Implantable pacemaker/cardioverter/defibrillator device for incorporating multiple bradycardia support pacing rates

Abstract: An implantable cardioverting/defibrillating pacemaker and method for treating arrhythmias of a patient's heart are disclosed. Bradycardia support pacing is initially provided at a normal standby rate, in the absence of a tachycardia. Upon detection and confirmation of a tachycardia, antitachycardia therapy in the form of antitachycardia pacing pulse therapy and/or cardioversion or defibrillation therapy is delivered to the heart. Thereafter, upon reversion of the tachycardia, bradycardia support pacing is again delivered to the heart but at a greater rate than the earlier normal standby rate and only for a predetermined time period. At the end of such time period, the bradycardia support pacing rate is returned to the normal standby rate, either directly or in decremental steps.

Description: TECHNICAL FIELD This invention relates to implantable medical devices which deliver energy to cardiac tissue in an attempt to revert tachycardia and restore a normal sinus rhythm to a patient, and, more particularly, to those of such devices which are provided with multiple bradycardia support pacing rates. BACKGROUND ART Implantable pacemaker/defibrillator devices are well known to the medical profession. One early example of such a device is U.S Patent No. 3,857,398 to L. Rubin. The Rubin device utilizes separate circuitries in dealing with the different functions of pacing and defibrillation. There is no provision in the Rubin device for changing the bradycardia standby rate. All of Rubin's bradycardia pacing pulses are apparently delivered at the same rate. Many advances have been made after Rubin in the development of devices and techniques for providing effective medical responses to a variety of heart disorders of arrhythmias. Recent efforts have resulted in the development of more sophisticated implantable pacing and defibrillating devices. One example of such a device is disclosed in U.S Patent No. 4,869,252 to N. L. Gilli, entitled "Apparatus and Method for Controlling Pulse Energy in Anti-tachyarrhythmia and Bradycardia Pacing Device". This Patent discloses an apparatus which provides bradycardia support pacing at different energy levels, including a higher pulse energy for a period following successful antitachycardia therapy, and a lower level during normal bradycardia support pacing. Capture is more efficient at the higher energy level since the heart has been traumatized by the tachycardia and/or the antitachycardia therapy. In the Gilli patent, again, the bradycardia therapy is delivered at a constant programmed standby rate. The implantable pacing and defibrillating device disclosed in U.S. Patent No. 4,940,054 to R. Grevis et al., entitled "Apparatus and Method for Controlling Multiple Sensitivities in Arrhythmia Control System Including Post Therapy Pacing Delay," is another example of a more sophisticated device of this type. Following antitachycardia therapy, which may be antitachycardia pacing or cardioversion/defibrillation, there is a pause or post therapy delay for a period of time substantially greater than a normal standby interval prior to the commencement of bradycardia support pacing. However, when bradycardia support pacing is required after antitachycardia therapy, it is delivered at a constant rate. A problem that is common to all existing antitachyarrhythmia devices is their failure, after reverting tachycardias, to compensate patients who are dependent on bradycardia support pacing for the hemodynamic compromise resulting from the tachycardia and/or the antitachycardia therapy. A tachycardia and/or antitachycardia therapy can temporarily reduce the heart's pumping efficiency. If so, the hemodynamic competence of a bradycardia support pacing-dependent patient being paced at a constant standby rate is impaired for as long as the pumping efficiency remains reduced. This can be traumatic to a patient and presents a real problem to some patients that are currently using existing devices. The standby rate of normal bradycardia support pacing therapy is a programmable parameter in the antitachyarrhythmia devices disclosed in US Patents 4,869,252 and 4,940,054, referred to above, but remains at a fixed value for a particular patient for all such therapy delivered to that patient. US Patent Specification 4587970 relates to an apparatus for treating arrhythmias of a patient's heart, comprising: bradycardia pulse therapy means for delivering bradycardia pacing pulses to the heart at a programmable standby rate; detection means for detecting the presence of a