Implantable medical devices with active component monitoring

An implantable medical device includes a housing, a power source and an operational circuit that is coupled to the power source. The operational circuit includes a first electrode terminal and a second electrode terminal, an output circuit configured to deliver an electrical stimulation therapy through the first and second electrode terminals and a control circuit configured to evaluate an electrical parameter associated with the output circuit and to control generation of the electrical stimulation therapy responsive to a result of the evaluated parameter. Among other things, the implantable medical device may modify a parameter of the therapy delivery in response to a result of the evaluation.

FIELD

The present disclosure relates to body implantable medical devices and, more particularly to circuits and techniques implemented in an implantable medical device to provide an electrical therapeutic output.

BACKGROUND

The human anatomy includes many types of tissues that can either voluntarily or involuntarily, perform certain functions. After disease, injury, or natural defects, certain tissues may no longer operate within general anatomical norms. For example, organs such as the heart may begin to experience certain failures or deficiencies. Some of these failures or deficiencies can be diagnosed, corrected or treated with implantable medical devices.

Implantable medical electrical leads are used with a wide variety of these implantable medical devices. The medical leads may be configured to allow electrodes to be positioned at desired cardiac locations so that the device can monitor and/or deliver stimulation therapy to the desired locations. For example, electrodes on implantable leads may detect electrical signals within a patient, such as an electrocardiogram, in addition to delivering electrical stimulation.

Currently, ICD's use endocardial or epicardial leads which extend from the ICD housing through the venous system to the heart. Electrodes positioned in or adjacent to the heart by the leads are used for pacing and sensing functions. Cardioversion and defibrillation shocks are generally applied between a coil electrode carried by one of the leads and the ICD housing, which acts as an active can electrode.

A subcutaneous implantable cardioverter defibrillator (SubQ ICD) differs from the more commonly used ICD's in that the housing and leads are typically implanted subcutaneously such that the sensing and therapy are accomplished subcutaneously. The SubQ ICD does not require leads to be placed in the heart or in contact with the heart. Instead, the SubQ ICD makes use of one or more electrodes on the housing, together with a subcutaneous lead that carries a defibrillation coil electrode and a sensing electrode.

The implantable medical devices are typically battery powered and often utilize capacitors or other electrical charge storage components to hold an electrical output to be made available to a patient. Due to the nature of defibrillation therapy or other high voltage therapy, it is not practical for the implantable medical device to supply the energy upon instantaneous demand by drawing from the power source. Instead, additional circuitry is provided to transfer and store the energy from the power source to accumulate a desired voltage level.

However, the placement of the SubQ ICD lead(s) and electrode(s) outside the heart presents a challenge to generating sufficient energy levels that are required to deliver appropriate therapy. As described herein, the present disclosure addresses the need in art to provide circuitry and techniques for generating appropriate electrical stimulation therapy in a SubQ ICD system.

SUMMARY

In accordance with aspects of this disclosure, circuits and techniques implemented in an implantable medical device are provided for generating an electrical stimulation therapy from a multi-cell power source. Therapy delivery by the implantable medical device is controlled as a function of an evaluation of a state of an operational circuitry of the implantable medical device.

In accordance with some embodiments, an implantable medical system comprises a housing, a power source disposed within the housing, and an operational circuit disposed within the housing and coupled to the power source, the operational circuit having (a) a first electrode terminal and a second electrode terminal, (b) an output circuit configured to deliver an electrical stimulation therapy through the first and second electrode terminals, and (c) a control circuit configured to evaluate an electrical parameter associated with the output circuit and to control generation of the electrical stimulation therapy responsive to a result of the evaluated parameter.

In further aspects of the embodiments of the present disclosure, the control circuit biases at least one component of the output circuit into a non-conducting state during the measurement of the electrical parameter.

In further aspects of the embodiments of the present disclosure, the control circuit is configured to perform a testing operation including controlling delivery of a sub-threshold electrical stimulation therapy through the output circuit to evaluate the electrical parameter based on the delivered sub-threshold electrical stimulation therapy.

In further aspects of the embodiments of the present disclosure, the control circuit is configured to evaluate the electrical parameter by performing a testing operation, including biasing at least one of the four interconnected switches in a conducting state, controlling delivery of the electrical stimulation therapy through the at least one biased switch to at least one of the first and second electrode terminals, and monitoring a voltage in response to delivered electrical stimulation therapy.

DETAILED DESCRIPTION

As will be outlined in the present disclosure, techniques are employed to control therapy delivery by an implantable medical device (IMD) as a function of an evaluation of a state of an operational circuitry of the IMD. By way of example, an electrical parameter of one or more components of the operational circuitry may be monitored and evaluated. The IMD may modify a parameter of the therapy delivery in response to the evaluation of the leakage current.

