FAULT TOLERANT CO-AXIALLY WIRED SENSORS AND METHODS FOR IMPLEMENTING SAME IN AN IMPLANTABLE MEDICAL DEVICE

Abstract

According to the invention, a possible fault scenario involves an insulation breach of a medical lead which couples signals and/or electrical energy between a sensor and a circuit-bearing, active implantable medical device (AIMD). An initial response involves disconnecting the power source from the sensor with subsequent responses including selective reconnection of the power source. If the fault spontaneously resolves, then power to the sensor can be restored and physiologic signals transmitted to operative circuitry of the AIMD. In addition, however, an intermediate mode is enabled with the power source only coupled temporarily, for example, during intervals when stimulation and/or capture of excitable tissue (e.g., myocardial tissue) is not likely to occur due to any electrical shunt current(s). Thus, applying energy to a sensor(s) during the refractory period of a cardiac chamber eliminates undesired tissue activation. Moreover, sensed physiologic parameters can be collected without interrupting therapy delivery

Description

FIELD OF THE INVENTION

The invention relates generally to fault tolerant sensors and related components that couple to an active implantable medical device (AIMD).

BACKGROUND OF THE INVENTION

Implantable medical devices are used to monitor, diagnose, and/or deliver therapies to patients suffering from a variety of conditions. Exemplary AIMDs include implantable pulse generators (IPGs) including pacemakers, gastric, nerve, brain and muscle stimulators, implantable drug pumps, implantable cardioverter-defibrillators (ICDs) and the like.

Due in part to the fact that an AIMD resides in a difficult environment and can be exposed to vibratory, tensile stresses, forces and caustic materials, there exists a need for a modicum of fault tolerance against a variety of possible device, component and system failures and improper operation. Among other things, certain forms, aspects and embodiments of the present invention provide improved and more predictable performance of an AIMD when subjected to a variety of failure modes.

BACKGROUND

There are many situations in which a patient requires long-term monitoring and when it may be desirable to implant a sensor for monitoring within the body of the patient. One such monitor is a pressure monitor, which can measure the pressure at a site in the body, such as a blood vessel or a chamber of the heart. When implanted in a vessel or a heart chamber, the sensor responds to changes in blood pressure at that site. Blood pressure is measured most conveniently in units of millimeters of mercury (mm Hg) (1 mm Hg=133 Pa).

The implanted pressure sensor is coupled to an implanted medical device, which receives analog signals from the sensor and processes the signals. Signals from the implanted pressure sensor may be affected by the ambient pressure surrounding the patient. If the patient is riding in an airplane or riding in an elevator in a tall building, for example, the ambient pressure around the patient may change. Changes in the ambient pressure affect the implanted pressure sensor, and may therefore affect the signals from the pressure sensor.

A typical implanted device that employs a pressure sensor is not concerned with total pressure, i.e., blood pressure plus ambient pressure. Rather, the device typically is designed to monitor blood pressure at the site of the internal sensor. To provide some compensation for changes in ambient pressure, some medical devices take additional pressure measurements with an external pressure sensor. The external pressure sensor, which may be mounted outside the patient's body, responds to changes in ambient pressure, but not to changes in blood pressure. The blood pressure is a function of the difference between the signals from the internal and external pressure sensors.

Although the internal pressure sensor may generate analog pressure signals as a function of the pressure at the monitoring site, the pressure signals are typically converted to digital signals, i.e., a set of discrete binary values, for digital processing. An analog-to-digital (A/D) converter receives an analog signal, samples the analog signal, and converts each sample to a discrete binary value. In other words, the pressure sensor generates a pressure signal as a function of the pressure at the monitoring site, and the A/D converter maps the pressure signal to a binary value.

The A/D converter can generate a finite number of binary values. An 8-bit A/D converter, for example, can generate 256 discrete binary values. The maximum binary value corresponds to a maximum pressure signal, which in turn corresponds to a maximum pressure at the monitoring site. Similarly, the minimum binary value corresponds to a minimum pressure signal, which in turn corresponds to a minimum site pressure. Accordingly, there is a range of pressure signals, and therefore a range of site pressures, that can be accurately mapped to the binary values.

In a patient, the actual site pressures are not constrained to remain between the maximum and minimum monitoring site pressures. Due to ambient pressure changes or physiological factors, the pressure sensor may experience a site pressure that is “out of range,” i.e., greater than the maximum monitoring site pressure or less than the minimum monitoring site pressure. In response to an out-of-range pressure, the pressure sensor generates an analog signal that is greater than the maximum pressure signal or less than the minimum pressure signal. An out-of-range pressure cannot be mapped accurately to a binary value.

For example, the pressure sensor may experience a high pressure at the monitoring site that exceeds the maximum site pressure. In response, the pressure signal generates a pressure signal that exceeds the maximum pressure signal. The pressure signal is sampled and the data samples are supplied to the A/D converter. When the A/D converter receives a data sample that is greater than the maximum pressure signal, the A/D converter maps the data sample to a binary value that reflects the maximum pressure signal, rather than the true value of the data sample. In other words, the data sample is “clipped” to the maximum binary value. Similarly, when the A/D converter receives a data sample that is below the minimum pressure signal, the converter generates a binary value that reflects the minimum pressure signal rather than the true value of the data sample.

