Patent Grant
12172021
The techniques, methods, and processes of this disclosure generally relate to implantable medical devices, systems, and methods for ventricle-from-atrium (VfA) cardiac resynchronization therapy (CRT). Additionally, techniques, methods, and processes of this disclosure may be applied, or used with, cardiac therapy, including single chamber or multiple chamber pacing (e.g., dual or triple chamber pacing), atrioventricular synchronous pacing, asynchronous pacing, triggered pacing, or tachycardia-related therapy.
A VfA device may be implanted in the right atrium (RA) with a tissue-piercing electrode extending from the right atrium into the left ventricular myocardium. The tissue-piercing electrode may be used to deliver pacing therapy to the left ventricular for various cardiac therapies. To determine whether the pacing has captured the left ventricle and/or whether the pacing is effective, electrical activity may be measured, or other physiological response measurements may be taken, following a left ventricular pace. The electrical activity and other physiological response measurements may be evaluated (e.g., compared to various thresholds, etc.) to determine whether the pacing therapy has effectively captured the left ventricle.
Additionally, if the ventricular pacing therapy is determined to be ineffective or not having captured the left ventricle, the ventricular pacing therapy may be adjusted until the ventricular pacing therapy is made to be effectively capturing the left ventricle. For example, one or more paced settings may be adjusted, or modified, and the electrical activity or other physiological information may be monitored. The monitored electrical activity or other physiological information may again be evaluated to determine whether the ventricular pacing therapy has now effectively captured the left ventricle. For example, the atrioventricular (A-V) pacing delay may be adjusted until left ventricular capture is determined. Advantageously, in one or more embodiments, the techniques of this disclosure may be used to calibrate or deliver more optimal pacing therapy without using monitored electrical activity of the right ventricle of the patient's heart.
In other words, this disclosure describes methods of monitoring effectiveness of ventricular capture and modifying one or more therapy parameters in context of a leadless VfA pacing device that is implanted in the AV septal area with electrodes that can sense/pace the atrium as well as the ventricle, especially the left ventricle for resynchronization pacing.
One illustrative implantable medical device may include a plurality of electrodes. The plurality of electrodes may include a tissue-piercing electrode implantable from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body to deliver cardiac therapy to or sense electrical activity of the left ventricle in the basal and/or septal region of the left ventricular myocardium of a patient's heart, and a right atrial electrode positionable within the right atrium to deliver cardiac therapy to or sense electrical activity of the right atrium of the patient's heart. The illustrative implantable medical device may further include a therapy delivery circuit operably coupled to the plurality of electrodes to deliver cardiac therapy to the patient's heart, a sensing circuit operably coupled to the plurality of electrodes to sense electrical activity of the patient's heart, and a controller comprising processing circuitry operably coupled to the therapy delivery circuit and the sensing circuit. The controller may be configured to monitor effectiveness of left ventricular capture. Monitoring effectiveness of left ventricular capture may include delivering a left ventricular pace using the tissue-piercing electrode, monitoring electrical activity of the left ventricle using the tissue-piercing electrode following the left ventricular pace, and determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity.
One illustrative method may include providing a tissue-piercing electrode implanted from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body to deliver cardiac therapy to or sense electrical activity of the left ventricle in the basal and/or septal region of the left ventricular myocardium of a patient's heart and providing a right atrial electrode positionable within the right atrium to deliver cardiac therapy to or sense electrical activity of the right atrium of the patient's heart. The illustrative method may further include delivering a left ventricular pace using the tissue-piercing electrode, monitoring electrical activity of the left ventricle using the tissue-piercing electrode following the left ventricular pace, and determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity.
One illustrative implantable medical device may include a plurality of electrodes, the plurality of electrodes including at least a tissue-piercing electrode implantable from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body to deliver cardiac therapy to or sense electrical activity of the left ventricle in the basal and/or septal region of the left ventricular myocardium of a patient's heart and a right atrial electrode positionable within the right atrium to deliver cardiac therapy to or sense electrical activity of the right atrium of the patient's heart. The illustrative implantable medical device may further include a therapy delivery circuit operably coupled to the plurality of electrodes to deliver cardiac therapy to the patient's heart, a sensing circuit operably coupled to the plurality of electrodes to sense electrical activity of the patient's heart, and a controller comprising processing circuitry operably coupled to the therapy delivery circuit and the sensing circuit. The controller may be further configured to deliver a left ventricular pace therapy using the tissue-piercing electrode, monitor effectiveness of left ventricular capture over a plurality of cardiac cycles based on electrical activated monitored using at least the tissue-piercing electrode, determine that effective left ventricular capture is not occurring based on the monitored of effectiveness of left ventricular capture over the plurality of cardiac cycles, and adjust left ventricular pacing in response to determination that effective left ventricular capture is not occurring.
One exemplary VfA device is a leadless pace/sense device for delivering AV synchronous ventricular sensing therapy. The device may be implanted in the AV septal area with sense/pace cathodes (e.g., an atrial cathode) in the atrium and sense/pace cathodes (e.g., a ventricular cathode) in the ventricle and a third electrode as a common anode. During delivery of ventricular pacing from such a device, effectiveness of therapy may be monitored based on analyzing morphologic features of a near-field paced electrogram (e.g., the ventricular cathode to the atrial anode) based on the following criteria: (1) absolute amplitude of electrogram baseline<a threshold in millivolts; (2) the minimum negative deflection within a certain time window from the paced event is more negative than a certain threshold in millivolts; and (3) the timing of the negative minimum measured relative to the timing of the paced event is less than a certain interval in milliseconds. If all of the above three criteria is met, effective tissue capture may be determined to occur for that particular ventricular pace and a diagnostic for effective ventricular pacing may be provided for such a VfA device.
The exemplary devices may also do continuous therapy adjustments based on indication of effective or ineffective pacing. For example, if pacing is ineffective for at least X out of Y beats, the device may run a series of diagnostic tests to correct it. If in DDD(R) mode, the device may initiate a capture test to measure capture thresholds and re-set outputs based on a certain value above the capture threshold. If pacing continues to be ineffective for X out of Y beats, the device may decrement AV delays for pacing in certain steps and continue to monitor the degree of effectiveness. There may be a lower bound (e.g., 60 milliseconds for intrinsic atrial sensing and 70 milliseconds for atrial pacing) to the AV delay beyond which it would not be further decremented. If in VVI (R) mode, and the device gets at least X out Y ineffective pacing beats and at least W out of Y sense beats, it may increase the heart rate and continue to monitor effectiveness of capture. The increment in heart rate may be modified up to a certain maximum rate (e.g., 130 beats per minute) while in VVI mode. If in VVI mode, the device determines at least X out of Y ineffective pacing beats but no sensed beats, it may initiate a capture threshold test to establish capture thresholds and reset pacing outputs. The exemplary devices may continue to track proportion of effective pacing and issue an alert if the effective pacing falls below a certain degree.
The details of one or more aspects of the disclosure are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of the techniques described in this disclosure will be apparent from the description and drawings, and from the claims.
The processes, methods, and techniques of this disclosure generally relate to implantable medical devices, systems, and methods for ventricle-from-atrium (VfA) cardiac resynchronization therapy. Additionally, the processes, methods, and techniques of this disclosure generally relate to other cardiac therapy including single chamber or multiple chamber pacing (e.g., dual or triple chamber pacing), atrioventricular synchronous pacing, asynchronous pacing, triggered pacing, cardiac resynchronization pacing, or tachycardia-related therapy. Although reference is made herein to implantable medical devices, such as a pacemaker or ICD, the methods and processes may be used with any medical devices, systems, or methods related to a patient's heart. Various other applications will become apparent to one of skill in the art having the benefit of the present disclosure.
It may be beneficial to provide an implantable medical device that is free of transvenous leads (e.g., a leadless device). It may also be beneficial to provide an implantable medical device capable of being used for various cardiac therapies, such as cardiac resynchronization pacing, single or multiple chamber pacing (e.g., dual or triple chamber pacing), atrioventricular synchronous pacing, asynchronous pacing, triggered pacing, or tachycardia-related therapy. Further, it may be beneficial to provide a system capable of communicating with a separate medical device, for example, to provide triggered pacing or to provide shock therapy in certain cases of tachycardia. Further still, it may be beneficial to configure the implantable medical device to provide adaptive pacing therapy using only an intracardiac device or in conjunction with one or more leads or a separate medical device.
The present disclosure provides an implantable medical device including a tissue-piercing electrode and optionally a right atrial electrode and/or a right atrial motion detector. The implantable medical device may be a VfA device implanted from the right atrium into the left ventricular myocardium. The implantable medical device may be used in adaptive cardiac therapy, for example, that adapts pacing delays based on one or more of a measured heart rate, intrinsic AV conduction, etc. Physiological response measurements may be taken, and the VfA device may be configured to deliver cardiac therapy based on the physiological response information. In particular, the VfA device may be configured to adapt pacing therapy based on different heartrates and/or intrinsic AV conduction, for example, by determining and delivering pacing therapy with an optimal atrioventricular (AV) pacing delay. Advantageously, in one or more embodiments, the techniques of this disclosure may be used to calibrate or deliver pacing therapy without using monitored electrical activity of the right ventricle of the patient's heart.
The tissue-piercing electrode may be implanted in the basal and/or septal region of the left ventricular myocardium of the patient's heart from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body. In a leadless implantable medical device, the tissue-piercing electrode may leadlessly extend from a distal end region of a housing of the device, and the right atrial electrode may be leadlessly coupled to the housing (e.g., part of or positioned on the exterior of the housing). In one or more embodiments, a right atrial motion detector may be within the implantable medical device. In a leaded implantable medical device, one or more of the electrodes may be coupled to the housing using an implantable lead. When the device is implanted, the electrodes may be used to sense electrical activity in one or more atria and/or ventricles of a patient's heart. The motion detector may be used to sense mechanical activity in one or more atria and/or ventricles of the patient's heart. In particular, the activity of the right atrium and the left ventricle may be monitored and, optionally, the activity of the right ventricle may be monitored. The electrodes may be used to deliver cardiac therapy, such as single chamber pacing for atrial fibrillation, atrioventricular synchronous pacing for bradycardia, asynchronous pacing, triggered pacing, cardiac resynchronization pacing for ventricular dyssynchrony, anti-tachycardia pacing, or shock therapy. Shock therapy may be initiated by the implantable medical device. A separate medical device, such as an extravascular ICD, which may also be implanted, may be in operative communication with the implantable medical device and may deliver an electrical shock in response to a trigger, such as a signaling pulse (e.g., triggering, signaling, or distinctive electrical pulse) provided by the device.
