US3747604A - Atrial and ventricular demand pacer with separate atrial and ventricular beat detectors - Google Patents

Atrial and ventricular demand pacer with separate atrial and ventricular beat detectors Download PDF

Info

Publication number
US3747604A
US3747604A US00205195A US3747604DA US3747604A US 3747604 A US3747604 A US 3747604A US 00205195 A US00205195 A US 00205195A US 3747604D A US3747604D A US 3747604DA US 3747604 A US3747604 A US 3747604A
Authority
US
United States
Prior art keywords
ventricular
atrial
beat
heart
patient
Prior art date
Legal status (The legal status 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 status listed.)
Expired - Lifetime
Application number
US00205195A
Inventor
B Berkovits
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
American Optical Corp
Original Assignee
American Optical Corp
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
Application filed by American Optical Corp filed Critical American Optical Corp
Application granted granted Critical
Publication of US3747604A publication Critical patent/US3747604A/en
Assigned to COOK PACEMAKER CORPORATION reassignment COOK PACEMAKER CORPORATION LICENSE (SEE DOCUMENT FOR DETAILS). EFFECTIVE 03/27/81 Assignors: ATLANTIC RICHFIELD COMPANY
Assigned to TELECTRONICS PTY. LIMITED reassignment TELECTRONICS PTY. LIMITED CONFIRMS THE GRANTING OF LICENSE AGREEMENT DATED JULY 1, 1973 SUBJECT TO CONDITIONS IN AGREEMENT DATED JANUARY 16, 1984 (SEE REORD FOR DETAILS). Assignors: HONEYWELL MEDICAL ELECTRONICS B.V.
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

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
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions

Definitions

  • This invention relatesto atrial and ventricular pacers, and more particularly to such pacers in which competition between spontaneous atrial activity and atrial stimulation is prevented.
  • Atrial and ventricular pacer There are many patients who require an atrial and ventricular pacer, as opposed to the more usual ventricular pacer.
  • a detector monitors the spontaneous ventricular beating of the heart; if too long a time interval has elapsed since the last beat, a stimulating pulse is generated to trigger the ventricular beat.
  • an additional circuit is provided for generating atrial stimulating pulses to compensate for irregular atrial activity. To maintain synchronism between the two pulsing circuits, as disclosed in my above-identified application, every ventricular beat whether natural or stimulated causesthe atrial timing period to re-start together with the (longer) ventricular timing period.
  • an atrial stimulating pulse is generated a short time after the next atrial beat should occur.
  • the atrial stimulating pulse is generated even if a natural atrial beat occurs.
  • a ventricular stimulating pulse is generated, but only if a natural ventricular beat does not occur within a predetermined time interval subsequent to the previous ventricular beat.
  • an atrial stimulating pulse is generated following an atrial contraction, that is, during the refractory interval of the atria, it has no effect on the beating action of the patients heart. It is only.the generation of a ventricular stimulating pulse during the refractory interval of the ventricles that can be dangerous. For this reason, the detection of a spontaneous ventricular beat inhibits the generation of the ventricular stimulating pulse which would otherwise soon occur. But atrial stimulating pulses are not inhibited. In fact, even if the heart beats perfectly, in the conventional type atrial and ventricular pacer, an atrial stimulating pulse is generated during every heartbeat cycle. Of course, the timing of the atrial pulse generator is keyed to the ventricular beats so that at all times both pulsers and the natural heart activity remain in synchronism.
  • a conventional type ECG wave detector is provided 'to detect atrial depolarization signals in the prior art type atrial and ventricular pacer.
  • the detection of a ventricular beat still re-starts the timing of the atrial pulse generating circuit (along with that of the ventricular pulse generating circuit), but now the atrial pulse generator is also inhibited from producing an atrial simulating pulse whenever a spontaneous atrial beat is detected.
  • the major advantage of this design is that atrial stimulating pulses are not generated when they are not needed; the drain on the battery is reduced and the pacer has to be replaced lessfr'equently. (Although some atrial contractions may not be detected, that simply results in the type of operation described in my copending application. It is for each atrial beat which is detected that the drain on the battery is reduced.)
  • FIG. 1 depicts schematically the atrial and ventricular pacer disclosed in my co-pendling application
  • FIG. 2 consists of timing waveforms which will be helpful in understanding the operation of the circuit of FIG. 1;
  • FIG. 3 depicts schematically the illustrative embodi ment of the invention.
  • FIG. 4 consits of timing waveforms which will be helpful in understanding the operation of the circuit of FIG. 3.
  • FIG. 1 depicts three circuit blocks, the details of which are disclosed in my co-pending application.
  • Ventricular demand stimulator 10 applies a ventricular stimulating pulse, on ventricular electrodes El and E2, 800 milliseconds after the previous ventricular beat, whether spontaneous or stimulated.
  • a ventricular beat also results in the appearance of a pulse on the electrodes which is extended to ventricular beat (VB) detector 20.
  • the VB detector extends a signal over conductor 40 to the ventricular demand stimulator, in response to the detection of a ventricular beat, to inhibit the generation of the next ventricular pulse which otherwise would be generated and to control the start of a new 800-millisecond timing interval.
  • Atrial demand stimulator 30 is provided to extend an atrial stimulating pulse to electrodes E3 and E4.
  • the atrial stimulator timing period starts together with the ventircular stimulator timing period, the VB detector output being extended to both pulse generators.
  • the timing period of the atrial stim ulator is 600 milliseconds rather than 800 milliseconds.
  • FIG. 2 depicts the operation of the pacer during seven heartbeat cycles.
  • the letters R and P indicate respectively spontaneous ventricular and atrial contractions which occur during the seven cycles.