Because of changes in ambient pressure, pressures sensed by the internal pressure sensor may be in range at one time and move out of range at another time. When the pressures move out of range, some data associated with the measured pressures may be clipped, and some data reflecting the true site pressures may be lost. In such a case, the binary values may not accurately reflect the true blood pressures at the monitoring site.

To avoid clipping, the implanted device may be programmed to accommodate an expected range of site pressures. Estimating the expected range of site pressures is difficult, however, because ambient pressure may depend upon factors such as the weather, the patient's altitude and the patient's travel habits. Pressures may be in range when the patient is in one environment, and out of range when the patient is in another environment.

The risk of clipping can further be reduced by programming the implanted device with a high maximum site pressure that corresponds to the maximum binary value and with a low minimum site pressure that corresponds to the minimum binary value. Programming the device for a high maximum and a low minimum creates a safety margin. The price of safety margins, however, is a loss of sensitivity. Safety margins mean that pressures near the maximum and minimum site pressures are less likely to be encountered. As a result, many of the largest and smallest binary values are less likely to be used, and the digital data is a less precise representation of the site pressures.

BRIEF SUMMARY OF THE INVENTION

The present invention provides one or more structures, techniques, components and/or methods for avoiding or positively resolving one or more possible failure modes for a chronically implanted medical device that couples to one or more sensors.

In one embodiment of the invention, a possible fault scenario involving a breach of a portion of a layer of insulation on an elongated medical electrical lead which couples signals and/or electrical energy between a sensor and a circuit-bearing, active AIMD disposed within a substantially hermetic housing. According to this scenario, an initial response to a fault involves disconnecting or removing the power source from the sensor. Subsequently, the power source is periodically, aperiodically or otherwise reconnected in order to determine if the original fault persists. If not, then the power to the sensor can be restored and physiologic signals transmitted to operative circuitry of the AIMD.

According to another aspect of the invention, however, an intermediate sensor operating mode is enabled; for example, the power source for the sensor is only coupled thereto temporarily. In an exemplary embodiment, the power source is limited to intervals of time when stimulation and/or capture of excitable tissue (e.g., myocardial tissue, nerve fibers, muscular tissue, etc.) is not likely to occur. One manner of achieving involves applying energy to a sensor(s) during the absolute and/or relative refractory period of the myocardium to thereby minimize any undesired tissue activation. One advantage of this selective coupling and uncoupling of sensor energy is that substantially beat-to-beat physiologic parameters can continue to be collected without interrupting therapy delivery. Thus, one aspect of this form of the invention involves the ability to maintain AIMD (and sensor) functionality and avoid the possibility of having to explant the AIMD and/or sensor from the patient.

In one embodiment the AIMD provides only physiological sensing of a patient parameter, such as endocardial pressure. In one form of this embodiment, the sensor comprises an absolute pressure sensor adapted for chronic implantation within a portion of a right ventricle (RV) of a patient. The portion could include the RV outflow tract (RVOT) which is a region of relatively high-rate blood flow which correspondingly requires a robust sensor capsule and coupling to a medical electrical lead coupled thereto. Thus in lieu of providing therapy at some time when the relevant tissue remains excitable, the sensor power-switching regimen operates to ensure that no current or voltage shunting occurs to the tissue when it is non-refractory.

In another embodiment, an AIMD is configured to sense a physiologic parameter of a patient (e.g., blood pressures, acceleration, pH levels, lactate, saturated oxygen, blood sugar, calcium, potassium, sodium, etc.) and provide a therapy such as cardiac pacing, high-energy cardioversion/defibrillation therapy and/or a drug or substance delivery regimen or the like. For example, in an AIMD configured to chronically measure blood pressure, provide cardiac pacing therapy and, as appropriate, deliver high-energy defibrillation therapy, an outer insulation breach of a medical electrical lead could cause a malfunction requiring explant of the AIMD. According to the invention, a refinement of the fault mitigation for this particular embodiment involves coupling the energy to the sensor during the refractory period and, in addition, decoupling the power from the sensor during or in anticipation of high energy therapy delivery (e.g., cardioversion and/or defibrillation)

In yet another embodiment of the invention, an AIMD configured with three or more discrete medical electrical leads that each independently couple to relatively low power AIMD circuitry disposed within the AIMD housing can be rendered highly robust vis-à-vis a voltage- or current-shunt or path to the body or body fluids. In this form of the invention, the ventricular-based sensor(s) should only be coupled to a power source during a refractory period of both ventricles. Accordingly, in the event that an atrial-based sensor is utilized the power source should only be coupled to the sensor during the atrial refractory period (absolute and/or relative refractory period).

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram of a human body with an implanted medical device and pressure sensors.

FIG. 2 is a simplified block diagram illustrating an exemplary system that implements the an embodiment of the invention wherein a physiologic sensor provides chronic monitoring and diagnostic for a patient.

