US3814106A - Atrial and ventricular pacer having independent rate controls and means to maintain a constant av delay - Google Patents

Atrial and ventricular pacer having independent rate controls and means to maintain a constant av delay Download PDF

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Publication number
US3814106A
US3814106A US00244156A US24415672A US3814106A US 3814106 A US3814106 A US 3814106A US 00244156 A US00244156 A US 00244156A US 24415672 A US24415672 A US 24415672A US 3814106 A US3814106 A US 3814106A
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ventricular
atrial
potentiometer
interval
timing interval
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US00244156A
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English (en)
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B Berkovits
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American Optical Corp
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American Optical Corp
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Priority to US00244156A priority Critical patent/US3814106A/en
Priority to DE2314315A priority patent/DE2314315C2/de
Priority to NL7304895A priority patent/NL7304895A/xx
Priority to JP4147073A priority patent/JPS567701B2/ja
Priority to BR732718A priority patent/BR7302718D0/pt
Priority to GB1830073A priority patent/GB1421485A/en
Application granted granted Critical
Publication of US3814106A publication Critical patent/US3814106A/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.
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    • 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

  • the ventricular rate control circuit includea one potentiometer. and :52] 0.5.
  • CI mil-tn P. l28/42l will P t s circuit include Mi p f s l 1 Int. Cl Main use wflmtrd in one of which is ranged in ⁇ SM Ftdd r SQQ -h n t 10, 2.05 105 R. the ventricular rate potentiometer. II the impedance g t p. 3 1.
  • This invention relates to atrial and ventricular dentand pacers. and more particularly to such pacers ln which the rate and AV delay controls are Independent of each other.
  • Atrial and ventricular pacers In prior art atrial and ventricular pacers. two separate pulse generating circuits are provided to generate stimulating pulses at respective predetermined time inter- ⁇ allS following the last ventricular heat.
  • the ventricular escape interval (the time period between succeaive entricular beats) is longer than the atrial escape interml (the time period between successive ventricular and atrial heats) so that an atrial stimulating pulse is gener- .tlctl before a ventricular stimulating pulse.
  • Each detected spontaneous ventricular beat controls the resetttng of both pulse generating circuits.
  • Each ofthc pulse generating circuits in some prior art paccrs is free-running; respective atrial or ventricular slllflulitllllx pulses are generated at fixed intervals in the absence of the resetting of the pulse generating circuit.
  • the pacer timing is synchronized to the natural heartbeats by controlling the resetting of the two circuits u on the detection of each ventricular beat. While systents of this type are satisfactory for implantable pacera. a problem has been encountered when they are used in connection with external pacers. that is. pacers which are external to the patient except for electrical leads.
  • each of the pulse generating circuits includes a potentiometer which can be adjusted for setting the respective escape interval. Since the pulse generating circuits are frcerun' ning in the absence of a resetting pulse. it is apparent that if the atrial escape interval is less than 50 percent of the ventricular escape interval. then two or more atrial stimulating pulses may be generated between each pair of ventricular stimulating pulses. The detectinn of a ventricular beat. or the generation of a ventricular stimulating pulse. causes both pulse generating circuits to be reset. If the ventricular escape interval is N milliseconds and the atrial escape interval is less than .V/2 milliseconds. since both pulse generating circuits are free-running.
  • Atrial stimulating pulses are generated continunutty and at fixed time intervals in the absence of the detection of a spontaneous ventricular beat or the generalion of a ventricular stimulating pulse.
  • Multiple atrial stimulating pulses. of course. can only produce deleterious effects since the atria should not be stimulured too close in time to a ventricular beat.
  • the atrial escape interval can be set to be less than 50 percent of the ventrlcular escape interval. in which case multiple atrial stimulations are possible.
  • the multivibt'atot is fired and an atrial stimulating pulse is generated. Thereafter. the multivibrator returns to the quiescent state. no further atrial stimulating pulses are generated. In order for the multivibrator to be triggered once again. a new timing period must be initiated. and this takes place only when the nest spontaneous ventricular beat is detected or the neat ventricular stimulating pulse is generated. Even if the atrial escape interval is set to be less than percent of the ventricular escape interval. the multivibrator is triggered only once for each ventricular beat. Consequently. it is not possible for there to be multiple atrial stimulations between ventricular beats.
  • the ventricular pulse generator includes a potentiometer for varying the ventricular escape interval; the atrial pulse generator includes a potentiometer for varying the atrial escape interval.
  • This latter interval is the timeperiod between a ventricular beat and the rotlowing atrial stimulating pulse and is referred to herein as the VA interval.
  • the interval between each atrial stimulating pulse and the following ventricular stimulaling pulse is known as the AV delay.
  • VV interval as used herein refers to the time interval between successive ventricular stimulating pulses. in the pacer disclosed in my aforesaid application. it is apparent that adjustment of the ventricular pulse generator entiometcr controls not only the VV interval. but also the AV delay. if the VV interval is increased.
  • the ventricular pulse generator includes a single potentiometer; the larger the impedance setting. the longer the VV interval.
  • the alrall pulse generator includes two serially connected potentlometers: the larger the series impedance. the longer the VA interval.
  • One of the atrial pulse generators potentiometers is ganged to the ventricular pulse generator potentiometer; as the latter potentiometer is turned to increase its impedance.
  • the ganged potentiometer in the atrial pulse generator is similarly turned to increase its impedance.
  • the physiclan desires to increase the VV interval.
  • the W interval is extended as a result of the increase in the impedance of the ventricular pulse generator potentiometer.
  • the ganged atrial pulse generator potentiometer is turned so that its impedance increases as well.
  • the VA interval also increases.
  • the two ganged potentiometers have the same maximum impedances and function so that the same change in impedance in each potentiometer affects the VV interval or the VA interval to the same degree. Consequently. it the VV interval is increased by turning the shaft which gangs the two potentiomctcrs together.