FIG. 1is a conceptual diagram of a patient4implanted with an example extravascular cardiac defibrillation system2. In the example illustrated inFIG. 1, extravascular cardiac defibrillation system2is an implanted subcutaneous defibrillation system. However, the techniques of this disclosure may also be utilized in other extravascular implanted cardiac defibrillation systems, such as a cardiac defibrillation system having a lead implanted at least partially in a substernal or submuscular location. Additionally, the techniques of this disclosure may also be utilized with other IMD systems, such as implantable cardioverter defibrillator systems, implantable cardiac resynchronization therapy (CRT) systems (e.g., CRT-P or CRT-D systems), implantable pacing systems, other implantable cardiac systems that include combinations of the cardiac systems above. Likewise the techniques may be used in non-cardiac implantable systems, including in implantable neurostimulation systems, drug delivery systems or other systems in which leads, catheters or other components are implanted at extravascular locations within patient4. This disclosure, however, is described in the context of an implantable extravascular cardiac defibrillation system for purposes of illustration.

Extravascular cardiac defibrillation system2includes an implantable cardiac defibrillator (ICD)8connected to at least one implantable cardiac defibrillation lead10. ICD8ofFIG. 1is implanted subcutaneously on the left side of patient4. Defibrillation lead10, which is connected to ICD8, extends medially from ICD8toward sternum42and xiphoid process40of patient4. At a location near xiphoid process40defibrillation lead10bends or turns and extends subcutaneously superior, substantially parallel to sternum42. In the example illustrated inFIG. 1, defibrillation lead10is implanted such that lead10is offset laterally to the left side of the body of sternum42(i.e., towards the left side of patient4).

ICD8includes a housing that forms a hermetic seal that protects components within ICD8. The housing of ICD8may be formed of a conductive material, such as titanium or other biocompatible conductive material or a combination of conductive and non-conductive materials. In some instances, the housing of ICD8functions as an electrode30(sometimes referred to as a housing electrode or can electrode) that is used in combination with one of electrodes on the defibrillation lead10to deliver a therapy to heart6or to sense electrical activity, such as cardiac electrogram (EGM) signals, of heart6. ICD8may also include a connector assembly (sometimes referred to as a connector block or header) that includes electrical feedthroughs through which electrical connections are made between conductors within defibrillation lead10and electronic components included within the housing. Housing may enclose one or more components, including processors, memories, transmitters, receivers, sensors, sensing circuitry, therapy circuitry and other appropriate components (often referred to herein as modules).

Defibrillation lead10includes a lead body having a proximal end that includes a connector configured to connect to ICD8and a distal end that includes one or more electrodes36,34, or32. The lead body of defibrillation lead10may be formed from a non-conductive material, including silicone, polyurethane, fluoropolymers, mixtures thereof, and other appropriate materials, and shaped to form one or more lumens within which the one or more conductors extend. However, the techniques are not limited to such constructions. Although defibrillation lead10is illustrated as including three electrodes36,34, or32, defibrillation lead10may include more or fewer electrodes.

Defibrillation lead10includes one or more elongated electrical conductors (not illustrated) that extend within the lead body from the connector on the proximal end of defibrillation lead10to electrodes36,34, or32. In other words, each of the one or more elongated electrical conductors contained within the lead body of defibrillation lead10may engage with respective ones of electrodes36,34, or32. The connector at the proximal end of defibrillation lead10is connected to ICD8to electrically couple to circuitry, such as a therapy module or a sensing module, of ICD8via connections in connector assembly, including associated feedthroughs. The circuitry of ICD8is provided with electrode terminals that couple to the electrical conductors. The electrical conductors transmit therapy from the operational circuitry within ICD8to one or more of electrodes36,34and32and transmit sensed electrical signals from one or more of electrodes36,34and32to the sensing module within ICD8.

Defibrillation lead10is placed along sternum42such that a therapy vector between a defibrillation electrode34and a second electrode (such as a housing or can electrode30of ICD8or an electrode placed on a second lead) is substantially across the ventricle of heart6. The therapy vector may, in one example, be viewed as a line that extends from a point on the defibrillation electrode34to a point on the housing or can electrode30of ICD8. In another example, defibrillation lead10may be placed along sternum42such that a therapy vector between defibrillation electrode34and the housing or can electrode30of ICD8(or other electrode) is substantially across an atrium of heart6. In this case, extravascular ICD system2may be used to provide atrial therapies, such as therapies to treat atrial fibrillation.

The embodiment illustrated inFIG. 1is an example configuration of an extravascular ICD system2and should not be considered limiting of the techniques described herein. For example, although illustrated as being offset laterally from the midline of sternum42in the example ofFIG. 1, defibrillation lead10may be implanted such that lead10is offset to the right of sternum42or over sternum42. Additionally, defibrillation lead10may be implanted such that it is not substantially parallel to sternum42, but instead offset from sternum42at an angle (e.g., angled lateral from sternum42at either the proximal or distal end). As another example, the distal end of defibrillation lead10may be positioned near the second or third rib of patient4. However, the distal end of defibrillation lead10may be positioned further superior or inferior depending on the location of ICD8, location of electrodes36,34, and32, or other factors.

Although ICD8is illustrated as being implanted near a midaxillary line of patient4, ICD8may also be implanted at other subcutaneous locations on patient4, such as further posterior on the torso toward the posterior axillary line, further anterior on the torso toward the anterior axillary line, in a pectoral region, or at other locations of patient4. In instances in which ICD8is implanted pectorally, lead10would follow a different path, e.g., across the upper chest area and inferior along sternum42. When the ICD8is implanted in the pectoral region, the extravascular ICD system may include a second lead including a defibrillation electrode that extends along the left side of the patient such that the defibrillation electrode of the second lead is located along the left side of the patient to function as an anode or cathode of the therapy vector of such an ICD system.