FIG. 3 is an illustration of an exemplary implantable medical device (AIMD) connected to monitor a patient's heart.

FIG. 4 is a block diagram summarizing the data acquisition and processing functions appropriate for practicing the invention.

FIGS. 5A and 5B are elevational side views depicting a pair of exemplary medical electrical leads wherein in FIG. 5A a pair of defibrillation coils are disposed with a sensor capsule intermediate the coils and in FIG. 5B the sensor capsule is disposed distal the coils.

FIG. 6 is a cross sectional view of a coaxial conductor adapted for use with an implantable sensor.

FIG. 7 is a schematic illustration of a sensor capsule coupled to a housing of an IMD and a source of reference potential.

FIG. 8. is a schematic view of a sensor capsule coupled to a electrical current detector and operative circuitry housed within an IMD.

FIG. 9 is a schematic view of an IMD having a proximal lead-end set screw for mechanically retaining the proximal end of a medical electrical lead within a connector block, wherein said set screw couples to a source of reference potential.

DETAILED DESCRIPTION

FIG. 1 is a diagram of a body of a patient 10 having an AIMD 12 according to one embodiment of the present invention. As depicted in FIG. 1 lead 14 operatively couples to circuitry (not shown) within the AIMD 12 and extends into the right ventricle 16 of the heart 18. A chronically implantable pressure sensor 20 is shown disposed within a portion of a right ventricle (RV) 16 and couples to lead 14. The pressure sensor 20 monitors and measures changes in blood pressure in the RV 16. The blood pressure in RV 16 is a function of factors such as the volume of RV 16, the pressure exerted by the contraction of heart 18 and the ambient pressure around patient 10 and the blood pressure varies throughout the cardiac cycle as is well known in the art. While a pressure sensor 20 is depicted in FIG. 1 diverse other sensors can directly benefit from the teaching of the present invention as noted hereinabove.

In one form of the invention the AIMD 12 receives analog signals from the implanted pressure sensor 20 via lead 14 although digital sensors and/or circuitry can be utilized in conjunction with the invention. As noted, in the depicted embodiment the signals are a function of the pressure sensed by implanted pressure sensor 20 at the monitoring site (e.g. RV 16) which can of course include myriad different locations on or about the heart and other muscles, circulatory system, nervous system, digestive system, skeleton, brain, diverse organs, and the like. In the depicted embodiment, patient 10 carries or otherwise provides or maintains access to an external pressure sensor or reference 22 which is used to correct the readings of the implanted absolute-type pressure sensor 20. FIG. 1 depicts external pressure sensor 22 coupled to a belt or strap 24 coupled to the arm of patient 10, but this is but one of many possible sites for external pressure sensor 22. The external pressure sensor 22 responds to changes in ambient pressure, and is unaffected by blood pressure in the RV 16. The AIMD 12 receives signals from external pressure sensor 22 via communication such as radio frequency (RF) telemetry. Alternatively, the AIMD 12 need not communicate with external pressure sensor 22 in any way.

The AIMD 12 optionally includes a digital processor. Thus, the analog signals from implanted pressure sensor 20 are converted to digital signals for processing. Referring briefly to FIG. 2, the analog signals are first amplified by an amplifier 32 and are sampled and are mapped to discrete binary values by an A/D converter 34. Each binary value corresponds to a pressure signal that in turn corresponds to a site pressure. The A/D converter 34 maps each sample to a binary value that corresponds most closely to the actual pressure signal and site pressure reflected by the sample.

The sensitivity of AIMD 12 to changes in pressure is a function of the range of pressures that map to a single binary value. The smaller the pressure change represented by consecutive binary values, the more sensitive implanted medical device 12 is to changes in pressure. For example, an 8-bit A/D converter may be configured to map pressures between a minimum site pressure of 760 mm Hg and a maximum site pressure of 860 mm Hg to discrete binary values. In this example, a one-bit increase represents a pressure increase of about 0.4 mm Hg.

In a conventional implanted medical device, there may be a tradeoff between range and sensitivity. When the number of possible discrete binary values is fixed, expanding the range of site pressures that are represented by the binary values results in a decrease in sensitivity, because a one-bit change represents a larger pressure change. Similarly, decreasing the range results in an increase in sensitivity because a one-bit change represents a smaller pressure change.

In an illustrative example, an 8-bit A/D converter may be configured to map pressures between 760 mm Hg and 860 mm Hg to discrete binary values, with a one-bit increase representing a pressure increase of about 0.4 mm Hg. When the same 8-bit A/D converter is configured to map pressures between 746 mm Hg and 874 mm Hg to discrete binary values, the overall range of site pressures that can be mapped to binary values expands by 128 mm Hg. The sensitivity, however, decreases. A one-bit increase represents a pressure increase of 0.5 mm Hg.

Not all changes to range affect sensitivity. In some circumstances, a range may be offset without affecting sensitivity. In an offset, the minimum site pressure and the maximum site pressure are increased or decreased by the same amount. For example, a 8-bit A/D converter may be configured to map pressures between 760 mm Hg and 860 mm Hg to discrete binary values, with a one-bit increase representing a pressure increase of about 0.4 mm Hg. When the pressure range is shifted downward to pressures between 740 mm Hg and 840 mm Hg, the range is offset but not expanded. When the range is offset, sensitivity is not affected. A one-bit increase still represents a pressure increase of about 0.4 mm Hg.

