing can unipolar vector, etc.).
In an example, if a right ventricular electrode fails, such as a right ventricular ring electrode, then a right ventricle to housing can unipolar vector (e.g., using a right ventricular tip electrode and the housing can electrode) can be used, for example, in to sense a right ventricular activation in place of using the failed electrode in conjunction with one or more other electrodes.
In certain examples, an atrial lead can have a lower cost than a ventricular lead. In an example, a right atrium to housing can unipolar vector can be used, for example, to reduce the overall cost of the system, or in place of a failed left ventricular or other electrode.

Additional Notes

The above detailed description includes references to the accompanying drawings, which form a part of the detailed description. The drawings show, by way of illustration, specific embodiments in which the invention can be practiced. These embodiments are also referred to herein as “examples.” Such examples can include elements in addition to those shown and described. However, the present inventors also contemplate examples in which only those elements shown and described are provided.
All publications, patents, and patent documents referred to in this document are incorporated by reference herein in their entirety, as though individually incorporated by reference. In the event of inconsistent usages between this document and those documents so incorporated by reference, the usage in the incorporated reference(s) should be considered supplementary to that of this document; for irreconcilable inconsistencies, the usage in this document controls.
In this document, the terms “a” or “an” are used, as is common in patent documents, to include one or more than one, independent of any other instances or usages of “at least one” or “one or more.” In this document, the term “or” is used to refer to a nonexclusive or, such that “A or B” includes “A but not B,” “B but not A,” and “A and B,” unless otherwise indicated. In the appended claims, the terms “including” and “in which” are used as the plain-English equivalents of the respective terms “comprising” and “wherein.” Also, in the following claims, the terms “including” and “comprising” are open-ended, that is, a system, device, article, or process that includes elements in addition to those listed after such a term in a claim are still deemed to fall within the scope of that claim. Moreover, in the following claims, the terms “first,” “second,” and “third,” etc. are used merely as labels, and are not intended to impose numerical requirements on their objects.
The above description is intended to be illustrative, and not restrictive. For example, the above-described examples (or one or more aspects thereof) may be used in combination with each other. Other embodiments can be used, such as by one of ordinary skill in the art upon reviewing the above description. The Abstract is provided to comply with 37 C.F.R. §1.72(b), to allow the reader to quickly ascertain the nature of the technical disclosure. It is submitted with the understanding that it will not be used to interpret or limit the scope or meaning of the claims. Also, in the above Detailed Description, various features may be grouped together to streamline the disclosure. This should not be interpreted as intending that an unclaimed disclosed feature is essential to any claim. Rather, inventive subject matter may lie in less than all features of a particular disclosed embodiment. Thus, the following claims are hereby incorporated into the Detailed Description, with each claim standing on its own as a separate embodiment. The scope of the invention should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.

Claims

1. A system configured for sensing a left ventricular activation while avoiding oversensing a right ventricular activation or avoiding sensing a cardiac event other than a left ventricular activation, the system comprising:

an implantable medical device including:

a first sensing channel configured to receive information from a left ventricle;

a second sensing channel configured to receive information from an internal thoracic location external to a heart; and

wherein the implantable medical device is configured to deliver a defibrillation energy to the heart; and

a processor configured to receive information from the first and second sensing channels, wherein the left ventricle and the internal thoracic location external to the heart define a unipolar sensing or pacing vector, and wherein the processor is configured to sense a left ventricular activation using the received information from the first and second sensing channels.

2. The system of claim 1, wherein the first sensing channel is configured to electrically couple the left ventricle to the processor, and the second sensing channel is configured to electrically couple the internal thoracic location external to the heart to the processor.

3. The system of claim 1, wherein the implantable medical device is configured to deliver the defibrillation energy to the heart using the sensed left ventricular activation.

4. The system of claim 1, wherein the processor is configured to inhibit energy delivery to the left ventricle using the sensed left ventricular activation.

5. The system of claim 1, wherein the implantable medical device includes a housing, wherein at least a portion of the housing includes a conductor, and wherein the housing is configured to receive information from the internal thoracic location external to the heart.

6. The system of claim 1, including a lead coupled to the first sensing channel, wherein the lead includes an electrode configured to be coupled to and receive information from the left ventricle.

7. The system of claim 1, wherein the unipolar sensing or pacing vector is defined only between the left ventricle and the internal thoracic location external to the heart.

8. The system of claim 1, wherein the implantable medical device is configured to provide a stimulation energy to the heart using the unipolar sensing or pacing vector.

9. A method for sensing a left ventricular activation while avoiding oversensing a right ventricular activation or avoiding sensing a cardiac event other than a left ventricular activation, the method comprising:

receiving information from a left ventricle and an internal thoracic location external to a heart using an implantable medical device, wherein the left ventricle and the internal thoracic location external to the heart define a unipolar sensing or pacing vector;

sensing a left ventricular activation using the received information to avoid oversensing a right ventricular activation or to avoid sensing a cardiac event other than a left ventricular activation; and

wherein the implantable medical device is configured to deliver a defibrillation energy to the heart.

10. The method of claim 9, including delivering the defibrillation energy to the heart using the sensed left ventricular activation.

11. The method of claim 9, including inhibiting energy delivery to the left ventricle using the sensed left ventricular activation.

12. The method of claim 9, wherein the receiving the information from the internal thoracic location external to the heart includes receiving information from a housing can electrode.

13. The method of claim 9, wherein the receiving the information from left ventricle includes receiving information from an electrode located proximate to the left ventricle.

14. The method of claim 9, including providing a stimulation energy to the heart using the unipolar sensing or pacing vector.

15. The method of claim 9, including:

providing an implantable medical device including a housing can electrode, a first lead including a proximal defibrillation coil electrode and a distal defibrillation coil electrode coupled to the implantable medical device, and a second lead including a distal pacing or sensing electrode coupled to the implantable medical device, wherein the housing can electrode is electrically uncoupled from the proximal defibrillation coil electrode;

using the first lead such that the proximal defibrillation coil is located in the right atrium or the superior vena cava and the distal defibrillation coil electrode is located in the right ventricle;

using the second lead such that the distal pacing or sensing electrode is located in the coronary vasculature proximate to the left ventricle; and

unipolarly sensing a left ventricular activation between the distal pacing or sensing electrode and the housing can electrode.

16. The method of claim 15, including delivering a defibrillation shock between the housing can electrode, the proximal defibrillation coil electrode, and the distal defibrillation coil electrode, wherein the housing can electrode is electrically coupled to the proximal defibrillation coil electrode.

17. An apparatus comprising:

an implantable medical device including a housing can electrode;

a proximal defibrillation coil electrode operatively coupled to the implantable medical device;

a distal pacing or sensing electrode operatively coupled to the implantable medical device; and

wherein the housing can electrode is electrically uncoupled from the proximal defibrillation coil electrode such that unipolar sensing is performed between the distal pacing or sensing electrode and the housing can electrode.

18. The apparatus of claim 17, wherein the proximal defibrillation coil electrode is disposed along a first lead, and wherein the distal pacing or sensing electrode is disposed on a second lead.

19. The apparatus of claim 17, wherein the first lead is configured such that the proximal defibrillation coil is implantable within the right atrium or the superior vena cava, and wherein the second lead is configured such that the distal pacing or sensing electrode is implantable within the coronary vasculature.

20. The apparatus of claim 17, wherein the unipolar sensing is performed between only distal pacing or sensing electrode and the housing can electrode.