  • the ⁇ A interval increases to the same extent. Since the AV delay is equal to the difference between the VV interval and the VA interval. it is apparent that the AV delay remains constant. In order to adjust the AV dclit). all that is necessary is to change the setting of the other (independent) potentiometer in the atrial pulse generator. This potentiometer affects only the VA interval. and thus the AV delay can be adjusted independently.
  • FIG. I is the same as FIG. 2 in my above-identified application and depicts an atrial and ventricular pacer in which the rate and AV delay controls are not independent of each other;
  • FIG. 2 depicts the illustrative embodiment of my invention in which independent rate and AV delay adjustments may be made.
  • the pacer includes a pair of electrodes El and E2. which are used for ventricular stimulotion and spontaneous beat detection. and a pair of electrodes. E3 and E4. which are used for atrial stimulaliott.
  • a spontaneous ventricular beat causes a signal to appear on electrodes El and E2. and this signal is processed and results in a pulse being applied through capacitor 53 to the base of transistor T6 and through capacitor 54 to the base of transistor TtO. (lt switch 5 is closed. then the pacer operates in a continuous mode and no pulses are extended to the bases of transistors T6 and T10. Similarly. in the presence of 604i: noise.
  • transistor! T3 and T4 function to prevent the applicalinrt of pulses to the bases of transistors T6 and T10 so that the pacer can operate in the continuous mode.
  • Capacitor $7 normally charges from batteries 1-5 through potentiometer J3.
  • transistor T9 fires and capacitor 65 discharges through the transistor. the electrodes and the heart tissue to stimu' late the ventricles.
  • capacitor 65 recharges in preparation for the generation or another stimulating pulse.
  • the setting of potentiometer 35 determines the magnitude of the charging current for capacitor 57. This. in turn. determines the ventricular escape interval.
  • transistor T6 conducts and capacitor 57 discharges through it. in such an event. the ventricular stimulating pulse which would otherwise have been generated when the voltage acrou capacitor 57 would have reached the firing level is not generated. instead. a new timing cycle begins. with a ventricular stimulating pulse being generated only it the ventricular escape interval elapses before the detection of another spontaneous ventricular beat.
  • the atrial pulse generating circuit similarly includes a timing capacitor 58 and a potentiometer 62 which is used to control the VA interval.
  • the detection of a spontaneous beat or the detection of a ventricular stimulating pulse results in the pulsing of the base of transistor T10.
  • capacitor 58 fully discharges through the transistor.
  • the capacitor charges through potentiometer 62.
  • a pulse. whose duration is detcrmincd by the setting of potentiometer 95. appears across atrial stimulating electrodes E3 and E4. Even after the atrial stimulating pulse is generated.
  • transistors TI] and Ti hoth remain on. and capacitor 58 remains charged.
  • transistor Tl0 that controls the discharge of capacitor 58. the turning off of transistors TI! and T12. and the start of a new VA timing interval. Since an atrial stimulating pulse can only be generated after capacitor 58 is first discharged through transistor TN). and transistor Tl0 is only turned on when a spontaneous ventricular beat is detected or an atrial stimulating pulse is generated. it is apparent that only one atrial stimulating pulse can be generated following each ventricular beat.
  • Potentiometer 35 in H0. l is replaced by a fixed resistor 35b and a potentiometer 35a.
  • Potentiometer 62 of FIG. I is replaced by two serially connected potentiometers 62a and 62b.
  • the dotted lines 35a-62a represents a single shaft which gangs potentiomctcrs 35a and 62a together. The settings of these two potentiometers are changed in the same way when the pacer rate adjusting shaft is turned. In all other respects the pacer of FIG. 2 operates as does the pacer of HG. I.
  • Resistor 35h in the ventricular pulse generator is proitled to insure a minimum VV interval. no matter how low the setting of potentiometer 350.
  • a similar fixed re istor can be included in series with potentiometer: b2 and 62h if desired.
  • pro- ⁇ itlr another potentiometer in series with potentiometer 35a. although an adjustment to the setting of this potentiometer would necessarily affect the AV delay alon with the pacer rate. It is the ganging of at least one potentiometer in the ventricular pulse generating circuit to at least one potentiometer in the atrial pulse generating circuit that allows the pacer rate to be changed without affecting the AV delay.
  • An atrial and ventricular eer comprising ventricular pulse generating means or generating a ventricu- In stimulating pulse for extension to a patients heart following the expiration of a ventricular escape timing interval.
  • first potentiometer means for varying said ventricular escape timing interval.
  • timing means responsive to the operation of said detecting means for measuring an atrial escape timing interval.
  • second potentiometer means for adjusting the width of said atrial escape timing interval.
  • means responsive to the espiration of said atrial escape timing interval for generating an atrial stimulating pulse for extension to said paticnts heart.
  • said controlling means includes a shaft which is ganged to said first and second potentiometer means. and wherein said ventricular escape timing interval is a linear function of the setting of said first potentiometer means and the width of said atrial escape timing interval is a linear function ofthe setting of said second potentiometer means. and said controlling means functions to maintain a constant difference between said ventricular escape timing interval and said atrial escape timing interval.
  • An atrial and ventricular pacer in accordance with claim I further including third potentiometer means for adjusting the width of said atrial escape timing interval independent of the width of said ventricular escape timing interval.
  • An atrial and ventricular pacer comprising ventricular pulse generating means for generating ventricular stimulating pulses for extension to a patients heart.
  • first means for varying the rate at which ventricular stimulating pulses are generated.
  • timing means for operating in synchronisrn with the beating action ofa patient's heart for measuring an atrial escape timing interval.
  • second means for adjusting the width ofsaid atrial escape timing interval.
  • the rate at which ventricular stimulating pulses are generated is a linear function of the setting of said first means and the width of said atrial escape timing interval is a linear function of the setting of said second means. and said controlling means is operative to maintain constant the time interval between the generation of an atrial stimulating pulse and the generation of the next ventricular stimulating pulse independent of the setting of the said first means.
  • An atrial and ventricular pacer in accordance with claim 3 further including third means for varying the width of said atrial escape timing interval independent of said controlling means 0 Q Q 0 O