Implanted medical device 12 implements techniques for automatically adjusting mapping parameters in response to changes in pressure conditions. In particular, implanted medical device 12 periodically evaluates the digital pressure data to determine whether pressure data may be going out of range, and expands and/or offsets the range to avoid having data go out of range. In addition, implanted medical device 12 determines whether the range can be decreased so that sensitivity can be enhanced.

FIG. 2 is a block diagram of an exemplary system 30 that implements the invention. Pressure sensor 20 supplies an analog pressure signal to amplifier 32. The analog pressure signal is a function of the site pressure, where pressure sensor 20 is disposed. The analog pressure signal may be, for example, a voltage signal. Amplifier 32 amplifies the signal by, for example, amplifying the voltage. Amplifier 32 may perform other operations such as serving as an anti-aliasing filter. Amplifier 32 has an adjustable gain and an adjustable offset. The gain and offset of amplifier 32 are adjustable under the control 42 of a controller, which may take the form of a microprocessor 36. The controller may take other forms, such as an application-specific integrated circuit (ASIC), a field programmable gate array (FPGA), or any other circuit including discrete and/or integrated components and that has control capabilities.

Amplifier 32 supplies the amplified analog signal to A/D converter 34. The range and resolution of pressure signals supplied to A/D converter 34 is a function of the gain of amplifier 32 and the offset of amplifier 32. By adjusting the gain and/or offset of amplifier 32, microprocessor 36 regulates the mapping parameters; that is, the correspondence between site pressures and binary values. A/D converter 34 samples the pressure signals from amplifier 32 and converts the samples into discrete binary values, which are supplied to microprocessor 36. In this way, microprocessor 36, amplifier 32 and A/D converter 34 cooperate to map the site pressures to binary values.

The number of possible discrete binary values that can be generated by A/D converter 34 is fixed. When there is a risk of data out of range, it is not feasible to increase the number of binary values that represent the site pressures. As will be described in more detail below, microprocessor 36 adjusts the gain and/or the offset of amplifier 32 so that the data remain in range and so that the digital pressure data generated by A/D converter 34 accurately reflect the site pressures sensed with pressure sensor 20.

Microprocessor 36 processes the digital pressure data according to algorithms embodied as instructions stored in memory units such as read-only memory (ROM) 38 or random access memory (RAM) 40. Microprocessor 36 may, for example, control a therapy delivery system (not shown in FIG. 2) as a function of the digital pressure data.

Microprocessor 36 may further compile statistical information pertaining to the digital pressure data. In one embodiment, microprocessor 36 generates a histogram of the digital pressure data. The histogram, which may be stored in RAM 40, reflects the distribution of pressures sensed by pressure sensor 20.

The histogram includes a plurality of “bins,” i.e., a plurality of numbers of digital data samples of comparable magnitude. For example, a histogram that stores the number of digital values corresponding to pressures between 760 mm Hg and 860 mm Hg may include twenty bins, with each bin recording the number of data samples that fall in a 5 mm Hg span. The first bin holds the number of values between 760 mm Hg and 765 mm Hg, while the second bin holds the number of values between 765 mm Hg and 770 mm Hg, and so on. More or fewer bins may be used.

The distribution of values in the bins provides useful information about the pressures in right ventricle 16. Data accumulates in the histogram over a period of time called a “storage interval,” which may last a few seconds, a few hours or a few days. At the end of the storage interval, microprocessor 36 stores in RAM 40 information about the distribution of pressures, such as the mean, the standard deviation, or pressure values at selected percentiles. Microprocessor 36 may then clear data from the histogram and begin generating a new histogram.

When microprocessor 36 adjusts the mapping parameters, the new histogram may be different from the preceding histogram. In particular, the new histogram may record the distribution of an expanded range of pressure data, or a reduced range of pressure data, or a range that has been offset up or down. In general, the adjustments to the mapping parameters tend to center the distribution in the histogram, and tends to reduce the number of values in the highest and lowest bins. Microprocessor 36 adjusts the mapping parameters based upon the distribution of digital pressure data in the preceding histogram. Microprocessor 36 may make the adjustments to avoid data out of range, to avoid having unused range, or both.

In one embodiment of the invention, microprocessor 36 senses the possibility of out-of-range data or unused range by sensing the contents of the boundary bins of the histogram, for example by checking whether the data distribution has assigned values to the bins that accumulate the lowest values and the highest values of the histogram. As a result of checking the bins, microprocessor 36 may automatically adjust the gain, or the offset, or both of amplifier 32.

