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WO1993020890A1 - Stimulateur cardiaque a reflectometre a dimension temporelle - Google Patents

Stimulateur cardiaque a reflectometre a dimension temporelle Download PDF

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Publication number
WO1993020890A1
WO1993020890A1 PCT/US1993/003218 US9303218W WO9320890A1 WO 1993020890 A1 WO1993020890 A1 WO 1993020890A1 US 9303218 W US9303218 W US 9303218W WO 9320890 A1 WO9320890 A1 WO 9320890A1
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WO
WIPO (PCT)
Prior art keywords
tdr
electrode
signal
time domain
reading
Prior art date
Application number
PCT/US1993/003218
Other languages
English (en)
Inventor
Jack Raymond Robson
Original Assignee
Random Technologies, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US07/866,850 external-priority patent/US5231987A/en
Priority claimed from US07/971,415 external-priority patent/US5233986A/en
Priority claimed from US07/971,281 external-priority patent/US5251622A/en
Application filed by Random Technologies, Inc. filed Critical Random Technologies, Inc.
Publication of WO1993020890A1 publication Critical patent/WO1993020890A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/37—Monitoring; Protecting
    • A61N1/3706—Pacemaker parameters

Definitions

  • This invention relates to a device, system and method used in medical testing, and, in particular, to a technique for testing the integrity of an electrode or cable (or combination thereof) nrough which electrical signals, such as heart pacing pulses, pass, and relates to a responsive system for adjusting the waveform, such as the pacing rate, of a pacemaker in response to changes in physiological activity of the user.
  • electrical signals such as heart pacing pulses
  • a number of medical devices are available which provide assistance in the performance of various physiological functions for an individual experiencing difficulties. Some of these devices are implanted within the patient's body while others are external and are typically utilized under temporary or emergency situations.
  • Electrodes or cable connected to the patient for the performance of a physiological function or for the receipt of information from the patient.
  • Cardiac pacemakers, defibrillators, the Jarvis heart and insulin pumps are a few examples of devices which may be implanted within the patient's body.
  • External devices also include cardiac pacemakers and defibrillators and ECG monitors and other diagnostic equipment.
  • implantable devices are usually comprised of a power source coupled with electrical and/or mechanical components necessary to perform the desired function.
  • the power source and the other components may require replacement or repair over the life of the patient. Therefore, many implantable devices provide a mechanism for non-invasively providing vital information regarding the device's performance. In this manner, it may be determined without surgery whether the device is in need of repair or replacement or whether the device is approaching a threshold thereby indicating the need for replacement or repair.
  • a number of cardiac pacemakers available on the market today are capable of being both programmed and evaluated non-invasively. These pacemakers include, for example, the Model 402B Multicor* II manufactured by Cordis Corporation of Miami, Florida, the Quantum* Model 254-09 manufactured by Intermedics, inc. of Freeport, Texas, the Chorus DDD manufactured by ELA Medical, Inc. of Minnetonka, Minnesota, and the DDDR and GenesisTM pacemakers from
  • the Ventak® P Mode 1600 automatic implantable cardioverter defibrillator is another example of an implantable device providing remote programming and evaluation capabilities. These devices typically include an RF transceiver to communicate with an external user interface system, which includes a "programming wand.”
  • the external system such as the Pacesetter* APS-II Model 3000 Programmer with Model 3030 Function Pack, available from Pacesetter Systems, inc. of Sylmar
  • the California includes controls to allow physician or medical technician program the diagnostic functions of the device and evaluate its operating parameters.
  • the types of information which may be telemetered from, for example, a pacemaker to such an external system include the device's model number, serial number, mode in which the pacemaker is programmed, magnet rate, lead impedance, and electrode/lead information such as the type of electrode implanted in the patient.
  • battery life one of the vital characteristics affecting the performance of the pacemaker, may also be telemetered.
  • defibrillators such as the Ventak* P AICDTM Model 1600 manufactured by Cardiac Pacemakers, inc. of St. Paul, Minnesota, also are capable of telemetering performance information to such a programming system.
  • Some types of problems are not readily discernable with the pacemakers and the defibrillators currently available. Specifically, with regard to an electrode connected to such devices, little information, with the exception of type of electrode used, is available through an external programming system. Various types of problems can occur with such electrodes including lead fracture, lead displacement, body reaction to the lead interface, migration of the lead through body tissue, unsatisfactory electrode position and faulty connection with the implantable device. For example, the electrode may be improperly fastened to the pacemaker resulting in an ohmic or loose junction or, after the electrode is implanted, it may rub against a bone within the patient's body and strip the electrode's insulation. Thus, it is desireable to develop an implantable device having an electrode which is capable of providing information about the integrity of the electrode in a non- invasive manner both at the time the device is implanted and throughout the time the electrode remains implanted.
  • X-ray radiographs are not adequate for integrity testing as they are unable to provide information about the connection between the device and the electrode or the condition of the electrode in a reliable manner.
  • an X-ray radiograph may, in some cases, indicate that a fault is located at the point where the electrode is connected to the pacemaker.
  • the performance of other tests or examination of the electrode during a surgical proceeding may reveal a pseudofracture, i.e., no actual fracture is present, such as is caused by the excessive tightening of a suture at that point.
  • pseudofracture i.e., no actual fracture is present, such as is caused by the excessive tightening of a suture at that point.
  • bipolar electrodes are those in which the anode is the case of the planted device and the cathode is the electrical lead.
  • Bipolar electrodes are those in which the anode is the proximal lead electrode and the cathode is the lead electrode. Examples of bipolar electrodes include the VS1 Bipolar Tined Electrode manufactured by Oscor Medical, Inc. of Palm Harbor, Florida.
  • Some devices such as defibrillators require the utilization of bipolar electrodes so that the defibrillator may deliver shocks to the heart as well as simultaneously monitor the heart's function. Thus, it is desirable to develop an integrity testing system which may be used to test the integrity of both unipolar and bipolar electrodes.
  • Electrodes for many applications are insulated so as to avoid affecting or being affected by the surrounding tissue. However, the electrodes can deteriorate over time. Thus, it is desirable to develop an integrity testing system for an implanted electrode which is not significantly affected by the natural deterioration of the electrode.
  • a pacemaker for example, must send pulses to the heart at a specified rate such as 60 pulses per second. For the pacemaker to continue to operate during the testing procedure, the integrity test must be performed without interfering with those pulses.
  • External pacemakers, defibrillators and the like are usually portable devices which are battery-powered and capable of being recharged.
  • the device's portability is important because it is typically used in emergency situations or as a temporary resolution to a patient's problems before a more permanent solution can be rendered.
  • defibrillators may be carried in an ambulance or used in hospital emergency rooms to revive a patient or to restore a normal heart rhythm.
  • An external pacemaker may be used to provide assistance to a patient who has not yet had an internal pacemaker implanted or to provide pacing while the patient is in surgery to implant or replace an implantable pacemaker.
  • cables, electrodes or wires extend from the device to the patient.
  • the Medtronic Model 5345 Temporary Pulse Generator available from Medtronic, Inc. of Minneapolis, Minnesota, is a temporary pacemaker such as may be used by a patient prior to implanting a permanent pacemaker.
  • a patient cable is connected to the device and unipolar or bipolar pacing leads contacting the patient are connected to the patient cable.
  • the Medtronic model 5311 pacing system analyzer is used to test sensing and pacing thresholds of heart electrodes.
  • the Code Master Defibrillators available from Hewlett Packard of Andover, Massachusetts, provide the capabilities of defibrillation and ECG monitoring. Both integral defibrillator paddies and optional gel electrodes may be used with the device to accomplish these functions.