The device 10 may be described as a leadless implantable medical device. As used herein, “leadless” refers to a device being free of a lead extending out of the patient's heart 8. In other words, a leadless device may have a lead that does not extend from outside of the patient's heart to inside of the patient's heart. Some leadless devices may be introduced through a vein, but once implanted, the device is free of, or may not include, any transvenous lead and may be configured to provide cardiac therapy without using any transvenous lead. Further, a leadless VfA device, in particular, does not use a lead to operably connect to an electrode in the ventricle when a housing of the device is positioned in the atrium. Additionally, a leadless electrode may be coupled to the housing of the medical device without using a lead between the electrode and the housing.
The device 10 may include a dart electrode assembly 12 defining, or having, a straight shaft extending from the distal end region of device 10. The dart electrode assembly 12 may be placed, or at least configured to be placed, through the atrial myocardium and the central fibrous body and into the ventricular myocardium 14, or along the ventricular septum, without perforating entirely through the ventricular endocardial or epicardial surfaces. The dart electrode assembly 12 may carry, or include, an electrode at the distal end region of the shaft such that the electrode may be positioned within the ventricular myocardium for sensing ventricular signals and delivering ventricular pulses (e.g., to depolarize the left ventricle to initiate a contraction of the left ventricle). In some examples, the electrode at the distal end region of the shaft is a cathode electrode provided for use in a bipolar electrode pair for pacing and sensing. While the implant region 4 as illustrated may enable one or more electrodes of the dart electrode assembly 12 to be positioned in the ventricular myocardium, it is recognized that a device having the aspects disclosed herein may be implanted at other locations for multiple chamber pacing (e.g., dual or triple chamber pacing), single chamber pacing with multiple chamber sensing, single chamber pacing and/or sensing, or other clinical therapy and applications as appropriate.
It is to be understood that although device 10 is described herein as including a single dart electrode assembly, the device 10 may include more than one dart electrode assembly placed, or configured to be placed, through the atrial myocardium and the central fibrous body, and into the ventricular myocardium 14, or along the ventricular septum, without perforating entirely through the ventricular endocardial or epicardial surfaces. Additionally, each dart electrode assembly may carry, or include, more than a single electrode at the distal end region, or along other regions (e.g., proximal or central regions), of the shaft.
The cardiac therapy system 2 may also include a separate medical device 50 (depicted diagrammatically in
In the case of shock therapy (e.g., defibrillation shocks provided by the defibrillation electrode of the defibrillation lead), the separate medical device 50 (e.g., extravascular ICD) may include a control circuit that uses a therapy delivery circuit to generate defibrillation shocks having any of a number of waveform properties, including leading-edge voltage, tilt, delivered energy, pulse phases, and the like. The therapy delivery circuit may, for instance, generate monophasic, biphasic, or multiphasic waveforms. Additionally, the therapy delivery circuit may generate defibrillation waveforms having different amounts of energy. For example, the therapy delivery circuit may generate defibrillation waveforms that deliver a total of between approximately 60-80 Joules (J) of energy for subcutaneous defibrillation.
The separate medical device 50 may further include a sensing circuit. The sensing circuit may be configured to obtain electrical signals sensed via one or more combinations of electrodes and to process the obtained signals. The components of the sensing circuit may include analog components, digital components, or a combination thereof. The sensing circuit may, for example, include one or more sense amplifiers, filters, rectifiers, threshold detectors, analog-to-digital converters (ADCs), or the like. The sensing circuit may convert the sensed signals to digital form and provide the digital signals to the control circuit for processing and/or analysis. For example, the sensing circuit may amplify signals from sensing electrodes and convert the amplified signals to multi-bit digital signals by an ADC, and then provide the digital signals to the control circuit. In one or more embodiments, the sensing circuit may also compare processed signals to a threshold to detect the existence of atrial or ventricular depolarizations (e.g., P- or R-waves) and indicate the existence of the atrial depolarization (e.g., P-waves) or ventricular depolarizations (e.g., R-waves) to the control circuit.
The device 10 and the separate medical device 50 may cooperate to provide cardiac therapy to the patient's heart 8. For example, the device 10 and the separate medical device 50 may be used to detect tachycardia, monitor tachycardia, and/or provide tachycardia-related therapy. For example, the device 10 may communicate with the separate medical device 50 wirelessly to trigger shock therapy using the separate medical device 50. As used herein, “wirelessly” refers to an operative coupling or connection without using a metal conductor between the device 10 and the separate medical device 50. In one example, wireless communication may use a distinctive, signaling, or triggering electrical-pulse provided by the device 10 that conducts through the patient's tissue and is detectable by the separate medical device 50. In another example, wireless communication may use a communication interface (e.g., an antenna) of the device 10 to provide electromagnetic radiation that propagates through patient's tissue and is detectable, for example, using a communication interface (e.g., an antenna) of the separate medical device 50.
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In some embodiments, a pacing delay between the RV electrode on lead 414 to pace the RV and the LV electrode on lead 410 to pace the LV (e.g., RV-LV pacing delay, or more generally, VV pacing delay) may be calibrated or optimized, for example, using a separate medical device, such as an electrode apparatus (e.g., ECG belt). Various methods may be used to calibrate or optimize the VV delay. In some embodiments, the medical device 428 may be used to test pacing at a plurality of different VV delays. For example, the RV may be paced ahead of the LV by about 80, 60, 40, and 20 milliseconds (ms) and the LV may be paced ahead of the RV by about 80, 60, 40, and 20 ms, as well as simultaneous RV-LV pacing (e.g., about 0 ms VV pacing delay). The medical device 428 may then be configured, for example, automatically, to select a VV pacing delay that, when used for pacing, corresponds to a minimal electrical dyssynchrony measured using the electrode apparatus. The test pacing at different VV pacing delays may be performed using a particular AV delay, such as a nominal AV delay set by the medical device 428 or at a predetermined optimal AV delay based on patient characteristics.
In at least one embodiment, the housing 30 may be described as extending between a distal end region 32 and a proximal end region 34 in a generally cylindrical shape to facilitate catheter delivery. In other embodiments, the housing 30 may be prismatic or any other shape to perform the functionality and utility described herein. The housing 30 may include a delivery tool interface member 26, e.g., at the proximal end region 34, for engaging with a delivery tool during implantation of the device 10.
All or a portion of the housing 30 may function as an electrode during cardiac therapy, for example, in sensing and/or pacing. In the example shown, the housing-based electrode 24 is shown to circumscribe a proximal portion (e.g., closer to the proximal end region 34 than the distal end region 32) of the housing 30. When the housing 30 is formed from an electrically conductive material, such as a titanium alloy or other examples listed above, portions of the housing 30 may be electrically insulated by a non-conductive material, such as a coating of parylene, polyurethane, silicone, epoxy, or other biocompatible polymer, leaving one or more discrete areas of conductive material exposed to define the proximal housing-based electrode 24. When the housing 30 is formed from a non-conductive material, such as a ceramic, glass or polymer material, an electrically-conductive coating or layer, such as a titanium, platinum, stainless steel, or alloys thereof, may be applied to one or more discrete areas of the housing 30 to form the proximal housing-based electrode 24. In other examples, the proximal housing-based electrode 24 may be a component, such as a ring electrode, that is mounted or assembled onto the housing 30. The proximal housing-based electrode 24 may be electrically coupled to internal circuitry of the device 10, e.g., via the electrically-conductive housing 30 or an electrical conductor when the housing 30 is a non-conductive material.
In the example shown, the proximal housing-based electrode 24 is located nearer to the housing proximal end region 34 than the housing distal end region 32 and is therefore referred to as a “proximal housing-based electrode” 24. In other examples, however, the housing-based electrode 24 may be located at other positions along the housing 30, e.g., more distal relative to the position shown.
At the distal end region 32, the device 10 may include a distal fixation and electrode assembly 36, which may include one or more fixation members 20 and one or more dart electrode assemblies 12 of equal or unequal length. In one example, a single dart electrode assembly 12 includes a shaft 40 extending distally away from the housing distal end region 32 and one or more electrode elements, such as a tip electrode 42 at or near the free, distal end region of the shaft 40. The tip electrode 42 may have a conical or hemi-spherical distal tip with a relatively narrow tip-diameter (e.g., less than about 1 millimeter (mm)) for penetrating into and through tissue layers without using a sharpened tip or needle-like tip having sharpened or beveled edges.
The shaft 40 of the dart electrode assembly 12 may be a normally straight member and may be rigid. In other embodiments, the shaft 40 may be described as being relatively stiff but still possessing limited flexibility in lateral directions. Further, the shaft 40 may be non-rigid to allow some lateral flexing with heart motion. However, in a relaxed state, when not subjected to any external forces, the shaft 40 may maintain a straight position as shown to hold the tip electrode 42 spaced apart from the housing distal end region 32 at least by the height 47 of the shaft 40. In other words, the dart electrode assembly 12 may be described as resilient.
The dart electrode assembly 12 may be configured to pierce through one or more tissue layers to position the tip electrode 42 within a desired tissue layer, e.g., the ventricular myocardium. As such, the height 47, or length, of the shaft 40 may correspond to the expected pacing site depth, and the shaft 40 may have a relatively high compressive strength along its longitudinal axis to resist bending in a lateral or radial direction when pressed against the implant region 4. If a second dart electrode assembly 12 is employed, its length may be unequal to the expected pacing site depth and may be configured to act as an indifferent electrode for delivering of pacing energy to the tissue. A longitudinal axial force may be applied against the tip electrode 42, e.g., by applying longitudinal pushing force to the proximal end 34 of the housing 30, to advance the dart electrode assembly 12 into the tissue within the target implant region. The shaft 40 may be described as longitudinally non-compressive and/or elastically deformable in lateral or radial directions when subjected to lateral or radial forces to allow temporary flexing, e.g., with tissue motion, but may return to its normally straight position when lateral forces diminish. When the shaft 40 is not exposed to any external force, or to only a force along its longitudinal central axis, the shaft 40 may retain a straight, linear position as shown.
The one or more fixation members 20 may be described as one or more “tines” having a normally curved position. The tines may be held in a distally extended position within a delivery tool. The distal tips of tines may penetrate the heart tissue to a limited depth before elastically curving back proximally into the normally curved position (shown) upon release from the delivery tool. Further, the fixation members 20 may include one or more aspects described in, for example, U.S. Pat. No. 9,675,579 (Grubac et al.), issued 13 Jun. 2017, and U.S. Pat. No. 9,119,959 (Rys et al.), issued 1 Sep. 2015, each of which is incorporated herein by reference in its entirety.
In some examples, the distal fixation and electrode assembly 36 includes a distal housing-based electrode 22. In the case of using the device 10 as a pacemaker for multiple chamber pacing (e.g., dual or triple chamber pacing) and sensing, the tip electrode 42 may be used as a cathode electrode paired with the proximal housing-based electrode 24 serving as a return anode electrode. Alternatively, the distal housing-based electrode 22 may serve as a return anode electrode paired with tip electrode 42 for sensing ventricular signals and delivering ventricular pacing pulses. In other examples, the distal housing-based electrode 22 may be a cathode electrode for sensing atrial signals and delivering pacing pulses to the atrial myocardium in the target implant region 4. When the distal housing-based electrode 22 serves as an atrial cathode electrode, the proximal housing-based electrode 24 may serve as the return anode paired with the tip electrode 42 for ventricular pacing and sensing and as the return anode paired with the distal housing-based electrode 22 for atrial pacing and sensing.