  • the letters VS and AS identify respectively the generations of ven tricular and atrial stimulating pulses. Since the detection of a ventricular beat re-starts the atrial timing period, and the atrial timing period is 600 milliseconds, the time interval between each spontaneous ventricular beat and the next atrial stimulating (AS) pulse is 600 milliseconds as shown.
  • the notation 600(F) is used to indicate that the interval separating any spontaneous ventricular contraction and the next atrial stimulating pulse is fixed.
  • each stimulating ventricular beat (VS) results in VB detector 20 energizing its output 40 to re-start both timing periods
  • the interval between each VS pulse and the next AS pulse is similarly 600 milliseconds and is shown by the notation 600(F).
  • a ventricular stimulating pulse is generated 800 milliseconds after the previous ventricular beat under control of ventricular demand stimulator 10. Since the interval is always 800 milliseconds, the notation 800 (F) is used to indicate the time between a spontaneous ventricular beat (R) and the next ventricular stimulating (VS) pulse if such a pulse is generated, and the time interval between one ventricular stimulating pulse and the next ventricular stimulating pulse in the absence of an intervening spontaneous ventricular beat.
  • R spontaneous ventricular beat
  • VS ventricular stimulating
  • each capacitor charges from an initial value toward a respective firing level. It takes 600 milliseconds for the atrial capacitor (57 in my co-pending application to reach the atrail firing level, at which time an atrial stimulating pulse is generated, the capacitor is discharged and a new timing interval begins; it requires 800 milliseconds for the ventricular timing capacitor (57) in my copending application to reach the ventricular firing level, at which time a ventricular stimulating pulse is generated, the capacitor is discharged and a new ventricular timing period begins.
  • Both capacitors are discharged and new timing periods begin when either a spontaneous ventricular beat (R) is detected or a ventricular stimilating (VS) pulse is generated.
  • the two sawtooth waveforms depict the respective capacitor voltage waveforms. The little arrows directly above the peaks of the waveforms indicate when, for the seven illustrative cycles, atrial and ventricular stimulating pulses are generated as a result of the voltages of the respective capacitors rising to the respective firing levels.
  • the voltage across the capacitor has sufficient time to rise to the ventricular firing level only in the absence of a spontaneous ventricular beat. Consequently, it is only at the end of each of cycles 3 and 4 that a ventricular stimulating pulse is generated.
  • the voltage across it always reaches the atrial firing level 600 milliseconds after the detection of a spontaneous ventricular beat (R) or the generation of a ventricular stimulating (VS) pulse. Consequently, an atrial stimulating pulse is shown as occuring during every cycle.
  • the atrialcapacitor voltage starts to rise. But the QRS detector causes the capacitor to be discharged at the end of each cycle when a spontaneous ventricular beat (R) is detected, or a ventricular stimulating (VS) pulse is generated.
  • the circuit of FIG. 3 is similar to that of FIG. 1 except that atrial beat (AB) detector 50 is provided.
  • the atrial electrodes E3 and E4 are connected to inputs of the AB detector.
  • the AB detector is similar to the VB detector 20, and may in fact be identical. Although it was believed to be difficult to detect atrial beats (that is, the atrial depolarization signal), this is no longer always true. The problem in the past was that the atrial electrodes would shift slightly after implantation. But newer atrial electrodes which have become available commercially permit far more reliable detection of atrial depolarization signals.
  • the output of AB detector 50 and the output of V8 detector 20 are both extended to respective inputs or OR gate 60, the output of which is extended to atrial demand stimulator 30.
  • the only difference between the pacers of FIGS. 1 and 3 is that in the latter circuit the timing period of the atrial demand stimulator is restarted whenever a spontaneous atria] beat is detected, as well as when a spontaneous ventricular beat is detected or a ventricular stimulating pulse is generated.
  • FIG. 4 shows the capacitor waveforms for the same seven heartbeat cycles depicted in FIG. 2.
  • each spontaneous atrial beat (P) re-starts the atrial timing period.
  • atrial simulating (AS) pulses are generated.
  • the ventricular sawtooth waveforms are thus the same in FIGS. 2 and 4, the atrial sawtooth waveforms are considerably different.
  • the atrial firing level is reached during only three of the seven heartbeat cycles.
  • an atrial stimulating pulse is not generated by the pacer of FIG. 3 when a spontaneous atrial beat is detected, there is reduced battery dissipation. This contributes to extended life of the pacer.
  • a pacer comprising terminal means for connection to a patients heart for atrial stimulation, terminal means for connection to said patients heart for ventricular stimulation, means for detecting an atrial beat of said patients heart, means for detecting a ventricular beat of said patients heart, means responsive to the operation of said ventricular detecting means for generating an electrical stimulus on said ventricular terminal means following a first predetermined time interval after the last detected ventricular beat only of said patients heart, means for generating an electricalstimulus on said atrial terminal means following a second predetermined time interval after the last ventricular beat only of said patients heart, and means for preventing the generation of an electrical stimulus on said atrail terminal means responsive to the detection of an atrial beat of said patients heart during said second predetermined time interval.
  • a pacer comprising terminal means for connection to a patients heart for ventricular stimulation, terminal means for connection to said patients heart for atrial stimulation, a first timing circuit means for generating an electrical impulse on said ventricular terminal means, a second timing circuit means for generating an electrical impulse on said atrial terminal means, means for detecting a ventricular beat of said patients heart and responsive thereto for resetting both of said first and second timing circuit means, and means for detecting an atrial beat of said patients heart and responsive thereto for resetting said second timing circuit.