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  • 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)
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US00244156A 1972-04-14 1972-04-14 Atrial and ventricular pacer having independent rate controls and means to maintain a constant av delay Expired - Lifetime US3814106A (en)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US00244156A US3814106A (en) 1972-04-14 1972-04-14 Atrial and ventricular pacer having independent rate controls and means to maintain a constant av delay
DE2314315A DE2314315C2 (de) 1972-04-14 1973-03-20 Bedarfsgesteuerter atrialer und ventrikularer Herzschrittmacher
NL7304895A NL7304895A (enrdf_load_stackoverflow) 1972-04-14 1973-04-09
BR732718A BR7302718D0 (pt) 1972-04-14 1973-04-13 Aperfeicoamentos em ritmador atrial e ventricular
JP4147073A JPS567701B2 (enrdf_load_stackoverflow) 1972-04-14 1973-04-13
GB1830073A GB1421485A (en) 1972-04-14 1973-04-16 Heart pacers

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US00244156A US3814106A (en) 1972-04-14 1972-04-14 Atrial and ventricular pacer having independent rate controls and means to maintain a constant av delay

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JP (1) JPS567701B2 (enrdf_load_stackoverflow)
BR (1) BR7302718D0 (enrdf_load_stackoverflow)
DE (1) DE2314315C2 (enrdf_load_stackoverflow)
GB (1) GB1421485A (enrdf_load_stackoverflow)
NL (1) NL7304895A (enrdf_load_stackoverflow)

