METHOD AND APPARATUS FOR HEART TRANSPLANT MONITORING AND ANALOG TELEMETRY CALIBRATION

Abstract: A cardiac pacemaker with an analog telemetry system. A calibration circuit within the pacemaker is adapted to provide a reference signal of known character to the pacemaker's telemetry system. The reference signal is transmitted across the telemetry link as if it were an actual cardiac signal, and received by an external programmer. Since the reference signal has known, predetermined qualities, the programmer can automatically calibrate and scale the telemetry signal from the pacemaker, thereby increasing the accuracy of the telemetry channel. The increased accuracy is particularly useful in assessing rejection of a transplanted heart, which is known to be associated with a 15 % decline in the peak R-wave amplitude of the cardiac signal.

Description: METHOD AND APPARATUS FOR HEART TRANSPLANT MONITORING AND ANALOG TELEMETRY CALIBRATION FIELD OF THE INVENTION This invention relates to the field of cardiac pacemakers, and more particularly to a pacemaker having an automatic calibration signal for an analog telemetry channel. BACKGROUND OF THE INVENTION As of January 1, 1991, over 16,000 heart transplants have taken place worldwide, more than 87% of these since 1984 (according to Kreitt et al., "The Registry of the International Society for Heart and Lung Transplantation: Eight Annual Report", The Journal of Heart and Lung Transplantation, Number 4, July-August 1991, pp. 491 - 498). Rejection of the transplanted heart within two years is the cause of death in 40% or more of all cases. Currently, the preferred method for monitoring rejection is by serial transvenous endomyocardial biopsy. Such a procedure is invasive and relatively traumatic, and must usually be performed at specialized facilities. Typically, two such tests are performed during the first six post-implant months; thereafter, the tests are given less frequently, but throughout the patient's lifetime. Up to a day may be required to obtain results from such a test. One known shortcoming of the serial transvenous endomyocardial biopsy in evaluating heart rejection is that existing scar tissue in the heart, which can occur for various reasons other than heart rejection, can be erroneously interpreted as indicating rejection. It has also been found, however, that certain features of the electrical cardiac signal in transplant patients may also be utilized as an indicator of heart rejection. See, e.g., Warnecke et al. , "Noninvasive Monitoring of Cardiac Allograft Rejection by Intramyocardial Electrogram Recordings", Circulation 74 (suppl. Ill), 111-72 - 111-76, 1986. In particular, it has been found that the onset of heart rejection is accompanied by a reduction of up to 15% in the magnitude of intracardiac R-wave and T-wave peaks. See, e.g., Rosenbloom et al., "Noninvasive Detection of Cardiac Allograft Rejection by Analysis of the Unipolar Peak-to-Peak Amplitude of Intramyocardial Electrograms", Ann. Thorac. Surg. , 1989;47:407-411; see also, e.g., Grace et al., "Diagnosis of Early Cardiac Transplant Rejection by Fall in Evoked T Wave Amplitude Measured Using an Externalized QT Driven Rate Responsive Pacemaker", PACE, vol. 14, June 1991. The ability to monitor and detect this phenomenon would therefore facilitate the early detection and treatment of rejection. To this end, an implantable pacemaker with an accurate analog telemetry channel for transmitting intracardiac signals would greatly enhance the ability of a monitoring physician to assess the cardiac condition. Intracardiac electrogram signals have been used to evaluate heart rejection. Typically, however, several or perhaps up to five or more epicardial leads may be used for this purpose, since it is believed that the manifestations of heart rejection are initially localized and can begin at various sites in the heart muscle. The intracardiac leads associated with an implanted pacemaker might also be used in the evaluation of cardiac signals. Unfortunately, even today's state-of-the-art pacemakers have rather inaccurate telemetry channels, varying greatly in their response from one device to another and susceptible to problems with drift, change with temperature, and battery condition. The inaccuracies in the peripheral (programmer) can compound the pacemaker and telemetry channel errors. In some cases, the accuracy of a telemetered intracardiac EGM signal from an implanted pacemaker may be only ± 35%. SUMMARY OF THE INVENTION It is believed by the inventors, therefore, that it would be desirable to provide a more accurate analog telemetry channel for an implantable cardiac pacemaker, so that an accurate and reliable assessment of cardiac activity can be made. In accordance with the present invention, a signal is provided to automatically calibrate a pacemaker's analog telemetry channel. The increased accuracy of the telemetered EGM signal would allow it to be used not only in transplant rejection monitoring, but also for measuring amplitude and slew rate in cardiac signals, evaluation of lead maturation effects, general pacemaker system troubleshooting, and