  • the ⁇ fepak* 6 Cardiac Care System available from Physio- Control* Corporation of Redmond, Washington, uses paddles for defibrillation and patient cables for monitoring ECG.
  • a combination pacemaker and defibrillator such as the Zoll PDTM 1200 Pacemaker/Defibrillator, available from ZMI Corporation of Wobum, Massachusetts, uses paddles or gel electrodes for defibrillation and gel electrodes for pacing and for monitoring ECG signals. In all instances, the integrity of the defibrillator, patient cable, or electrode is of utmost importance for the proper operation of the external device.
  • Some external devices such as the Code Master Defibrillators and the Zoll PDTM 1200 Pacemaker/Defibrilfator, provide information to the operator or technician regarding the "integrity" of the electrode. Specifically, these systems provide a warning when a complete circuit is not provided.
  • a complete circuit is one in which there is current flow between the electrodes and there are no severe discontinuities in the electrodes. Thus, the electrodes must be place against a patient's body to complete an electrical circuit in order to determine whether a break exists in the cables, electrodes or the connectors of either. Because the cables or electrodes must contact the patient before a test may be performed does not allow a fault in the system to be identified until the system must be used.
  • the electrodes or cables connected to such external devices which does not require that the patient be connected to the electrodes or cables so that the cables or electrodes may be tested on a routine basis.
  • Many of the electrodes used with these external devices are disposable. A sterilized package containing the electrodes is opened just prior to use.
  • an electrode integrity testing system which is time efficient so as to avoid delaying the provision of the assistance necessary. Furthermore, because physicians will often be utilizing an integrity testing system under stressful circumstances, it must be easy to use and the results of the test must lead to quick interpretation of the integrity of the electrodes or cables.
  • Time domain reflectometers such as the 1502C Metallic Time Domain Reflectometer manufactured by Tektronix, Inc. of Beaverton, Oregon, are used to test the integrity of cable such as co-axial cables. For such integrity testing, time domain reflectometers send electrical pulses down the cable and detect any reflections made by any discontinuities in the cable. Specifically, time domain reflectometers send out successive pulses and measure the respective reflected pulses at times corresponding to points along the cable. Measurements are provided in terms of voltage versus time which can then be converted to resistance over the length of the cable. Time domain reflectometers can locate shorts, opens, defects in the shield of the cable, foreign substances in the cable, kinks, and more.
  • Time domain reflectometers may operate on either a closed or an open circuit. For an open circuit the signal continues to be reflected from the wire and returns to the instrument. In general, variations in the resistance measured by the time domain reflectometer indicates a fault such as a bad connection, the stripping of insulation, pressure on the cable, or a break in the cable. Time domain reflectometry has been used for a variety of applications. In U.S.
  • time domain reflectometry is used to evaluate vibrations.
  • the level of fluid in a vessel may be determined by time domain reflectometry as disclosed in U.S. Patent No. 3,922,914.
  • the constituents of a multi-phased fluid system have been evaluated as disclosed in U.S. Patent No. 4,786,857.
  • time domain reflectometry has been used for optical systems as well.
  • optical time domain reflectometers such as that disclosed in U.S. Patent No. 4,960,989, may be used to determine the tip location of a consumable electrode within an electric furnace as disclosed in U.S. Patent No. 4,843,234.
  • optical time domain reflectometry is used in U.S. Patent No. 5,033,826 to determine which surface of a photographic lens is impairing transmissivity. It is desirable to provide a method and device using time domain reflectometry to determine the integrity of electrodes or cables connected to an external device to thereby alert the cardiologist or the technician of a potential or existing problem associated with the electrode or cable.
  • time domain reflectometry may be used with both unipolar or bipolar electrodes. The velocity of propagation of any electrode is necessary for time domain reflectometry measurements. Such a parameter could be stored in the device.
  • the integrity testing system must be able to be integrated within the device and must not consume a great deal of power.
  • the pacemaker may be designed to generate heart stimulating pulses continually, or only when the patient's natural heart rate falls below a predetermined rate or (internal) threshold. In either case, the generated pulses will occur at a predetermined rate (the "pace rate.")
  • some pacemakers are "rate responsive,” which means that they automatically adjust the pace rate if the patient's suspected physical activity increases or decreases. They are many different systems used in pacemakers to predict when a patient's physical activity has increased, and therefore, when the pacing rate should be increased.
  • pacing rate of a pacemaker
  • the EliteTM Models 7074, 7075, 7076, and 7077 manufactured by Medtronic, inc. of Minneapolis, Minnesota may be programmed to vary the pacing rate in response to detected changes in body motion.
  • a sensor within the device typically a piezoelectric crystal placed on the inside wall of the pacemaker, detects pressure waves within the body caused by body motion. The device then converts these pressure waves into electrical signals.
  • the pacing rate is set in proportion to the frequency and amplitude of these electrical signals.
  • Other systems such as the Relay 1 " Models 293-03 and 294-03 manufactured by Intermedics, Inc. of Freeport, Texas, use an accelerometer instead of a piezoelectric crystal to detect physical motion.
  • the accelerometer computes acceleration by measuring the force exerted by restraints that hold a mass in a fixed position.
  • the accelerometer may either be electrically excited or self-generating, using a piezoelectric crystal as discussed above.
  • Some systems also include multiple accelerometers oriented in different axes, so that movement in different directions can be discerned and used to reduce to obtain are more accurate indication of the extent of physical movement.
  • motion-based responsive systems will increase the pacing rate when a patient is driving down a bumpy road, even though there is no increase in physical activity.
  • a patient may undertake significant physical activity that does not involve movement of the motion sensor, such as when performing bench presses with heavy barbells. In such circumstances, no physical motion will be detected so the pacemaker will not increase the pacing rate, even though an increase would be appropriate.
  • motion-based responsive pacemakers can not distinguish between motions that relate to increased physical activity and those that do not.
  • unnecessary pacing is activated by these devices, battery power consumption results in a shortened battery life.
  • Shortened battery life may require a patient to undergo a surgical procedure to replace the battery sooner than may otherwise be required. It is also desirable to develop a rate-responsive system that requires little power to operate so as to extend pacemaker battery life.
  • Other rate adjusting systems are responsive to certain physiological conditions of a patient.
  • Some pacemaker systems vary the pace rate based on changes in body temperature. These systems use a temperature sensing device such as a thermistor to sample the temperature of the body. The thermistor is built into an electrode of the pacemaker. The resistance of the thermistor varies as a function of temperature so that the device can generate an electrical signal that corresponds to the sensed temperature. This signal may be translated into a pre-programmed activity level used to set the pace rate.
  • body temperature sensitive systems also result in many of the problems that occur in motion sensitive rate-responsive systems as changes in body temperature may occur without regard to physical activity. Thus, the system may attempt to filter out such extraneous temperature changes. Yet, such a filtering system poses the risk that changes in temperature that should be used to vary the pacing rate will be ignored. Further, because the thermistor is built into a specialized electrode, that electrode can only be used with a pacemaker sold by a particular manufacturer, thereby limiting the physician's and patient's choice of pacemakers. Due to cost and insurance regulations, it is not normally feasible to replace a previously implanted electrode or pacemaker. Thus, temperature responsive systems have the shortcomings of being poor predictors of a change in physiological activity, and of having only a limited choice of pacemakers from which to select.
  • QT systems adjust the pace rate by determining the activity level as measured by the QT interval measurement; that is, the time between when a pacing pulse is sent to the heart and the time the QT interval of the heartbeat begins.
  • the heart responds more quickly to a pacing pulse. Therefore, QT systems increase the pacing rate when they sense that this time period is reduced.