tachycardia of the heart; antitachycardia therapy means responsive to said detection means for delivering antitachycardia therapy to the heart to revert said tachycardia; and bradycardia pacing rate setting means for setting the rate of said bradycardia pacing pulses at a normal pacing rate value and setting said bradycardia pacing rate to at least one other standby rate value for bradycardia pacing after reversion of a tachycardia. It is therefore a primary object of the present invention to provide an improved apparatus for treating cardiac arrhythmias which, following reversion from tachycardia compensate for hemodynamic compromise experienced during tachycardia and/or following antitachycardia therapy. It is a further object of the invention to provide an improved apparatus for treating cardiac arrhythmias which delivers antitachycardia pacing therapy and cardioversion/defibrillation therapy when needed and includes temporarily increasing the bradycardia support pacing rate following the delivery of antitachycardia therapy. Further objects and advantages of this invention will become apparent as the following description proceeds. According to the present invention, there is provided an apparatus for treating arrhythmias of a patient's heart with the features of claim 1. BRIEF DESCRIPTION OF THE DRAWINGS While the specification concludes with claims particularly pointing out and distinctly claiming the subject matter regarded as the invention herein, it is believed that the present invention will be more readily understood upon consideration of the following detailed description, taken in conjunction with the accompanying drawings, in which: FIG. 1 is a block diagram of an arrhythmia control system in which the present invention may be used; FIG. 2 is a block diagram of a pacemaker utilized in FIG. 1; FIG. 3 is a block diagram of a microprocessor utilized in FIG. 1; and FIG. 4 is a logic flow diagram of software executed by the microprocessor of FIG. 3 in accordance with the present invention. BEST MODE FOR CARRYING OUT THE INVENTION As used herein, the term "antitachycardia pacing" includes any pacing used for the reversion of tachycardia. The term "tachycardia" refers to any fast abnormal rhythm of the heart which may be amenable to treatment by electrical discharges, and specifically includes ventricular tachycardia (VT), supraventricular tachycardia (SVT), ventricular flutter and/or ventricular fibrillation (VF). The term "therapy" as used herein includes the process-used between the detection and reversion of a tachyarrhythmia and includes the actions of antitachycardia pacing, cardioversion shock and defibrillation shock The term "cardioversion" refers to the discharge of electrical energy into cardiac tissue in an attempt to terminate or revert a tachyarrhythmia. This may take the form of a high energy discharge (up to 40 Joules or more) or a low energy discharge (less than 1 Joule). Cardioversion shocks may or may not be synchronized to the rhythm of the heart. Defibrillation is a particular example of cardioversion. This invention applies equally to devices which deliver energy synchronized to an R-wave and to those that do not, and applies to devices which use lower energy pulses (up to 1 Joule) as well as to devices which use higher energy pulses (up to 40 Joules or more). The invention applies to devices which deliver cardioverting shocks alone, as well as to devices which deliver antitachycardia pacing pulses alone or in a combination with cardioverting shocks. The invention will usually apply to ventricular implantable cardioverters, but is equally applicable to atrial cardioverters or multiple chamber cardioverters or defibrillators. The invention applies also to the delivery of any antitachycardia pacing pulse and post-reversion pacing therapy. Referring to FIG.1, there is depicted a block diagram of an arrhythmia control system 10. System 10 is designed to be implantable and includes a pulse module 11 and appropriate leads. More particularly, system 10 will generally include: a cardiac lead 12 connected to the patient's heart 14; a pacemaker 15 for the detection of analog signals representing cardiac electrical activity and for the delivery of pacing pulses to the heart; a microprocessor 16 which, in response to various inputs received from the pacemaker 15 as well as from a defibrillator 17, performs various operations so as to generate different control and data outputs to both pacemaker 15 and defibrillator 17; and a power supply 18 for the provision of a reliable voltage level to pacemaker 15, microprocessor 16 and defibrillator 17 by suitable electrical conductors (not