congestive heart failure (CHF) monitoring. In accordance with one embodiment of the present invention, a known and accurate test signal at the lead tip electrode is transmitted through the telemetry channel, allowing the external programmer or other peripheral to automatically calibrate and auto-range the entire telemetry system, which includes the pacemaker filtering circuitry, pacemaker gain control circuitry, a voltage-to-frequency converter or some other type analog-to-digital converter, a data encoder, radio frequency link, a data decoder, and signal reconstruction and display circuitry. BRIEF DESCRIPTION OF THE DRAWINGS The foregoing and other aspects of the present invention will be best understood with reference to the following detailed description of a specific embodiment of the invention, when read in conjunction with the accompanying drawings, wherein: Figure 1 is an illustration of a pacemaker and pacemaker leads in accordance with one embodiment of the present invention, implanted in a patient; Figure 2 is an illustration of the pacemaker and leads from Figure 1 ; Figure 3 is a block diagram showing a portion of the circuitry of the pacemaker of Figure 1 and an external programmer; Figure 4 is a timing diagram illustrating clock signals utilized by the circuitry of Figure 3; Figure 5 is a block diagram of the calibration circuit of Figure 3; Figure 6 is a schematic diagram of the calibration circuit of Figure 3; Figure 7 is a timing diagram illustrating signals in the calibration circuit of Figure 6; and Figures 8a and 8b are timing diagrams illustrating the calibration signal after transmission to the programmer of Figure 3. DETATLED DESCRIPTION OF A SPECIFIC EMBODIMENT OF THE INVENTION In Figure 1, a pacemaker 10 in accordance with one embodiment of the present invention is shown implanted in a patient 12. Pacemaker 10 is electrically coupled to heart 16 of patient 12 by means of four unipolar epicardial leads 18-1, 18-2, 18-3, and 18-4. One pacemaker which may be readily adapted for use in accordance with the presently disclosed embodiment of the invention is disclosed in U.S. Patent No. 5,052,388 issued to Sivula et al. on October 1, 1991, which patent is hereby incorporated by reference in its entirety. It is believed by the inventors, however, that from the following detailed description of a specific embodiment of the present invention it should be apparent to a person of ordinary skill in the pacemaker art how the present invention may be practiced in conjunction with a variety of known pacemaker designs. As shown in Figure 2, pacemaker 10 is provided with a connector block 11 for receiving connector pins 20 and 22 of two "IS-1 to bifurcated" adapters 24 and 26. Adapters 24 and 26 allow the four unipolar leads 18-1, 18-2, 18-3, and 18-4 to be interfaced with industry standard IS-1 connection points in dual bipolar connector block 11. Leads 18-1, 18-2, 18-3, and 18-4 may be Medtronic Models 5069 or 5071 Unipolar Epicardial leads or the like. Adapters 24 and 26 may be, for example, Model 5866- 24M IS-1 to bifurcated adapters manufactured and commercially available from Medtronic, Inc., Minneapolis, Minnesota. In an alternative embodiment, a connector block 11 capable of receiving all four leads 18-1, 18-2, 18-3, and 18-4 could be provided, thereby eliminating the need for adapters 24 and 26. Turning now to Figure 3, a block diagram showing selected relevant portions of internal circuitry of pacemaker 10, as well as an external programmer 32 which communicates with pacemaker 10 via a radio-frequency telemetry link. In Figure 3, leads 18-1, 18-2, 18-3, and 18-4 are shown being directly connected to a multiplexer 30 in pacemaker 10, it being understood that adapters 24 and 26 may be required to facilitate the connection of four leads to pacemaker 10, as previously described with reference to Figure 2. Multiplexer 30 functions to sequentially couple each of leads 18-1, 18-2, 18-3, and 18-4 one at a time to internal conductor 34 of pacemaker 10. For example, and as shown in Figure 3, a four-phase clock comprising individual phase signals φ φ 2 , Φ 3 , and 4 may be applied to multiplexer 30, such that lead 18-1 is coupled to conductor 34 during assertion of φ lead 18-2 is coupled to conductor 34 during assertion of φ 2 , and so on. It is believed that the design and implementation of multiplexer 30 would be a matter of routine to a person of ordinary skill in the circuit art. If clock signals φ_, φ 2 , φ 3 , and φ 4 shown in Figure 4 were applied to multiplexer 30, for example, each one of leads 18-1, 18-2, 18-3, and 18-4 would be coupled to conductor 34 for 1.95-mSec at a time, 128 times per second. A pacing output circuit 36 is also shown in Figure 3. The inventors have contemplated several different pacing arrangements for pacemaker 10. One or more of leads 18-1, 18-2, 18-3, and 18-4 could be utilized as both a pacing and sensing lead. This can be implemented in two ways: either multiplexer 30 may be controlled by signals φ_, φ 2 , Φi and φ to apply pacing pulses produced on line 40 by pacing output circuit 36 to a selected one or more of leads 18-1, 