  • a particular shortcoming of QT systems is that in order to sense when pacing should be initiated or increased, they must actually send a pacing pulse to the heart, regardless of the patient's intrinsic heart rate. In general, it is medically undesirable to send pacing pulses to the heart unless it is known that the heart actually requires a pulse. In addition, unnecessary pulses also needlessly consume battery power.
  • Another type of rate-responsive system is based on measuring a patient's blood oxygen saturation levels. These systems assume that when a patient increases physical activity, there is a corresponding increase in the blood oxygen saturations level. These systems employ special electrodes equipped with a light emitting diode (“LED”) and a phototransistor which measures the occlusion or blockage between the two. This blockage roughly corresponds to the amount of oxygen in the blood tissue. While the device is based on a physiological phenomenon, it has two drawbacks. First, the LED require a significant amount of power which reduces the life of the battery powering the pacemaker. Additionally, the system requires special electrodes that may lock the physician into the selection of a particular system.
  • LED light emitting diode
  • Rate-responsive systems are also available which depend upon a patient's respiration to alter the pacing rate. These systems assume that increased air volume in the lungs means a patient is breathing deeper, suggesting that the patient is engaged in increased physical activity.
  • Alt et al.. "Function and Selection of Sensors for Optimum Rate-Modulated Pacing," New Perspectives In Cardiac Pacino. ed. Barold et al., 1991, p. 189-196.
  • a system measures the respiratory rate by detecting the electrical impedance between an auxiliary electrode lead and the pacemaker can. Because the electrical conductivity of lung tissue decreases with inspiration, breathing can be detected by monitoring changes in electrical resistance. The resistance can be measured between different points within the system.
  • respiration-dependent respiration-dependent system is likely to detect high impedance changes if the pacemaker user moves his arms or has chest movements. Such measurements may be interpreted by the system as deep breaths that require an increased pace rate. Further, these system requires bipolar electrodes as one wire is needed to emit an RF wave and another wire is required to sense voltage.
  • rate-responsive pacemaker is based on the determination of changes in the stroke volume of the heart.
  • Alt et al.. p. 172-177 As an individual increases physical activity, the stroke volume of the heart increases, regardless of whether the heart rate remains constant due to a condition such as chronotropic incompetence.
  • To measure stroke volume a specialized electrode having two or more electrode poles is positioned with the right ventricle.
  • These impedance-based rate-responsive systems transmit a low-amplitude AC pulse or short intermittent electrical pulses to the multipolar electrode to measure resistance between the electrode poles. As resistance is affected by the amount of blood between the electrode poles, stroke volume is estimated. The pacing rate is increased when an increase in heart stroke volume is detected.
  • these systems also have limitations.
  • stroke volume may be measured as the measurements are dependent upon the position of the electrode pairs. Also, a multipolar rather than a unipolar electrode is required and the electrode must be carefully placed into position. Furthermore, stroke volume may only be measured for endocardia! lead systems, i.e., those residing within the heart, but not for epicardial lead systems. Therefore, selection of a pacemaker that uses a specialized electrode is limited. Though stoke volume is a physiological phenomenon which accurately reflects the pacing requirements, it is desirable to provide a rate- responsive system using stroke volume which is not dependent upon the critical placement of multipolar specialized electrode. It is also desirable to provide a rate-responsive system which works in conjunction with both endocardia! and epicardial lead systems.
  • It is another object of the present invention is to provide a method and apparatus for testing the integrity of cables, leads and/or electrodes connected to external medical devices, such as defibrillators, temporary pacemakers or pacing system analyzers, to thereby alert the physician or a technician of potential for existing problems associated with the electrode or cable that may be detrimental to the patient.
  • external medical devices such as defibrillators, temporary pacemakers or pacing system analyzers
  • the invention comprises a device and method for testing the integrity of an electrode/wire, such as a pacemaker electrode, and electrical wires connected thereto, and a responsive heart stimulating device and method for operating the device.
  • An electrical device has a receptacle for an electrode and includes a time domain reflectometer comprising an output signal mechanism operatively connected to the electrode receptacle.
  • the method of analyzing the integrity of an electrode comprises the steps of generating a time domain reflectometer (TDR) reading (output signal) from the electrode, and transmitting the signal to an output device.
  • the output signal may be analyzed to determined whether it varies by a predetermined threshold, or it may be displayed so that differences in the electrical characteristics of the electrode may be identified.
  • the present invention allows a cardiologist or technician to ensure that the electrode is properly engaged and to determine the integrity of the electrode.
  • the invention also comprises a responsive heart stimulating device and method for operating the device which includes a heart stimulating waveform generator for transmitting a waveform to an electrode.
  • a time domain refisctometer (TDR) is also connectable to the electrode for generating TDR signals.
  • a logic and control unit processes TDR readings from the electrode, and is adapted to alter the heart stimulating waveform in response to the TDR readings.
  • the TDR may be connected to a pacemaker pacing electrode to detect changes in heart stroke volume or cardiac output, or to one or more probes capable of detecting motion of the patient, and the logic and control unit may adjust the pacing rate accordingly.
  • Fig. 1 shows a block diagram of one embodiment of a device of the present invention when used in connection with a programmable cardiac pacemaker.
  • Fig. 2 a representative computer touch screen user interface for configuring and testing an implantable electrode according to the invention.
  • Fig. 3 is a representative computer screen list window displaying an index of previous TDR readings which have been stored in the device.
  • Fig. 4 is a representative computer screen list window displaying a partial index of electrode manufacturers and models, one of which may be selected to provide a set of default electrode, sampling and display options for a particular electrode.
  • Fig. 5 is a representative graphically displayed baseline TDR reading for an electrode in good condition.
  • Fig. 6 is a representative graphically displayed baseline TDR reading having superimposed over it a more recent TDR reading for the same electrode showing that a break has occurred in the electrode and that the electrode is now defective.
  • Fig. 7 is a representative graphically displayed TDR reading for an electrode have a short in it.
  • Fig. 8. is a representative time graph showing the trailing end of a stimulating pulse on the electrode, a TDR incident pulse, and reflective pulse.
  • Fig. 9 shows a block representative diagram of one embodiment of the device of the present invention when used in connection with a portable, external defibriliator/pacemaker.
  • Fig. 10 is a representative graphically displayed baseline TDR reading and a corresponding representative diagram a patient cable connected to an electrode, both of which are in good condition.
  • Fig. 11 is a representative computer screen of a defibriliator/pacemaker in which the patient cable is defective.
  • Figs. 12a and 12b are views of a heart in which a pacemaker is implanted in which the heart is at its respective minimum and maximum stroke volumes.
  • Figs. 13a and 13b are representative TDR readings from an electrode taken at times when the heart is at its respective minimum and maximum stroke volumes.
  • Figs. 14 and 15 are side and top sectional views, respectively, of an enclosed chamber having liquid and TDR probes therein, and which acts as a motion sensor component.
  • Figs. 16-18 are representative TDR readings from the TDR probes in Figs 14 and 15.
  • Fig. 1 there is shown a representative block diagram of one embodiment of the present invention.
  • the invention is located in an implantable multi-programmable pacemaker, which includes logic and control unit 11 (which includes a CPU and appropriate software to carry out the functions described herein), rate limit section 12, and output section/voltage multiplier 13.
  • logic and control unit 11 which includes a CPU and appropriate software to carry out the functions described herein
  • rate limit section 12 and output section/voltage multiplier 13.
  • Conventional microcircuitry and preferably, an application specific integrated circuit, is used to package the TDR and other components in the implantable case.
  • the pacemaker is designed to provide periodic pulse to two implantable pacing electrodes through electrode receiving means, namely connectors 14 and 15, and 16 and 17 respectively.
  • the invention may also be used with a device connected to a single electrode.