shown). Defibrillator 17 produces a high voltage to charge its capacitors and then discharges them in response to control signals from microprocessor 16. A defibrillator electrode lead 19 transfers the energy of a defibrillator shock 20 from the implanted pulse module to the surface of the heart 14. Microprocessor 16 is connected to an external memory 21 by an address and data bus 22. An end-of-life (EOL) signal line 24 is used to provide, to microprocessor 16, a logic signal indicative of the approach of battery failure in power supply 18. As more fully described below, microprocessor 16 and pacemaker 15 are connected by a communication bus 25, a sense line 26, a pace control line 27, a sensitivity control bus 28, and a pacing rate control bus 29. As also more fully described below, microprocessor 16 is connected to defibrillator 17 by a charge voltage level line 30, a charge control bus 31, a shock control bus 32, and a dump control bus 34. Referring to FIG.2, pacemaker 15 comprises pacing circuit 35 which includes a pacing pulse generator 36, sensing circuit 37, and telemetry circuit 38. In addition, there is a control block 39 which includes an interface to microprocessor 16. In operation, sensing circuit 37 detects analog signals 45 from the heart 14 and converts the detected signals to digital signals. In addition, sensing circuit 37 receives an input sense control signal (which determines the sensitivity of the detection circuits in sensing circuit 37) by way of a sense control bus 41 from control block 39. A change in this sensitivity will affect the voltage deviation required at the sensing electrode for a sense to be registered in sensing circuit 37. The operation of the logic which changes the sensitivity is described in more detail in the aforementioned U.S. Patent No. 4,940,054. Pacing circuit 35 also receives inputs from control block 39, including a pace control and a pacing rate control by way of pacing control bus 42 which carries the signals on pace control line 27 and pacing rate control bus 29. The pace control determines the type of pacing to occur and the bradycardia standby rate is established by the pacing rate control. Pacing circuit 35 causes pulse generator 36 to generate pacing pulses 44 which are delivered to the patient's heart 14 by means of cardiac lead 12. Telemetry circuit 38 provides a bi-directional link between control block 39 of pacemaker 15 and an external device such as an external programmer (not shown). It allows data such as the operating parameters to be read from or altered in the implanted pulse module 11 (FIG. 1). Referring to FIG. 3, microprocessor 16 comprises two 16-bit timers 47 and 48, a CPU 49, a vectored interrupt block 50, a RAM 54, a ROM 55, a ports interface 57 and an internal communication bus 58. RAM 54 acts as a scratch pad memory during execution of the various programs stored in ROM 55 and used by microprocessor 16. These programs include system supervisory programs, detection algorithms, and programming implementing the logic flow diagram of FIG. 4, as well as storage programs for storing, in external memory 21, data concerning the functioning of module 11 and the electrogram provided by cardiac lead 12. Timers 47 and 48 and associated control software implement some timing functions required by microprocessor 16 without resorting entirely to software, thus reducing computational loads on and power dissipation by CPU 49. Signals received from telemetry circuit 38 permit the external programmer to change the operating parameters of pacemaker 15 by supplying appropriate signals to control block 39. Communication bus 25 serves to provide signals indicative of such control to microprocessor 16. Thus, it is also possible for an external programmer to control operation of defibrillator 17 by means of signals provided to microprocessor 16. Appropriate telemetry commands may cause telemetry circuit 38 to transmit data to the external programmer. Data stored is read out, by microprocessor 16, on to communication bus 25, through control block 39 in pacemaker 15, and into telemetry circuit 38 for transmission to the external programmer by a transmitter in the telemetry circuit. Microprocessor 16 receives various status and/or control inputs from pacemaker 15 and defibrillator 17. During normal pacer operations the input signal to pacemaker 15 is a sense signal on sense line 26 which is used by microprocessor 16 to perform operations such as arrhythmia detection. Microprocessor 16 produces outputs such as the pace control on pace control line 27 which determines the type of pacing to take place. Other pacemaker control outputs generated by microprocessor 