18-2, 18-3, and 18-4; or pacing output circuit could provide pacing pulses on line 40' to a lead select circuit 42 adapted to convey pacing pulses on line 40' to a selected one or more of leads 18-1, 18-2, 18-3 and 18-4, the selection being indicated, for example, by means of control signals from pacemaker control circuitry not shown in Figure 3. Cardiac electrical signals from leads 18-1, 18-2, 18-3, and 18-4 are conducted on line 34 to a bandpass filter circuit 44, which in the presently disclosed embodiment of the invention comprises a high-pass filter made up of a capacitor 46 and a resistor 48, and a low-pass filter made up of resistor 50 and capacitor 52. In the presently preferred embodiment of the invention, bandpass filter 44 has a high-pass pole at 0.072-Hz and a low-pass pole at 182-Hz. After filtering, cardiac signals from leads 18-1, 18-2, 18-3 and 18-4 are applied to a telemetry circuit 54. A telemetry circuit that is suitable for the purposes of the present invention is described in U.S. Patent No. 4,556,063 issued to Thompson et al. on December 3, 1985 entitled "Telemetry System for a Medical Device", which patent is hereby incorporated by reference in its entirety. Another telemetry system suitable for the purposes of the present invention is disclosed in U.S Patent Application S.N. 07/765,475 in the name of Wyborny et al., entitled "Telemetry Format for Implanted Medical Device", which patent is also incorporated herein by reference in its entirety. Telemetry circuit 54 is coupled to a radio-frequency (RF) transmitting/receiving antenna 56 capable of transmitting signals to a compatible antenna 58 associated with external programmer 32. Programmer 32 may also have associated therewith various display devices such as a CRT 60 or a paper strip recorder 62, allowing a physician to view the telemetered EGM signal. Further in accordance with the presently disclosed embodiment of the invention, pacemaker 10 is provided with a calibration circuit 64 coupled to conductor 34. As will be hereinafter described in greater detail, calibration circuit 64 is adapted to generate on conductor 34 known "test" or "reference" signals that may be applied to the pacemaker's telemetry channel. Upon receipt of this reference signal, external programmer 32 is thus able to automatically calibrate and auto-range the complete system, compensating for the effects of filter 44, pacemaker circuitry gain variability, telemetry system conversion inaccuracies, RF link decoding variations (i.e., "noise"), and peripheral ranging, signal reconstruction variations and inaccuracies. According to one embodiment of the present invention, the reference signal generated by calibration circuit 64 is a 0.5-Hz square wave passed through a low pass filter at 10-mN amplitude, that is switched into the telemetry channel (i.e., onto conductor 34) for processing and transmission to programmer 32. Programmer 32 then uses the reference signal to calibrate the telemetry channel and automatically set the range of the received signal for display on CRT 60 or strip recorder 62. Calibration circuit 64 is also capable of producing a "differential wave" output reference signal, produced by differentiation of the square wave reference signal at each pulse edge. The "differential wave" signal thus comprises a stream of alternating positive and negative voltage spikes having a peak magnitude of ± 10-mV. The maximum value of the differential signal, after transmission across the telemetry link, would be detected in programmer 32 using a peak detector for each polarity. The advantage of the "differential wave" reference signal is that it allows accurate, simultaneous dual-polarity calibration of the telemetry channel. Referring now to Figure 5, a block diagram of calibration circuit 64 is shown. It is to be understood in Figure 5 that the various input signals to calibration circuit 64 are provided from elsewhere in the circuitry of pacemaker 10. For example, the signals SQ_WAVESEL and DIF_CALSEL are provided from controller circuitry (not shown) to enable selection of either a square-wave reference signal or a "differential wave" reference signal. The NREFIN input signal to calibration circuit 64 is a 1.2-V reference voltage that is applied to voltage divider 66. Voltage divider 66 derives a regulated 10-mV signal that is applied to a 0.5-Hz oscillator circuit 68. It is believed by the inventors that the design and implementation of voltage divider circuit 66 would be a matter of routine to a person of ordinary skill in the circuit art. The CLK_0_5 input signal to oscillator 68 is a 0.5-Hz clock signal. The CALON input signal enables voltage divider 66 and oscillator 68; thus, when CALON is not asserted, voltage divider 66 and oscillator 68 are disabled and draw no bias current. This is particularly desirable in implanted medical devices, where power conservation is critical to maximum device longevity. Finally, the LP1KHZ_CLK input signal to calibration circuit 64 is a 1-kHz clock signal utilized by a 5-Hz low-pass filter circuit 70. A schematic diagram of calibration circuit 64 is shown in Figure 6. As shown in