As shown in this illustration, the target implant region 4 in some pacing applications is along the atrial endocardium 18, generally inferior to the AV node 15 and the His bundle 5. The dart electrode assembly 12 may at least partially define the height 47, or length, of the shaft 40 for penetrating through the atrial endocardium 18 in the target implant region 4, through the central fibrous body 16, and into the ventricular myocardium 14 without perforating through the ventricular endocardial surface 17. When the height 47, or length, of the dart electrode assembly 12 is fully advanced into the target implant region 4, the tip electrode 42 may rest within the ventricular myocardium 14, and the distal housing-based electrode 22 may be positioned in intimate contact with or close proximity to the atrial endocardium 18. The dart electrode assembly 12 may have a total combined height 47, or length, of tip electrode 42 and shaft 40 from about 3 mm to about 8 mm in various examples. The diameter of the shaft 40 may be less than about 2 mm, and may be about 1 mm or less, or even about 0.6 mm or less.
The device 10 may include an acoustic or motion detector 11 within the housing 30. The acoustic or motion detector 11 may be operably coupled to one or more a control circuit 80 (
The acoustic or motion detector 11 may also be used for rate response detection or to provide a rate-responsive IMD. Various techniques related to rate response may be described in U.S. Pat. No. 5,154,170 (Bennett et al.), issued Oct. 13, 1992, entitled “Optimization for rate responsive cardiac pacemaker,” and U.S. Pat. No. 5,562,711 (Yerich et al.), issued Oct. 8, 1996, entitled “Method and apparatus for rate-responsive cardiac pacing,” each of which is incorporated herein by reference in its entirety.
In various embodiments, acoustic or motion sensor 11 may be used as an HS sensor and may be implemented as a microphone or a 1-, 2- or 3-axis accelerometer. In one embodiment, the acoustical sensor is implemented as a piezoelectric crystal mounted within an implantable medical device housing and responsive to the mechanical motion associated with heart sounds. The piezoelectric crystal may be a dedicated HS sensor or may be used for multiple functions. In the illustrative embodiment shown, the acoustical sensor is embodied as a piezoelectric crystal that is also used to generate a patient alert signal in the form of a perceptible vibration of the IMD housing. Upon detecting an alert condition, control circuit 80 may cause patient alert control circuitry to generate an alert signal by activating the piezoelectric crystal.
Control circuit may be used to control whether the piezoelectric crystal is used in a “listening mode” to sense HS signals by HS sensing circuitry or in an “output mode” to generate a patient alert. During patient alert generation, HS sensing circuitry may be temporarily decoupled from the HS sensor by control circuitry.
Examples of other embodiments of acoustical sensors that may be adapted for implementation with the techniques of the present disclosure may be described generally in U.S. Pat. No. 4,546,777 (Groch, et al.), U.S. Pat. No. 6,869,404 (Schulhauser, et al.), U.S. Pat. No. 5,554,177 (Kieval, et al.), and U.S. Pat. No. 7,035,684 (Lee, et al.), each of which is incorporated herein by reference in its entirety.
Various types of acoustical sensors may be used. The acoustical sensor may be any implantable or external sensor responsive to one or more of the heart sounds generated as described in the foregoing and thereby produces an electrical analog signal correlated in time and amplitude to the heart sounds. The analog signal may be then be processed, which may include digital conversion, by the HS sensing module to obtain HS parameters, such as amplitudes or relative time intervals, as derived by HS sensing module or control circuit 80. The acoustical sensor and HS sensing module may be incorporated in an IMD capable of delivering CRT or another cardiac therapy being optimized or may be implemented in a separate device having wired or wireless communication with IMD or an external programmer or computer used during a pace parameter optimization procedure as described herein.
In some embodiments, any of the tissue-piercing electrodes of the present disclosure may be implanted in the basal and/or septal region of the left ventricular myocardium of the patient's heart. In particular, the tissue-piercing electrode may be implanted from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body.
Once implanted, the tissue-piercing electrode may be positioned in the target implant region 4 (
In some embodiments, the tissue-piercing electrode may be positioned in the basal septal region of the left ventricular myocardium when implanted. The basal septal region may include one or more of the basal anteroseptal area 2, basal inferoseptal area 3, mid-anteroseptal area 8, and mid-inferoseptal area 9.
In some embodiments, the tissue-piercing electrode may be positioned in the high inferior/posterior basal septal region of the left ventricular myocardium when implanted. The high inferior/posterior basal septal region of the left ventricular myocardium may include a portion of one or more of the basal inferoseptal area 3 and mid-inferoseptal area 9 (e.g., the basal inferoseptal area only, the mid-inferoseptal area only, or both the basal inferoseptal area and the mid-inferoseptal area). For example, the high inferior/posterior basal septal region may include region 324 illustrated generally as a dashed-line boundary. As shown, the dashed line boundary represents an approximation of where the high inferior/posterior basal septal region is located, which may take a somewhat different shape or size depending on the particular application.
The distal housing-based electrode 22 may include a ring formed of an electrically conductive material, such as titanium, platinum, iridium, or alloys thereof. The distal housing-based electrode 22 may be a single, continuous ring electrode. In other examples, portions of the ring may be coated with an electrically insulating coating, e.g., parylene, polyurethane, silicone, epoxy, or other insulating coating, to reduce the electrically conductive surface area of the ring electrode. For instance, one or more sectors of the ring may be coated to separate two or more electrically conductive exposed surface areas of the distal housing-based electrode 22. Reducing the electrically conductive surface area of the distal housing-based electrode 22, e.g., by covering portions of the electrically conductive ring with an insulating coating, may increase the electrical impedance of the distal housing-based 22, and thereby, reduce the current delivered during a pacing pulse that captures the myocardium, e.g., the atrial myocardial tissue. A lower current drain may conserve the power source, e.g., one or more rechargeable or non-rechargeable batteries, of the device 10.
As described above, the distal housing-based electrode 22 may be configured as an atrial cathode electrode for delivering pacing pulses to the atrial tissue at the implant site in combination with the proximal housing-based electrode 24 as the return anode. The electrodes 22 and 24 may be used to sense atrial P-waves for use in controlling atrial pacing pulses (delivered in the absence of a sensed P-wave) and for controlling atrial-synchronized ventricular pacing pulses delivered using the tip electrode 42 as a cathode and the proximal housing-based electrode 24 as the return anode. In other examples, the distal housing-based electrode 22 may be used as a return anode in conjunction with the cathode tip electrode 42 for ventricular pacing and sensing.
The power source 98 may provide power to the circuitry of the device 10 including each of the components 80, 82, 84, 86, 88, 90 as needed. The power source 98 may include one or more energy storage devices, such as one or more rechargeable or non-rechargeable batteries. The connections (not shown) between the power source 98 and each of the components 80, 82, 84, 86, 88, 90 may be understood from the general block diagram illustrated to one of ordinary skill in the art. For example, the power source 98 may be coupled to one or more charging circuits included in the therapy delivery circuit 84 for providing the power used to charge holding capacitors included in the therapy delivery circuit 84 that are discharged at appropriate times under the control of the control circuit 80 for delivering pacing pulses, e.g., according to a dual chamber pacing mode such as DDI(R). The power source 98 may also be coupled to components of the sensing circuit 86, such as sense amplifiers, analog-to-digital converters, switching circuitry, etc., sensors 90, the telemetry circuit 88, and the memory 82 to provide power to the various circuits.
The functional blocks shown represent functionality included in the device 10 and may include any discrete and/or integrated electronic circuit components that implement analog, and/or digital circuits capable of producing the functions attributed to the medical device 10 herein. The various components may include processing circuitry, such as an application specific integrated circuit (ASIC), an electronic circuit, a processor (shared, dedicated, or group), and memory that execute one or more software or firmware programs, a combinational logic circuit, state machine, or other suitable components or combinations of components that provide the described functionality. The particular form of software, hardware, and/or firmware employed to implement the functionality disclosed herein will be determined primarily by the particular system architecture employed in the medical device and by the particular detection and therapy delivery methodologies employed by the medical device.
The memory 82 may include any volatile, non-volatile, magnetic, or electrical non-transitory computer readable storage media, such as random-access memory (RAM), read-only memory (ROM), non-volatile RAM (NVRAM), electrically-erasable programmable ROM (EEPROM), flash memory, or any other memory device.
Furthermore, the memory 82 may include a non-transitory computer readable media storing instructions that, when executed by one or more processing circuits, cause the control circuit 80 and/or other processing circuitry to calibrate pacing therapy and/or perform a single, dual, or triple chamber calibrated pacing therapy (e.g., single or multiple chamber pacing), or other cardiac therapy functions (e.g., sensing or delivering therapy), attributed to the device 10. The non-transitory computer-readable media storing the instructions may include any of the media listed above.
The control circuit 80 may communicate, e.g., via a data bus, with the therapy delivery circuit 84 and the sensing circuit 86 for sensing cardiac electrical signals and controlling delivery of cardiac electrical stimulation therapies in response to sensed cardiac events, e.g., P-waves and R-waves, or the absence thereof. The tip electrode 42, the distal housing-based electrode 22, and the proximal housing-based electrode 24 may be electrically coupled to the therapy delivery circuit 84 for delivering electrical stimulation pulses to the patient's heart and to the sensing circuit 86 and for sensing cardiac electrical signals.
The sensing circuit 86 may include an atrial (A) sensing channel 87 and a ventricular (V) sensing channel 89. The distal housing-based electrode 22 and the proximal housing-based electrode 24 may be coupled to the atrial sensing channel 87 for sensing atrial signals, e.g., P-waves attendant to the depolarization of the atrial myocardium. In examples that include two or more selectable distal housing-based electrodes, the sensing circuit 86 may include switching circuitry for selectively coupling one or more of the available distal housing-based electrodes to cardiac event detection circuitry included in the atrial sensing channel 87. Switching circuitry may include a switch array, switch matrix, multiplexer, or any other type of switching device suitable to selectively couple components of the sensing circuit 86 to selected electrodes. The tip electrode 42 and the proximal housing-based electrode 24 may be coupled to the ventricular sensing channel 89 for sensing ventricular signals, e.g., R-waves attendant to the depolarization of the ventricular myocardium.