ICD8may sense electrical activity of heart6via one or more sensing vectors that include combinations of electrodes36and32and a housing or can electrode30of ICD8. For example, ICD8may obtain electrical signals sensed using a sensing vector between electrodes36and32, obtain electrical signals sensed using a sensing vector between electrode36and the conductive housing or can electrode30of ICD8, obtain electrical signals sensed using a sensing vector between electrode32and the conductive housing or can electrode30of ICD8, or a combination thereof. In some instances, ICD8may even sense cardiac electrical signals using a sensing vector that includes defibrillation electrode34, such as a sensing vector between defibrillation electrode34and one of electrodes32or36, or a sensing vector between defibrillation electrode34and the housing or can electrode30of ICD8.

ICD may analyze the sensed electrical signals to detect tachycardia, such as ventricular tachycardia or ventricular fibrillation, and in response to detecting tachycardia may generate and deliver an electrical therapy to heart6. For example, ICD8may deliver one or more defibrillation shocks via a therapy vector that includes defibrillation electrode34of defibrillation lead10and the housing/can electrode30. Defibrillation electrode34may, for example, be an elongated coil electrode or other type of electrode. In some instances, ICD8may deliver one or more pacing therapies prior to or after delivery of the defibrillation shock, such as anti-tachycardia pacing (ATP) or post shock pacing. In these instances, ICD8may generate and deliver pacing pulses via therapy vectors that include one or both of electrodes36and32and/or the housing/can electrode. Electrodes36and32may comprise ring electrodes, hemispherical electrodes, coil electrodes, helix electrodes, segmented electrodes, directional electrodes, or other types of electrodes, or combination thereof. Electrodes36and32may be the same type of electrodes or different types of electrodes, although in the example ofFIG. 1both electrodes36and32are illustrated as ring electrodes.

Defibrillation lead10may also include an attachment feature38at or toward the distal end of lead10. The attachment feature38may be a loop, link, or other attachment feature. For example, attachment feature38may be a loop formed by a suture. As another example, attachment feature38may be a loop, link, ring of metal, coated metal or a polymer. The attachment feature38may be formed into any of a number of shapes with uniform or varying thickness and varying dimensions. Attachment feature38may be integral to the lead or may be added by the user prior to implantation. Attachment feature38may be useful to aid in implantation of lead10and/or for securing lead10to a desired implant location. In some instances, defibrillation lead10may include a fixation mechanism in addition to, or instead of, the attachment feature. Although defibrillation lead10is illustrated with an attachment feature38, in other examples lead10may not include an attachment feature38. In this case, defibrillation lead10may be connected to or secured to an implant tool via an interference fit. An interference fit, sometimes also referred to as a friction fit, is a fastening between two parts which is achieved by friction after the parts are pushed together, rather than by any other means of fastening.

Lead10may also include a connector at the proximal end of lead10, such as a DF4 connector, bifurcated connector (e.g., DF-1/IS-1 connector), or other type of connector. The connector at the proximal end of lead10may include a terminal pin that couples to a port within the connector assembly of ICD8. In some instances, lead10may include an attachment feature at the proximal end of lead10that may be coupled to an implant tool to aid in implantation of lead10. The attachment feature at the proximal end of the lead may separate from the connector and may be either integral to the lead or added by the user prior to implantation.

Defibrillation lead10may also include a suture sleeve or other fixation mechanism (not shown) located proximal to electrode30that is configured to fixate lead10near the xiphoid process or lower sternum location. The fixation mechanism (e.g., suture sleeve or other mechanism) may be integral to the lead or may be added by the user prior to implantation.

The example illustrated inFIG. 1is exemplary in nature and should not be considered limiting of the techniques described in this disclosure. For instance, extravascular cardiac defibrillation system2may include more than one lead. In one example, extravascular cardiac defibrillation system2may include a pacing lead in addition to defibrillation lead10.

In the example illustrated inFIG. 1, defibrillation lead10is implanted subcutaneously, e.g., between the skin and the ribs and/or sternum. In other instances, defibrillation lead10(and/or the optional pacing lead) may be implanted at other extravascular locations. In one example, defibrillation lead10may be implanted at least partially in a substernal location. In such a configuration, at least a portion of defibrillation lead10may be placed under or below the sternum in the mediastinum and, more particularly, in the anterior mediastinum. The anterior mediastinum is bounded laterally by pleurae, posteriorly by pericardium, and anteriorly by sternum. Defibrillation lead10may be at least partially implanted in other extra-pericardial locations, i.e., locations in the region around, but not in direct contact with, the outer surface of heart6. These other extra-pericardial locations may include in the mediastinum but offset from sternum42, in the superior mediastinum, in the middle mediastinum, in the posterior mediastinum, in the sub-xiphoid or inferior xiphoid area, near the apex of the heart, or other location not in direct contact with heart6and not subcutaneous.