  • a telemetry system Connected to logic and control unit 11 is a telemetry system comprised of telemetry transmitter 18 and program receiver 19, both of which on connected to common antenna 20.
  • the telemetry system allows the pacemaker to be interrogated to determine its operating conditions after it has been implanted, and also allows the pacemaker to be reprogrammed without surgery.
  • the device can be reprogrammed to generate stimulating pulses on the pacing electrode at set rate, or at a varying rate depending on cardiac activity.
  • Other parameters such as the pulse width and pulse amplitude can also be specified after the pacemaker has been implanted.
  • These operating parameters are stored in random access memory (RAM) 22, while the control program is stored in read only memory (ROM) 21.
  • the invention also includes time domain reflectometer (TDR) I/O control 23, which includes the circuitry necessary to generate a TDR pulse on the electrodes and to detect the resulting voltage.
  • TDR applies a narrow pulse of current (typically by a tunnel diode) to the electrode and monitors the resulting reflected voltage on the electrode over a period of time.
  • a stored reflected voltage waveform comprises a raw TDR reading. If the electrode has a known propagation velocity (V p ), the time delay to a particular reflection may be interpreted in distance from the pulse generator.
  • a TDR comprises an I/O controller, a digital timebase, an analog timebase, and a pulse generator. As described further below and shown in Fig. 8, the TDR generates a short, square output pulse.
  • the pulse as reflected back by the electrode is monitored. This comprises means for deferring the storing of the TDR signal until the amount time specified by the TDR base time signal has elapsed after the generation of a TDR incident pulse.
  • a portion or "slice" of the reflected wave is stored in an analog timebase. This value is then converted to a digital value by an analog to digital converter and stored in memory.
  • the pulse generating - wave storing process is repeated, except that the time period between the pulse generation an when a portion of the reflected wave is stored is increased slightly, causing a different "slice" of the reflected wave to be stored.
  • a compilation of the stored waveform readings provides a view of the entire reflected wave.
  • a representative TDR pulse may comprise a 300 mV amplitude into a 50 ohm load, with a 25 microsecond pulse duration, and the reflected rise may be detected in less than 200 picoseconds.
  • the system may merely measure the time between the incident pulse and the beginning of the reflected waveform.
  • Logic and control 11 is designed to periodically send pacing signals via output line 24 to output section/voltage multiplier 13.
  • Logic and control section 11 is programmed to cause output section / voltage multiplier to generate cardiac stimulating pulses of predetermined amplitude, duration and frequency according to parameters stored in RAM 22.
  • a typical cardiac pacemaker generates stimulating pulses at frequencies of .5 to 3 per second, at amplitudes from 2.5 V to 8.5 V, and at durations of .15 to 2.3 milliseconds. Accordingly there is a substantial time gap of at least 300 milliseconds between pulses.
  • TDR pulse and reflection reading time can be accomplished with a pulse repetition rate of 200 microseconds, it is possible to take an entire set of 256 readings in well under 60 milliseconds. Thus a complete TDR reading can be generated between the stimulating pulses periodically provided to the pacing electrode. However, it is also within the scope of the invention to space out the TDR pulses between multiple stimulating pulses.
  • the device Prior to implantation of the device in body, the device will be programmed with various default parameters. Conventional pacemakers are programmed, for example to specify the stimulating pulse repetition rate, pulse amplitude, positive and negative sensitivities and control mode. Prior to implantation, one or more pacing electrodes will be selected and connected to pacing leads 14, 15 and 16, 17 of the pacemaker.
  • Each model of electrode has its own characteristics, including a textual model number, polarity, number of filaments, electrical length, physical length, V p and source resistance.
  • Representative electrode parameters to assist in taking later TDR readings are shown as electrode menu options 40 in Fig. 2.
  • each electrode will ideally have a set of default sampling 41 and display 42 options.
  • the electrode parameters, sampling and display options may be specified by the electrode manufacturer and used to set default values in the pacemaker prior to implantation. Storing these parameters into the pacemaker is accomplished using conventional telemetry programming equipment with appropriate software to carry out the functions described herein.
  • external programmer 28 is first turned on, and the telemetry head of wand antenna 27 is positioned over the pacemaker.
  • the telemetry head generates a magnetic field which activates reed switch 25 inside the pacemaker.
  • This switch causes logic and control unit 11 to activate program receiver 19 and to receive instructions from programmer 28.
  • programmer 28 has a touch screen and various options are selected by touching the indicated portion of the screen.
  • the physician wilt initially step through the prompts displayed on programmer 28 to transmit the desired pacemaker settings (e.g. stimulation rate, pulse amplitudes, sensitivities and mode) into the pacemaker.
  • the physician may then select a TDR option on programmer 28, which will cause programmer 28 permit the TDR parameters to be specified and displayed, such as through the TDR options screen shown in Fig. 2.
  • programmer 28 will include a database of electrode manufacturers and models, with default electrode, sampling and display options for each electrode model.
  • the database may be periodically updated by programmer 28 manufacturer via a floppy disk with information concerning new electrodes on the market.
  • the physician first enters the TDR menu, the top "Read Configuration for Pacemaker” option will be highlighted in reverse video.
  • the physician presses down arrow 43 to cause the "Select Configuration from Electrode Database” option to be highlighted. The physician then depresses the
  • Select button 50 on the screen. This causes an overlapping window to be displayed on the screen as shown in Fig. 4, displaying a list of electrode manufacturers and model numbers.
  • the physician may repeatedly depress the down arrow until the electrode to be implanted is highlighted, then depress the Select option 50 on the touch screen. This will close the display window, and cause the Electrode, Sampling and Display options to be set to the default values recorded in the database for the particular electrode. While in this window (or any other window which may be opened) at any time prior to depressing the Select option 50, the physician may depress the Escape 47 portion on the screen, which will close the window and cause the display to revert to its previous status.
  • a representative window and set of electrode default information values is shown in Fig. 1.
  • the physician may repeatedly depress the down arrow until the value to be changed is highlighted. The physician may then depress the left 48 and/or right 49 arrows, which will cause the highlighted values to be decremented or incremented, respectively.
  • the physician may store them in the pacemaker so that they do not have to be reprogrammed each time a TDR reading is taken. This is done by depressing the up or down arrows until the "Store Configuration to Pacemaker" option is selected. The Select button is then depressed, which causes all of the displayed electrode information to be transmitted to the pacemaker by RF transceiver "7 and stored in RAM 22. If the pacemaker provides means for connecting to a second electrode such as for multiple leads, or includes two leads for single electrode (i.e. a pulse and a ground) then .he pacemaker RAM 22 may be configured with sufficient memory to store a separate setting for each electrode or lead.
  • pulse selector will include switch means fo; selecting whether the time domain reflectometer is operably connected to the means for connecting the first implantable electrode or the means for connecting to the second implantable electrode.
  • the location for each storage will be designated by the "Electrode No.” option in Fig. 2. If a pacemaker having capability for storing only one set of electrode readings receives an instruction and data to store electrode settings for an electrode other than no. 1, the number information may be ignored and the values replaced by the received values.
  • the physician may take an initial TDR reading. This is done by using the up and down arrows to highlight the
  • the pacemaker waits until no stimulating pulse is present on the electrode.
  • logic and control unit 11 will wait until the trailing edge of stimulating pulse 101 has been generated. Because stimulating pulse 101 may cause noise to be present on the electrode for a short time period after the pulse is generated, no action is taken during the time previously specified as TDR Blanking Interval 103.
  • This system comprises means for deferring generation of the TDR incident pulse until the amount of time specified by the TDR blanking interval has elapsed after the transmission of a stimulating pulse on the electrode, or the detection of an identified physiological event.
  • TDR blanking interval 103 may begin after completing of physiological event such as the atria!