Each of the atrial sensing channel 87 and the ventricular sensing channel 89 may include cardiac event detection circuitry for detecting P-waves and R-waves, respectively, from the cardiac electrical signals received by the respective sensing channels. The cardiac event detection circuitry included in each of the channels 87 and 89 may be configured to amplify, filter, digitize, and rectify the cardiac electrical signal received from the selected electrodes to improve the signal quality for detecting cardiac electrical events. The cardiac event detection circuitry within each channel 87 and 89 may include one or more sense amplifiers, filters, rectifiers, threshold detectors, comparators, analog-to-digital converters (ADCs), timers, or other analog or digital components. A cardiac event sensing threshold, e.g., a P-wave sensing threshold and an R-wave sensing threshold, may be automatically adjusted by each respective sensing channel 87 and 89 under the control of the control circuit 80, e.g., based on timing intervals and sensing threshold values determined by the control circuit 80, stored in the memory 82, and/or controlled by hardware, firmware, and/or software of the control circuit 80 and/or the sensing circuit 86.
Upon detecting a cardiac electrical event based on a sensing threshold crossing, the sensing circuit 86 may produce a sensed event signal that is passed to the control circuit 80. For example, the atrial sensing channel 87 may produce a P-wave sensed event signal in response to a P-wave sensing threshold crossing. The ventricular sensing channel 89 may produce an R-wave sensed event signal in response to an R-wave sensing threshold crossing. The sensed event signals may be used by the control circuit 80 for setting pacing escape interval timers that control the basic time intervals used for scheduling cardiac pacing pulses. A sensed event signal may trigger or inhibit a pacing pulse depending on the particular programmed pacing mode. For example, a P-wave sensed event signal received from the atrial sensing channel 87 may cause the control circuit 80 to inhibit a scheduled atrial pacing pulse and schedule a ventricular pacing pulse at a programmed atrioventricular (AV) pacing interval. If an R-wave is sensed before the AV pacing interval expires, the ventricular pacing pulse may be inhibited. If the AV pacing interval expires before the control circuit 80 receives an R-wave sensed event signal from the ventricular sensing channel 89, the control circuit 80 may use the therapy delivery circuit 84 to deliver the scheduled ventricular pacing pulse synchronized to the sensed P-wave.
In some examples, the device 10 may be configured to deliver a variety of pacing therapies including bradycardia pacing, cardiac resynchronization therapy, post-shock pacing, and/or tachycardia-related therapy, such as ATP, among others. For example, the device 10 may be configured to detect non-sinus tachycardia and deliver ATP. The control circuit 80 may determine cardiac event time intervals, e.g., P-P intervals between consecutive P-wave sensed event signals received from the atrial sensing channel 87, R-R intervals between consecutive R-wave sensed event signals received from the ventricular sensing channel 89, and P-R and/or R-P intervals received between P-wave sensed event signals and R-wave sensed event signals. These intervals may be compared to tachycardia detection intervals for detecting non-sinus tachycardia. Tachycardia may be detected in a given heart chamber based on a threshold number of tachycardia detection intervals being detected.
The therapy delivery circuit 84 may include atrial pacing circuit 83 and ventricular pacing circuit 85. Each pacing circuit 83, 85 may include charging circuitry, one or more charge storage devices such as one or more low voltage holding capacitors, an output capacitor, and/or switching circuitry that controls when the holding capacitor(s) are charged and discharged across the output capacitor to deliver a pacing pulse to the pacing electrode vector coupled to respective pacing circuits 83, 85. The tip electrode 42 and the proximal housing-based electrode 24 may be coupled to the ventricular pacing circuit 85 as a bipolar cathode and anode pair for delivering ventricular pacing pulses, e.g., upon expiration of an AV or VV pacing interval set by the control circuit 80 for providing atrial-synchronized ventricular pacing and a basic lower ventricular pacing rate.
The atrial pacing circuit 83 may be coupled to the distal housing-based electrode 22 and the proximal housing-based electrode 24 to deliver atrial pacing pulses. The control circuit 80 may set one or more atrial pacing intervals according to a programmed lower pacing rate or a temporary lower rate set according to a rate-responsive sensor indicated pacing rate. Atrial pacing circuit may be controlled to deliver an atrial pacing pulse if the atrial pacing interval expires before a P-wave sensed event signal is received from the atrial sensing channel 87. The control circuit 80 starts an AV pacing interval in response to a delivered atrial pacing pulse to provide synchronized multiple chamber pacing (e.g., dual or triple chamber pacing).
Charging of a holding capacitor of the atrial or ventricular pacing circuit 83, 85 to a programmed pacing voltage amplitude and discharging of the capacitor for a programmed pacing pulse width may be performed by the therapy delivery circuit 84 according to control signals received from the control circuit 80. For example, a pace timing circuit included in the control circuit 80 may include programmable digital counters set by a microprocessor of the control circuit 80 for controlling the basic pacing time intervals associated with various single chamber or multiple chamber pacing (e.g., dual or triple chamber pacing) modes or anti-tachycardia pacing sequences. The microprocessor of the control circuit 80 may also set the amplitude, pulse width, polarity, or other characteristics of the cardiac pacing pulses, which may be based on programmed values stored in the memory 82.
The device 10 may include other sensors 90 for sensing signals from the patient for use in determining a need for and/or controlling electrical stimulation therapies delivered by the therapy delivery circuit 84. In some examples, a sensor indicative of a need for increased cardiac output may include a patient activity sensor, such as an accelerometer. An increase in the metabolic demand of the patient due to increased activity as indicated by the patient activity sensor may be determined by the control circuit 80 for use in determining a sensor-indicated pacing rate. The control circuit 80 may be used to calibrate and/or deliver pacing therapy based on the patient activity sensor (e.g., a measured heartrate).
Control parameters utilized by the control circuit 80 for sensing cardiac events and controlling pacing therapy delivery may be programmed into the memory 82 via the telemetry circuit 88, which may also be described as a communication interface. The telemetry circuit 88 includes a transceiver and antenna for communicating with an external device, such as a programmer or home monitor, using radio frequency communication or other communication protocols. The control circuit 80 may use the telemetry circuit 88 to receive downlink telemetry from and send uplink telemetry to the external device. In some cases, the telemetry circuit 88 may be used to transmit and receive communication signals to/from another medical device implanted in the patient.
A distal fixation and electrode assembly 736 may be coupled to the housing distal end region 732. The distal fixation and electrode assembly 736 may include an electrically insulative distal member 772 coupled to the housing distal end region 732. The tissue-piercing electrode assembly 712 extends away from the housing distal end region 732, and multiple non-tissue piercing electrodes 722 may be coupled directly to the insulative distal member 772. The tissue-piercing electrode assembly 712 extends in a longitudinal direction away from the housing distal end region 732 and may be coaxial with the longitudinal center axis 731 of the housing 730.
The distal tissue-piercing electrode assembly 712 may include an electrically insulated shaft 740 and a tip electrode 742 (e.g., tissue-piercing electrode). In some examples, the tissue-piercing electrode assembly 712 is an active fixation member including a helical shaft 740 and a distal cathode tip electrode 742. The helical shaft 740 may extend from a shaft distal end region 743 to a shaft proximal end region 741, which may be directly coupled to the insulative distal member 772. The helical shaft 740 may be coated with an electrically insulating material, e.g., parylene or other examples listed herein, to avoid sensing or stimulation of cardiac tissue along the shaft length. The tip electrode 742 is at the shaft distal end region 743 and may serve as a cathode electrode for delivering ventricular pacing pulses and sensing ventricular electrical signals using the proximal housing-based electrode 724 as a return anode when the tip electrode 742 is advanced into ventricular tissue. The proximal housing-based electrode 724 may be a ring electrode circumscribing the housing 730 and may be defined by an uninsulated portion of the longitudinal sidewall 735. Other portions of the housing 730 not serving as an electrode may be coated with an electrically insulating material as described above in conjunction with
Using two or more tissue-piercing electrodes (e.g., of any type) penetrating into the LV myocardium may be used for more localized pacing capture and may mitigate ventricular pacing spikes affecting capturing atrial tissue. In some embodiments, multiple tissue-piercing electrodes may include two or more dart-type electrode assemblies (e.g., electrode assembly 12 of
In some embodiments, one or more tissue-piercing electrodes (e.g., of any type) that penetrate into the LV myocardium may be a multi-polar tissue-piercing electrode. A multi-polar tissue-piercing electrode may include one or more electrically active and electrically separate elements, which may enable bipolar or multi-polar pacing from one or more tissue-piercing electrodes.
Multiple non-tissue piercing electrodes 722 may be provided along a periphery of the insulative distal member 772, peripheral to the tissue-piercing electrode assembly 712. The insulative distal member 772 may define a distal-facing surface 738 of the device 710 and a circumferential surface 739 that circumscribes the device 710 adjacent to the housing longitudinal sidewall 735. Non-tissue piercing electrodes 722 may be formed of an electrically conductive material, such as titanium, platinum, iridium, or alloys thereof. In the illustrated embodiment, six non-tissue piercing electrodes 722 are spaced apart radially at equal distances along the outer periphery of insulative distal member 772, however, two or more non-tissue piercing electrodes 722 may be provided.
Non-tissue piercing electrodes 722 may be discrete components each retained within a respective recess 774 in the insulative member 772 sized and shaped to mate with the non-tissue piercing electrode 722. In other examples, the non-tissue piercing electrodes 722 may each be an uninsulated, exposed portion of a unitary member mounted within or on the insulative distal member 772. Intervening portions of the unitary member not functioning as an electrode may be insulated by the insulative distal member 772 or, if exposed to the surrounding environment, may be coated with an electrically insulating coating, e.g., parylene, polyurethane, silicone, epoxy, or other insulating coating.
When the tissue-piercing electrode assembly 712 is advanced into cardiac tissue, at least one non-tissue piercing electrode 722 may be positioned against, in intimate contact with, or in operative proximity to, a cardiac tissue surface for delivering pulses and/or sensing cardiac electrical signals produced by the patient's heart. For example, non-tissue piercing electrodes 722 may be positioned in contact with right atrial endocardial tissue for pacing and sensing in the atrium when the tissue-piercing electrode assembly 712 is advanced into the atrial tissue and through the central fibrous body until the distal tip electrode 742 is positioned in direct contact with ventricular tissue, e.g., ventricular myocardium and/or a portion of the ventricular conduction system.
Non-tissue piercing electrodes 722 may be coupled to the therapy delivery circuit 84 and the sensing circuit 86 (see
Certain non-tissue piercing electrodes 722 selected for atrial pacing and/or atrial sensing may be selected based on atrial capture threshold tests, electrode impedance, P-wave signal strength in the cardiac electrical signal, or other factors. For example, a single one or any combination of two or more individual non-tissue piercing electrodes 722 functioning as a cathode electrode that provides an optimal combination of a low pacing capture threshold amplitude and relatively high electrode impedance may be selected to achieve reliable atrial pacing using minimal current drain from the power source 98.