FIG. 3 is an illustration of an exemplary AIMD 100 configured to deliver bi-ventricular, triple chamber cardiac resynchronization therapy (CRT) wherein AIMD 100 fluidly couples to monitor cardiac electrogram (EGM) signals and blood pressure developed within a patient's heart 120. The AIMD 100 may be configured to integrate both monitoring and therapy features, as will be described below. AIMD 100 collects and processes data about heart 120 from one or more sensors including a pressure sensor and an electrode pair for sensing EGM signals. AIMD 100 may further provide therapy or other response to the patient as appropriate, and as described more fully below. As shown in FIG. 3, AIMD 100 may be generally flat and thin to permit subcutaneous implantation within a human body, e.g., within upper thoracic regions or the lower abdominal region. AIMD 100 is provided with a hermetically-sealed housing that encloses a processor 102, a digital memory 104, and other components as appropriate to produce the desired functionalities of the device. In various embodiments, AIMD 100 is implemented as any implanted medical device capable of measuring the heart rate of a patient and a ventricular or arterial pressure signal, including, but not limited to a pacemaker, defibrillator, electrocardiogram monitor, blood pressure monitor, drug pump, insulin monitor, or neurostimulator. An example of a suitable AIMD that may be used in various exemplary embodiments is the CHRONICLE® implantable hemodynamic monitor (IHM) device available from Medtronic, Inc. of Minneapolis, Minn., which includes a mechanical sensor capable of detecting a pressure signal.

In a further embodiment, AIMD 100 comprises any device that is capable of sensing a pressure signal and providing pacing and/or defibrillation or other electrical stimulation therapies to the heart. Another example of an AIMD capable of sensing pressure-related parameters is described in commonly assigned U.S. Pat. No. 6,438,408B1 issued to Mulligan et al. on Aug. 20, 2002.

Processor 102 may be implemented with any type of microprocessor, digital signal processor, application specific integrated circuit (ASIC), field programmable gate array (FPGA) or other integrated or discrete logic circuitry programmed or otherwise configured to provide functionality as described herein. Processor 102 executes instructions stored in digital memory 104 to provide functionality as described below. Instructions provided to processor 102 may be executed in any manner, using any data structures, architecture, programming language and/or other techniques. Digital memory 104 is any storage medium capable of maintaining digital data and instructions provided to processor 102 such as a static or dynamic random access memory (RAM), or any other electronic, magnetic, optical or other storage medium.

As further shown in FIG. 3, AIMD 100 may receive one or more cardiac leads for connection to circuitry enclosed within the housing. In the example of FIG. 3, AIMD 100 receives a right ventricular endocardial lead 118, a left ventricular coronary sinus lead 122, and a right atrial endocardial lead 120, although the particular cardiac leads used will vary from embodiment to embodiment. In addition, the housing of AIMD 100 may function as an electrode, along with other electrodes that may be provided at various locations on the housing of AIMD 100. In alternate embodiments, other data inputs, leads, electrodes and the like may be provided. Ventricular leads 118 and 122 may include, for example, pacing electrodes and defibrillation coil electrodes (not shown) in the event AIMD 100 is configured to provide pacing, cardioversion and/or defibrillation. In addition, ventricular leads 118 and 122 may deliver pacing stimuli in a coordinated fashion to provide biventricular pacing, cardiac resynchronization, extra systolic stimulation therapy or other therapies. AIMD 100 obtains pressure data input from a pressure sensor that is carried by a lead such as right ventricular endocardial lead 118. AIMD 100 may also obtain input data from other internal or external sources (not shown) such as an oxygen sensor, pH monitor, accelerometer or the like.

In operation, AIMD 100 obtains data about heart 120 via leads 118, 120, 122, and/or other sources. This data is provided to processor 102, which suitably analyzes the data, stores appropriate data in memory 104, and/or provides a response or report as appropriate. Any identified cardiac episodes (e.g. an arrhythmia or heart failure decompensation) can be treated by intervention of a physician or in an automated manner. In various embodiments, AIMD 100 activates an alarm upon detection of a cardiac event or a detected malfunction of the AIMD. Alternatively or in addition to alarm activation, AIMD 100 selects or adjusts a therapy and coordinates the delivery of the therapy by AIMD 100 or another appropriate device. Optional therapies that may be applied in various embodiments may include drug delivery or electrical stimulation therapies such as cardiac pacing, resynchronization therapy, extra systolic stimulation, neurostimulation.

FIG. 4 is a block diagram summarizing the data acquisition and processing functions appropriate for practicing the invention. The functions shown in FIG. 4 may be implemented in an AIMD system, such as AIMD 100 shown in FIG. 3. Alternatively, the functions shown in FIG. 4 may be implemented in an external monitoring system that includes sensors coupled to a patient for acquiring pressure signal data. The system includes a data collection module 206, a data processing module 202, a response module 218 and/or a reporting module 220. Each of the various modules may be implemented with computer-executable instructions stored in memory 104 and executing on processor 102 (shown in FIG. 3), or in any other manner.