16 include a pacing rate control signal on pacing rate control bus 29 which determines the bradycardia standby rate, and a sensitivity control signal on sensitivity control bus 28, which determines the sensitivity setting of the sensing circuit. Microprocessor 16 provides to defibrillator 17 a shock control signal on shock control bus 32 which indicates that a shock is to be delivered to the patient, a dump control signal on dump control bus 34 which indicates that a shock is to be dumped at an internal load within defibrillator 17, and a charge control signal on charge control bus 31 which determines the voltage level of the shock to be delivered. Charge voltage level line 30 provides a digital signal representative of charge voltage from an analog to digital converter within defibrillator 17, thus providing a feedback loop which assures that a shock of proper energy level is delivered by defibrillator 17. FIG. 4 is a logic diagram of the microprocessor flow control for changing pulse energies and pacing rates. The start is shown at 80, and at 81 the pacing rate is set to a predetermined programmed normal value. At 82 a determination is made as to whether a bradycardia condition exists. If it does, then bradycardia support pacing is delivered at this normal pacing rate, as shown at 83. If there is no bradycardia condition, as shown at 82B, then branching occurs based on whether or not there is a tachyarrhythmia condition, as shown at 84. If there is no detection of a tachyarrhythmia condition, as shown at 84A, then the program proceeds to logic block 94 (to be described hereinafter) and either loops back through 82 or 80, depending on the decision made at 94. If a tachyarrhythmia condition is detected at 84, as shown at 84B, then a follow-up check is made for confirmation of the tachyarrhythmia, as shown at 85. If a tachyarrhythmia condition is not confirmed, as shown at 85A, then the program proceeds to logic block 94 and either loops back to 82 or 80, depending on the decision made at 94. If a tachyarrhythmia condition is confirmed, as shown at 85B, then antitachyarrhythmia therapy is delivered to the patient, as shown at 87. Following delivery of such therapy, a determination is made at 88 as to whether or not the tachyarrhythmia has been reverted. If the tachyarrhythmia condition has not been reverted, as shown at 88B, then further antitachyarrhythmia therapy is delivered at 87. The therapy continues until reversion takes place at 88A, or for a given limited time, as determined at 89 and as more fully explained below. Reversion of a tachyarrhythmia at 88A starts a post-pacing timer at 90. As long as the time elapsed following reversion does not exceed a predetermined time interval, the pacing rate is set to a predetermined programmed high value at 91 and it will remain at that high value until the expiration of the post-pacing timeout period at 90. The post-pacing timeout is a programmed period of time following antitachyarrhythmia pacing therapy during which the bradycardia pacing rate is set at the high programmed value in order to more quickly restore the patient to full hemodynamic competence. Programming may be performed by the physician just prior to implantation, and it may be changed after implantation through telemetry circuit 38. If the pacing rate is at the high programmed value and the post-pacing timeout period is exceeded, as shown at 90A, a command is given to set the pacing rate back to the normal programmed value at 81. If the time since tachyarrhythmia reversion has not exceeded the post-pacing timeout period, or if the pacing rate has been set back to the normal value following the expiration of the post-pacing timeout period as shown at 90A, then at 82 branching occurs based on whether or not bradycardia has been detected. If a bradycardia condition is detected, as shown at 82A, then bradycardia support pacing is delivered, as shown at 83. This bradycardia support pacing will be delivered either at the high programmed rate if the post-pacing timeout period has not expired, or at the normal programmed rate value if the post-pacing timeout period has expired. In any event, following reversion of the tachyarrhythmia condition, if the post-pacing timeout has not occurred, at 90B the pacing rate is set to the high programmed value, as shown at 91, and the program then proceeds to logic block 94 where, again, if the time since reversion is not equal to or greater than the post therapy time out, the loop passes back to 82. If the post therapy time out has occurred, the loop passes back to 81, via 94, and, also, at 90A of logic block 90, branching to 81 occurs. Accordingly, the pacing