In some instances, the distal-facing surface 738 may uniformly contact the atrial endocardial surface when the tissue-piercing electrode assembly 712 anchors the housing 730 at the implant site. In that case, all the electrodes 722 may be selected together to form the atrial cathode. Alternatively, every other one of the electrodes 722 may be selected together to form a multi-point atrial cathode having a higher electrical impedance that is still uniformly distributed along the distal-facing surface 738. Alternatively, a subset of one or more electrodes 722 along one side of the insulative distal member 772 may be selected to provide pacing at a desired site that achieves the lowest pacing capture threshold due to the relative location of the electrodes 722 to the atrial tissue being paced.
In other instances, the distal-facing surface 738 may be oriented at an angle relative to the adjacent endocardial surface depending on the positioning and orientation at which the tissue-piercing electrode assembly 712 enters the cardiac tissue. In this situation, one or more of the non-tissue piercing electrodes 722 may be positioned in closer contact with the adjacent endocardial tissue than other non-tissue piercing electrodes 722, which may be angled away from the endocardial surface. By providing multiple non-tissue piercing electrodes along the periphery of the insulative distal member 772, the angle of the tissue-piercing electrode assembly 712 and the housing distal end region 732 relative to the cardiac surface, e.g., the right atrial endocardial surface, may not be required to be substantially parallel. Anatomical and positional differences may cause the distal-facing surface 738 to be angled or oblique to the endocardial surface, however, multiple non-tissue piercing electrodes 722 distributed along the periphery of the insulative distal member 772 increase the likelihood of good contact between one or more electrodes 722 and the adjacent cardiac tissue to promote acceptable pacing thresholds and reliable cardiac event sensing using at least a subset of multiple electrodes 722. Contact or fixation circumferentially along the entire periphery of the insulative distal member 772 may not be required.
The non-tissue piercing electrodes 722 are shown to each include a first portion 722a extending along the distal-facing surface 738 and a second portion 722b extending along the circumferential surface 739. The first portion 722a and the second portion 722b may be continuous exposed surfaces such that the active electrode surface wraps around a peripheral edge 776 of the insulative distal member 772 that joins the distal facing surface 738 and the circumferential surface 739. The non-tissue piercing electrodes 722 may include one or more of the electrodes 722 along the distal-facing surface 738, one or more electrodes along the circumferential surface 739, one or more electrodes each extending along both of the distal-facing surface 738 and the circumferential surface 739, or any combination thereof. The exposed surface of each of the non-tissue piercing electrodes 722 may be flush with respective distal-facing surfaces 738 and/or circumferential surfaces. In other examples, each of the non-tissue piercing electrodes 722 may have a raised surface that protrudes from the insulative distal member 772. Any raised surface of the electrodes 722, however, may define a smooth or rounded, non-tissue piercing surface.
The distal fixation and electrode assembly 736 may seal the distal end region of the housing 730 and may provide a foundation on which the electrodes 722 are mounted. The electrodes 722 may be referred to as housing-based electrodes. The electrodes 722 may not be not carried by a shaft or other extension that extends the active electrode portion away from the housing 730, like the distal tip electrode 742 residing at the distal tip of the helical shaft 740 extending away from the housing 730. Other examples of non-tissue piercing electrodes presented herein that are coupled to a distal-facing surface and/or a circumferential surface of an insulative distal member include the distal housing-based ring electrode 22 (
The non-tissue piercing electrodes 722 and other examples listed above are expected to provide more reliable and effective atrial pacing and sensing than a tissue-piercing electrode provided along the distal fixation and electrode assembly 736. The atrial chamber walls are relatively thin compared to ventricular chamber walls. A tissue-piercing atrial cathode electrode may extend too deep within the atrial tissue leading to inadvertent sustained or intermittent capture of ventricular tissue. A tissue-piercing atrial cathode electrode may lead to interference with sensing atrial signals due to ventricular signals having a larger signal strength in the cardiac electrical signal received via tissue-piercing atrial cathode electrodes that are in closer physical proximity to the ventricular tissue. The tissue-piercing electrode assembly 712 may be securely anchored into ventricular tissue for stabilizing the implant position of the device 710 and providing reasonable certainty that the tip electrode 742 is sensing and pacing in ventricular tissue while the non-tissue piercing electrodes 722 are reliably pacing and sensing in the atrium. When the device 710 is implanted in the target implant region 4, e.g., as shown in
The method 600 may include filtering the motion signal within the atrial contraction detection window, rectifying the filtered signal, and generating a derivative signal of the filtered and rectified motion signal 634 within the atrial contraction detection window. The method 600 may include determining whether an amplitude of the derivative signal within the atrial contraction detection window exceeds a threshold 636. In response to determining that the amplitude of the derivative signal within the atrial contraction detection window exceeds the threshold (YES of 636), the method 600 may proceed to detecting atrial contraction 638. Otherwise (NO of 636), the method 600 may return to filtering, rectifying, and generating a derivative signal 634. Various techniques for using a motion detector that provides a motion signal may be described in U.S. Pat. No. 9,399,140 (Cho et al.), issued Jul. 26, 2016, entitled “Atrial contraction detection by a ventricular leadless pacing device for atrio-synchronous ventricular pacing,” which is incorporated herein by reference in its entirety.
As will be described with respect to
Separation of the closure of the mitral and tricuspid valves due to ventricular dyssynchrony can be observed as separate M1 and T1 peaks in the S1 signal. Merging of the M1 (mitral valve closure sound) and the T1 (tricuspid valve closure sound) can be used as an indication of improved ventricular synchrony.
Generally, left ventricular pressure (LVP) rises dramatically following the QRS complex of the ECG and closure of the mitral valve and continues to build during ventricular systole until the aortic and pulmonary valves open, ejecting blood into the aorta and pulmonary artery. Ventricular contraction typically continues to cause blood pressure to rise in the ventricles and the aorta and pulmonary artery during the ejection phase. As the contraction diminishes, blood pressure decreases until the aortic and pulmonary valves close.
The second heart sound, S2, may be generated by the closure of the aortic and pulmonary valves, near the end of ventricular systole and start of ventricular diastole. S2 may therefore be correlated to diastolic pressure in the aorta and the pulmonary artery. S2 generally has a duration of about 120 ms and a frequency on the order of 25 to 350 Hz. The time interval between S1 and S2, i.e., S1-S2 time interval, may represent the systolic time interval (STI) corresponding to the ventricular isovolumic contraction (pre-ejection) and ejection phase of the cardiac cycle. This S1-S2 time interval may provide a surrogate measurement for stroke volume. Furthermore, the ratio of pre-ejection period (Q-S1) to S1-S2 time may be used as an index of myocardial contractility.
The third heart sound, S3, is associated with early, passive diastolic filling of the ventricles, and the fourth heart sound, S4, may be associated with late, active filling of the ventricles due to atrial contraction. The third sound is generally difficult to hear in a normal patient using a stethoscope, and the fourth sound is generally not heard in a normal patient. Presence of the third and fourth heart sounds during an examination using a stethoscope may indicate a pathological condition. The S3 and S4 heart sounds may be used in optimizing pace parameters as they relate to diastolic function of the heart. Generally, these sounds would be minimized or disappear when an optimal pace parameter is identified. Other aspects of the S1 through S4 heart sounds and timing thereof that may be useful in cardiac pace parameter optimization as known to one having ordinary skill in the art.
A pace parameter optimization method may be initiated at block 802. The optimization process may be initiated in response to a user command received via an external programmer. At a time of initial IMD implantation or during office follow-up visits, or during a remote patient monitoring session, a user may initiate a HS-base optimization procedure using an external programmer or networked computer.
Additionally, or alternatively, the process shown by flow chart 800 may be an automated process started periodically or in response to sensing a need for therapy delivery or therapy adjustment based on a sensed physiological signal, which may include sensed HS signals.
At block 804 a pace control parameter to be optimized is selected. A control parameter may be a timing-related parameter, such as AV interval or VV interval. Pacing vector is another control parameter that may be selected at block 804 for optimization. For example, when a multi-polar lead is used, such as a coronary sinus lead, multiple bipolar or unipolar pacing vectors may be selected for pacing in a given heart chamber. The pacing site associated with a particular pacing vector may have a significant effect on the hemodynamic benefit of a pacing therapy. As such, pacing vector is one pace control parameter that may be optimized using methods described herein.
A pacing sequence is initiated at block 806 using an initial parameter setting for the test parameter selected at block 804. In one embodiment, the AV interval is being optimized, and ventricular pacing is delivered at an initial AV interval setting. It is understood that an initial AV interval setting may be selected at block 806 by first measuring an intrinsic AV interval in a patient having intact AV conduction, i.e. no AV block. An initial AV interval may be a default pacing interval, the last programmed AV interval, or a minimum or maximum AV interval to be tested. Alternatively, if the VV interval is selected for optimization, an intrinsic inter-ventricular conduction time may be measured first and paced VV intervals may be iteratively adjusted beginning at a VV interval longer, shorter or approximately equal to the intrinsic VV conduction time.
An iterative process for adjusting the selected test parameter to at least two different settings is performed. The parameter may be adjusted to different settings in any desired order, e.g., increasing, decreasing, random etc. For example, during adjustment of AV interval, an initial AV interval may be set to just longer than or approximately equal to a measured intrinsic AV conduction time then iteratively decreased down to a minimum AV interval test setting. During pacing using each pace parameter setting, HS signals are acquired at block 808. The iterative process advances to the next test parameter setting at block 812 until all test parameter settings have been applied, as determined at block 810, and HS signals have been recorded for each setting.
HS signals may be acquired for multiple cardiac cycles to enable ensemble averaging or averaging of HS parameter measurements taken from individual cardiac cycles. It is understood that amplification, filtering, rectification, noise cancellation techniques or other signal processing steps may be used for improving the signal-to-noise ratio of the HS signals and these steps may be different for each of the heart sounds being acquired, which may include any or all types of heart sounds.
At least one HS parameter measurement is determined from the recorded HS signals for each test parameter setting at block 814. The IMD processor or an external processor, e.g. included in a programmer, or a combination of both may perform the HS signal analysis described herein. In one embodiment, S1 and S2 are recorded and HS parameters are measured using the S1 and S2 signals at block 814. For example, the amplitude of S1, the V-S2 interval (where the V event may be a V pace or a sensed R-wave), and the S1-S2 interval are measured. The presence of S3 and/or S4 may additionally be noted or measurements of these signals may be made for determining related parameters. HS signal parameters are determined for at least two different test parameter settings, e.g. at least two different AV intervals, two or more different VV intervals, or two or more different pacing vectors.
At block 818, a trend for each HS parameter determined at block 810 as a function of the pace parameter test settings is determined. In one embodiment, a trend for each of the V-S2 interval, S1 amplitude and S1-S2 interval is determined. Other embodiments may include determining a separation of the M1 and T1 sounds during the S1 signal. Based on the trends of the HS parameter(s) with respect to the varied pace control parameter, an optimal pace parameter setting may be identified automatically by the processor at block 820. Additionally, alternatively, and/or optionally the HS trends are reported and displayed at block 822 on an external device such as programmer or at a remote networked computer.