Landscapes

  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biophysics (AREA)
  • Physiology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Electrotherapy Devices (AREA)

Abstract

An atrial and ventricular pacer in which competition between spontaneous atrial activity and atrial stimulation is prevented. In the conventional type atrial and ventricular pacer, the detection of a QRS wave re-starts both the atrial and ventricular timing circuits, but spontaneous atrial activity does not inhibit the generation of an atrial stimulating pulse. In the description of an illustrative embodiment contained herein, by preventing the generation of such a pulse when a spontaneous atrial beat is detected the batteries have a longer life.

Description

United States Patent 11 1 Berkovits ATRIAL AND VENTRICULAR DEMAND PACER WITH SEPARATE ATRIAL AND 1 VENTRICULAR BEAT DETECTORS Inventor: Barouh V. Berkovits, Newton Highlands, Mass.
American Optical Corporation, Southbridge, Mass.
Filed: Dec. 6, 1971 Appl. No.2 205,195
Related US. Application Data ['73] Assignee:
1969, Pat. No. 3,661,158.
52 US. Cl 1 References Cited UNITED STATES PATENTS Continuation-impart of Ser. No. 884,825, Dec. 15,
128/419 P, 128/421 Int. Cl A6111 1/38 Field of Search 128/419 P, 421, 422
3,593,718 7/1971 Krasner et al. 128/419 P 1451 July 24, 1973 3/1972 Greatbatch 128/419 P 3/1969 Keller, Jr 128/419 P P m w xamin -iwil mfim!" 1 Attorney William C. Nealon, Joel Wall et al.
7 Claims, 4 Drawing Figures 40 I0 El 15 1 ATRIAL DEMAND AB VD VENTRICULAR DEMAND 4 STIMULATDR DETECTOR DETECTDR STIMULATOR Patented July 24, 1973 ATRIAL DEMAND STINULATDR 600IFI/ VENTRICULAR DEIIAND STIIIULATDR I I soon;
I vinnucuua FIRING LEVEL ATRIAI.
FIRING LEVEL name LEVEL ATIIIAL FIRING LEVEL VENTRICULAR 40 I0 E/ 30/ 5' mm 0mm) A a v 8 VENTRICULAR I mama srmumon DETECTOR DE more R snnumoa ATRIAL AND VENTRICULAR DEMAND PACER WITH SEPARATE ATRIAL AND VENTRICULAR BEAT DETECTORS This application is a continuation-in-part of my copending application, S er. No. 884,825, filed on Dec. 15, 1969 and which has matured into U.S. Pat. No. 3,661,158.
This invention relatesto atrial and ventricular pacers, and more particularly to such pacers in which competition between spontaneous atrial activity and atrial stimulation is prevented.
There are many patients who require an atrial and ventricular pacer, as opposed to the more usual ventricular pacer. In demand pacers of the latter type, a detector monitors the spontaneous ventricular beating of the heart; if too long a time interval has elapsed since the last beat, a stimulating pulse is generated to trigger the ventricular beat. In pacers of the former type, an additional circuit is provided for generating atrial stimulating pulses to compensate for irregular atrial activity. To maintain synchronism between the two pulsing circuits, as disclosed in my above-identified application, every ventricular beat whether natural or stimulated causesthe atrial timing period to re-start together with the (longer) ventricular timing period. Following any ventricular beat, an atrial stimulating pulse is generated a short time after the next atrial beat should occur. The atrial stimulating pulse is generated even if a natural atrial beat occurs. Thereafter, a ventricular stimulating pulse is generated, but only if a natural ventricular beat does not occur within a predetermined time interval subsequent to the previous ventricular beat.
As explained in my co-pending application, if an atrial stimulating pulse is generated following an atrial contraction, that is, during the refractory interval of the atria, it has no effect on the beating action of the patients heart. It is only.the generation of a ventricular stimulating pulse during the refractory interval of the ventricles that can be dangerous. For this reason, the detection of a spontaneous ventricular beat inhibits the generation of the ventricular stimulating pulse which would otherwise soon occur. But atrial stimulating pulses are not inhibited. In fact, even if the heart beats perfectly, in the conventional type atrial and ventricular pacer, an atrial stimulating pulse is generated during every heartbeat cycle. Of course, the timing of the atrial pulse generator is keyed to the ventricular beats so that at all times both pulsers and the natural heart activity remain in synchronism.
In my co-pendiug application, I described the possibility of detecting an atrial contraction and in response thereto re-starting the atrial timing period. However, it was believed to be difficult to detect an atrial contraction (or, more accurately, the atrial depolarization signal), and for that reason an atrial beat detector was no provided in my earlier pacer.
It is a general object of my invention to provide an atrial and ventricular pacer of the prior art type but in which the detection of an atrial beat inhibits the generation of the atrial stimulating pulse which otherwise would be generated soon thereafter.
In accordance with the principles of my invention, a conventional type ECG wave detector is provided 'to detect atrial depolarization signals in the prior art type atrial and ventricular pacer. The detection of a ventricular beat still re-starts the timing of the atrial pulse generating circuit (along with that of the ventricular pulse generating circuit), but now the atrial pulse generator is also inhibited from producing an atrial simulating pulse whenever a spontaneous atrial beat is detected. The major advantage of this design is that atrial stimulating pulses are not generated when they are not needed; the drain on the battery is reduced and the pacer has to be replaced lessfr'equently. (Although some atrial contractions may not be detected, that simply results in the type of operation described in my copending application. It is for each atrial beat which is detected that the drain on the battery is reduced.)
It is a feature of my invention to provide an atrial beat detector in an atrial and ventricular pacer, the detection of an atrial beat resulting in the re'starting of the atrial timing period and the inhibition of the generation of the atrial stimulating pulse which otherwise would be generated.
Further objects,features, and advantages of my invention will become apparent upon consideration of the following detailed description. in conjunction with the drawing in which: i
FIG. 1 depicts schematically the atrial and ventricular pacer disclosed in my co-pendling application;
FIG. 2 consists of timing waveforms which will be helpful in understanding the operation of the circuit of FIG. 1; I
FIG. 3 depicts schematically the illustrative embodi ment of the invention; and
FIG. 4 consits of timing waveforms which will be helpful in understanding the operation of the circuit of FIG. 3.
FIG. 1 depicts three circuit blocks, the details of which are disclosed in my co-pending application. Ventricular demand stimulator 10 applies a ventricular stimulating pulse, on ventricular electrodes El and E2, 800 milliseconds after the previous ventricular beat, whether spontaneous or stimulated. A ventricular beat also results in the appearance of a pulse on the electrodes which is extended to ventricular beat (VB) detector 20. The VB detector extends a signal over conductor 40 to the ventricular demand stimulator, in response to the detection of a ventricular beat, to inhibit the generation of the next ventricular pulse which otherwise would be generated and to control the start of a new 800-millisecond timing interval. Atrial demand stimulator 30 is provided to extend an atrial stimulating pulse to electrodes E3 and E4. The atrial stimulator timing period starts together with the ventircular stimulator timing period, the VB detector output being extended to both pulse generators. However, the timing period of the atrial stim ulator is 600 milliseconds rather than 800 milliseconds.
FIG. 2 depicts the operation of the pacer during seven heartbeat cycles. The letters R and P indicate respectively spontaneous ventricular and atrial contractions which occur during the seven cycles. The letters VS and AS identify respectively the generations of ven tricular and atrial stimulating pulses. Since the detection of a ventricular beat re-starts the atrial timing period, and the atrial timing period is 600 milliseconds, the time interval between each spontaneous ventricular beat and the next atrial stimulating (AS) pulse is 600 milliseconds as shown. The notation 600(F) is used to indicate that the interval separating any spontaneous ventricular contraction and the next atrial stimulating pulse is fixed. Similarly, since each stimulating ventricular beat (VS) results in VB detector 20 energizing its output 40 to re-start both timing periods, the interval between each VS pulse and the next AS pulse is similarly 600 milliseconds and is shown by the notation 600(F).