The exemplary modules and blocks shown in FIG. 4 are intended to illustrate one logical model for implementing an AIMD 100, and should not be construed as limiting. Indeed, the various practical embodiments may have widely varying software modules, data structures, applications, processes and the like. As such, the various functions of each module may in practice be combined, distributed or otherwise differently-organized in any fashion across a patient monitoring system. For example, a system may include an implantable pressure sensor and EGM circuit coupled to an AIMD used to acquire pressure and EGM data, an external device in communication with the AIMD to retrieve the pressure and EGM data and coupled to a communication network for transferring the pressure and EGM data to a remote patient management center for analysis. Examples of remote patient monitoring systems in which aspects of the present invention could be implemented are generally disclosed in U.S. Pat. No. 6,497,655 issued to Linberg and U.S. Pat. No. 6,250,309 issued to Krichen et al., both of which patents are incorporated herein by reference in their entirety.

Pressure sensor 210 may be deployed in an artery for measuring an arterial pressure signal or in the left or right ventricle for measuring a ventricular pressure signal. In some embodiments, pressure sensor 210 may include multiple pressure sensors deployed at different arterial and/or ventricular sites. Pressure sensor 210 may be embodied as the pressure sensor disclosed in commonly assigned U.S. Pat. No. 5,564,434, issued to Halperin et al., hereby incorporated herein in its entirety.

Data sources 207 may include other sensors 212 for acquiring physiological signals useful in monitoring a cardiac condition such as an accelerometer or wall motion sensor, a blood flow sensor, a blood gas sensor such as an oxygen sensor, a pH sensor, or impedance sensors for monitoring respiration, lung wetness, or cardiac chamber volumes. The various data sources 207 may be provided alone or in combination with each other, and may vary from embodiment to embodiment.

Data collection module 206 receives data from each of the data sources 207 by polling each of the sources 207, by responding to interrupts or other signals generated by the sources 207, by receiving data at regular time intervals, or according to any other temporal scheme. Data may be received at data collection module 206 in digital or analog format according to any protocol. If any of the data sources generate analog data, data collection module 206 translates the analog signals to digital equivalents using an analog-to-digital conversion scheme. Data collection module 206 may also convert data from protocols used by data sources 207 to data formats acceptable to data processing module 202, as appropriate.

Data processing module 202 is any circuit, programming routine, application or other hardware/software module that is capable of processing data received from data collection module 206. In various embodiments, data processing module 202 is a software application executing on processor 102 of FIG. 3 or another external processor.

Reporting module 220 is any circuit or routine capable of producing appropriate feedback from the AIMD to the patient or to a physician. In various embodiments, suitable reports might include storing data in memory 204, generating an audible or visible alarm 228, producing a wireless message transmitted from a telemetry circuit 230.

In a further embodiment, the particular response provided by reporting module 220 may vary depending upon the severity of the hemodynamic change. Minor episodes may result in no alarm at all, for example, or a relatively non-obtrusive visual or audible alarm. More severe episodes might result in a more noticeable alarm and/or an automatic therapy response.

When the functionality diagramed in FIG. 4 is implemented in an AIMD, telemetry circuitry 230 is included for communicating data from the AIMD to an external device adapted for bidirectional telemetric communication with AIMD. The external device receiving the wireless message may be a programmer/output device that advises the patient, a physician or other attendant of serious conditions (e.g., via a display or a visible or audible alarm). Information stored in memory 204 may be provided to an external device to aid in diagnosis or treatment of the patient. Alternatively, the external device may be an interface to a communications network such that the AIMD is able to transfer data to an expert patient management center or automatically notify medical personnel if an extreme episode occurs.

Response module 218 comprises any circuit, software application or other component that interacts with any type of therapy-providing system 224, which may include any type of therapy delivery mechanisms such as a drug delivery system, neurostimulation, and/or cardiac stimulation. In some embodiments, response module 218 may alternatively or additionally interact with an electrical stimulation therapy device that may be integrated with an AIMD to deliver pacing, extra systolic stimulation, cardioversion, defibrillation and/or any other therapy. Accordingly, the various responses that may be provided by the system vary from simple storage and analysis of data to actual provision of therapy in various embodiments.

The various components and processing modules shown in FIG. 4 may be implemented in an AIMD 100 (e.g., as depicted in FIG. 1 or 3) and housed in a common housing such as that shown in FIG. 3. Alternatively, functional portions of the system shown in FIG. 4 may be housed separately. For example, portions of the therapy delivery system 224 could be integrated with AIMD 100 or provided in a separate housing, particularly where the therapy delivery system includes drug delivery capabilities. In this case, response module 218 may interact with therapy delivery system 224 via an electrical cable or wireless link.

FIGS. 5A-B are plan views of medical electrical leads according to alternate embodiments of the present invention. FIG. 5A illustrates a lead 10 including a lead body 11 having a proximal portion 12 and a distal portion 13; distal portion 13 includes a distal tip 14, to which a fixation element 15 and a cathode tip electrode 16 are coupled, a defibrillation electrode 19 positioned proximal to distal tip 14 and a sensor 17 positioned proximal to defibrillation electrode 19. FIG. 5B illustrates a lead 100 also including lead body 11, however, according to this embodiment, sensor 17 is positioned distal to defibrillation electrode 19 and distal tip 14 further includes an anode ring electrode 18 and cathode tip electrode 16 is combined into fixation element 15. Appropriate cathode electrode, anode electrode and defibrillation electrode designs known to those skilled in the art may be incorporated into embodiments of the present invention. Although FIGS. 5A-B illustrate proximal portion 12 including a second defibrillation electrode 20, embodiments of the present invention need not include second defibrillation electrode 20. For those embodiments including defibrillation electrode 20, electrode 20 is positioned along lead body such that electrode 20 is located in proximity to a junction between a superior vena cava 310 and a right atrium 300 when distal portion 13 of lead body 11 is implanted in a right ventricle 200 (FIG. 3). Additionally, tip electrode 16 and ring electrode 18 are not necessary elements of embodiments of the present invention.