Figure 6, a number of internal phase signals PI, NP1, P2, and NP2 are derived from the CLK_0_5 input signal as applied to a non-overlap (NOLS) shifter 74; these phase signals are used elsewhere in the calibration circuit, as shown in Figure 6, to enable various transmission gates Tl, T2, and so on. With continued reference to Figure 6, the CALON signal enables amplifier AMP1 prior to a calibration pulse. As would be appreciated by one of ordinary skill in the circuit art, AMP1 is an operational transconductance amplifier. The NREFIN voltage is sampled on capacitor C 1 (which in the presently preferred embodiment of the invention has a capacitance of 1.14-pF) during phase 2 (i.e., when P2 is asserted). Also during P2, the offset for amplifier AMP1 is sampled on capacitor C5 (with capacitance of 120- pF) to implement a standard offset compensation scheme. During phase 1 (i.e., when PI is asserted), the sampled voltage is divided by the ratio C1/C2. The DIF_CALSEL input enables transistor P3, allowing the calibration pulses output from AMP1 to appear on the DIFF_WANE output line. The SQ_WANESEL input, when asserted, enables transistor P2, gating the calibration pulse output from AMP1 through a low-pass switched capacitor filter with a 5-Hz pole formed by l/2τRC where R=l/fC. A timing diagram illustrating the relationship between the various signals in the schematic diagram of Figure 6 is shown in Figure 7. As shown in Figure 7, the SQUARE_WANE output signal is a simple 0.5-Hz, 10-mV square wave, while the DIFF_WANE output signal is a stream of alternating positive and negative spikes having peak voltages of 10-mV. Figures 8a and 8b show what the SQUARE_WAVE and DIFF_WAVE output signals, respectively look like after having been transmitted by telemetry circuit 54 and printed on strip recorder 62. It is contemplated by the inventors that a comparison between the transmitted reference signal received by programmer 32 may be either automatically or manually analyzed for the purpose of determining the effect of the telemetry channel on transmitted signals. Thus, for example, the amount of attenuation of the transmitted signal can be detected (either manually, or by applying the transmitted signal to a threshold detector or the like) by comparing the transmitted signal with the known reference signal level. As an alternative to transmitting the cardiac signals from leads 18-1, 18-2, 18-3, and 18-4 to an external peripheral as described above with reference to Figure 3, it has been further contemplated by the inventors that heart transplant monitoring may be accomplished by providing in pacemaker 10 circuitry for storing long-term averages of peak values of those signals. These stored values could be subsequently transmitted to the external device for analysis. An implantable device capable of computing long-term average values of various diagnostic values is extensively described in pending U.S. Patent Application Serial No. 07/881,996 filed on May 1, 1992 by Nichols et al., entitled "Diagnostic Function Data Storage and Telemetry Out for Rate Responsive Cardiac Pacemaker", which application is hereby incorporated by reference in its entirety. The inventors have also contemplated a further refinement of the presently disclosed embodiment of the invention, wherein an internal clock in pacemaker 10 would enable amplitude evaluation as described hereinabove at periodic intervals, for example, every twenty-four hours. By performing the amplitude evaluation only at periodic intervals, advantages in memory and battery efficiency may be realized. In addition, this arrangement would provide a method of obtaining a stable baseline of the values, since the effects of normal short-term or cycle-to-cycle variations in the cardiac signal would be minimized. As an example, the amplitude evaluation could occur during the middle of the night to ensure the patient is at rest. Still another refinement to the presently disclosed embodiment of the invention has been contemplated, wherein an activity sensor is also provided in pacemaker 10. As noted in the above-referenced Rosenbloom article, exercise-induced regional ischemia may also produce abrupt and substantial declines in the peak R-wave, which may be erroneously interpreted as indicating rejection. If the present invention were practiced with a pacemaker having an activity sensor, however, exercise-induced R-wave variations could be readily distinguished from the decline in peak R-wave amplitudes associated with rejection by sampling data during periods of patient inactivity. Still another refinement to the presently disclosed embodiment of the invention has been contemplated, wherein electrodes 18-1, 18-2, 18-3, and 18-4 of Figure 2 are sequentially paced unipolarly with respect to the can of pacemaker 10. The three non- paced electrodes monitor the wavefront propagation as the ventricles depolarize. Each sensing lead monitors a different summation of conducted wavelets and, by monitoring the signal arrival at each sensing site, cardiac conduction velocity and intrinsic cardiac tissue status may be monitored. This concept of sensing twelve