rate is set to normal. If there has been no indication at 88 of reversion of the tachyarrhythmia and the time limit set at 89 for the duration of reversion therapy is exceeded, branching occurs to 89A and defibrillation shock therapy is applied at 92. A post-defibrillation timer at 93 is reset at this time, and the pacing rate is then set to the high programmed value, as shown at 93B and 91. The program then proceeds to logic block 94 where, again, if the time since reversion is not equal to or greater than the post therapy time out, the loop passes back to 82. If the post therapy time out has occurred, the loop passes back to 81, via 94, and, also, at 93A of logic block 93, branching to 81 occurs. Thus, again, the pacing rate is set to normal. In FIG. 4, the timeouts for high rate bradycardia pacing may be different time intervals (as programmed into or fixed by the timers 90 and 93) depending upon whether antitachycardia has been reverted at 88 or defibrillation has occurred at 92. It is possible to implement a system wherein the same programmable timer is used in both cases by, for example, eliminating timer 93 and connecting the output of block 92 as an additional input to timer 90, which could then be called, generally, a post-therapy timer. In that case, the timeout interval would be programmed (or fixed) to be the same following both antitachycardia pacing therapy and defibrillation shock therapy. It is also preferable that bradycardia support pacing be inhibited for programmable periods of time after reversion of a tachyarrhythmia by either antitachycardia pacing therapy or defibrillation shock therapy, so as to avoid any pro-arrhythmic effect. The use of such a delay is described in the aforementioned U.S. Patent No. 4,940,054. The time limit for the application of antitachyarrhythmia therapy at 87, determined at 89, is of importance. In this regard, reference is made to U.S. Patent No. 4,895,151 to R. Grevis et al., entitled "Apparatus and Method for Therapy Adjustment in Implantable Cardioverter". This patent discloses an apparatus and method for treating tachyarrhythmias wherein upon detection of the presence of a patient tachyarrhythmia, a first antitachyarrhythmia therapy (antitachycardia pacing) is given at a first energy level. Concurrently, the hemodynamic condition (e.g., the average cardiac cycle length) of the patient is measured and a length of time to therapy switchover is continually derived during the application of the first antitachyarrhythmia therapy. The length of time to a therapy switchover is a function of the hemodynamic condition of the patient. When the time following detection of the patient tachyarrhythmia exceeds the length of time to switchover, a second antitachyarrhythmia therapy (a high energy shock) at a second energy level is provided. It will be apparent from the foregoing description that the present invention provides an improved apparatus for treating cardiac arrhythmias in which, following reversion of tachycardia, hemodynamic compromise experienced during or following the tachycardia is compensated for by setting the bradycardia support pacing rate for any bradycardia support pacing delivered immediately following the reversion of the tachycardia to a higher than normal rate, for a predetermined time period following such reversion. It will also be apparent that the present invention is equally applicable to antitachyarrhythmia devices capable of delivering one or more cardioversion or defibrillation shocks, as well as to devices which deliver antitachycardia pacing pulses alone or in combination with cardioversion or defibrillation shocks. The antitachycardia pacing may be delivered to the atrium, the ventricle, or to both the atrium and the ventricle. It will be understood that various other implementations of the invention are contemplated. For example, although the use of a microprocessor is disclosed herein, the operations of FIG. 4 may be implemented using hard-wired logic rather than software, as the distinction between hardware and software has become less significant. In general, engineering judgement, including considerations of conserving energy so as to prolong battery life, is exercised in deciding on a particular implementation of the invention for a given application. Although the invention has been shown and described with reference to particular embodiments, it is to be understood that such embodiments are merely illustrative of the application of the principles of the invention. Numerous modifications may be made therein and other arrangements may be devised without departing from the broader aspects of this invention as claimed.