FIGS. 5A-B illustrate fixation element 15 as a distally extending helix, however element 15 may take on other forms, such as tines or barbs, and may extend from distal tip 14 at a different position and in a different direction, so long as element 15 couples lead body 11 to an endocardial surface of the heart in such a way to accommodate positioning of defibrillation electrode 19 and sensor 17 appropriately.

According to alternate embodiments of the present invention, sensor 17 is selected from a group of physiological sensors, which should be positioned in high flow regions of a circulatory system in order to assure proper function and long term implant viability of the sensor; examples from this group are well known to those skilled in the art and include, but are not limited to oxygen sensors, pressure sensors, flow sensors and temperature sensors. Commonly assigned U.S. Pat. No. 5,564,434 describes the construction of a pressure and temperature sensor and means for integrating the sensor into an implantable lead body. Commonly assigned U.S. Pat. No. 4,791,935 describes the construction of an oxygen sensor and means for integrating the sensor into an implantable lead body. The teachings U.S. Pat. Nos. 5,564,434 and 4,791,935, which provide means for constructing some embodiments of the present invention, are incorporated by reference herein.

FIGS. 5A-B further illustrates lead body 11 joined to connector legs 2 via a first transition sleeve 3 and a second transition sleeve 4; connector legs 2 are adapted to electrically couple electrodes 15, 16, 19 and 20 and sensor 17 to an AIMD in a manner well known to those skilled in the art. Insulated electrical conductors, not shown, coupling each electrode 15, 16, 19 and 20 and sensor 17 to connector legs 2, extend within lead body 11. Arrangements of the conductors within lead body 11 include coaxial positioning, non-coaxial positioning and a combination thereof; according to one exemplary embodiment, lead body 11 is formed in part by a silicone or polyurethane multilumen tube, wherein each lumen carries one or more conductors.

FIG. 6 is a cross sectional view of a coaxial conductive lead body 11 adapted for operative coupling proximal of a sensor capsule taken along the line 6-6 of FIG. 5B according to the invention. In FIG. 6, an inner conductor 50 is spaced from an outer conductor 52 with an insulative material 54 disposed therebetween. The exterior of the biocompatible outer insulation 56 of the lead body 11 shields the conductors 50,52 from contact with conductive body fluid. One aspect of the instant invention involves failure of the outer insulation 56 and ways to render such a failure essentially innocuous to a patient.

FIG. 7 is a schematic illustration of a sensor capsule 17 coupled to a housing 100 of an IMD and a source of reference potential 53 according to certain embodiments of the invention described herein.

FIG. 8. is a schematic view of a sensor capsule 17 coupled to a electrical current detector 55 and operative circuitry housed within an IMD 100. As described herein in the event that excess current is detected energy for the sensor capsule 17 can be interrupted, either permanently or temporarily.

FIG. 9 is a schematic view of an IMD 100 having a proximal lead-end set screw 13 for mechanically retaining the proximal end of a medical electrical lead 11 within a connector block 57, wherein said set screw couples to a source of reference potential 53. The set screw can also promote electrical communication between conductors on the proximal end of the lead 11 and corresponding conductive portions of the connector block 57. The conductive portions connect via hermetically sealed conductive feedthrough pins to operative circuitry within the IMD 100.

Employing the foregoing methods and apparatus and equivalents thereof, a variety of component failures can be selectively retested and possibly restored by energizing an implantable physiologic sensor (IPS) at relatively low voltages and/or during periods of time when adjacent tissue is non-excitatory (e.g., the absolute and/or relative refractory period for myocardial tissue). The relatively low voltages help ensure that in the event electrical energy is restored to an IPS and adjacent tissue is in fact in an excitable state, an inadvertent delivery of energy to the tissue might not capture (i.e., evoke a response). In the event that the adjacent tissue comprises myocardial tissue, a threshold indicating failure during a retest can include a direct current (dc) of about 9.5 or 10 microamps. Alternately, if an impedance measurement reveals very high impedance in the IPS circuitry (e.g., 10 megaohms) likely no errant electrical currents are being inadvertently delivered via the IPS.

A retesting regimen can include a period of time between successive retesting episodes (e.g., several minutes, hours, etc.). In order to declare a previously detected errant current flow episode absent, confirmation criteria can require several successive successful retesting sequences (e.g., three-of-three, etc.). Such criteria helps mitigate the possibility of noise (i.e., improves noise rejection). In addition, in the case an IPG includes activity sensing capability the then-present heart rate and/or activity sensor output signals can be used to select an advantageous time to retest the IPS circuitry.