In the absence of a spontaneous ventricular beat, a ventricular stimulating pulse is generated 800 milliseconds after the previous ventricular beat under control of ventricular demand stimulator 10. Since the interval is always 800 milliseconds, the notation 800 (F) is used to indicate the time between a spontaneous ventricular beat (R) and the next ventricular stimulating (VS) pulse if such a pulse is generated, and the time interval between one ventricular stimulating pulse and the next ventricular stimulating pulse in the absence of an intervening spontaneous ventricular beat. Finally, in the example shown in the drawing, it is assumed that a spontaneous ventricular beat (R) occurs 700 milliseconds after a previous ventricular beat, whether spontaneous (R) or stimulated (VS). Consequently, 700 milliseconds separate each R-R pair or VS-R pair. Since each of these time intervals is not fixed, and instead is a function of the condition of the patient, the letter F is not used together with the 700-millisecond designations.
, In the circuit of FIG. 1, as shown in FIG. 4 of my copending application, two capacitors are provided to control the 600-millisecond atrial timing period and the 800millisecond ventricular timing period. Each capacitor charges from an initial value toward a respective firing level. It takes 600 milliseconds for the atrial capacitor (57 in my co-pending application to reach the atrail firing level, at which time an atrial stimulating pulse is generated, the capacitor is discharged and a new timing interval begins; it requires 800 milliseconds for the ventricular timing capacitor (57) in my copending application to reach the ventricular firing level, at which time a ventricular stimulating pulse is generated, the capacitor is discharged and a new ventricular timing period begins. Both capacitors are discharged and new timing periods begin when either a spontaneous ventricular beat (R) is detected or a ventricular stimilating (VS) pulse is generated. The two sawtooth waveforms depict the respective capacitor voltage waveforms. The little arrows directly above the peaks of the waveforms indicate when, for the seven illustrative cycles, atrial and ventricular stimulating pulses are generated as a result of the voltages of the respective capacitors rising to the respective firing levels.
With respect to the ventricular capacitor voltage waveform, the voltage across the capacitor has sufficient time to rise to the ventricular firing level only in the absence of a spontaneous ventricular beat. Consequently, it is only at the end of each of cycles 3 and 4 that a ventricular stimulating pulse is generated. In the case of the atrial capacitor, however, the voltage across it always reaches the atrial firing level 600 milliseconds after the detection of a spontaneous ventricular beat (R) or the generation of a ventricular stimulating (VS) pulse. Consequently, an atrial stimulating pulse is shown as occuring during every cycle. Immediately after the generation of an AS pulse, the atrialcapacitor voltage starts to rise. But the QRS detector causes the capacitor to be discharged at the end of each cycle when a spontaneous ventricular beat (R) is detected, or a ventricular stimulating (VS) pulse is generated. The
capacitor then starts to charge again and the atrial firing level is reached 600 milliseconds later.
The circuit of FIG. 3 is similar to that of FIG. 1 except that atrial beat (AB) detector 50 is provided. The atrial electrodes E3 and E4 are connected to inputs of the AB detector. The AB detector is similar to the VB detector 20, and may in fact be identical. Although it was believed to be difficult to detect atrial beats (that is, the atrial depolarization signal), this is no longer always true. The problem in the past was that the atrial electrodes would shift slightly after implantation. But newer atrial electrodes which have become available commercially permit far more reliable detection of atrial depolarization signals.
The output of AB detector 50 and the output of V8 detector 20 are both extended to respective inputs or OR gate 60, the output of which is extended to atrial demand stimulator 30. The only difference between the pacers of FIGS. 1 and 3 is that in the latter circuit the timing period of the atrial demand stimulator is restarted whenever a spontaneous atria] beat is detected, as well as when a spontaneous ventricular beat is detected or a ventricular stimulating pulse is generated.
FIG. 4 shows the capacitor waveforms for the same seven heartbeat cycles depicted in FIG. 2. The major difference between the two timing sequences is that with the circuit of FIG. 3 each spontaneous atrial beat (P) re-starts the atrial timing period. It is only in the absence of a spontaneous atrial beat, during heartbeat cycles 4, 5 and 7, that atrial simulating (AS) pulses are generated. While the ventricular sawtooth waveforms are thus the same in FIGS. 2 and 4, the atrial sawtooth waveforms are considerably different. In FIG. 4, the atrial firing level is reached during only three of the seven heartbeat cycles. In general, because an atrial stimulating pulse is not generated by the pacer of FIG. 3 when a spontaneous atrial beat is detected, there is reduced battery dissipation. This contributes to extended life of the pacer.
Although the invention has been described with reference to a particular embodiment, it is to be understood that this embodiment is merely illustrative of the application of the principles of the invention. Numerous modifications may be made therein and other arrangements may be devised without departing from the spirit and scope of the invention.
What I claim is:
l. A pacer comprising terminal means for connection to a patients heart for atrial stimulation, terminal means for connection to said patients heart for ventricular stimulation, means for detecting an atrial beat of said patients heart, means for detecting a ventricular beat of said patients heart, means responsive to the operation of said ventricular detecting means for generating an electrical stimulus on said ventricular terminal means following a first predetermined time interval after the last detected ventricular beat only of said patients heart, means for generating an electricalstimulus on said atrial terminal means following a second predetermined time interval after the last ventricular beat only of said patients heart, and means for preventing the generation of an electrical stimulus on said atrail terminal means responsive to the detection of an atrial beat of said patients heart during said second predetermined time interval.
2. A pacer in accordance with claim 1 wherein said first predetermined time interval is longer than said second predetermined time interval.
3. A pacer in accordance with claim 2 wherein said second predetermined time interval is shorter than a probable minimum interval between successive ventricular beats of said patients heart and is longer than a probable maximum interval between a ventricular beat and the next atrail beat of said patients heart.
4. A pacer in accordance with claim 3 wherein said first predetermined time interval is longer than the usually-occurring interval between successive ventricular beats of said patients heart.
5. A pacer comprising terminal means for connection to a patients heart for ventricular stimulation, terminal means for connection to said patients heart for atrial stimulation, a first timing circuit means for generating an electrical impulse on said ventricular terminal means, a second timing circuit means for generating an electrical impulse on said atrial terminal means, means for detecting a ventricular beat of said patients heart and responsive thereto for resetting both of said first and second timing circuit means, and means for detecting an atrial beat of said patients heart and responsive thereto for resetting said second timing circuit.
6. A pacer in accordance with claim 5 wherein the period of said first timing circuit means is longer than a probable maximum interval between two successive ventricular beats of said patients heart.
7. A pacer in accordance with claim 6 wherein the period of said second timing circuit means is longer than a probable maximum interval between a ventricular beat and the next atrail beat of said patients heart. v