Claims: Apparatus (10) for treating arrhythmias of a patient's heart (14), comprising: bradycardia pulse therapy means (35, 36, 39) for delivering bradycardia pacing pulses to the heart (14) at a programmable standby rate; detection means (37) for detecting the presence of a tachycardia of the heart (14); antitachycardia therapy means responsive to said detection means for delivering antitachycardia therapy to the heart to revert said tachycardia; and bradycardia pacing rate setting means (16) for setting the rate of said bradycardia pacing pulses at a normal pacing rate value and setting said bradycardia pacing rate to one other standby rate value for bradycardia pacing after reversion of a tachycardia, wherein said one other post-reversion standby rate value is set for a predetermined post-reversion period of time and in that said one other standby rate value is set at a value nigher than said normal pacing rate value, to compensate for hemodynamic compromise experienced during tachycardia and/or following antitachycardia therapy. Apparatus according to claim 1, wherein said antitachycardia therapy means includes at least one means from the group of means comprising an antitachycardia pacing pulse generator means, a cardioversion means, and a defibrillator means (17). Apparatus of claim 1, further comprising tachycardia confirmation means for confirming the presence of a detected tachycardia subsequent to the detection thereof, said antitachycardia therapy means being activated only after said tachycardia is confirmed by said tachycardia confirmation means. Apparatus according to claim 1, further comprising determining means for determining whether said tachycardia has been reverted, said determining means causing said antitachycardia therapy means to terminate said antitachycardia therapy when said tachycardia has been reverted. Apparatus according to claim 1, wherein said antitachycardia therapy comprises a selected therapy from the group of therapies including antitachycardia pacing therapy, cardioversion therapy and defibriliation therapy, wherein said one other rate value is a first value set by said bradycardia pacing rate setting means following antitachycardia pacing therapy or a second value set by said bradycardia pacing rate setting means following defibrillation or cardioversion therapy. Apparatus according to claim 1, further comprising delay means for delaying delivery of said bradycardia pacing after said antitachycardia therapy means delivers said antitachycardia therapy. Apparatus according to claim 1, wherein said bradycardia pacing rate setting means sets at least one intermediate bradycardia standby pacing rate between said post-reversion pacing rate and said normal pacing rate, thereby achieving a gradual resumption of the normal pacing rate following reversion of said tachycardia. Apparatus according to claim 1, further comprising first timing means for setting said period of time as a fixed time interval. Apparatus according to claim 1, further comprising second programming timing means (38) for programming said predetermined period of time. Apparatus according to claim 8 or 9, wherein after said predetermined period of time said first or second timing means causes said bradycardia pacing rate setting means to again deliver said bradycardia pacing pulses at said normal standby pacing rate value. Apparatus according to claim 8 or 9, wherein said antitachycardia therapy comprises a therapy selected from the group of therapies including antitachycardia pacing therapy, cardioversion therapy and defibrillation therapy, and wherein said first or second timing means comprises a plurality of timers, each of said timers being responsive to the delivery of one of said antitachycardia therapies by said antitachycardia therapy means, each of said timers causing the setting of said at least one other rate value to be for a period of time that is independent of the settings thereof caused by the others of said timers. Apparatus according to claim 4, wherein said antitachycardia therapy means includes: first therapy means for delivering antitachycardia pacing therapy to the heart; and second therapy means for delivering cardioversion or defibrillation therapy to the heart if said determining means does not determine that tachycardia reversion has occurred within a predetermined time interval. Apparatus according to claim 6, wherein said delay means delays said delivery of bradycardia pacing for a predetermined programmable time interval. Apparatus according to claim 7, wherein the durations of each of the said intermediate bradycardia standby pacing rates may be set according to at least one programmable time delay. Apparatus according to claim 7, wherein the durations of each of the said intermediate bradycardia standby pacing rates may be set according to at least one programmable number of bradycardia pacing pulses to be delivered at each of the corresponding ones of said intermediate pacing rates. Apparatus according to claim 7, wherein the normal bradycardia standby pacing rate, rather than being immediately resumed upon expiration of said post-reversion period of time, is resumed following a further period of gradually decreasing pacing rates. Apparatus according to claim 16, wherein said further period of gradually decreasing pacing rates is set as a programmed time period. Apparatus according to claim 16, wherein the said further period of gradually decreasing pacing rates is set as a programmable number of pacing pulses. Apparatus according to claim 16, wherein said further period of gradually decreasing pacing rates is derived from a programmed decrement in the bradycardia standby pacing rate applied to successive pacing pulses. Apparatus according to claim 16, wherein said further period of gradually decreasing pacing rates is derived from a programmed increment in the bradycardia standby pacing interval applied to successive pacing pulses. Apparatus according to claim 1, wherein said at least one other standby rate value is programmed.

Inventors: STEPHENS ANTHONY CLYDE, WILSON STEPHEN GORDON, STEPHENS, ANTHONY CLYDE, WILSON, STEPHEN GORDON
Applicants: PACESETTER INC, PACESETTER, INC.
Application year: 1992
Main classification: A61N1
IPC codes: A61N1