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4386610A (en) * 1980-05-27 1983-06-07 Cordis Corporation Ventricular-inhibited cardiac pacer
US4390023A (en) * 1981-04-30 1983-06-28 Medtronic, Inc. Patterned electrical tissue stimulator
US4453547A (en) * 1981-04-06 1984-06-12 Physio Technology, Inc. T-Wave inhibiting system
US4856525A (en) * 1985-10-10 1989-08-15 Minnesota Mining And Manufacturing Company Multichannel electrical stimulator with improved channel isolation
US6711437B2 (en) 2001-07-30 2004-03-23 Medtronic, Inc. Pacing channel isolation in multi-site cardiac pacing systems
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
US20050055058A1 (en) * 2003-09-08 2005-03-10 Mower Morton M. Method and apparatus for intrachamber resynchronization
USRE39897E1 (en) 1989-01-23 2007-10-23 Mirowski Family Ventures, L.L.C. Method and apparatus for treating hemodynamic disfunction
US20090018608A1 (en) * 2004-02-12 2009-01-15 Schwartz Robert S Cardiac stimulation apparatus and method for the control of hypertension
US20120302904A1 (en) * 2011-05-26 2012-11-29 Jie Lian Heart stimulator and method for a-v delay optimization
US9008769B2 (en) 2012-12-21 2015-04-14 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US9370662B2 (en) 2013-12-19 2016-06-21 Backbeat Medical, Inc. Methods and systems for controlling blood pressure by controlling atrial pressure
US10342982B2 (en) 2015-09-11 2019-07-09 Backbeat Medical, Inc. Methods and systems for treating cardiac malfunction
US10485658B2 (en) 2016-04-22 2019-11-26 Backbeat Medical, Inc. Methods and systems for controlling blood pressure

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3952750A (en) * 1974-04-25 1976-04-27 Mieczyslaw Mirowski Command atrial cardioverting device
AU612143B2 (en) * 1987-03-19 1991-07-04 Xytronyx, Inc. Systems for the visualization of exposure to ultraviolet radiation and for the utilization of ultraviolet radiation to effect color changes
CN113546319B (zh) * 2021-07-19 2023-06-23 乐普医学电子仪器股份有限公司 一种自动心房起搏阈值搜索的方法和电路

Citations (3)

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Publication number Priority date Publication date Assignee Title
US3426748A (en) * 1965-11-23 1969-02-11 Gen Electric Stimulator analyzer and locater
US3595242A (en) * 1969-03-26 1971-07-27 American Optical Corp Atrial and ventricular demand pacer
US3717153A (en) * 1970-10-19 1973-02-20 Gen Electric Standby external rate control and implanted standby heart pacer

Family Cites Families (1)

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US3661158A (en) * 1969-12-15 1972-05-09 American Optical Corp Atrio-ventricular demand pacer with atrial stimuli discrimination

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3426748A (en) * 1965-11-23 1969-02-11 Gen Electric Stimulator analyzer and locater
US3595242A (en) * 1969-03-26 1971-07-27 American Optical Corp Atrial and ventricular demand pacer
US3717153A (en) * 1970-10-19 1973-02-20 Gen Electric Standby external rate control and implanted standby heart pacer

Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4386610A (en) * 1980-05-27 1983-06-07 Cordis Corporation Ventricular-inhibited cardiac pacer
US4453547A (en) * 1981-04-06 1984-06-12 Physio Technology, Inc. T-Wave inhibiting system
US4390023A (en) * 1981-04-30 1983-06-28 Medtronic, Inc. Patterned electrical tissue stimulator
US4856525A (en) * 1985-10-10 1989-08-15 Minnesota Mining And Manufacturing Company Multichannel electrical stimulator with improved channel isolation
USRE39897E1 (en) 1989-01-23 2007-10-23 Mirowski Family Ventures, L.L.C. Method and apparatus for treating hemodynamic disfunction
US6711437B2 (en) 2001-07-30 2004-03-23 Medtronic, Inc. Pacing channel isolation in multi-site cardiac pacing systems
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
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
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
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
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
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
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
US20070191893A1 (en) * 2003-09-05 2007-08-16 Mirowski Family Ventures, L.L.C. Method and apparatus for providing ipselateral therapy background
US9901739B2 (en) 2003-09-08 2018-02-27 Mirowski Family Ventures, LLC Method and apparatus for intrachamber resynchronization
US20050055058A1 (en) * 2003-09-08 2005-03-10 Mower Morton M. Method and apparatus for intrachamber resynchronization
US11207524B2 (en) 2003-09-08 2021-12-28 Mirowski Family Ventures, LLC Method and apparatus for intrachamber resynchronization
US8428729B2 (en) 2004-02-12 2013-04-23 Backbeat Medical, Inc. Cardiac stimulation apparatus and method for the control of hypertension
US12029909B2 (en) 2004-02-12 2024-07-09 Backbeat Medical, Llc Cardiac stimulation apparatus and method for the control of hypertension
US9320903B2 (en) 2004-02-12 2016-04-26 Backbeat Medical, Inc. Cardiac stimulation apparatus and method for the control of hypertension
US11406829B2 (en) 2004-02-12 2022-08-09 Backbeat Medical, Llc Cardiac stimulation apparatus and method for the control of hypertension
US8086315B2 (en) 2004-02-12 2011-12-27 Asap Medical, Inc. Cardiac stimulation apparatus and method for the control of hypertension
US20090018608A1 (en) * 2004-02-12 2009-01-15 Schwartz Robert S Cardiac stimulation apparatus and method for the control of hypertension
US10232183B2 (en) 2004-02-12 2019-03-19 Backbeat Medical, Inc. Cardiac stimulation apparatus and method for the control of hypertension
US8718750B2 (en) * 2011-05-26 2014-05-06 Biotronik Se & Co. Kg Heart stimulator and method for A-V delay optimization
US20120302904A1 (en) * 2011-05-26 2012-11-29 Jie Lian Heart stimulator and method for a-v delay optimization
US9526900B2 (en) 2012-12-21 2016-12-27 Backbeat Medical, Inc. Methods and systems for controlling blood pressure by controlling atrial pressure
US11452875B2 (en) 2012-12-21 2022-09-27 Backbeat Medical, Llc Methods and systems for lowering blood pressure through reduction of ventricle filling
US9937351B2 (en) 2012-12-21 2018-04-10 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US10071250B2 (en) 2012-12-21 2018-09-11 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US9656086B2 (en) 2012-12-21 2017-05-23 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US10252061B2 (en) 2012-12-21 2019-04-09 Backbeat Medical, Inc. Methods and systems for controlling blood pressure by controlling atrial pressure
US12246180B2 (en) 2012-12-21 2025-03-11 Backbeat Medical, Llc Methods and systems for controlling blood pressure by controlling atrial pressure
US10441794B2 (en) 2012-12-21 2019-10-15 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US12208271B2 (en) 2012-12-21 2025-01-28 Backbeat Medical, Llc Methods and systems for controlling blood pressure by controlling atrial pressure
US10610689B2 (en) 2012-12-21 2020-04-07 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US10967188B2 (en) 2012-12-21 2021-04-06 Backbeat Medical, Llc Methods and systems for controlling blood pressure by controlling atrial pressure
US11097108B2 (en) 2012-12-21 2021-08-24 Backbeat Medical, Llc Methods and systems for lowering blood pressure through reduction of ventricle filling
US9008769B2 (en) 2012-12-21 2015-04-14 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US11986661B2 (en) 2012-12-21 2024-05-21 Backbeat Medical, Llc Methods and systems for lowering blood pressure through reduction of ventricle filling
US9333352B2 (en) 2012-12-21 2016-05-10 Backbeat Medical, Inc. Methods and systems for lowering blood pressure through reduction of ventricle filling
US11712567B2 (en) 2012-12-21 2023-08-01 Backbeat Medical, Llc Methods and systems for controlling blood pressure by controlling atrial pressure
US9878162B2 (en) 2012-12-21 2018-01-30 Backbeat Medical, Inc. Methods and systems for controlling blood pressure by controlling atrial pressure
US9370662B2 (en) 2013-12-19 2016-06-21 Backbeat Medical, Inc. Methods and systems for controlling blood pressure by controlling atrial pressure
US11389658B2 (en) 2015-09-11 2022-07-19 Backbeat Medical, Llc Methods and systems for treating cardiac malfunction
US10342982B2 (en) 2015-09-11 2019-07-09 Backbeat Medical, Inc. Methods and systems for treating cardiac malfunction
US11426589B2 (en) 2016-04-22 2022-08-30 Backbeat Medical, Llc Methods and systems for controlling blood pressure
US11969598B2 (en) 2016-04-22 2024-04-30 Backbeat Medical, Llc Methods and systems for controlling blood pressure
US10485658B2 (en) 2016-04-22 2019-11-26 Backbeat Medical, Inc. Methods and systems for controlling blood pressure

Also Published As

Publication number Publication date
DE2314315C2 (de) 1982-06-16
GB1421485A (en) 1976-01-21
NL7304895A (enrdf_load_stackoverflow) 1973-10-16
DE2314315A1 (de) 1973-10-25
JPS567701B2 (enrdf_load_stackoverflow) 1981-02-19
BR7302718D0 (pt) 1974-08-29
JPS4920982A (enrdf_load_stackoverflow) 1974-02-23

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