Claims (7)

1. A pacer comprising terminal means for connection to a patient''s heart for atrial stimulation, terminal means for connection to said patient''s heart for ventricular stimulation, means for detecting an atrial beat of said patient''s heart, means for detecting a ventricular beat of said patient''s heart, means responsive to the operation of said ventricular detecting means for generating an electrical stimulus on said ventricular terminal means following a first predetermined time interval after the last detected ventricular beat only of said patient''s heart, means for generating an electrical stimulus on said atrial terminal means following a second predetermined time interval after the last ventricular beat only of said patient''s heart, and means for preventing the generation of an electrical stimulus on said atrail terminal means responsive to the detection of an atrial beat of said patient''s heart during said second predetermined time interval.
2. A pacer in accordance with claim 1 wherein said first predetermined time interval is longer than said second predetermined time interval.
3. A pacer in accordance with claim 2 wherein said second predetermined time interval is shorter than a probable minimum interval between successive ventricular beats of said patient''s heart and is longer than a probable maximum interval between a ventricular beat and the next atrail beat of said patient''s heart.
4. A pacer in accordance with claim 3 wherein said first predetermined time interval is longer than the usually-occurring interval between successive ventricular beats of said patient''s heart.
5. A pacer comprising terminal means for connection to a patient''s heart for ventricular stimulation, terminal means for connection to said patient''s heart for atrial stimulation, a first timing circuit means foR generating an electrical impulse on said ventricular terminal means, a second timing circuit means for generating an electrical impulse on said atrial terminal means, means for detecting a ventricular beat of said patient''s heart and responsive thereto for resetting both of said first and second timing circuit means, and means for detecting an atrial beat of said patient''s heart and responsive thereto for resetting said second timing circuit.
6. A pacer in accordance with claim 5 wherein the period of said first timing circuit means is longer than a probable maximum interval between two successive ventricular beats of said patient''s heart.
7. A pacer in accordance with claim 6 wherein the period of said second timing circuit means is longer than a probable maximum interval between a ventricular beat and the next atrail beat of said patient''s heart.
US00205195A 1969-12-15 1971-12-06 Atrial and ventricular demand pacer with separate atrial and ventricular beat detectors Expired - Lifetime US3747604A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US88482569A 1969-12-15 1969-12-15
US20519571A 1971-12-06 1971-12-06

Publications (1)

Publication Number Publication Date
US3747604A true US3747604A (en) 1973-07-24

Family

ID=26900202

Family Applications (1)

Application Number Title Priority Date Filing Date
US00205195A Expired - Lifetime US3747604A (en) 1969-12-15 1971-12-06 Atrial and ventricular demand pacer with separate atrial and ventricular beat detectors

Country Status (1)

Country Link
US (1) US3747604A (en)

Cited By (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2528817A1 (en) * 1974-07-10 1976-01-29 Medtronic Inc ARRHYTHMIA PREVENTING DEVICE
US4088140A (en) * 1976-06-18 1978-05-09 Medtronic, Inc. Demand anti-arrhythmia pacemaker
DE2701104A1 (en) * 1977-01-12 1978-07-13 Medtronic France S A PACEMAKER
EP0001708A2 (en) * 1977-10-17 1979-05-02 Medtronic, Inc. Heart pacemaker and monitor
US4166470A (en) * 1977-10-17 1979-09-04 Medtronic, Inc. Externally controlled and powered cardiac stimulating apparatus
US4172459A (en) * 1977-10-17 1979-10-30 Medtronic, Inc. Cardiac monitoring apparatus and monitor
US4187854A (en) * 1977-10-17 1980-02-12 Medtronic, Inc. Implantable demand pacemaker and monitor
FR2471791A1 (en) * 1979-12-12 1981-06-26 Medtronic Inc SYNCHRONOUS CARDIAC STIMULATOR
DE3145149A1 (en) * 1980-11-14 1982-07-22 Cordis Corp., 33172 Miami, Fla. IMPLANTABLE HEART PACEMAKER
WO1982003781A1 (en) * 1981-05-04 1982-11-11 Nettelhorst Herwig Pacemaker
US4378020A (en) * 1981-08-20 1983-03-29 Telectronics Pty. Ltd. Dual chamber pacer
WO1983001389A1 (en) * 1981-10-13 1983-04-28 Keller, J., Walter, Jr. Bidirectional pacemaker
US4386610A (en) * 1980-05-27 1983-06-07 Cordis Corporation Ventricular-inhibited cardiac pacer
US4432362A (en) * 1980-05-27 1984-02-21 Cordis Corporation Atrial-based, atrial-ventricular sequential cardiac pacer
US4453547A (en) * 1981-04-06 1984-06-12 Physio Technology, Inc. T-Wave inhibiting system
US4503857A (en) * 1981-10-26 1985-03-12 Vitatron Medical B.V. Programmable cardiac pacemaker with microprocessor control of pacer rate
US4510945A (en) * 1982-07-12 1985-04-16 Cordis Corporation P Wave detection system
US4572193A (en) * 1984-01-27 1986-02-25 Mann Brian M DDI Programmable cardiac tissue stimulator
US4890617A (en) * 1987-11-25 1990-01-02 Medtronic, Inc. Dual chamber activity responsive pacer
US4920965A (en) * 1987-11-25 1990-05-01 Medtronic, Inc. Dual chamber pacemaker with adaptive atrial escape interval
US5027815A (en) * 1987-11-25 1991-07-02 Medtronic, Inc. Dual chamber pacemaker with adaptive atrial escape interval
US5265601A (en) * 1992-05-01 1993-11-30 Medtronic, Inc. Dual chamber cardiac pacing from a single electrode
WO2002051499A1 (en) 2000-12-21 2002-07-04 Medtronic, Inc. Preferred adi/r: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US20030078627A1 (en) * 2000-12-21 2003-04-24 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US20050021096A1 (en) * 2003-07-24 2005-01-27 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US20050055057A1 (en) * 2003-09-05 2005-03-10 Mirowski Famliy Ventures, L.L.C. Method and apparatus for providing ipselateral therapy
US20050055059A1 (en) * 2000-12-21 2005-03-10 Betzold Robert A. Ventricular event filtering for an implantable medical device
US20050055058A1 (en) * 2003-09-08 2005-03-10 Mower Morton M. Method and apparatus for intrachamber resynchronization
US20050177197A1 (en) * 2000-12-21 2005-08-11 Medtronic, Inc. System and method for ventricular pacing with progressive conduction check interval
US20050267539A1 (en) * 2000-12-21 2005-12-01 Medtronic, Inc. System and method for ventricular pacing with AV interval modulation
US20060089677A1 (en) * 2004-10-25 2006-04-27 Casavant David A Self limited rate response
US20060167506A1 (en) * 2005-01-21 2006-07-27 Stoop Gustaaf A Implantable medical device with ventricular pacing protocol
US20060167508A1 (en) * 2005-01-21 2006-07-27 Willem Boute Implantable medical device with ventricular pacing protocol including progressive conduction search
US7254441B2 (en) 2000-12-21 2007-08-07 Medtronic, Inc. Fully inhibited dual chamber pacing mode
US20070203523A1 (en) * 2006-02-28 2007-08-30 Betzold Robert A Implantable medical device with adaptive operation
US20070219589A1 (en) * 2006-01-20 2007-09-20 Condie Catherine R System and method of using AV conduction timing
USRE39897E1 (en) 1989-01-23 2007-10-23 Mirowski Family Ventures, L.L.C. Method and apparatus for treating hemodynamic disfunction
US20070293899A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Ventricular Interval Smoothing Following a Premature Ventricular Contraction
US20070293897A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Promoting Instrinsic Conduction Through Atrial Timing Modification and Calculation of Timing Parameters
US20070293900A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Promoting Intrinsic Conduction Through Atrial Timing
US20070293898A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Determining Intrinsic AV Interval Timing
US20080027490A1 (en) * 2006-07-31 2008-01-31 Sheldon Todd J Pacing Mode Event Classification with Rate Smoothing and Increased Ventricular Sensing
US20080027493A1 (en) * 2006-07-31 2008-01-31 Sheldon Todd J System and Method for Improving Ventricular Sensing
US7502647B2 (en) 2006-07-31 2009-03-10 Medtronic, Inc. Rate smoothing pacing modality with increased ventricular sensing
US7515958B2 (en) 2006-07-31 2009-04-07 Medtronic, Inc. System and method for altering pacing modality
US7689281B2 (en) 2006-07-31 2010-03-30 Medtronic, Inc. Pacing mode event classification with increased ventricular sensing
US7720537B2 (en) 2006-07-31 2010-05-18 Medtronic, Inc. System and method for providing improved atrial pacing based on physiological need
US20100222834A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing
US20100222837A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing
US20100222838A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing
US7856269B2 (en) 2006-07-31 2010-12-21 Medtronic, Inc. System and method for determining phsyiologic events during pacing mode operation
US9931509B2 (en) 2000-12-21 2018-04-03 Medtronic, Inc. Fully inhibited dual chamber pacing mode

