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Numéro de publicationUS3857399 A
Type de publicationOctroi
Date de publication31 déc. 1974
Date de dépôt19 mars 1971
Date de priorité24 mars 1970
Numéro de publicationUS 3857399 A, US 3857399A, US-A-3857399, US3857399 A, US3857399A
InventeursZacouto F
Cessionnaire d'origineZacouto F
Exporter la citationBiBTeX, EndNote, RefMan
Liens externes: USPTO, Cession USPTO, Espacenet
Heart pacer
US 3857399 A
Résumé
Device for stimulating the heart comprises means for producing stimulating pulses at regular intervals and means responsive to spontaneous heart signals for controlling the transmission of said pulses to the heart in dependence upon the timing and magnitude of the spontaneous heart signals and/or the average intramyocardial pressure. In the absence of spontaneous heart signals, stimulating pulses are produced at predetermined intervals. When spontaneous heart signals occur, an adjustable waiting period is introduced in which to allow a second spontaneous signal instead of a stimulating pulse. The duration of the waiting period is varied as a function of the interval of time which separates two consecutive spontaneous detected signals (i.e., not separated by any artificially induced heart signal).
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Description  (Le texte OCR peut contenir des erreurs.)

Zacouto [111 3,857,399 [451 Dec. 31, 1974 HEART PACER' [76] Inventor: Fred Zacouto, 16, rue de la Convention, Paris l5eme, France 9/1972 Cole 128/419 P Primary Examiner-William E. Kamm Attorney, Agent, or Firm-Brisebois & Kruger 57 ABSTRACT Device for stimulating the heart comprises means for producing stimulating pulses at regular intervals and means responsive to spontaneous heart signals for controlling the transmission of said pulses to the heart in dependence upon the timing and magnitude of the spontaneous heart signals and/or the average intramyocardial pressure. In the absence of spontaneous heart signals, stimulating pulses are produced at predetermined intervals. When spontaneous heart signals occur, an adjustable waiting period is introduced in whichto allow a second spontaneous signal instead of a stimulating pulse. The duration of the waiting period is varied as a function of the interval of time which separates two consecutive spontaneous detected signals (i.e., not separated by any artificially induced heart signal).

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PATEHTEU 8 1 I914 SHEU OBBF 15 pyggmgg miss 1 I974 SHEET IOUF 15 HEART PACER SUMMARY OF THE INVENTION This invention relates to a method and apparatus for the electrical stimulation of the cardiac muscle.

Known devices for electrically stimulating the cardiac muscle include demand heart pacers which normally stimulate the cardiac muscle at a given frequency by transmitting thereto stimulating impulses at predetermined intervals corresponding to that frequency. When a spontaneous electrical signal (called a heart signal) from the cardiac muscle occurs which is detected by the electrodes and corresponds, for example, to a cardiac systole, the stimulation is interrupted after this signal for a constant waiting period regardless of whether the spontaneous systole is early or late, and regardless ofthe nature of this systole. Such devices, while currently in use, have a number of disadvantages.

In particular, they offer only an unpersonalized rerhythm to be established when it should on the contrary provide corrective intervention.

It is an object of the present invention to provide a process and apparatus making it possible to adapt the artificial electrical stimulation to the instantaneous condition of the cardiac muscle so as to supply a stimulating-response which takes into account whether the spontaneous systoles are or are not dangerous.

Another object of the invention is to provide a method and apparatus making it possible to take the cardiac muscle under control when a rapid and dangerous spontaneous rhythm tends to become established.

Another object of the invention is to provide a method and apparatus making it possible to let the heart beat at its own characteristic rhythm when nondangerous delayed spontaneous systoles occur.

Another object of the invention is to provide a process and apparatus for temporarily increasing the frequency of the stimulation when a dangerous rhythm tends to become established.

Another object of the invention is to differentiate the responses in dependence on whether the detected electrical signals are of ventricular or auricular origin.

Another object of the invention is to also provide means for adapting. the stimulating response to the hemodynamic conditions and/or the intramyocardial pressure.

Another object of the invention is to provide inexpensive and reliable devices .which may be simply adjusted to adapt the responses of the devices very precisely to the instantaneous state of the cardiac patient.

Yet another object of the invention is to provide a device of very simple construction, which is very reliable and consumes very little electrical energy so that it may be implanted in the body.