different sensing configurations allows for a more complete monitoring of cardiac tissue than the hereinabove-described four-site intrinsic waveform monitoring. From the foregoing detailed description of a specific embodiment of the invention, it should be apparent that a method and apparatus for calibrating a telemetry channel has been disclosed. The disclosed method and apparatus are particularly well-suited to the situation in which an implanted cardiac device is used to transmit electrical cardiac signals to an external device, for the purpose of monitoring changes in peak amplitude of the cardiac signals. Such changes, as previously noted can be indicative of certain cardiac conditions, such as rejection of a transplanted heart. Although a particular embodiment of the present invention has been disclosed herein in some detail, it is to be understood that this has been done for the purposes of illustration only, and is not intended to limit the scope of the present invention as defined in the appended claims. It is believed by the inventors that various alterations, modifications, and substitutions may be made to the disclosed embodiment of the invention without departing from the spirit and scope of the invention. In particular, while in the disclosed embodiment a reference signal having a known amplitude is transmitted on the telemetry channel in order to determine whether any attenuation of the reference signal amplitude has occurred in the telemetry channel, it is also contemplated by the inventors that other types of reference signals, for instance sinusoidal signals or the like, may be provided in order to additionally assess the telemetry channel's effect on the phase or frequency spectrum of the reference signal.

Claims: WHAT IS CLAIMED IS: 1. An implantable medical device having a telemetry system for communicating analog signals to an external peripheral device, said telemetry system being coupled to a source of electrical cardiac signals, said telemetry system comprising: a calibration circuit, adapted to generate a reference signal having at least one known attribute; a filter circuit, adapted to be alternately coupled to said calibration circuit and said cardiac signal source and adapted to filter said reference signal and said cardiac signal; an encoding circuit, coupled to said filter circuit and adapted to digitally encode said filtered signals; a transmitter, coupled to said encoding circuit and adapted to transmit said digitally encoded signals to said external peripheral device to provide for determination of a difference with respect to said attribute between said transmitted reference signal and said reference signal 2. A device in accordance with claim 1, wherein said reference signal is a square wave comprising a stream of square pulses and wherein said at least one known attribute of said reference signal is amplitude of said pulses. 3. A device in accordance with claim 1, wherein said reference signal is a square wave comprising a stream of square pulses and wherein said least one known attribute is pulse width. 4. A device in accordance with claim 1, wherein said reference signal comprises a stream of alternating positive and negative spikes, and wherein said at least one known attribute is peak spike magnitude. 5. A device in accordance with claim 1, wherein said reference signal comprises a sinusoidal waveform, and wherein said at least one known attribute is amplitude. 6. A method of operating a telemetry system having a source signal filter, an encoder, a transmitter, a receiver, and a decoder, said method comprising the steps of: (a) generating a reference signal having at least one known attribute; (b) filtering said reference signal; (c) encoding said signal filtered in step (b); (d) transmitting said signal encoded in step (c); (e) receiving said signal transmitted in step (d); (f) decoding said signal received in step (f); (g) detecting a difference between an attribute of said signal decoded in step (f) and said known reference signal attribute. 7. A method in accordance with claim 6, wherein said step of generating a reference signal comprises selectively generating a square wave and a stream of alternative positive and negative spikes, said square wave and said positive and negative spikes having predetermined amplitudes. 8. A method in accordance with claim 6, wherein said step of generating a reference signal comprises generating a sinusoidal wave having a predetermined amplitude. 9. A method in accordance with claim 8., wherein said known attribute is said predetermined amplitude. 10. A method in accordance with claim 7, wherein said known attribute is said predetermined amplitudes of said square wave and said positive and negative spikes. 11. A heart monitoring system, comprising: an implantable device, adapted to be coupled to a patient's heart via at least one lead; a telemetry channel, adapted to convey analog signals from said implanted device to an external device, said telemetry channel having an unpredictable . 