  • This method in combination of the minimal current needed to generate a TDR incident pulse, minimizes the likelihood of causing an irregular heartbeat.
  • This system constitutes an anti-coincidence detector adapted to prevent a stimulating signal or physiological event from interfering with the incident pulse signal generated by the time domain reflectometer and its reflected wave.
  • logic and control system 11 sends an signal to pulse selector unit 26, which causes the electrode leads to be switched from an electrical connection with output section 13 to the TDR I/O and control section 23.
  • pulse selector unit 26 causes the electrode leads to be switched from an electrical connection with output section 13 to the TDR I/O and control section 23.
  • TDR I/O and control 23 is insulated by pulse selector 26 from the stimulating pulses, to minimize the possibility that the relatively large currents and voltages of the stimulating pulses will harm the TDR circuitry.
  • Logic and control 11 then sends a signal to TDR I/O and control 23, which comprises means for transmitting an electrical signal to the electrode receiving means, commanding the TDR to generate an incident pulse 104 (see Fig.8) on the selected electrode lead.
  • logic and control section 11 may include in the signal it sends to TDR I/O 23 a signal representing a impedance through which the TDR pulse should be sent.
  • the impedance equals the impedance of the electrode.
  • TDR I/O 23 may include an internal array of source resistors of various impedances through which an incident pulse may be transmitted, and be connected to a multiplexor to select which resistor the pulse should be transmitted. This provides a preferred TDR reflection waveform.
  • TDR I/O After generation of incident pulse 104, TDR I/O waits the amount of time represented by TDR Base time 105. Normally, this amount of time will be selected to represent the amount of time it will take for a reflected pulse to be detected by TDR I/O 23, and may be on the order of 1 - 10,000 nanoseconds, depending on the electrical characteristics and length of the electrode.
  • TDR Base Time 105 After TDR Base Time 105 passes, the TDR stores analog voltage detected 106 on the electrode in an analog timebase. Voltage 106 represents only a small portion of the entire reflected waveform 107. This analog voltage value is then converted to digital format by an analog-to-digital converter in TDR I/O 23, and then transmitted to logic and control section 11 for storage in output device, such as RAM 22.
  • TDR I/O 23 After a predetermined amount of time, such as 200 microseconds from the initiation of the first incident pulse, TDR I/O 23 generates second TDR pulse 108.
  • the above process is repeated numerous (e.g. 256) times, except the time at which an analog voltage reading is stored in the analog timebase is incremented slightly with each cycle.
  • RAM 22 has stored in it a raw TDR reading representing the reflected waveform.
  • logic and control section 11 sends a signal to pulse selector 26 causing the electrode connectors 14, 15 and/or 16,17 to be electrically reconnected to the output section 13, and electrically disconnected from TDR I/O 23.
  • the isolation of TDR I/O 23 from output section 13 by pulse selector 26 guards against any damage to the circuitry of TDR I/O 23 from stimulating pulses generated by output section 13. Thereafter, the generation of stimulating pulses may resume.
  • the TDR reading process may be repeated, either immediately, if the time until the next stimulating pulse to be generated is sufficiently long, or else after the next stimulating pulse is generated. Taking multiple TDR readings and averaging them reduces any noise that may be inherent in a single reading.
  • the digital values instead of storing the each set of individual TDR waveform readings to the same RAM address, the digital values may be added to the previously stored values. After the total number of TDR readings specified by the "No. of Readings Averaged" parameter has been completed, the each sum may be divided by the number of readings comprising the sum to obtain a composite reading, namely the average.
  • the time domain reflectometer i.e. the system for generating incident oulses and storing the reflected wave form, comprises a logic and control system as is already found in conventional pacemakers, as well as TDR I/O circuitry.
  • logic and control section 11 transmits the stored raw or composite waveform through TDR reading output signal means, such as transceiver means comprised of telemetry transmitter 18 and antenna 20, to wand 27 of programmer 28.
  • TDR reading output signal means such as transceiver means comprised of telemetry transmitter 18 and antenna 20, to wand 27 of programmer 28.
  • logic and control section 11 will also transmit to programmer 28, the stored sampling values used to take the TDR reading to programmer 28. This transmission assures that the correct parameter values may be displayed in association with the TDR reading.
  • Programmer 28 displays the received TDR reading in graphical form on a monitor (in graphical display window 411) or a printer, or both.
  • programmer 28 includes a Print button which when depressed, causes the displayed graph, and current configuration information to be printed.
  • a representative TDR waveform for a working electrode is shown in Fig. 7.
  • the horizontal axis represents the time, or sequential samples of the TDR reading, which can be directly converted into electrode distance if the V p of the electrode is known. As discussed above, this information may be supplied by the electrode manufacturer or manually programmed into the programmer. With a known V p , the vertical gridlines, or divisions, represent a specific length from the TDR I/O output to the end of the electrode.
  • the vertical axis of the waveform represents millirhos, which is directly convertible into impedance. Thus, a rise in the waveform represents increased resistance along the electrode, while a fall in the waveform represents a short circuit between the electrode and the pacemaker ground.
  • waveform rise 52 represents an increase in resistance, which in this representative case, is attributable to the internal pacemaker wiring connection between the application specific integrated circuit on which pacemaker circuitry Is connected and the wires connected to the pacing leads 14, 15, and 16, and 17.
  • Second waveform rise 53 is attributable to the interconnection between electrode receptacle and the electrode plug. Thereafter, the waveform is fiat, indicating a constant impedance throughout the length of the electrode, with no breaks or shorts.
  • Fig. 5 shows a representative TDR reading in which the electrode has a partial short and is in need of replacement.
  • a short may be caused, for example, by defective insulation between the leads of a bipolar electrode, or by the exterior insulation of the electrode becoming worn by, for example, excessive rubbing against a bone, pacemaker case or other structure.
  • the short is evident by waveform fall 60, indicating the impedance of the electrode at that point has fallen.
  • the physician may depress the cursor left 45 or cursor right 46 arrows below the display to cause graphical cursor 48 to move left or right.
  • cursor 48 and displays 54 and 55 comprise means for superimposing a distance scale measurement corresponding to the length of the implanted electrode on the graphical display.
  • the reading may be transmitted back to the pacemaker and stored in RAM 22, which comprises means for storing multiple TDR output signals. As shown in Fig. 2, this may be done by depressing the down arrow until the "Archive Current TDR Reading in Pacemaker * menu option is highlighted. The Select button is then depressed.
  • programmer 28 display a dialogue box on the screen in which the physician may type a short descriptive summary of the reading using a keyboard connected to programmer 28, such as "Pre-implant readings w/ Technitronics 1000", and in which the physician may enter his or her name.
  • the Select button is again depressed, causing programmer 28 to transmit the TDR waveform, along with the
  • Sampling Options, Display Options and textual information (including the date, which comprises a means for associating each stored output signal with a time reference indicating when the output signal is generated) through wand antenna 27 to antenna 20 of the pacemaker, accompanied by a command instructing the pacemaker logic and control 11 to store the information in RAM 22.
  • This stored reading may be used as a baseline TDR reading against which future TDR readings may be compared to assist in evaluating electrode integrity.
  • RAM 22 has sufficient capacity to store up to 512 TDR readings and associated information.
  • Logic and control 11 stores in RAM 22 an incremental counter indicating the total number of readings that have been stored in RAM 22 and the address of the next subsequent reading to be stored.
  • the physician may proceed with implantation of the pacemaker and electrode. Following implantation, but prior to closing the surgical incision in the patient, the physician may take a second TDR reading to ensure that no damage to the pacemaker or electrode occurred during implantation. Assuming the TDR reading is acceptable, the physician may close the incision.