If the pace parameter being tested is, for example, pacing site or pacing vector when a multipolar electrode is positioned along a heart chamber, such as a quadripolar lead along LV, a pacing site or vector may be selected based on maximizing a HS-based surrogate for ventricular contractility. In one embodiment, the amplitude of S1 is used as a surrogate for ventricular contractility, and a pacing site or vector associated with a maximum S1 is identified at block 820 as the optimal pacing vector setting.
Determining the trend of each HS parameter at block 818 may include determining whether the V-S2 interval trend presents a sudden slope change, e.g. from a substantially flat trend to a decreasing trend. An AV interval associated with a sudden change in the V-S2 interval trend may be identified as an optimal AV interval setting. The optimal AV interval may be further identified based on other HS trends, for example a maximum S1 amplitude and/or a maximum S1-S2 interval.
In some embodiments, an automatically-identified optimal pace parameter setting may also be automatically programmed in the IMD at block 824. In other embodiments, the clinician or user reviews the reported HS data and recommended pace parameter setting(s) and may accept a recommended setting or select another setting based on the HS data.
HS sensing module, or circuitry, may be operably coupled to the control circuit 80 (
Bioimpedance, or intracardiac impedance, may be measured and used to represent physiological response information. For example, any of the IMDs described herein may measure an intracardiac impedance signal by injecting a current and measuring a voltage between electrodes of an electrode vector configuration (e.g., selected electrodes). For example, the IMD may measure an impedance signal by injecting a current (e.g., a non-pacing threshold current) between a first electrode (e.g., LV electrode) and an electrode located in the RA and measuring a voltage between the first and second electrodes. One will recognize that other vector pair configurations may be used for stimulation and measurement. Impedance can be measured between any set of electrodes that encompass the tissue or cardiac chamber of interest. Thus, one can inject current and measure voltage to calculate the impedance on the same two electrodes (a bipolar configuration) or inject current and measure voltage on two separate pairs of electrodes (e.g., one pair for current injection and one pair for voltage sense), hence, a quadripolar configuration. For a quadripolar electrode configuration, the current injection and voltage sense electrodes may be in line with each other (or closely parallel to) and the voltage sense electrodes may be within the current sense field. In such embodiments, a VfA lead may be used for the LV cardiac therapy or sensing. The impedance vectors can be configured to encompass a particular anatomical area of interest, such as the atrium or ventricles.
The exemplary methods and/or devices described herein may monitor one or more electrode vector configurations. Further, multiple impedance vectors may be measured concurrently and/or periodically relative to another. In at least one embodiment, the exemplary methods and/or devices may use impedance waveforms to acquire selection data (e.g., to find applicable fiducial points, to allow extraction of measurements from such waveforms, etc.) for optimizing CRT.
As used herein, the term “impedance signal” is not limited to a raw impedance signal. It should be implied that raw impedance signals may be processed, normalized, and/or filtered (e.g., to remove artifacts, noise, static, electromagnetic interference (EMI), and/or extraneous signals) to provide the impedance signal. Further, the term “impedance signal” may include various mathematical derivatives thereof including real and imaginary portions of the impedance signal, a conductance signal based on the impedance (i.e., the reciprocal or inverse of impedance), etc. In other words, the term “impedance signal” may be understood to include conductance signals, i.e. signals that are the reciprocal of the impedance signal.
In one or more embodiments of the methods and/or devices described herein, various patient physiological parameters (e.g., intracardiac impedance, heart sounds, cardiac cycle intervals such as R-R interval, etc.) may be monitored for use in acquiring selection data to optimize CRT (e.g., set AV and/or VV delay, optimize cardiac contractility, for example, by using and/or measuring impedance first derivative dZ/dt, select pacing site, select pacing vector, lead placement, or assess pacing capture from both the electrical and mechanical points of view (e.g., electrical capture may not mean mechanical capture, and the heart sounds and impedance may assist in assessing whether the electrical stimulus captures the heart or not by looking at the mechanical information from the heart sounds and impedance), select an effective electrode vector configuration for pacing, etc.). For example, intracardiac impedance signals between two or more electrodes may be monitored for use in providing such optimization.
As shown, pacing therapy is delivered using one of the plurality of device options (block 852) (e.g., the plurality of device parameter options may be selected, determined and/or calculated AV delays, such as percentages of intrinsic AV delay, for example, 40% of intrinsic AV delay, 50% of intrinsic AV delay, 60% of intrinsic AV delay, 70% of intrinsic AV delay, 80% of intrinsic AV delay, etc.). For the device parameter option used to pace (block 852), selection data is acquired at each of a plurality of electrode vector configurations (e.g., intracardiac impedance is monitored over a plurality of cardiac cycles and selection data is extracted using such impedance signal). As indicated by the decision block 854, if selection data has not been acquired from all desired electrode vector configurations, then the loop of acquiring selection data (e.g., the loop illustrated by blocks 858, 860, 862, and 864) is repeated. If selection data has been acquired from all desired electrode vector configurations, then another different device parameter option is used to deliver therapy (block 856) and the method 850 of
As shown in the repeated loop of acquiring selection data for each of the desired electrode vector configurations (e.g., blocks 858, 860, 862, and 864), one of the plurality of electrode vector configurations is selected for use in acquiring selection data (block 858). Temporal fiducial points associated with at least a part of a systolic portion of at least one cardiac cycle and/or temporal fiducial points associated with at least a part of a diastolic portion of at least one cardiac cycle for the selected electrode vector configuration are acquired (block 860) (e.g., such as with use of heart sounds, analysis of impedance signal minimum and maximums, application of algorithms based on physiological parameters such as R-R intervals, etc.). For example, temporal fiducial points associated with the systolic and/or diastolic portions of the cardiac cycle may be acquired, temporal fiducial points associated with one or more defined segments within systolic and/or diastolic portions of the cardiac cycle may be acquired, and/or temporal fiducial points within or associated with one or more points and/or portions of a systolic and/or diastolic portion of the cardiac cycle may be acquired. Yet further, for example, temporal fiducial points associated with just the systolic portion or just the diastolic portion of the cardiac cycle may be acquired, temporal fiducial points associated with one or more defined segments within just the systolic portion or just the diastolic portion of the cardiac cycle may be acquired, and/or temporal fiducial points within or associated with one or more points and/or portions of just the systolic portion or just the diastolic portion of the cardiac cycle may be acquired. In other words, fiducial points may be acquired that are associated with either both the systolic and diastolic portions of the cardiac cycle or associated with just one of such portions of the cardiac cycle. Further, for example, such fiducial points may be representative or indicative of a measurement window and/or time period (e.g., interval, point, etc.) at or during which intracardiac impedance may be measured for use in analysis as described herein.
In about the same timeframe (e.g., about simultaneously with the acquired fiducial points), an intracardiac impedance signal is acquired at the selected electrode vector configuration (block 862). With the acquired fiducial points and the acquired intracardiac impedance signal, measurements from the impedance signal are extracted based on the temporal fiducial points (block 864) (e.g., integral of the impedance signal in a measurement window defined between fiducial points, maximum slope of impedance signal in a measurement window defined between fiducial points, time between the fiducial points, maximum impedance at a fiducial point, etc.). One or more of such measurements may be comparable to desired values for such measurements allowing for a determination of whether the measurement may indicate that the device parameter option may be an effective device parameter for optimizing therapy (e.g., a scoring algorithm may be used to determine if a device parameter option may be an optimal parameter based on whether a plurality of such measurements meet certain criteria or thresholds).
The measurement data for each of the device parameter options (e.g., obtained such as described in
An illustrative method 200 for monitoring effectiveness of left ventricular capture for use with, e.g., the illustrative systems and devices of
As shown, the method 200 includes monitoring effectiveness of left ventricular capture 210, determining whether effective or ineffective left ventricular capture exits 220, and adjusting the left ventricular pacing 230 if it is determined that the left ventricular pacing is not effective or is ineffective. As shown, the method 200 may continue to loop or be executed periodically to provide continuous monitoring of effectiveness of left ventricular capture. For example, monitoring effectiveness 210 may be continuously performed while determining whether effective or ineffective left ventricular capture exits 220 may be performed periodically or intermittently. Further, for example, monitoring effectiveness 210 may be continuously performed and determining whether effective or ineffective left ventricular capture exits 220 may be performed on the most current selected period of time (e.g., the last 10 cardiac cycles).
A more detailed flow diagram of one embodiment of method 200 depicted in
In particular, a selected period of time, selected time period, or time window, 254 following a left ventricular pace may be monitored using a near-field signal. For example, the near-field signal may be monitored using two or more electrodes of the VfA device. In particular, the tissue-piercing electrode implanted from the triangle of Koch region of the right atrium through the right atrial endocardium and central fibrous body may be one of the two electrodes. Another electrode may be a right atrial electrode positioned in the right atrium of the patient. In one embodiment, the right atrial electrode may be positioned in contact with the right atrial septum or other atrial tissue, and in another embodiment, the right atrial electrode may be positioned in the right atrium without contacting the right atrial tissue (e.g., “free floating” in the right atrium). Nonetheless, the electrical signal monitored may be referred to as a near-field signal because, e.g., the signal is not monitored using any electrodes positioned outside or far away from the heart.
The selected period of time, selected time, period, or time window, 254 following the left ventricular pace may be between about 40 milliseconds and about 150 milliseconds. In one embodiment, the selected period of time is about 84 milliseconds.
The electrogram of the near-field signal over the selected period of time may be evaluated using one or more various metrics or comparisons. For example, various morphological features and timings of such morphological features may be analyzed. In particular, one or more of amplitudes at baseline immediately before or at the time of delivery of pacing, minimum values of amplitude relative to the baseline amplitude, maximum values relative to the baseline amplitude, times of occurrence of the minimum value, minimum or maximum values occurring first or last, minimum or maximum values occurring during selected durations or following other events, slopes (first derivatives), second derivatives, absolute minimums or maximums, etc. may be used to analyze the near-field electrogram for use in determining effective capture of the left ventricle.
A portion of illustrative monitored near-field electrogram 250 following a ventricular pace for use in determining effectiveness of left ventricular capture is depicted in
The absolute baseline amplitude 251 may be used to determine effectiveness of left ventricular capture of the left ventricular pacing therapy 216. The baseline amplitude 251 may be defined as the amplitude immediately before or at the time pace is delivered. The absolute baseline amplitude 251 may be compared to an absolute baseline threshold value. The absolute baseline threshold value may be between about 0 millivolts and about 1 millivolts. In one embodiment, the absolute baseline threshold value is 0.63 millivolts. If the absolute baseline amplitude 251 is less than the absolute baseline threshold, then it may be determined that effective left ventricular capture is occurring.