Other objects and advantages of the invention will appear from reading the following description of the invention, with reference to the accompanying drawings in which:

FIG. I is a schematic view of an electrocardiogram illustrating theprocess according to the invention;

FIG. 2 is a general schematic view ofa device accord- 2. ing to the invention comprising three parts A, B and C; FIG. 3 is an alternative embodiment of the part A;

FIG. 4 is a detailed circuit'dia gram of the apparatus shown in FIG. 3;

FIGS. 5 and 6 are graphical representations illustrating the operation of the device of FIG. 3;

FIG. 7 shows another embodiment of the part A; FIG. 8 is a circuit diagram of the delay means of FIG. 7;

FIG. 9 is a diagramatic representation illustrating the operation of FIG. 7;v

FIG. 10 shows another embodiment of the device of FIG. 7 adapted to detect ventricular systoles;

FIG. 11 is a diagram illustrating the operation of FIG. 10;

FIG. 12 is another embodiment of the apparatus of part A;

FIG. 13 is a circuit diagram of the device shown in FIG. 12;

FIG. 14 is a diagram illustrating the operation of the device shown in FIG. 12;

FIG. 15 shows another embodiment of the part A;

FIG. [6 schematically illustrates yet another embodiment of the part A;

FIG. 17 illustrates an example ofthe function Y of K;

FIg. 18 is a circuit diagram of the part C;

FIGS. 19, 20 and 21 show a device responsive to the intramyocardial pressure;

FIG. 22 is a schematic view of another embodiment of the part A; and

FIG. 23 is a diagram illustrating the operation of the device of FIG. 22. I

GENERAL DESCRIPTION OF THE PROCESS It is the object of the invention to provide a method of electrically stimulating the cardiac muscle by means of an automatic device comprising one or more stimulating and detecting electrodes, in which method electrical stimulating impulses having a predetermined frequency are transmitted to the cardiac musclein the absence of a spontaneous systole, and the transmission of a stimulating electrical impulse is'delayed for a predetermined waiting period when a spontaneous systole of at least a certain type occurs after a stimulating im pulse. The waiting period may be of two different durations, at least the shortest of which is less than, or at most equal to, the predetermined period, and the choice of one of the two durations is determined by the interval of time separating the spontaneous systole from the stimulating impulse which directly preceded it. The selected duration of said waiting period is an at least partially increasing function of said interval of time.

FIG. 1 represents an electrocardiogram illustrating the process according to the invention. On this electrical cardiogram three spontaneous systoles SS are shown. After the third spontaneous systole, there is no further spontaneous systole and, in a conventional manner, the device waits a certain period of time .I. When no systole occurs during this time, the automatic device, of the demand heart pacer type, transmits a in the absence of the appearance of extrasystoles or spontaneous systoles. After the third pulse I, a new spontaneous systole SS, is produced, which is separated from the immediately preceding pulse 1 by an interval of time K,. From this moment, in accordance with the invention, a waiting period is permitted to pass which is represented on the drawing by Y,. The drawing also shows at I the moment at which the next stimulating pulse would have taken place if SS, had not taken place. If, as shown on the drawing, no new spontaneous systole appears during the period Y,, the apparatus emits a stimulating pulse l, at the end of this period. Since no new spontaneous systole appears after I,, the device resumes its stimulation at the intervals X by transmitting pulses I as shown on the drawing. If, after such a pulse I, for example the first one on the drawing, a new spontaneous systole SS appears, a new waiting period Y, is initiated and if no spontaneous systole occurs during this time, a stimulating pulse 1 is transmitted to the cardiac muscle at the end of the delay period Y2.

In accordance with the invention, the waiting period Y (such as Y, or Y may have any one of several different values, these values being preferably the smaller as the interval of time, such as K, or K separating the spontaneous systole from the preceding stimulating pulse is the smaller. As shown on the drawing, the value Y, is smaller than the value Y because the period K, is less than the interval K More exactly, it willbe seen on the example shown on the drawing that Y, is less than the period X, and Y, is greater than the period X. Of course Y, and Y may both be less than the interval -X. On the other hand, in accordance with the invention, Y is an increasing function of K, when K increases over a part at least of its range of variation. Neverthe-,

less, in certain particular applications, Y may be a decreasing function of K over a certain part of the range of variation ofK.

When, before the end ofthe waiting period, generally represented by Y, a new spontaneous systole takes place, a new waiting period is established. In a first embodiment, this new waiting period is selected, like the length of the waiting period Y, as a function, this time of the interval of time separating the new spontaneous systole from the preceding spontaneous systole such as SS, or $8,. In a second embodiment of the invention, this new-waiting period is, on the contrary, fixed, and preferably equal to the predetermined stimulating period (X on the drawing). This means that if two directly consecutive spontaneous systoles take place, the second systole is treated as a stimulating pulse and the normal rhythm of stimulation at the predetermined intervals X is resumed.