Electrodes36,34, and32may comprise ring electrodes, hemispherical electrodes, coil electrodes, helical electrodes, ribbon electrodes, or other types of electrodes, or combinations thereof. Electrodes36,34, and32may be the same type of electrodes or different types of electrodes. In the illustrated example, electrode34is a coil electrode and electrodes36and32are ring, or hemispherical electrodes.

Also shown inFIG. 1is medical device programmer20, which is configured to program, and retrieve data from ICD8. Programmer20may be a handheld computing device, desktop computing device, a networked computing device, etc. Programmer20may include a computer-readable storage medium having instructions that cause a processor of programmer20to provide the functions attributed to programmer20in the present disclosure. ICD8may wirelessly communicate with programmer20. For example, ICD8may transfer data to programmer20and may receive data from programmer20. Programmer20may also wirelessly program and/or wirelessly charge ICD8. The programmer20may also issue an alert signal to notify a user in response to a measured electrical parameter of the ICD8as will be described in more detail below.

Data retrieved from ICD8using programmer20may include measurement data pertaining to components of the operational circuitry as will be described herein. Other examples include data pertaining to functionality of the ICD8or physiologic data such as cardiac EGMs stored by the ICD that indicates electrical activity of heart6and marker channel data indicating the occurrence and timing of sensing, diagnosis, and therapy events associated with ICD8. Data transferred to ICD8using programmer20may include, for example, operational programs for the ICD8that causes the ICD to operate as described herein. Data transferred to the ICD8may include any programmable parameters of the ICD8or other IMDs described herein, such as the lengths of any intervals or delays described herein, the width and/or amplitude of the electrical pulses delivered by the other IMD, such as ICD8, and the electrode vectors used by the IMDs to deliver and sense electrical pulses indicative of intrinsic depolarization of another chamber.

FIG. 2is a schematic diagram of operational circuitry48included in ICD8according to an embodiment of the present disclosure. It is understood that the system ofFIG. 2includes both low power circuitry and high power circuitry. The present disclosure may be employed in a device that provides either or both of a high power electrical stimulation therapy, such as a high power defibrillation therapy, or a low power electrical stimulation therapy, such a pacing pulse, or both. Accordingly, the components in the operational circuitry48may support generation and delivery of either one or both such therapies. For ease of description, this disclosure will describe an operational circuitry48that supports only a high power electrical stimulation therapy, such as cardioversion and/or defibrillation stimulation therapy. However, it should be noted that the operational circuitry48may also provide defibrillation threshold (DFT) induction therapy, anti-tachycardia pacing (ATP) therapy, or post-shock pacing.

The operational circuitry48is powered by one or more power source(s)46. The power source46may include a battery which may be rechargeable or non-rechargeable, an energy harvesting device, or any other energy source that can provide sufficient energy to power the functions of the ICD8.

In the illustrative example, the ICD8functions are controlled by means of stored software, firmware and hardware that cooperatively monitor the cardiac electrical signals of the patient (e.g., EGM), determine when a cardioversion or defibrillation shock necessary, and deliver prescribed defibrillation therapies. The schematic diagram ofFIG. 2incorporates circuitry set forth, for example, in commonly assigned U.S. Pat. No. 5,103,427 “Apparatus for Delivering Single and Multiple Cardioversion and Defibrillation Pulses” to Keimel and U.S. Pat. No. 5,188,105 “Apparatus and Method for Treating a Tachyarrhythmia” to Keimel, both incorporated herein by reference in their entireties, for selectively delivery of single phase, simultaneous biphasic and sequential biphasic cardioversion-defibrillation stimulation therapy. In an exemplary implementation, ICD8may deliver stimulation therapy employing housing electrode30coupled to the electrode node HV-A and at least one electrode such as electrode34coupled to the electrical node HV-B (at electrode terminals30aand34a, respectively) of the output circuit56. In alternative embodiments, the ICD8may employ additional electrodes such as electrodes32,36coupled to nodes such as S1, S2 (at terminals32aand36a, respectively) for sensing or stimulation therapy.

The cardioversion-defibrillation stimulation therapy energy and capacitor charge voltages can be intermediate to those supplied by implantable medical systems having at least one cardioversion-defibrillation electrode in contact with the heart and most AEDs having cardioversion-defibrillation electrodes in contact with the skin. The typical maximum voltage necessary for ICD8using most biphasic waveforms is approximately 750 Volts with an associated maximum energy of approximately 40 Joules. The typical maximum voltage necessary for AEDs is approximately 2000-5000 Volts with an associated maximum energy of approximately 200-360 Joules depending upon the waveform used. The ICD8of the present disclosure uses maximum voltages in the range of about 700 to about 3150 Volts and is associated with energies of about 25 Joules to about 210 Joules. The total high voltage capacitance could range from about 50 to about 74 microfarads.

Such cardioversion-defibrillation stimulation therapies are only delivered when a malignant tachyarrhythmia, e.g., ventricular fibrillation is detected through processing of the far field cardiac ECG employing one of the available detection algorithms known in the ICD8art.

InFIG. 2, pacer timing/sense amplifier circuit52processes the far field ECG SENSE signal that is developed across a particular ECG sense vector defined by a selected pair of the electrodes30,34, and optionally, electrodes36,32if present as noted above. The selection of the sensing electrode pair is made through a control circuit54in a manner to provide the most reliable sensing of the EGM signal of interest, which would be the R wave for patients who are believed to be at risk of ventricular fibrillation leading to sudden death. The far field ECG signals are passed through the control circuit54to the input of a sense amplifier in the pacer timing/sense amplifier circuit52.