The minimum negative deflection 252 within a selected negative deflection time period may be used to determine effectiveness of left ventricular capture of the left ventricular pacing therapy 216. In particular, the minimum negative deflection 252 may be compared to a minimum threshold value. The minimum threshold value may be between about 1 millivolts and about 10 millivolts. In one embodiment, the minimum threshold value is 1 millivolts. If the minimum negative deflection 252 is less than the minimum threshold (in other words, more negative than the minimum threshold), then it may be determined that effective left ventricular capture is occurring.
Additionally, as mentioned, the minimum negative deflection 252 is evaluated within, or taken from, a selected negative deflection time period. The selected negative deflection time period may be between about 40 milliseconds and about 100 milliseconds following the left ventricular pace. In one embodiment, the selected negative deflection time period is 84 milliseconds.
The time period between the left ventricular pace and the minimum negative deflection, or the timing of the minimum negative deflection, 253 may be used to determine effectiveness of left ventricular capture of the left ventricular pacing therapy 216. In particular, the time period between the left ventricular pace and the minimum negative deflection 253 may be compared to an interval threshold. The interval threshold may be between about 40 milliseconds and about 60 milliseconds. In one embodiment, the interval threshold is 45 milliseconds. If the time period between the left ventricular pace and the minimum negative deflection 253 is less than the interval threshold, then it may be determined that effective left ventricular capture is occurring.
The relative order of occurrence of the maximum amplitude and minimum amplitude within the selected time period 254 may be used to determine effectiveness of left ventricular capture of the left ventricular pacing therapy 216. For example, if the occurrence, or timing, of the minimum amplitude precedes, or occurs before, the occurrence, or timing, of the maximum amplitude, then it may be determined that effective left ventricular capture is occurring. In other words, if a minimum negative deflection of the monitored electrical activity occurs prior to a maximum positive deflection of the monitored electrical activity, then it may be determined that effective left ventricular capture is occurring. In one embodiment, a negative, or minimum, deflection time stamp corresponding to the minimum negative deflection or amplitude may be compared to a positive, or maximum, deflection time stamp corresponding to the maximum positive deflection or amplitude.
As such, four illustrative criteria or metrics are described herein for use in determining effectiveness of left ventricular capture of a left ventricular pace. These four illustrative criteria or metrics may be each used by themselves or in conjunction with each other. For example, a pace may be determined to have effectively captured the left ventricle if all four of the illustrative criteria have been met. In other embodiments, meeting less than all four criteria such as two of the four or three of the four criteria may indicate effective capture.
Thus, the effectiveness of capture of the left ventricular pace may be determined 216, and the method or process 210 may continuously loop (as indicated by the arrow extending form the process 216 to process 212) thereby monitoring and evaluating the capture of each left ventricular pace. In effect, an amount of effective left ventricular paces may be counted over a plurality of paced and/or intrinsic (e.g., unpaced) heart beats depending on the particular cardiac therapy being delivered. Such a count over an elapsed time period (e.g., one day or longer, a week or longer, device life-time, time period since last device interrogation, etc.) may be expressed on a device programmer interface as a diagnostic of effective left ventricular pacing.
The exemplary method 200 may further adjust the left ventricular pacing 230 if it is determined that the left ventricular pacing does not have effective capture. Such determination to adjust may occur over a plurality of paces or cardiac cycles to, e.g., eliminate anomalies, etc.
Further, different therapies may have different kinds of adjustments of left ventricular pacing therapy for improving effective capture over time. As shown in
Thus, evaluation of the effectiveness of left ventricular pacing over a plurality of cardiac cycles may be used to determine whether to adjust pacing in DDD(r) cardiac therapy. This metric may be described as being “rolling” such that it may evaluate the previous m cardiac cycles on a continual basis. Additionally, process 222 may be described in terms of a selected percentage of effective left ventricular paces over the past m cardiac cycles. For example, if at least 90 left ventricular paces are determined to be effective over the past 100 left ventricular paced cardiac cycles, then it may be determined that the DDD(r) cardiac therapy has effective left ventricular capture and does not need adjustment. Conversely, if less than 90 left ventricular paces are determined to be effective over the past 100 left ventricular paced cardiac cycles, then it may be determined that the DDD(r) cardiac therapy does not have adequate left ventricular capture and should be adjusted 232.
For instance, the left ventricular pacing amplitude may be increased 232 by a selected value or a selected percentage. The selected value may be between about 0.25 millivolts and about 1 millivolts. In one embodiment, the selected value is 0.5 millivolts. Additionally, the left ventricular pacing amplitude may be increased until a threshold, limit, or boundary is reached. In other words, an upper threshold may be used such that the amplitude may be increased until it reaches the upper threshold. The upper threshold may be between 4 mV and 10 mV. In one embodiment, the upper threshold is 6 about mV.
In other embodiments, instead of or in conjunction with increasing pacing amplitude, one or more other pacing settings may be increased or adjusted such as pulse width, pulse frequency, etc.
Further, the A-V delay may be adjusted 232. As used herein, the term “A-V delay” or “AV pacing interval” refers to a determined delay between atrial activation (As or Ap) and timing of delivery of ventricular pacing (Vp), wherein the atrial activation may include an intrinsic atrial activation (As), or atrial sense, or a paced atrial activation (Ap). Specifically, the A-V delay (which may include a plurality of different A-V delays corresponding to a plurality of different heartrates) may be decreased by a selected amount or selected percentage. For example, the A-V delay may be decreased by 10 milliseconds until effective left ventricular is captured or a lower bound is reached such as, e.g., 60 milliseconds for As and 70 milliseconds for Ap. Further, for example, the A-V delay may be decreased by 5% until effective left ventricular is captured or a lower bound is reached.
In some embodiments, the amplitudes, A-V delays, and other paced settings may be adjusted 232 until left ventricular capture is obtained, which may be determined using the same or similar processes as monitoring the effectiveness of left ventricular capture 210. After the left ventricular pacing has been adjusted to achieve effective capture, the method may return to monitoring the effectiveness of left ventricular capture 210. Additionally, it is be understood that monitoring the effectiveness of left ventricular capture 210 may be occurring continuously even while other processes of the method are being executed. In other words, monitoring the effectiveness of left ventricular capture 210 may be a permanent process that is always running.
Further as shown in
Thus, evaluation of the effectiveness of a left ventricular pace and intrinsic activity over a plurality of cardiac cycles may be used to determine whether to adjust pacing in VVI(r) cardiac therapy. This metric, similar to those used in DDD(r) therapy, may be described as being “rolling.”
For example, if at least 90 left ventricular paces are determined to be effective over the past 100 cardiac cycles including paced and intrinsic cardiac cycles, then it may be determined that the VVI(r) cardiac therapy has effective left ventricular capture and does not need adjustment. Conversely, if less than 90 left ventricular paces and if at least 10 intrinsic left ventricular activation are determined to be effective over the past 100 cardiac cycles, then it may be determined that the VVI(r) cardiac therapy does not have adequate left ventricular capture and should be adjusted 234. Additionally, process 224 may be described in terms of a selected percentage of effective left ventricular paces over the past m cardiac cycles and a selected percentage of effective intrinsic activations over the past m cardiac cycles.
The adjustment of the VVI(r) cardiac therapy may include adjusting the heart rate 232 using, e.g., a heart rate delay. For example, the heart rate delay, or LV-LV timing, may be decreased to obtain an increase in heartrate by, e.g., 10 beats per minute, until either effective left ventricular capture is obtained or a limit is reached such as, e.g., 130 beats per minute. In other embodiments, the heart rate delay may be decreased by a selected percentage until either effective left ventricular capture is obtained or a limit is reached. After the left ventricular pacing has been adjusted to achieve effective capture, the method may return to monitoring the effectiveness of left ventricular capture 210.
Still further, in VVI cardiac therapy, a number, n, of effective left ventricular paces over a number, m, of cardiac cycles and whether or not any intrinsic left ventricular activated were sensed over a number, m, of cardiac cycles 226 may be used to determine whether effective left ventricular capture is occurring. In other words, a determination 226 of whether a first amount of left ventricular paces have not achieved effective left ventricular capture and a determination that no intrinsic left ventricular activations have been sensed may be executed.
Thus, evaluation of the effectiveness of a left ventricular pace and intrinsic activity over a plurality of cardiac cycles may be used to determine whether to adjust pacing in VVI cardiac therapy. This metric, similar to those used in DDD(r) therapy, may be described as being “rolling.”
For example, if at least 90 left ventricular paces are determined to be effective over the past 100 cardiac cycles, then it may be determined that the VVI cardiac therapy has effective left ventricular capture and does not need adjustment. Conversely, if less than 90 left ventricular paces are determined to be effective and no intrinsic left ventricular activation have been sensed over the past 100 cardiac cycles, then it may be determined that the VVI cardiac therapy does not have adequate left ventricular capture and should be adjusted 236. The adjustment 236 of the VVI cardiac therapy may include adjusting pacing output including pacing amplitude and/or another paced setting which may be similar to the adjustment process 232 described herein with respect to DDD(r) pacing. After the left ventricular pacing has been adjusted to achieve effective capture, the method may return to monitoring the effectiveness of left ventricular capture 210.
Additionally, an alert may be issued if ineffective left ventricular tissue capture is determined by one or more processes as show in
Embodiment 1: An implantable medical device comprising:
Embodiment 2: A method comprising:
Embodiment 3: The embodiment as in any one of embodiments 1-2, wherein monitoring electrical activity of the left ventricle using the tissue-piercing electrode following the left ventricular pace comprises monitoring electrical activity of the left ventricle using the tissue-piercing electrode and the right atrial electrode.
Embodiment 4: The embodiment as in any one of embodiments 1-3, wherein determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity comprises comparing an absolute baseline amplitude of the monitored electrical activity to an absolute baseline amplitude threshold.
Embodiment 5: The embodiment as in any one of embodiments 1-4, wherein determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity comprises comparing a minimum negative deflection within a selected time period following the left ventricular pace to a minimum threshold.
Embodiment 6: The embodiment as in any one of embodiments 1-5, wherein determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity comprises comparing a time period between the left ventricular pace and a minimum negative deflection to an interval threshold.
Embodiment 7: The embodiment as in any one of embodiments 1-6, wherein determining effectiveness of left ventricular tissue capture of the left ventricular pace based on the monitored electrical activity comprises determining whether a minimum negative deflection of the monitored electrical activity occurs prior to a maximum positive deflection of the monitored electrical activity.
Embodiment 8: The embodiment as in any one of embodiments 1-7, wherein the controller is further configured to execute or the method further comprises:
Embodiment 9: The embodiments as in embodiment 8, wherein determining that effective left ventricular capture is not occurring based on the monitored of effectiveness of left ventricular capture over the plurality of cardiac cycles comprises determining whether a first amount of left ventricular paces have not achieved effective left ventricular tissue capture over a second amount of cardiac cycles.