Thus, a system and method have been described which provide methods and apparatus for mitigating possible failure mechanisms for AIMDs coupled to chronically implantable sensors. Aspects of the present invention have been illustrated by the exemplary embodiments described herein. Numerous variations for providing such robust structures and methods can be readily appreciated by one having skill in the art having the benefit of the teachings provided herein. The described embodiments are intended to be illustrative of methods for practicing the invention and, therefore, should not be considered limiting with regard to the following claims.

While exemplary embodiments have been presented in the foregoing detailed description of the invention, it should be appreciated that a vast number of variations exist. It should also be appreciated that these exemplary embodiments are only examples, and are not intended to limit the scope, applicability, or configuration of the invention in any way. Rather, the foregoing detailed description will provide a convenient road map for implementing an exemplary embodiment of the invention. Various changes may be made in the function and arrangement of elements described in an exemplary embodiment without departing from the scope of the invention as set forth in the appended claims and their legal equivalents.

Claims

1. An apparatus for rendering an active implantable medical device (AIMD) remotely coupled to an implantable physiologic sensor (IPS) fault tolerant to undesirable electrical shunt to a body, comprising: an implantable physiologic sensor (IPS) disposed within a sensor housing; an electrically conductive member switchably coupled to at least one of a pair of opposing electrical poles of said IPS; and means for switching the electrically conductive member, said means operable to alternately engage and disengage the conductive member from said one of the pair of opposing electrical poles when adjacent tissue is non-excitatory.

2. An apparatus according to claim 1, further comprising means for detecting electro-temporal signals during a cardiac cycle and for engaging the conductive member only during a portion of a refractory period of said cardiac cycle.

3. An apparatus according to claim 2, wherein the sensor comprises a mechanical sensor.

4. An apparatus according to claim 3, wherein the mechanical sensor comprises one of an accelerometer and a pressure sensor.

5. An apparatus according to claim 2, wherein the sensor comprises an optical-type blood-based sensor.

6. An apparatus according to claim 5, wherein the blood-based sensor comprises one of: a saturated oxygen sensor, a pH sensor, a potassium-ion sensor, a calcium-ion sensor, a lactate sensor, a metabolite sensor, a glucose sensor.

7. An apparatus according to claim 2, wherein the AIMD comprises one of: an implantable pulse generator, an implantable cardioverter-defibrillator, a substance delivery device.

8. An apparatus according to claim 7, wherein the implantable pulse generator comprises one of: a physiologic monitoring apparatus, a cardiac pacemaker, a gastric stimulator, a neurological stimulator, a brain stimulator, a skeletal muscle stimulator, a cardiac resynchronization device.

9. An apparatus according to claim 7, wherein the substance comprises: a drug, a hormone, a protein, a volume of genetic material, a peptide, a volume of biological material.

10. An apparatus according to claim 2, wherein the means for switching comprises at least one of: a multiplexing circuit, a solid state switch, a transistor, a field programmable gate array, an electronic logic circuit.

11. An apparatus according to claim 1, further comprising: means for detecting excessive electrical current drain of said IPS and for providing an IPS integrity signal in the event that no excessive current drain is detected; and means for resuming normal IPS operation in the event that an IPS integrity signal is provided.

12. A method for rendering an active implantable medical device (AIMD) remotely coupled to an implantable physiologic sensor (IPS) fault tolerant, comprising: switchably coupling at least one of a pair of elongated conductors to a chronically implantable physiologic sensor (IPS), wherein said IPS is disposed within a sensor capsule and wherein said pair of conductors are disposed within a single insulative sheath, wherein said coupling electrically connects the IPS to one of said at least the pair of elongated conductors only during a temporal interval when essentially no evoked response can be produced in a portion of tissue adjacent said IPS.

13. A method according to claim 12, further comprising: detecting electro-temporal signals during a cardiac cycle; and connecting the conductive member to the IPS only during a portion of a refractory period of said cardiac cycle.

14. A method according to claim 13, wherein the IPS comprises a mechanical sensor.

15. A method according to claim 13, wherein the mechanical sensor comprises one of an accelerometer and a pressure sensor.

16. A method according to claim 13, wherein the IPS comprises a blood-based sensor.

17. A method according to claim 16, wherein the blood-based sensor comprises one of: a saturated oxygen sensor, a pH sensor, a potassium-ion sensor, a calcium-ion sensor, a lactate sensor, a metabolite sensor, a glucose sensor.

18. A method according to claim 13, wherein the AIMD comprises one of a implantable pulse generator, an implantable cardioverter-defibrillator, a substance delivery device.

19. A method according to claim 18, wherein the implantable pulse generator comprises one of: a physiologic monitoring apparatus, a cardiac pacemaker, a gastric stimulator, a neurological stimulator, a brain stimulator, a skeletal muscle stimulator, an implantable cardioverter-defibrillator.

20. A method according to claim 12, wherein the switchably coupling step is accomplished by at least one of the following structures: a multiplexing circuit, a solid state switch, a transistor, a field programmable gate array, an electronic logic circuit.