Control circuit54may comprise one or more microprocessors, Application-Specific Integrated Circuits (ASICs), Digital Signal Processors (DSPs), Field-Programmable Gate Arrays (FPGAs), discrete electronic components, state machines, sensors, and/or other circuitry. Control circuit54may operate under the control of programmed instructions such as software and/or firmware instructions stored within a storage device53. The storage device53may include volatile, non-volatile, magnetic, optical, and/or electrical media for storing digital data and programmed instructions, including Random Access Memory (RAM), Read-Only Memory (ROM), Non-Volatile RAM (NVRAM), Electrically Erasable Programmable ROM (EEPROM), flash memory, removable storage devices, and the like. These one or more storage devices53may store programs executed by control circuit54.

Storage devices53may likewise store data, which may include, but is not limited to, programmed parameters, patient information, data sensed from the patient, and status information indicating the status of the ICD8. For instance, the data may include statistical information and other characteristic data that is used to evaluate one or more components of the operational circuitry48, such as the components of the output circuit56, as will be discussed in more detail below.

Detection of a malignant tachyarrhythmia is determined via the control circuit54as a function of one or more sensed signals (e.g., R-wave signals and/or P-wave signals) that are output from the pacer timing/sense amplifier circuit52to the control circuit54. An example detection algorithm is described in U.S. Pat. No. 7,103,404, titled “Detection of Tachyarrhythmia Termination”, issued to Stadler, which is incorporated herein by reference in its entirety. Certain steps in the performance of the detection algorithm criteria are cooperatively performed in a microcomputer50, including stored detection criteria that may be programmed into via a telemetry interface (not shown) conventional in the art.

The microcomputer50is generally representative of a processor and associated memory. The memory may reside internally within the microcomputer50, or separately in storage device53. The memory, for example, may include computer readable instructions that, when executed by processor, cause the operational circuitry and or any other component of the medical device to perform various functions attributed to them. For example, the memory may include any volatile, non-volatile, magnetic, optical, or electrical media, such as a random access memory (RAM), read-only memory (ROM), non-volatile RAM (NVRAM), electrically-erasable programmable ROM (EEPROM), flash memory, removable storage devices, or any other digital media for storing digital data and programmed instructions. Such memory will typically be non-transitory. The processor, may include any one or more of a microprocessor, a digital signal processor (DSP), a controller, an application specific integrated circuit (ASIC), a field programmable gate array (FPGA), or equivalent discrete or integrated logic circuitry. In one or more exemplary embodiments, the processor may include multiple components, such as any combination of one or more microprocessors, one or more controllers, one or more DSPs, one or more ASICs, or one or more FPGAs, as well as other discrete or integrated logic circuitry. The functions attributed to the microcomputer50may be embodied as software, firmware, hardware, or any combination thereof.

Data and commands are exchanged between microcomputer50and control circuit54, pacer timing/amplifier circuit52, and output circuit56via a bi-directional data/control bus61. The pacer timing/amplifier circuit52and the control circuit54are clocked at a slow clock rate. The microcomputer50is normally asleep, but is awakened and operated by a fast clock responsive to interrupts developed by sensed cardiac events or on receipt of a downlink telemetry programming instruction or upon delivery of cardiac pacing pulses to perform any necessary mathematical calculations, to perform tachycardia and fibrillation detection procedures, and to update the time intervals monitored and controlled by the timers in pace/sense circuitry52.

The detection algorithms are highly sensitive and specific for the presence or absence of life threatening ventricular arrhythmias, e.g., ventricular tachycardia (V-TACH) and ventricular fibrillation (V-FIB). As discussed above, the detection algorithms contemplated in accordance with this disclosure may utilize sensed cardiac signals to detect the arrhythmias. In addition, detection algorithms for atrial fibrillation may also be included. The ICD8of the present disclosure includes the automatic detection and therapy of the most malignant rhythm disorders.

When a malignant tachycardia is detected, high voltage capacitors (FIG. 3) are charged to a pre-programmed voltage level by a charging circuit58. It is generally considered inefficient to maintain a constant charge at all times on the high voltage capacitors. Instead, charging is initiated when control circuit54issues a high voltage charge command delivered to charging circuit58and charging is controlled by means of bi-directional signal line(s) from the HV output circuit56. Without intending to be limiting, the high voltage output capacitors may comprise film, aluminum electrolytic or wet tantalum construction. Some examples of the high voltage output capacitors are described in commonly assigned U.S. Pat. No. 8,086,312, titled “Capacitors for Medical Devices”, issued to Nielsen, which is incorporated herein by reference in its entirety.

The high voltage output capacitors may be charged to very high voltages, e.g., 700-3150V, to be discharged through the body and heart between the selected electrode pairs among first, second, and, optionally, third and/or fourth subcutaneous cardioversion-defibrillation electrodes30,34,32,36. The details of an exemplary charging circuit58and output circuit56will be discussed below. The high voltage capacitors are charged by charging circuit58and a high frequency, high-voltage transformer. The state of capacitor charge is monitored by circuitry within the output circuit56that provides a feedback signal indicative of the voltage to the control circuit54. Control circuit54terminates the high voltage charge command when the received signal matches the programmed capacitor output voltage, i.e., the cardioversion-defibrillation peak shock voltage.