  • the patient can be expected to have numerous follow-up visits with the physician, during which the integrity of the implanted electrode may be evaluated. This may be done using the same programmer 28 described above. After the programmer is turned on, wand 27 is positioned over the patient's pacemaker, and the ' TDR option is selected, the screen shown in Fig. 2 may appear. The physician choose to first retrieve a copy of the archived TDR reading from when the electrode was first implanted. This may be done by using up 44 and down 43 arrows to highlight the "Review Archived TDR Readings" option, and depressing Select.
  • the physician may specify a millirho value (predetermined threshold) by which, if a TDR reading deviates in a relevant portion, an indicating output warning signal, such as a flashing light, buzzer, or "DEFECTIVE" screen display is generated.
  • a millirho value predetermined threshold
  • an indicating output warning signal such as a flashing light, buzzer, or "DEFECTIVE” screen display.
  • High and low limits from the electrode portion of the display waveform may be represented as horizontal lines on the graphical display. Specifically, minimum warning line 64 and maximum warning line 65 as shown in Fig. 67 define the boundaries in which the entire electrode portion of the waveform is expected to fall. If a waveform deviates from these limits, DEFECTIVE legend 66 may be displayed on the screen, preferably in a highly contrasting color and accompanied by an audible alarm.
  • Fig. 6 shows a representative superimposed TDR reading, in which archived reading 61 shows an electrode in good condition, while current reading 62 shows that the electrode has broken. Specifically, reading 62 includes waveform rise 63, indicating that the impedance of the electrode has risen. This may be caused by, for example, a filament becoming cracked or completely severed. Because current reading 62 exceeds maximum alarm level 65, DEFECTIVE legend 66 is displayed on the screen, alerting the physician that the electrode may be defective.
  • the Current Configuration parameters 40, 41 and 42 shown in Fig. 2, as mentioned above, may be adjusted. With regard to Display Options 42, these parameters effect how a 1.8 particular TDR reading is displayed on the screen.
  • TDR readings have different impedance baselines and lengths.
  • the Vertical and Horizontal reference points and scales may be adjusted. These values will also be stored along with an archived TDR reading so that when the reading is retrieved, it will be initially displayed using the same viewing parameters as when it was stored.
  • the present invention may be used with virtually any type of medical electrode, such as ventricular, rate sensing, morphology, high voltage, mapping, sensor, temporary, ablation and angio/artheretomy electrodes.
  • Electrodes as used herein also include electrical conductors that are external to a patient used to send or receive electrical signals, such as, for example, ECG electrodes, or external pacemaker or defibrillator leads.
  • TDR reading is output through RAM and an RF antenna
  • other transceiver or output means are within the spirit and scope of the invention.
  • any other electromagnetic wave communication means may be used, at any desired frequency, including optical frequencies, or wire leads may be used to transmit a TDR reading.
  • the TDR reading described above is obtained by generating multiple incident pulses and storing a small portion of each reflected pulse. It is contemplated that with the development of faster electronic and CPU circuitry, that a TDR reading may possibly be generated by storing the reflected wave from a single incident pulse, and such systems included within the definition of a TDR.
  • a user-selected number of multiple raw TDR readings may be averaged to produce a composite reading to eliminate noise associated with individual readings.
  • the averaging function could easily be transferred from the internal implantable device to external programmer 28.
  • other manipulations of raw TDR readings such as by averaging multiple readings, would not necessarily alter their definition as being a TDR reading.
  • Other functions contemplated to be performed by the pacemaker could also be performed by external programmer 28.
  • the storage of TDR readings could be performed on external programmer 28, and optionally, may be indexed by a unique key, such as patient social security number or pacemaker serial number, to distinguish between stored readings from different patients.
  • graphical display of programmer 28 may include means for displaying the amplitude differential between the incident pulse and a selected portion of a TDR reading.
  • the defibriliator/pacemaker includes a central processing unit (CPU) 120 (which includes appropriate memory and software to carry out the functions described herein), power supply 121, battery 122, charging circuitry 123 and display 124.
  • the device is powered by battery 122 and may be recharged by charger circuitry 123.
  • Display 124 may comprise a computer screen, LCD display, plotter, or other such similar device, in this embodiment, three primary functions are provided by the defibriliator/pacemaker.
  • the device may serve as a defibrillator through defibrillator circuitry 125, which is responsible for the delivery of energy to defibrillator paddies connector 126 connected to defibrillator circuitry 125.
  • the second function of the defibriliator/pacemaker is as a pacemaker.
  • Pacing circuitry 127 connected to pacer output connector 128, delivers pulses to electrodes (see Fig. 11) connected to pacer output connector 128.
  • the defibriliator/pacemaker includes the capability to monitor the ECG signal of a patient through ECG circuitry 129 connected to ECG connector 130.
  • the device in addition to these conventional functions of the defibriliator/pacemaker, the device also includes TDR circuitry 131 connected to CPU 120 and to defibrillator paddles connector 126, pacer output connector 128 and ECG connector 130. As discussed in detail for the embodiment of the invention illustrated in Figs. 1-8,
  • TDR circuitry 131 includes the circuitry necessary to generate a TDR pulse and to detect the resulting voltage. Such a pulse may be caused to travel to individual defibrillator paddles connector 126 and the paddles connected thereto, or through an electrode connected to pacer output connector 28 or ECG connector 130. Circuitry for time domain reflectometers is well known and, in isolation, does not form the present invention.
  • Fig. 10 is a representative graphically displayed baseline TDR reading and a corresponding representative diagram of a patient cable connected to an electrode tip, both of which are in good condition.
  • a configuration may be such as connected to pacer output connector 128 (see Fig. 9) wherein a patient cable is connected to the pacer output connector and an electrode tip is connected to the patient cable.
  • the distance from the origin of the graph to distance D1 represents the internal circuitry of medical device 171 and the resistance of internal circuitry 151 is shown to be substantially constant.
  • First connector 191, connecting patient cable 192 to device 171 is represented by first connector resistance curve 153 between distances D1 and D2. A rise in resistance occurs over the distance comprising first connector 191.
  • Patient cable resistance 155 is shown.
  • Patient cable resistance 155 is substantially constant and is expected to be between minimum patient cable resistance value R1 and maximum patient cable resistance value R2. Should patient cable resistance 155 achieve a value outside of predetermined thresholds, namely the minimum and maximum values R1 and R2, respectively, it is known that there is a short, break or other discontinuity in patient cable
  • Second connector 193 connects patient cable 192 to electrode tip 194 and is represented by the distance D3 to D4. In the range between distance D3 and distance D4, second connector resistance 159 rises as indicated. From the beginning of the electrode 194 to the end of the electrode tip 194, represented by distance D4 to D5, electrode resistance 161 is substantially constant and should reside within the predefined threshold range between minimum electrode resistance value R3 to maximum electrode resistance value R4. At the termination of electrode 194 at a distance D5, the value of resistance rises as shown if electrode 194 is not connected to a patient, i.e., if there is an open circuit. In one embodiment, the upper and lower resistance thresholds are plus or minus ten percent (10%) of the expected resistance at any distance along the completed circuit.
  • First display section 180 illustrates defibriliator/pacemaker 181 having first and second defibrillator cables 184, 185 connected to first and second to paddles 186, 187 respectively and also connected at first and second defibrillator connectors 182, 183 of defibriliator/pacemaker 181.
  • Second graphical section 190 illustrates the configuration of defibriliator/pacemaker 181 when used in the pacing mode.
  • Patient cable 192 is connected to defibriliator/pacemaker 181 at cable connector 191 (which may be equivalent to pacer output connector 128 shown in Fig. 9).
  • cable connector 191 which may be equivalent to pacer output connector 128 shown in Fig. 9.