Embodiment 10: The embodiment as in any one of embodiments 8-9, wherein adjusting left ventricular pacing comprises adjusting one or both of a left ventricular pacing amplitude of the left ventricular pace and a delay between an atrial sense or pace and the left ventricular pace until effective left ventricular tissue capture of the left ventricular pace is determined.
Embodiment 11: The embodiments as in embodiment 8, wherein determining that effective left ventricular capture is not occurring based on the monitored of effectiveness of left ventricular capture over the plurality of cardiac cycles comprises:
Embodiment 12: The embodiments as in embodiment 11, wherein, in response to determining that the first amount of left ventricular paces did not achieve effective left ventricular capture and that the third amount of intrinsic left ventricular activations have been sensed, adjusting left ventricular pacing comprises:
adjusting a heart rate delay between a left ventricular sense or pace and the following left ventricular pace until effective left ventricular tissue capture of the left ventricular pace is determined.
Embodiment 13: The embodiments as in embodiment 11, wherein, in response to determining that the first amount of left ventricular paces have not achieved effective left ventricular capture and that no intrinsic left ventricular activations have been sensed, adjusting left ventricular pacing comprises:
adjusting a left ventricular pacing amplitude of the left ventricular pace until effective left ventricular tissue capture of the left ventricular pace is determined.
Embodiment 14: The embodiment as in any one of embodiments 1-13, wherein the controller is further configured to execute or the method further comprises issuing an alert if ineffective left ventricular tissue capture is determined.
Embodiment 15: The embodiment as in any one of embodiments 1-14, wherein monitoring effectiveness of left ventricular capture comprises periodically monitoring effectiveness of left ventricular capture over a selected amount of cardiac cycles.
Embodiment 16: An implantable medical device comprising:
Various aspects disclosed herein may be combined in different combinations than the combinations specifically presented in the description and accompanying drawings. It should also be understood that, depending on the example, certain acts or events of any of the processes or methods described herein may be performed in a different sequence, may be added, merged, or left out altogether (e.g., all described acts or events may not be necessary to carry out the techniques). In addition, while certain aspects of this disclosure are described as performed by a single module or unit for purposes of clarity, the techniques of this disclosure may be performed by a combination of units or modules associated with, for example, a medical device.
In one or more examples, the described techniques may be implemented in hardware, software, firmware, or any combination thereof. If implemented in software, the functions may be stored as one or more instructions or code on a computer-readable medium and executed by a hardware-based processing unit. Computer-readable media may include non-transitory computer-readable media, which corresponds to a tangible medium such as data storage media (e.g., RAM, ROM, EEPROM, flash memory, or any other medium that can be used to store desired program code in the form of instructions or data structures and that can be accessed by a computer).
Instructions may be executed by one or more processors, such as one or more digital signal processors (DSPs), general purpose microprocessors, application specific integrated circuits (ASICs), field programmable logic arrays (FPGAs), or other equivalent integrated or discrete logic circuitry. Accordingly, the term “processor” as used herein may refer to any of the foregoing structure or any other physical structure suitable for implementation of the described techniques. Also, the techniques could be fully implemented in one or more circuits or logic elements.
All references and publications cited herein are expressly incorporated herein by reference in their entirety for all purposes, except to the extent any aspect incorporated directly contradicts this disclosure.
All scientific and technical terms used herein have meanings commonly used in the art unless otherwise specified. The definitions provided herein are to facilitate understanding of certain terms used frequently herein and are not meant to limit the scope of the present disclosure.
Unless otherwise indicated, all numbers expressing feature sizes, amounts, and physical properties used in the specification and claims may be understood as being modified either by the term “exactly” or “about.” Accordingly, unless indicated to the contrary, the numerical parameters set forth in the foregoing specification and attached claims are approximations that can vary depending upon the desired properties sought to be obtained by those skilled in the art utilizing the teachings disclosed herein or, for example, within typical ranges of experimental error.
The recitation of numerical ranges by endpoints includes all numbers subsumed within that range (e.g. 1 to 5 includes 1, 1.5, 2, 2.75, 3, 3.80, 4, and 5) and any range within that range. Herein, the terms “up to” or “no greater than” a number (e.g., up to 50) includes the number (e.g., 50), and the term “no less than” a number (e.g., no less than 5) includes the number (e.g., 5).
The terms “coupled” or “connected” refer to elements being attached to each other either directly (in direct contact with each other) or indirectly (having one or more elements between and attaching the two elements). Either term may be modified by “operatively” and “operably,” which may be used interchangeably, to describe that the coupling or connection is configured to allow the components to interact to carry out at least some functionality (for example, a first medical device may be operatively coupled to another medical device to transmit information in the form of data or to receive data therefrom).
Terms related to orientation, such as “top,” “bottom,” “side,” and “end,” are used to describe relative positions of components and are not meant to limit the orientation of the embodiments contemplated. For example, an embodiment described as having a “top” and “bottom” also encompasses embodiments thereof rotated in various directions unless the content clearly dictates otherwise.
Reference to “one embodiment,” “an embodiment,” “certain embodiments,” or “some embodiments,” etc., means that a particular feature, configuration, composition, or characteristic described in connection with the embodiment is included in at least one embodiment of the disclosure. Thus, the appearances of such phrases in various places throughout are not necessarily referring to the same embodiment of the disclosure. Furthermore, the particular features, configurations, compositions, or characteristics may be combined in any suitable manner in one or more embodiments.
As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” encompass embodiments having plural referents, unless the content clearly dictates otherwise. As used in this specification and the appended claims, the term “or” is generally employed in its sense including “and/or” unless the content clearly dictates otherwise.
As used herein, “have,” “having,” “include,” “including,” “comprise,” “comprising” or the like are used in their open-ended sense, and generally mean “including, but not limited to.” It will be understood that “consisting essentially of” “consisting of,” and the like are subsumed in “comprising,” and the like.
The term “and/or” means one or all the listed elements or a combination of at least two of the listed elements.
The phrases “at least one of,” “comprises at least one of,” and “one or more of” followed by a list refers to any one of the items in the list and any combination of two or more items in the list.
This application is a divisional application of U.S. application Ser. No. 16/583,591, filed Sep. 26, 2019, now allowed, which claims the benefit of U.S. Provisional Application Ser. No. 62/736,905, filed Sep. 26, 2018, both of which are incorporated herein by reference in their entirety. The present disclosure is generally related to medical implantable devices and methods for ventricle-from-atrium (VfA) cardiac therapy. More specifically, the devices and methods relate to left ventricular capture using VfA cardiac therapy. The cardiac conduction system includes the sinus atrial (SA) node, the atrioventricular (AV) node, the bundle of His, bundle branches and Purkinje fibers. A heart beat is initiated in the SA node, which may be described as the natural “pacemaker” of the heart. An electrical impulse arising from the SA node causes the atrial myocardium to contract. The electrical impulse, or electrical pulse or signal, is conducted to the ventricles via the AV node which inherently delays the conduction to allow the atria to stop contracting before the ventricles begin contracting thereby providing proper AV synchrony. The electrical impulse is conducted from the AV node to the ventricular myocardium via the bundle of His, bundle branches, and Purkinje fibers. Patients with a conduction system abnormality, such as poor AV node conduction or poor SA node function, may receive an implantable medical device (IMD), such as a pacemaker, to restore a more normal heart rhythm and AV synchrony. Some types of IMDs, such as cardiac pacemakers, implantable cardioverter defibrillators (ICDs), or cardiac resynchronization therapy (CRT) devices, provide therapeutic electrical stimulation to a heart of a patient via electrodes on one or more implantable endocardial, epicardial, or coronary venous leads that are positioned in or adjacent to the heart. The therapeutic electrical stimulation may be delivered to the heart in the form of pulses or shocks for pacing, cardioversion, or defibrillation. In some cases, an IMD may sense intrinsic depolarizations of the heart, and control the delivery of therapeutic stimulation to the heart based on the sensing. Delivery of therapeutic electrical stimulation to the heart can be useful in addressing cardiac conditions such as ventricular dyssynchrony that may occur in patients. Ventricular dyssynchrony may be described as a lack of synchrony or a difference in the timing of contractions in the right and left ventricles of the heart. Significant differences in timing of contractions can reduce cardiac efficiency. CRT, delivered by an IMD to the heart, may enhance cardiac output by resynchronizing the electromechanical activity of the ventricles of the heart. CRT may include “triple chamber pacing” when pacing the right atrium, right ventricle, and left ventricle. Cardiac arrhythmias may be treated by delivering electrical shock therapy for cardioverting or defibrillating the heart in addition to cardiac pacing, for example, from an ICD, which may sense a patient's heart rhythm and classify the rhythm according to an arrhythmia detection scheme in order to detect episodes of tachycardia or fibrillation. Arrhythmias detected may include ventricular tachycardia (VT), fast ventricular tachycardia (FVT), ventricular fibrillation (VF), atrial tachycardia (AT) and atrial fibrillation (AT). Anti-tachycardia pacing (ATP) can be used to treat ventricular tachycardia (VT) to substantially terminate many monomorphic fast rhythms. Dual chamber medical devices are available that include a transvenous atrial lead carrying electrodes that may be placed in the right atrium and a transvenous ventricular lead carrying electrodes that may be placed in the right ventricle via the right atrium. The dual chamber medical device itself is generally implanted in a subcutaneous pocket and the transvenous leads are tunneled to the subcutaneous pocket. A dual chamber medical device may sense atrial electrical signals and ventricular electrical signals and can provide both atrial pacing and ventricular pacing as needed to promote a normal heart rhythm and AV synchrony. Some dual chamber medical devices can treat both atrial and ventricular arrhythmias. Intracardiac medical devices, such as a leadless pacemaker, have been introduced or proposed for implantation entirely within a patient's heart, eliminating the need for transvenous leads. A leadless pacemaker may include one or more electrodes on its outer housing to deliver therapeutic electrical signals and/or sense intrinsic depolarizations of the heart. Intracardiac medical devices may provide cardiac therapy functionality, such as sensing and pacing, within a single chamber of the patient's heart. Single chamber intracardiac devices may also treat either atrial or ventricular arrhythmias or fibrillation. Some leadless pacemakers are not intracardiac and may be positioned outside of the heart and, in some examples, may be anchored to a wall of the heart via a fixation mechanism. In some patients, single chamber devices may adequately address the patient's needs. However, single chamber devices capable of only single chamber sensing and therapy may not fully address cardiac conduction disease or abnormalities in all patients, for example, those with some forms of AV dyssynchrony or tachycardia. Dual chamber sensing and/or pacing functions, in addition to ICD functionality in some cases, may be used to restore more normal heart rhythms.
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| Number | Date | Country | |
|---|---|---|---|
| 20220111217 A1 | Apr 2022 | US |
| Number | Date | Country | |
|---|---|---|---|
| 62736905 | Sep 2018 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 16583591 | Sep 2019 | US |
| Child | 17559092 | US |