Control circuit54then develops a control signal that is applied to the output circuit56for triggering the delivery of cardioverting or defibrillating shocks. In this way, control circuitry54serves to control operation of the output circuit56, which delivers high energy cardioversion-defibrillation stimulation therapies between a selected pair or pairs of the first, second, and, optionally, the third and/or fourth cardioversion-defibrillation electrodes30,34, coupled to the HV-A, HV-B and optionally to other electrodes such as electrodes36,32coupled to the S1, S2 terminals as shown inFIG. 2.

Thus, ICD8monitors the patient's cardiac status and initiates the delivery of a cardioversion-defibrillation stimulation therapy through a selected pair or pairs of the first, second, third and/or fourth electrodes30,34,36, and32in response to detection of a tachyarrhythmia requiring cardioversion-defibrillation.

Typically, the charging cycle of the capacitors has a short duration, e.g., it can take anywhere from two seconds to twenty seconds, and occurs very infrequently. The ICD8can be programmed to attempt to deliver cardioversion shocks to the heart in the example implementations described above in timed synchrony with a detected R-wave or can be programmed or fabricated to deliver defibrillation shocks to the heart in the example implementations described above without attempting to synchronize the delivery to a detected R-wave. Episode data related to the detection of the tachyarrhythmia and delivery of the cardioversion-defibrillation stimulation therapy can be stored in RAM for uplink telemetry transmission to an external programmer as is well known in the art to facilitate in diagnosis of the patient's cardiac state.

Housing8may include telemetry circuit (not shown inFIG. 2), so that it is capable of being programmed by means of external device20(FIG. 1) via a 2-way telemetry link as is known in the art. Uplink telemetry allows device status and diagnostic/event data to be sent to external programmer for review by the patient's physician. Downlink telemetry allows the external programmer via physician control to allow the programming of device function and the optimization of the detection and therapy for a specific patient. Programmers and telemetry systems suitable for use in the practice of the present disclosure have been well known for many years. Known programmers typically communicate with an implanted device via a bi-directional telemetry link such as Bluetooth®, radio-frequency, near-field, or low frequency, so that the programmer can transmit control commands and operational parameter values to be received by the implanted device, and so that the implanted device can communicate diagnostic and operational data to the programmer.

Those skilled in the art will appreciate that the various components of the low power circuit60e.g., pacer/sense circuit52, control circuit54, and microcomputer50are illustrated as separate components for ease of discussion. In alternative implementations, the functions attributed to the components of the low power circuitry60may suitably be performed by a sole component.

Operational circuitry48further includes a state monitoring circuit100that is configured to evaluate the condition of one or more components of the output circuit56. The monitoring circuit100measures an electrical parameter of one or more of the components of the output circuit56for an evaluation to detect a potential failure state or actual failure state. By way of example, the electrical parameter measured by the monitoring circuit100may comprise a leakage current flowing through one or more components of the output circuit56. In another example, the electrical parameter measured by the monitoring circuit100may comprise a voltage across one or more components of the output circuit56. The results of the evaluation of the electrical parameter may trigger the control circuit54may modify a therapy delivery regimen in response to the result of the evaluation of the electrical parameter. In an alternative embodiment, the functionality of the monitoring circuit100may be implemented within the control circuit54. As such, the control circuit54will evaluate the state of the output circuit56and modify control therapy delivery by the ICD8as a function of the evaluation of the state of the output circuit56.

A notification module66issues a notification to a user such as the patient4. The notification may include an audible warning, a vibration, a mild electrical stimulus, or some combination of these warnings. In addition, the notification may include transmission of a radio signal to a programmer or an external device, such as a transceiver that responds by contacting a physician by telephone, paging, or electronic mail. Additionally, control circuit54may automatically activate life-critical features, such as ventricular fibrillation detection and therapy in response to detection of a potential or actual failure state.

FIG. 3illustrates an exemplary schematic showing a portion of the operational circuitry ofFIG. 2, in accordance with an embodiment of the disclosure, in greater detail. The output circuit56allows the controlled transfer of energy from the energy storage capacitors70,72,74, and76to the patient4.

The output circuit56includes four switches80,82,84, and86that are interconnected. The interconnection of the four switches comprises the switches80and82being configured in a parallel orientation alongside switches84and86and a bridge being provided to intersect each of the pair of parallel connected switches. As is shown inFIG. 3, the interconnected switches are arrayed to define an orientation that includes a high side pair of switches80and84and a low side pair of switches82and86in a configuration that may resemble a “H”. In other words, the four interconnected switches are arrayed having switches80and84defining the high side of the H-bridge and switches82and86defining the low side of the H-bridge.

The intersecting bridge includes two terminals that couple the output circuit56to the electrodes30and34. As previously described, patient4is connectable (e.g., using leads/electrodes30,32and any other suitable connections) between terminal HV-A located between the switch80and switch82and terminal HV-B located between switch84and switch86.