  • At the other end of patient cable 192 is connector 193 to which first and second pacing electrodes 194, 195 are connected. Thereafter, electrodes 194, 195 are connected to first and second pacing electrode pads 196, 197, respectively, which are placed on the patient. It should be noted that pacing electrodes 194, 195 need not be connected to pacing electrodes pads 196, 197 for integrity testing of electrodes 194, 195 to be performed.
  • Third graphical display section 200 shows defibriliator/pacemaker 181 when used is connection with first and second monitoring electrodes 204, 205 for the purpose of monitoring ECG signals.
  • patient cable 202 is connected to defibriliator/pacemaker 181 by connector 201 and to monitoring electrodes 204, 205 at its other end.
  • monitoring electrodes 204, 205 may be connected to monitoring electrode pads 206, 207, respectively, which are then in turn placed on the patient. It will be appreciated by those of skill in the art that the display actions are dependent on the device and connectors employed.
  • third graphical display function 200 may not be necessary should the ECG monitoring function operate through the same connectors and cables/wires as are used for the pacing function of defibriliator/pacemaker 181.
  • second graphical display section 190 is highlighted indicating defibriliator/pacemaker 181 is in its pacing configuration.
  • patient cable 192 is a marked or highlighted trouble area 198.
  • message 199 is also highlighted or marked.
  • This simple display which may be accompanied by an audible alarm, immediately informs the physician or technician that there is a discontinuity of significance in patient cable 192 which requires replacement of patient cable 192 for the proper operation of defibriliator/pacemaker 181.
  • first electrode 194 or second electrode 195 there may be discontinuities or breaks in either first electrode 194 or second electrode 195 in this configuration.
  • One of the advantages of the use of TDR technology is that more than one problem can be identified and displayed to the physician or technician.
  • the system may be easily tested by, for example, intentionally unplugging an electrode from the system and determining whether a BREAK IN CABLE message is displayed.
  • TDR technology may be used in connection with a variety of types of wires, cables, or electrodes extending from such a medical device.
  • the technology need not be limited to a particular type of cabling, nor should the requirement of the device to use a successive connections of various cable types preclude the use of the technology to determine defects in the attached cabling.
  • the term “electrode” as used in the claims may encompass defibrillator cables, patient cables, electrodes or other wires, or to any combination thereof, extending from such a medical device.
  • the term “medical device” as used in the claims may encompass any electrical device used in the medical profession wherein an "electrode,” as defined herein, is connected to the device.
  • the TDR technology is not limited to a single wire connected to a medical device. Rather, the technology may be used for any and all wires, cables, sensors or pads extending from the medical device. In this manner, the technician may check the system prior to its use to insure that the components are all operational. Accordingly, as used herein and in the claims, the term "electrode” includes all of the components used to carry an electrical signal from the instrumentation to the patient and back, even where this consists of discrete pieces electrically connected together. It will further be appreciated that the system of the present invention can not only test for electrode integrity prior to use, but during operation of the medical device.
  • CPU 120 is programmed through conventional software to monitor a patients heartbeat through ECG connector 130. As the heartbeat occurs on a periodic basis, CPU 120 can detect point in time when it is between heartbeats, and therefore little or no electrical activity on ECG electrodes. At such a point, CPU causes a signal to be transmitted to ECG 129 to cause its electrical connection to ECG connectors to be disabled, and a signal to be transmitted to TDR 131, to cause its output to be connected to ECG connector 130.
  • a TDR reading is then taken by TDR 131.
  • CPU 120 then transmits a signal to TDR 131 causing it to electrically disconnect from ECG connector 130, and to ECG 129, causing it to reconnect to ECG connector 130.
  • the combination of these components act as an anticoincidence detector to eliminate the possibility of a TDR reading being taken at the same time a signal is transmitted on the ECG electrodes to monitor the heartbeat. Due to the short time period needed to take a TDR reading, there is no appreciable interruption in ECG readings.
  • the TDR reading can be stored in memory and compared to a reference TDR signal for the ECG connectors, as described above. If the comparison indicates that a break or short in a ECG electrode has occurred, a graphical display showing the location of the break and an audible alarm are generated. It will also be appreciated that the above procedure can also be employed for the defibrillator output and pacing outputs, so the integrity of the entire system may be tested. As it is contemplated that the TDR circuitry may be reduced to a small and inexpensive application specific integrated circuit, it is also within the spirit and scope of the invention that separate TDR's be provided for each electrode circuit, instead of providing a single TDR with switch means which may be used to connect the TDR to different electrodes.
  • TDR readings may be taken for different types of electrodes. For example, for longer electrodes, it may be desirable to take a TDR reading consisting of 1,024 time divisions instead of 256 divisions.
  • the gain and resolution at which TDR reading may be graphically displayed may very depending on the electrode being tested. It is contemplated that such parameters may be separately stored for each electrode in a system, and automatically recalled and used to take a particular TDR reading.
  • the system of the present invention may include an integral graphical printer and a test mode switch. When the test mode switch is activated, CPU 120 automatically cycles through each electrode in the system and conducts an integrity test, the results of which may b printed out with a date and time stamp. Such a system allows its integrity to be checked on a routine basis and before a medical emergency. In addition, the printout can provide written documentation that the system was checked at the designated time.
  • the TDR may be used not only to test the integrity of an electrode, but also to provide a responsive heart stimulating system. This is done by performing additional analysis of the TDR readings from an implanted electrode which detects an increase in heart stroke volume.
  • the TDR may also be operatively connected to TDR probes in an enclosed chamber containing a fiowabie substance, which operates as a motion detector.
  • the conclusions reached from analyzing the implanted electrode and/or motion sensor TDR readings may be used to automatically adjust the waveform of a heart stimulating device, by, for example, increasing or decreasing the pacing rate of a pacemaker.
  • Fig. 12a there is shown a heart 220 during ' its minimum stroke volume in which a pacing electrode 221 is implanted. As heart 220 beats, it continually expands and contracts.
  • Rg. 12b shows heart 220 at its maximum stroke volume, as evidenced by the increased size of lower heart portion 222. It is known that when a person undertakes physical activity, their maximum heart stroke volume normally increases. This is generally true even for persons suffering from chronotropic incompetence, whose pulse rate does not sufficiently increase with increased physical activity. Thus, detection of a change in maximum heart stroke volume can be used in increase or decrease a pacemakers pace rate, or to otherwise alter the waveform generated by a heart stimulating device. in one embodiment of the present invention, a change in heart stroke volume can be detected by generating a TDR reading from the implanted electrode timed from a physiological event or stimulation pulse, or when the heart is at or near its maximum stroke volume.
  • Detection of when a heart is at or near its maximum stroke volume by monitoring implanted electrode is known in the art, and is used, for example, in existing bipolar heart stroke volume detectors.
  • a change in heart stroke volume using a TDR reading is possible in part because, as the heart continually expands and contracts, the end 223 of a pacemaker electrode is stretched and contracted. When the electrode end 223 is stretched, this results in a slightly lower conductance (higher resistance) in the stretched portion of the electrode. As stroke volume increases, the stretching of electrode tip 223 will correspondingly increase, as will its resistance.
  • an adjustment in the heart stimulating waveform such as an increased pacing rate, may be performed.
  • the waveform may also be altered, such as by decreasing the pacing rate.
  • a TDR reading from an implanted electrode taken during a heart's minimum stroke volume when electrode tip 223 is not stretched, shows a fairly even resistance at TDR reading portion 224.
  • TDR reading is taken during the maximum stroke volume as shown in Fig. 13b, there is a slight increase in resistance at TDR reading portion 225, as evidenced by the higher waveform portion 226.