5 attenuation factor associated therewith; a calibration circuit, coupled to said telemetry channel and adapted to provide an analog reference signal thereto for transmission to said external device, said analog reference signal having at least one known attribute; and a display device, coupled to said external device and adapted to display analog 10 signals conveyed over said telemetry channel and to indicate whether a difference between said known attribute of said reference signal and a corresponding attribute of said reference signal exists after said transmission to said external device. 12. A method for quantifying an unpredictable attenuation factor in a telemetry 15 channel between an implanted medical device and an external receiver, comprising the steps of: (a) generating, in said implantable device, a reference signal having a known amplitude; (b) transmitting said reference signal through said telemetry channel; 20 (c) comparing, in said receiver, an amplitude of said reference signal transmitted through said telemetry channel in step (b) with said known amplitude. 13. A method in accordance with claim 12, wherein said reference signal is a square wave. 14. A method in accordance with claim 12, wherein said reference signal is a stream - 25 of alternating positive and negative spikes. 15. A method in accordance with claim 12, wherein said reference signal is a sinusoidal wave. 16. An implantable heart transplant monitoring device, comprising: a plurality of epicardial leads, electrically coupled to a respective plurality of different sensing sites on a patient' s heart and adapted to conduct electrical cardiac signals; a cardiac signal processing circuit, coupled to said plurality of leads, adapted to generate digital values corresponding to peak values of said cardiac signals conducted on said leads; an averaging circuit, coupled to said cardiac signal processing circuit, for computing and periodically updating a long-term average of peak values of said cardiac signals; a digital data storage device, coupled to said averaging circuit and adapted to periodically store said long-term average of peak values; a telemetry system, coupled to said digital data storage device and adapted to transmit said stored long-term averages to an external receiver. 17. A heart transplant monitoring device in accordance with claim 16, further comprising a clock circuit, coupled to said averaging circuit, for enabling said averaging circuit only at a predetermined time of day. 18. A heart transplant monitoring system, comprising: a plurality of implanted, epicardial leads, electrically coupled to a respective plurality of different sensing sites on a patient's heart and adapted to conduct electrical cardiac signals; an implanted telemetry system, coupled to said plurality of leads and adapted to transmit said electrical cardiac signals to an external receiver; signal processing means, coupled to said external receiver and adapted to detect a reduction in said electrical cardiac signals indicative of heart rejection. US93/03450 15 19. A heart transplant monitoring system in accordance with claim 18, further comprising an implanted activity sensing circuit for producing an activity signal corresponding to detected levels of patient activity; wherein said electrical cardiac signals are transmitted via said telemetry system to said external receiver only when said activity signal indicates that the patient is at rest. 20. A method for monitoring rejection of a transplanted heart in a patient, comprising the steps of: (a) sensing, in an implanted device, electrical cardiac activity at at least one site on said heart; and (b) detecting, in said implanted device, a predetermined percentage decrease in peak values of said electrical cardiac activity. 21. A method in accordance with claim 20, wherein said step of detecting a decrease in peak values of said electrical cardiac activity occurs only when said patient is determined to be at rest. 22. A cardiac monitoring device, comprising: a plurality of epicardial pacing/sensing leads, electrically coupled to a patient's heart and adapted to conduct electrical cardiac signals and to conduct cardiac stimulating pulses to said heart; a pulse generator circuit, selectively coupled to each one of said plurality of pacing/sensing leads, for generating said cardiac stimulating pulses; a plurality of sensing circuits, each one of said sensing circuits associated with a respective one of said plurality of leads; a switching circuit, coupled to said pulse generator and to said plurality of leads, adapted to periodically couple one of said plurality of leads to said pulse generator circuit and to couple all others of said plurality of leads to their respectively associated sensing circuits; wherein said sensing circuits are adapted to determine cardiac conduction velocity when a cardiac stimulating pulse from said pulse generator is delivered to said heart via said one lead coupled to said pulse generator.

Inventors: MULIER PETER M J, THOMPSON DAVID L, WAHLSTRAND JOHN D, MULIER, PETER, M., J., THOMPSON, DAVID, L., WAHLSTRAND, JOHN, D.
Applicants: MEDTRONIC INC, MEDTRONIC, INC.
Application year: 1993
Main classification: A61N1
IPC codes: A61B5, A61N1