AlthoughFIG. 3is illustrated with four switches thereby providing two terminals, it should be noted that the output circuit56is not limited to four switches. In other embodiments, the output circuit56may include six switches for three output terminals, or eight switches for four output terminals, or any other number of switches based on the desired number of output terminals. Of course, additional modifications to the circuits of this disclosure would be made to accommodate such changes, but such modifications are within the comprehension of those skilled in the art having the benefit of this disclosure.

Switches80and84are coupled to a positive terminal of the energy storage capacitors70,72,74, and76. Unlike conventional output circuits which include a discharge switch that is coupled between the H-Bridge switches and energy storage capacitors, the present disclosure is provide without the discharge switch. Switches82and86are coupled to a negative terminal of the energy storage capacitors70,72,74, and76. The biasing into a conducting or non-conducting state of one or more of the switches80,82,84,86may be controlled by control signals issued by control circuit54. For example, control signals to bias one or more of switches80,82,84,86into a conducting state may be issued to configure the H-bridge in one or more configurations to provide one or more types of stimulation pulses, or may be used to provide active or passive recharge, etc.

For example, in accordance with an embodiment, the ICD8provides a biphasic defibrillation pulse to the patient in the following manner. With reference toFIG. 3, once the energy storage capacitors70,72,74, and76are charged to a selected energy level, the switches80and86are closed so as to provide a path from the capacitors70-76to electrodes30,34for the application of a first phase of a defibrillation pulse to the patient4. The stored energy travels from the positive terminal of the capacitors, through switch80, across the patient4, back through switch86to the negative terminal of the capacitors70-76. The first phase of the biphasic pulse therefore applies a positive pulse from the electrode30to the electrode34.

Before the energy storage capacitors70,72,74, and76are completely discharged, switch86is biased off in preparation for application of the second phase of the biphasic pulse. Once switch86is biased off, switch80will also become non-conducting because the current flowing through it falls to below its holding current.

After the end of the first phase of the biphasic defibrillation pulse, the switches84and82are switched on to start the second phase of the biphasic pulse. Switches84and82provide a path to apply a negative defibrillation pulse to the patient4. With reference toFIG. 3, the energy travels from the positive terminal of the capacitors70,72,74, and76, through switch84, across the electrodes34,30coupled to the patient4, and out through switch82to the negative terminal of the capacitors70,72,74, and76. The polarity of the second phase of the defibrillation pulse is therefore opposite in polarity to the first phase of the pulse.

As described in reference toFIG. 3, the four output switches80,82,84and86allow the transfer of energy from the energy storage capacitors70,72,74, and76. Switches80and84may be provided as a combination of solid-state semiconductor devices, such as a MOSFET-triggered anode gated thyristor (AGT), with the MOSFET being connected to the gate of the AGT. In such an embodiment, the MOSFET is controlled by the control circuit54from a conducting to a non-conducting state. Switches82and86are both solid-state semiconductor switches, such as insulated gate bipolar transistors (IGBT). In other embodiments, any one of the switches80-86may be embodied as any known solid-state semiconductor switching device including AGT, FET, IGBT, or silicon controlled rectifier (SCR). The four output switches80to86can be switched from an off (non-conducting) to an on (conducting) condition based on control signals provided by the control circuit54. Switches80to86remain in a conducting state as long as the control signal provided by the control circuit54is present.

Each of the switches80,82,84, and86is coupled to a monitoring circuit100. The monitoring circuit100is configured to perform a testing operation that includes measuring an electrical parameter of the switches80-86. The electrical parameter may include a current flowing through one or more of the switches80-86or a voltage across one or more of the switches80-86. For ease of illustration, the electrical parameter described in embodiments of the present disclosure will be considered to be a current flowing through the switches80-86.

In an embodiment, the control circuit54is configured to perform the testing operation by controlling delivery of a stimulation therapy pulse or a sub-threshold electrical stimulation pulse through the output circuit56. In contrast to the stimulation therapy pulse, the sub-threshold electrical stimulation pulse is a non-capturing electrical stimuli that is configured (e.g., too low amplitude and/or pulse width, etc.) so as not to generate an evoked response when delivered to the heart. During the testing operation, the control circuit54may bias the one or more of switches80-86that is being monitored into a non-conducting state prior to and/or during the measurement of the electrical parameter. In another embodiment, the testing operation to assess the condition of the switches80-86may be performed while the switches80-86are biased in a conducting state.

The inventors of the present disclosure have observed that a typical solid-state semiconductor switching device such as an SCR and IGBT in some applications may have a leakage current of around 1 milliamp. The solid-state semiconductor switching devices, such as the switches80-86of this disclosure rely on gate voltages to control the current flow. Without intending to be bound by theory, the inventors believe that the amount of leakage current flowing through one or more of the switches80-86may change during the operation of the ICD8. Changes in the amount of the leakage current flowing through the switches80-86may impact the delivery of therapy to the patient and affect the operation and functions of the ICD8. Depending on the magnitude of the change in the leakage current, a failure state of the ICD8may arise.

The measurement of the electrical parameter by the monitoring circuit100may be performed across a load, such as heart6of the patient. The output circuit56may be controlled to deliver an electrical pulse, such as a therapy stimulation pulse or a sub-threshold stimulation pulse. The current flowing through one or more of the switches80-86may be determined by, for example, measuring the voltage across a known load such as the heart6.