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3433228A (en) * 1966-05-06 1969-03-18 Cordis Corp Multimode cardiac pacer
US3593718A (en) * 1967-07-13 1971-07-20 Biocybernetics Inc Physiologically controlled cardiac pacer
US3648707A (en) * 1969-07-16 1972-03-14 Medtronic Inc Multimode cardiac paces with p-wave and r-wave sensing means

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3433228A (en) * 1966-05-06 1969-03-18 Cordis Corp Multimode cardiac pacer
US3593718A (en) * 1967-07-13 1971-07-20 Biocybernetics Inc Physiologically controlled cardiac pacer
US3648707A (en) * 1969-07-16 1972-03-14 Medtronic Inc Multimode cardiac paces with p-wave and r-wave sensing means

Cited By (103)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2528817A1 (en) * 1974-07-10 1976-01-29 Medtronic Inc ARRHYTHMIA PREVENTING DEVICE
US3937226A (en) * 1974-07-10 1976-02-10 Medtronic, Inc. Arrhythmia prevention apparatus
US4088140A (en) * 1976-06-18 1978-05-09 Medtronic, Inc. Demand anti-arrhythmia pacemaker
DE2701104A1 (en) * 1977-01-12 1978-07-13 Medtronic France S A PACEMAKER
EP0001708A2 (en) * 1977-10-17 1979-05-02 Medtronic, Inc. Heart pacemaker and monitor
EP0001708A3 (en) * 1977-10-17 1979-05-16 Medtronic, Inc. Heart pacemaker and monitor
US4166470A (en) * 1977-10-17 1979-09-04 Medtronic, Inc. Externally controlled and powered cardiac stimulating apparatus
US4172459A (en) * 1977-10-17 1979-10-30 Medtronic, Inc. Cardiac monitoring apparatus and monitor
US4187854A (en) * 1977-10-17 1980-02-12 Medtronic, Inc. Implantable demand pacemaker and monitor
EP0033418A1 (en) * 1979-12-12 1981-08-12 Medtronic, Inc. Ventricular synchronised atrial pacemaker
FR2471791A1 (en) * 1979-12-12 1981-06-26 Medtronic Inc SYNCHRONOUS CARDIAC STIMULATOR
US4284082A (en) * 1979-12-12 1981-08-18 Medtronic B.V.Kerkrade Ventricular synchronized atrial pacemaker and method of operation
DE3046681A1 (en) * 1979-12-12 1981-09-17 Medtronic, Inc., 55440 Minneapolis, Minn. SYNCHRONIZED HEART PACEMAKER
EP0033418B1 (en) * 1979-12-12 1984-11-07 Medtronic, Inc. Ventricular synchronised atrial pacemaker
US4386610A (en) * 1980-05-27 1983-06-07 Cordis Corporation Ventricular-inhibited cardiac pacer
US4432362A (en) * 1980-05-27 1984-02-21 Cordis Corporation Atrial-based, atrial-ventricular sequential cardiac pacer
DE3145149A1 (en) * 1980-11-14 1982-07-22 Cordis Corp., 33172 Miami, Fla. IMPLANTABLE HEART PACEMAKER
US4453547A (en) * 1981-04-06 1984-06-12 Physio Technology, Inc. T-Wave inhibiting system
WO1982003781A1 (en) * 1981-05-04 1982-11-11 Nettelhorst Herwig Pacemaker
US4378020A (en) * 1981-08-20 1983-03-29 Telectronics Pty. Ltd. Dual chamber pacer
WO1983001389A1 (en) * 1981-10-13 1983-04-28 Keller, J., Walter, Jr. Bidirectional pacemaker
US4503857A (en) * 1981-10-26 1985-03-12 Vitatron Medical B.V. Programmable cardiac pacemaker with microprocessor control of pacer rate
US4510945A (en) * 1982-07-12 1985-04-16 Cordis Corporation P Wave detection system
US4572193A (en) * 1984-01-27 1986-02-25 Mann Brian M DDI Programmable cardiac tissue stimulator
US4890617A (en) * 1987-11-25 1990-01-02 Medtronic, Inc. Dual chamber activity responsive pacer
US4920965A (en) * 1987-11-25 1990-05-01 Medtronic, Inc. Dual chamber pacemaker with adaptive atrial escape interval
US5027815A (en) * 1987-11-25 1991-07-02 Medtronic, Inc. Dual chamber pacemaker with adaptive atrial escape interval
USRE39897E1 (en) 1989-01-23 2007-10-23 Mirowski Family Ventures, L.L.C. Method and apparatus for treating hemodynamic disfunction
US5265601A (en) * 1992-05-01 1993-11-30 Medtronic, Inc. Dual chamber cardiac pacing from a single electrode
US8060202B2 (en) 2000-12-21 2011-11-15 Medtronic, Inc. Ventricular event filtering for an implantable medical device
US7881793B2 (en) 2000-12-21 2011-02-01 Medtronic, Inc. System and method for ventricular pacing with progressive conduction check interval
US6772005B2 (en) 2000-12-21 2004-08-03 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US9931509B2 (en) 2000-12-21 2018-04-03 Medtronic, Inc. Fully inhibited dual chamber pacing mode
US7254441B2 (en) 2000-12-21 2007-08-07 Medtronic, Inc. Fully inhibited dual chamber pacing mode
US20050055059A1 (en) * 2000-12-21 2005-03-10 Betzold Robert A. Ventricular event filtering for an implantable medical device
US20030078627A1 (en) * 2000-12-21 2003-04-24 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US20050177197A1 (en) * 2000-12-21 2005-08-11 Medtronic, Inc. System and method for ventricular pacing with progressive conduction check interval
US20050267539A1 (en) * 2000-12-21 2005-12-01 Medtronic, Inc. System and method for ventricular pacing with AV interval modulation
US20040143299A1 (en) * 2000-12-21 2004-07-22 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US7738955B2 (en) 2000-12-21 2010-06-15 Medtronic, Inc. System and method for ventricular pacing with AV interval modulation
US7599740B2 (en) 2000-12-21 2009-10-06 Medtronic, Inc. Ventricular event filtering for an implantable medical device
US7130683B2 (en) 2000-12-21 2006-10-31 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining back support
US7218965B2 (en) 2000-12-21 2007-05-15 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
EP2098265A2 (en) 2000-12-21 2009-09-09 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US7245966B2 (en) 2000-12-21 2007-07-17 Medtronic, Inc. Ventricular event filtering for an implantable medical device
WO2002051499A1 (en) 2000-12-21 2002-07-04 Medtronic, Inc. Preferred adi/r: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US9375579B2 (en) 2002-09-17 2016-06-28 Medtronic, Inc. Preferred ADI/R: a permanent pacing mode to eliminate ventricular pacing while maintaining backup support
US20070208387A1 (en) * 2003-07-24 2007-09-06 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US20050021096A1 (en) * 2003-07-24 2005-01-27 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US8249725B2 (en) 2003-07-24 2012-08-21 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US8761905B2 (en) 2003-07-24 2014-06-24 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US7231249B2 (en) 2003-07-24 2007-06-12 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US9566444B2 (en) 2003-07-24 2017-02-14 Mirowski Family Ventures, L.L.C. Methods, apparatus, and systems for multiple stimulation from a single stimulator