  • the maximum heart stroke volume will increase, stretching electrode end 223 more and more. This will result in increased resistance of electrode end 223 as shown by TDR reading portion 227.
  • TDR reading portion 228 will continue to rise.
  • logic and control unit 11 may be used to cause the heart stimulating waveform to be altered, such as by increasing the pacing rate. Also, when a decrease is detected, the pacing rate may be reduced, or the waveform otherwise altered. Detection of a change in electrode tip resistance obviously requires that TDR readings be stored so that they may be compared to current TDR readings. This may be accomplished by logic and control unit 11 storing digital TDR readings in RAM 22. In one embodiment of the invention, a TDR reading may be taken during the maximum stroke volume approximately every ten seconds, and thirty readings may be stored in RAM. This may provide logic and control until 11 with sufficient historical data to determine when a change in maximum heart stroke volume has occurred.
  • a decision on when to alter the heart stimulating waveform may be made on any number of factors, and the specific method used does not constitute the invention per se.
  • Algorithms for adjusting a heart stimulating waveform based on a change in heart stroke volume are known in the art. For example, after a pacemaker has been implanted and the patient is sufficiently healthy to undertake a stress test, a physician may monitor the TDR readings during the maximum stroke volume have telemetering the readings to an external programmer as described above. Of course, the programmer would include an option to take TDR readings at the approximate maximum stroke volume.
  • the physician may easily identify thresholds of electrode ends appropriate to cause an increase or decrease in the pacing rate, and may program such parameters into the pacemaker using an external programmer.
  • a programmer may be used to specify a predetermined set of pacing rates, such as 60, 75, 90 and 105 beats per minute.
  • a pacemaker may be programmed to automatically increase or decrease the pacing rate based on the extent to which the maximum heart stroke volume is between its levels when the patient is at rest and when the patient is engaged in strenuous physical activity. For example, the pacing rate could continuously vary between a baseline and maximum level, based on a baseline and maximum heart stroke volume, to thereby provide a pacemaker that is responsive to a patient's heart stroke volume.
  • the physician after viewing the results of TDR readings taken during a stress level test, may choose to program which portion of the TDR reading should be subject to processing to determine a change in stroke volume. For example, assuming a TDR processor is used that breaks up each reading into 256 individual reading, examination of readings may indicate that readings 150 - 200 are most representative of the portion of the electrode subject to stretching during the stroke volume period. In another patient or when a different electrode is used, readings 180 - 210 might be most appropriate.
  • Such parameters may be programmable into the pacemaker using a programmer, software and telemetering techniques well-known in the art. It will also be appreciated that the present invention may be used with either endocardia! or epicardial electrodes.
  • epicardial electrode When an epicardial electrode is used, the physician should ensure that the electrode is implanted against the exterior wall of the heart having the greatest movement during the heartbeat. in order to minimize the likelihood of incorrectly interpreting TDR readings, the above-waveform altering system may also incorporate motion sensor readings. Combining motion sensor readings with readings from other physiological readings to determine when an adjustment in a pacing rate is warranted is also known in the art.
  • enclosed chamber 230 which is preferably formed from a substantially non-conductive material, includes two slotted lugs 231 and 232 for physical connection to a pacemaker header can by screws 233. Alternatively, enclosed chamber may be implanted separately from pacemaker and connected thereto by electrodes. Enclosed chamber 230 includes conductive contact points, namely, three metal TDR probes, namely
  • a fiowabie substance such as a saline solution 237.
  • solution 237 occupies approximately 35% of the volume of enclosed chamber 230. It will be appreciated that as enclosed chamber 230 moves, solution 237 will move within chamber 230 and contact different portions of probes 234, 235 and 236. As different portions of these probes are contacted, their conductive properties as detected by a TDR reading will change. Figs.
  • TDR readings for probes indicating, respectively, no, moderate, and heavy movement as sensed by a single probe.
  • the techniques used to analyze the relevant TDR reading of each probe signal may be the same used to analyze accelerometer or piezoelectric motion detector signals.
  • the portions of the TDR readings representing the probe portion within enclosed chamber 230 over 0.5 - 2 minutes may be processed using well-known analysis of variance techniques, such as those described in Bendat and Piersol. Random Data: Analysis and Measurement Procedures, Wiley-lnterscience (1971) or Spie ⁇ el. Schaum's Outline of Theory and Problems of Probability and Statistics, McGraw-Hill (1975), which are incorporated herein by reference.
  • logic and control unit 11 can cause a change in the pacing rate.
  • all three probes may be processed to generate a composite variance reading.
  • the specific thresholds appropriate to justify a change in pacing rate will vary with materials used and sizes of the probes, the conductivity of enclosed chamber 230 fiowabie material 237, and the pacing levels appropriate for the particular patient as determined by a qualified physician.
  • the heart stroke volume detection system may be combined with the motion detection system to provide a responsive system based upon two different parameters.
  • the heart stimulating waveform may altered not just by varying the pacing rate, but by changing other waveform characteristics such as amplitude, pulse shape (i.e. square, triangular or sinusoidal) or pulse width.
  • other waveform characteristics such as amplitude, pulse shape (i.e. square, triangular or sinusoidal) or pulse width.
  • TDR "readings” such readings may include a composite reading generated by averaging the values of multiple individual TDR readings to reduce noise.
  • TDR readings may be taken using incident TDR pulses have different leading edge rise times (preemphasis), and the resulting waveform readings averaged.

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Abstract

Un dispositif électrique comprend un boîtier (14-17) pour une électrode ainsi qu'un réflectomètre à dimension temporelle (23) comportant un mécanisme de sortie de signaux connecté de manière fonctionnelle au boîtier (14-17) de l'électrode. Le procédé d'analyse de l'intégrité d'une électrode consiste à générer une lecture (un signal de sortie) du réflectomètre à dimension temporelle à partir de l'électrode, et à transmettre le signal à un dispositif de sortie (28) où il est analysé afin d'assurer que l'électrode est correctement enclenchée et de déterminer son intégrité. Le dispositif comprend également un générateur (11) de forme d'onde de stimulation cardiaque servant à transmettre une forme d'onde à une électrode. Un réflectomètre à dimension temporelle (23) génère également des signaux représentant le débit systolique ou le débit cardiaque. Une unité logique et de commande (11) analyse les lectures obtenues de l'électrode afin de modifier la forme d'onde ou le rythme de la stimulation cardiaque en réponse à ces lectures.
PCT/US1993/003218 1992-04-10 1993-04-07 Stimulateur cardiaque a reflectometre a dimension temporelle WO1993020890A1 (fr)

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US07/866,850 1992-04-10
US07/866,850 US5231987A (en) 1992-04-10 1992-04-10 Time domain reflectometer-integrity testing system and method for implantable electrode
US07/971,415 1992-11-04
US07/971,415 US5233986A (en) 1992-04-10 1992-11-04 Time domain reflectometer-integrity testing system and method for medical device electrode
US07/971,281 1992-11-04
US07/971,281 US5251622A (en) 1992-04-10 1992-11-04 Responsive pacemaker with time domain reflectometer and method of use

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US7664550B2 (en) 2004-11-30 2010-02-16 Medtronic, Inc. Method and apparatus for detecting left ventricular lead displacement based upon EGM change
US7873410B2 (en) 2006-04-26 2011-01-18 Medtronic, Inc. Implantable medical device with electromechanical delay measurement for lead position and ventricular

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7664550B2 (en) 2004-11-30 2010-02-16 Medtronic, Inc. Method and apparatus for detecting left ventricular lead displacement based upon EGM change
US7873410B2 (en) 2006-04-26 2011-01-18 Medtronic, Inc. Implantable medical device with electromechanical delay measurement for lead position and ventricular

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