The measured electrical parameter (for example, the leakage current) of one or more switches80-86of the output circuit56is utilized to detect a potential or actual failure state. The monitoring circuit100may be coupled to the control circuit54for transmission of the measured electrical parameter. The control circuit54evaluates the measured electrical parameter and utilizes the result of the evaluation of the electrical parameter to determine whether to modify a therapy delivery regimen. For example, the modification may comprise increasing the stimulation threshold of a stimulation therapy that is to be delivered to patient4. In another example, an alert signal may be generated responsive to the results of the evaluation as described, for example, in U.S. Pat. No. 6,082,367 and telemetered to a user in response to the result of the evaluation of the electrical parameter. In another example, an alert signal may be issued by the notification module66to alert a user such as patient4of the potential or actual failure in response to the result of the evaluation of the electrical parameter. As previously mentioned, the functionality of the monitoring circuit100may be implemented within the control circuit54. As such, the control circuit54may measure and evaluate the parameter of the one or more switches80-86and modify or control delivery of therapy by the ICD8as a function of the evaluation of the one or more switches80-86.

Referring toFIGS. 4 and 5, an exemplary monitoring circuit is provided for evaluating an electrical parameter of an output circuit56of the ICD8. InFIG. 4, the monitoring circuit100aincludes a multiplexer102, and a comparator104.

As depicted inFIG. 4, signal lines (Switch1-4) from each of the interconnected switches80-84are coupled to the multiplexer102. The multiplexer102selects one of the signal lines from a respective one of the switches80-84as the first input voltage to the comparator104. A reference signal (REF) is provided as the second input voltage into comparator104. The reference signal provides a predefined voltage signal against which the selected first input voltage is compared. For example, the predefined voltage may correspond to the maximum amount of leakage current that can flow through a given one of the switches80-84without impacting the operation of the ICD8. In an example, such reference signal values may be determined empirically and stored in storage device53.

The comparator104is configured to compare the magnitude of the selected first input voltage and the magnitude of the second input voltage. Then, as a result of the comparison, the comparator104outputs information about which one of the magnitudes is greater, as one digital value.

In an alternative embodiment, a voltage converter106may optionally be included to convert the leakage current flowing across the selected one of the switches80-86into a voltage prior to input into the comparator104.

In the alternative embodiment ofFIG. 5, the monitoring circuit100bmay be embodied to include a plurality of comparators104a-dsuch that each of the signal lines (Switch1-4) is coupled to a dedicated one of the plurality of comparators104a-d. In doing so, the multiplexer102may be rendered unnecessary. Voltage converter106a-dmay optionally be included to convert the leakage current flowing across the selected one of the switches80-86into a voltage prior to input into the comparator104. Such a configuration facilitates simultaneous evaluation of the plurality of components (e.g., switches80-84).

Turning now toFIG. 6, a flowchart is shown depicting the method tasks of an exemplary embodiment of a technique that is employed to control therapy delivery by an implantable medical device such as ICD8as a function of an evaluation of a condition of components of operational circuitry of the ICD8.

The method is initiated by delivering an electrical test pulse through the operational circuitry of the ICD8(200). The test pulse may comprise a therapy stimulation pulse or a sub-threshold stimulation pulse.

In response to delivering the test pulse, an electrical parameter of a component of the operational circuitry is measured (202). For example, the electrical parameter may comprise a current flowing through one or more of the switches80-86. In another example, the electrical parameter may comprise a voltage across a known load, such as the heart6. The electrical parameter may be measured as described, for example, in conjunction with the state monitoring circuit100inFIGS. 2-5.

A predetermined threshold value for the component(s) being assessed is provided (204). The predetermined threshold value may correspond to a potential or actual failure state of the component(s). For example, the components of the operational circuitry may include a switch. In that example, the predetermined threshold value will correspond to a leakage current value that represents the greatest amount of leakage current that can flow through the switch while maintaining appropriate functionality of the operational circuitry48.

The measured electrical parameter is evaluated to assess a state of an operational circuitry (206). The evaluation may comprise comparing the magnitude of the measured electrical parameter to the predetermined threshold value.

In response to the results of the evaluation of the electrical parameter being less than, or equal to, the threshold, the functionality of the ICD8will not be changed (208). For example, the ICD8may continue to deliver therapy at the pre-existing parameters.

However, responsive to the results of the evaluation of the electrical parameter being greater than the threshold, the functionality of the ICD8may be changed. For example, the ICD8may modify one or more therapy delivery parameters as discussed above in one embodiment (210). In an alternative embodiment, or in addition, the ICD8may issue an alert to notify a user such as the patient or a clinician about the detected potential or actual failure (212). The flow to tasks210and212is shown in dotted lines to illustrate that both tasks need not be present, but rather that one or both may be employed in a given ICD8.

Embodiments of the method as described inFIG. 6may be implemented as a computer-implemented method or computer-implemented instructions stored in a memory, such as the memory devices described above, that, when executed by processor (solely, or in conjunction with firmware or hardware), cause the operational circuitry and or any other component of the medical device to perform various functions attributed to them.