US20070191893A1 (en) * 2003-09-05 2007-08-16 Mirowski Family Ventures, L.L.C. Method and apparatus for providing ipselateral therapy background
US8744558B2 (en) 2003-09-05 2014-06-03 Mirowski Family Ventures, L.L.C. Method and apparatus for providing ipselateral therapy
US20050055057A1 (en) * 2003-09-05 2005-03-10 Mirowski Famliy Ventures, L.L.C. Method and apparatus for providing ipselateral therapy
US20050055058A1 (en) * 2003-09-08 2005-03-10 Mower Morton M. Method and apparatus for intrachamber resynchronization
US9901739B2 (en) 2003-09-08 2018-02-27 Mirowski Family Ventures, LLC Method and apparatus for intrachamber resynchronization
US11207524B2 (en) 2003-09-08 2021-12-28 Mirowski Family Ventures, LLC Method and apparatus for intrachamber resynchronization
US20060089677A1 (en) * 2004-10-25 2006-04-27 Casavant David A Self limited rate response
US20070299478A1 (en) * 2004-10-25 2007-12-27 Casavant David A Self Limited Rate Response
US7248924B2 (en) 2004-10-25 2007-07-24 Medtronic, Inc. Self limited rate response
US7904157B2 (en) 2004-10-25 2011-03-08 Medtronic, Inc. Self limited rate response
US20060167506A1 (en) * 2005-01-21 2006-07-27 Stoop Gustaaf A Implantable medical device with ventricular pacing protocol
US7542799B2 (en) 2005-01-21 2009-06-02 Medtronic, Inc. Implantable medical device with ventricular pacing protocol
US7593773B2 (en) 2005-01-21 2009-09-22 Medtronic, Inc. Implantable medical device with ventricular pacing protocol including progressive conduction search
US20060167508A1 (en) * 2005-01-21 2006-07-27 Willem Boute Implantable medical device with ventricular pacing protocol including progressive conduction search
US7925344B2 (en) 2006-01-20 2011-04-12 Medtronic, Inc. System and method of using AV conduction timing
US8229560B2 (en) 2006-01-20 2012-07-24 Medtronic, Inc. System and method of using AV conduction timing
US20110184299A1 (en) * 2006-01-20 2011-07-28 Medtronic, Inc. System and method of using av conduction timing
US20070219589A1 (en) * 2006-01-20 2007-09-20 Condie Catherine R System and method of using AV conduction timing
US9415227B2 (en) 2006-02-28 2016-08-16 Medtronic, Inc. Implantable medical device with adaptive operation
US8046063B2 (en) 2006-02-28 2011-10-25 Medtronic, Inc. Implantable medical device with adaptive operation
US20070203523A1 (en) * 2006-02-28 2007-08-30 Betzold Robert A Implantable medical device with adaptive operation
US7565196B2 (en) 2006-06-15 2009-07-21 Medtronic, Inc. System and method for promoting intrinsic conduction through atrial timing
US7783350B2 (en) 2006-06-15 2010-08-24 Medtronic, Inc. System and method for promoting intrinsic conduction through atrial timing modification and calculation of timing parameters
US20070293899A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Ventricular Interval Smoothing Following a Premature Ventricular Contraction
US8032216B2 (en) 2006-06-15 2011-10-04 Medtronic, Inc. System and method for determining intrinsic AV interval timing
US7869872B2 (en) 2006-06-15 2011-01-11 Medtronic, Inc. System and method for determining intrinsic AV interval timing
US20070293897A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Promoting Instrinsic Conduction Through Atrial Timing Modification and Calculation of Timing Parameters
US7894898B2 (en) 2006-06-15 2011-02-22 Medtronic, Inc. System and method for ventricular interval smoothing following a premature ventricular contraction
US20070293900A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Promoting Intrinsic Conduction Through Atrial Timing
US20070293898A1 (en) * 2006-06-15 2007-12-20 Sheldon Todd J System and Method for Determining Intrinsic AV Interval Timing
US20110112596A1 (en) * 2006-06-15 2011-05-12 Medtronic, Inc. System and method for determining intrinsic av interval timing
US7502646B2 (en) 2006-07-31 2009-03-10 Medtronic, Inc. Pacing mode event classification with rate smoothing and increased ventricular sensing
US20100174334A1 (en) * 2006-07-31 2010-07-08 Medtronic, Inc. System and method for providing improved atrial pacing based on physiological need
US20080027490A1 (en) * 2006-07-31 2008-01-31 Sheldon Todd J Pacing Mode Event Classification with Rate Smoothing and Increased Ventricular Sensing
US20080027493A1 (en) * 2006-07-31 2008-01-31 Sheldon Todd J System and Method for Improving Ventricular Sensing
US7502647B2 (en) 2006-07-31 2009-03-10 Medtronic, Inc. Rate smoothing pacing modality with increased ventricular sensing
US7856269B2 (en) 2006-07-31 2010-12-21 Medtronic, Inc. System and method for determining phsyiologic events during pacing mode operation
US7515958B2 (en) 2006-07-31 2009-04-07 Medtronic, Inc. System and method for altering pacing modality
US7689281B2 (en) 2006-07-31 2010-03-30 Medtronic, Inc. Pacing mode event classification with increased ventricular sensing
US7715914B2 (en) 2006-07-31 2010-05-11 Medtronic, Inc. System and method for improving ventricular sensing
US7720537B2 (en) 2006-07-31 2010-05-18 Medtronic, Inc. System and method for providing improved atrial pacing based on physiological need
US8565873B2 (en) 2006-07-31 2013-10-22 Medtronic, Inc. System and method for providing improved atrial pacing based on physiological need
US20100222837A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing
US8396553B2 (en) 2009-02-27 2013-03-12 Medtronic, Inc. System and method for conditional biventricular pacing
US8265750B2 (en) 2009-02-27 2012-09-11 Medtronic, Inc. System and method for conditional biventricular pacing
US20100222834A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing
US8244354B2 (en) 2009-02-27 2012-08-14 Medtronic, Inc. System and method for conditional biventricular pacing
US8229558B2 (en) 2009-02-27 2012-07-24 Medtronic, Inc. System and method for conditional biventricular pacing
US20100222839A1 (en) * 2009-02-27 2010-09-02 Medtronic, Inc. System and method for conditional biventricular pacing
US20100222838A1 (en) * 2009-02-27 2010-09-02 Sweeney Michael O System and method for conditional biventricular pacing

Similar Documents

Publication Publication Date Title
US3747604A (en) Atrial and ventricular demand pacer with separate atrial and ventricular beat detectors
US3669120A (en) Device for starting or stimulating heart contractions
US3648707A (en) Multimode cardiac paces with p-wave and r-wave sensing means
US5188105A (en) Apparatus and method for treating a tachyarrhythmia
EP0727241B1 (en) Device for heart stimulation
US3757792A (en) Automatic threshold compensating demand pacemaker
CA1091301A (en) P-wave control, r-wave inhibited ventricular stimulation device
US3595242A (en) Atrial and ventricular demand pacer
US4386610A (en) Ventricular-inhibited cardiac pacer
KR100574564B1 (en) Antitachycardial pacing
US4088140A (en) Demand anti-arrhythmia pacemaker
US4432362A (en) Atrial-based, atrial-ventricular sequential cardiac pacer
US3433228A (en) Multimode cardiac pacer
US5584867A (en) Method and apparatus for controlling a double atrial triple chamber cardiac pacemaker having a fallback mode
US3431912A (en) Standby cardiac pacer
US3677251A (en) Body organ stimulator with interference rejector
JPH08500758A (en) Combined pacemaker and defibrillator
US4825870A (en) Pacemaker having crosstalk protection feature
JPH05508574A (en) cardioversion pacing
GB1590100A (en) Heart stimulation devices
US4421116A (en) Heart pacemaker with separate A-V intervals for atrial synchronous and atrial-ventricular sequential pacing modes
JP2005230566A (en) Heart stimulator
EP0485521A1 (en) Programmable automatic implantable cardioverter/defibrillator and pacemaker system
EP0563122A1 (en) Apparatus for automatically inducing fibrillation.
US3661157A (en) Inhibited demand pacer with a two-rate pulse generator

Legal Events

Date Code Title Description
AS Assignment

Owner name: COOK PACEMAKER CORPORATION, INDIANA

Free format text: LICENSE;ASSIGNOR:ATLANTIC RICHFIELD COMPANY;REEL/FRAME:003852/0285

Effective date: 19810327

Owner name: COOK PACEMAKER CORPORATION, P.O. BOX 99, BLOOMINGT

Free format text: LICENSE;ASSIGNOR:ATLANTIC RICHFIELD COMPANY;REEL/FRAME:003852/0285

Effective date: 19810327

AS Assignment

Owner name: TELECTRONICS PTY. LIMITED

Free format text: CONFIRMS THE GRANTING OF LICENSE AGREEMENT DATED JULY 1, 1973 SUBJECT TO CONDITIONS IN AGREEMENT DATED JANUARY 16, 1984;ASSIGNOR:HONEYWELL MEDICAL ELECTRONICS B.V.;REEL/FRAME:004436/0297

Effective date: 19850306

STCF Information on status: patent grant

Free format text: PATENTED FILE - (OLD CASE ADDED FOR FILE TRACKING PURPOSES)