In one particular embodiment of the invention the different values (such as Y, and Y of the waiting period are discontinuous, the highest values being generally attained for the longest delayed spontaneous systoles and the lowest values for the most premature systoles. Thus, by way of example, if the predetermined interval X is 900 milliseconds, the waiting period Y is 600 milliseconds if the interval of duration K separating the spontaneous systole from the immediately preceding stimulating impulse is less than or equal to 500 milliseconds, but equal to 800 milliseconds if K is between 550 and 750 milliseconds, and equal to 1,100 milliseconds ifK is between 750 and 900 milliseconds. The three different values of the waiting period are thus respectively 600, 800 and 1,100 milliseconds. It will be seen that in this particular example the highest value of the waiting period is longer than the interval X. It could, however, be equal to or less than this period. In all cases, as has already been said, the smallest value, at least, of the waiting period, is less than or exactly equal to the duration of the interval X.

However, in a preferred embodiment of the invention, the different values of the waiting period are arranged in a continuous manner and the waiting period is then a continuous, generally increasing, function of the interval of time separating the last pulse from the consecutive spontaneous systole. This function may, however, have steps, especially when the interval approaches the value of said predetermined period X, or on the contrary, when the interval K becomes very small.

Nevertheless, in certain applications, the continuous function Y of X may have a decreasing portion over a certain portion of the range of variation of K.

By way of example, FIG. 17 shows the graphical representation of this function. The ordinate shows the duration Y of the waiting period before stimulation, while the abscissa, decreased by 400 milliseconds, (for reasons of expediency hereinafter explained) shows the interval separating a spontaneous systole from the directly preceding stimulating pulse. The abscissa thus shows the value K-400 milliseconds. This curve may comprise horizontal segments, especially for the highest values of Y, which moreover, be greater than the period X.

When the largest values of the waiting period Y are greater than X, that is to say, greater than the period of stimulation in the absence of a spontaneous systole, the value of the interval K beneath which Y is less than X and above which Y is greater than X lies preferably in the second half of the period X which follows the stimulating pulse I directly preceding the spontaneous systole which causes a waiting period. This limiting value is shown at m on FIG. 2. Naturally, if Y is a continuous function of K, Y is equal to X and K is equal to the distance separating I from m.

In one embodiment of the process according to the invention the waiting period is always greater than the interval separating a spontaneoussystole from the immediately preceding stimulating pulse, or, in an alternative form already mentioned, from the immediately preceding spontaneous systole. This means that Y is greater than K. On the contrary, in another form of the invention, Y is always less than K. In this particular embodiment, it is obviously impossible to have in the electrocardiogram three spontaneous systoles SS separated from each other by identical periods of time, as shown at the left of FIG. 2. This alternative has the advantage of insuring energetic taking in hand of the cardiac muscle while leaving it the least possible time within which to produce spontaneous systoles. However, in a third embodiment, Y may be greater than K when K is large and less than K when K is small. It is thus possible to check premature spontaneous systoles while lengthening the waiting period for delayed spontaneous systoles, so as to encourage the cardiac muscle to beat at its own characteristic rhythm, but at a frequency which is not too high.

As has been seen above, the process according to the invention is put in operation when a spontaneous systole of at least a certain type appears. By systole" is meant any electrical signal of sufficient strength received on at least one of the electrodes, regardless of whether there is or is not a contraction of the cardiac muscle. Thus, in a preferred embodiment of the invention, the process takes into account only those spontaneous systoles which occur after the end of the refractory period of the cardiac muscle, and the systoles which take place during this period are not taken into account. This refractory period is, for a normal cardiac rhythm, for example on the order of 300 to 400 milliseconds after a spontaneous systole or an electrosystole. However, according to the invention, the choices of the type of spontaneous systole which is taken into account may also be a function either of the shape of the systole on the electrocardiogram or of the origin of the spontaneous systole. Thus, the systoles of a certain type may, for example, be limited to ventricular extrasystoles, which are often the most dangerous.

In this .case, the detecting electrode may, in accordance with the invention, amount to a waveform discriminator (which will be hereinafter described) or a plurality of electrodes may be used which are located in, or in contact with, the cardiac muscle, the first electrode exciteddetermining the origin of this spontaneous systole..

In accordance with an improved form of the invention, the stimulating pulse normally. delivered, or delivered after a waiting period according to the invention, may be at least doubled or its strength may be automatically adjusted, to increase it if a spontaneous systole appears, when the interval of time K is smaller. This assures more certain electrical control of the cardiac muscle, the electrical conductivity of which varies as a function of the instantaneous frequency of the. systoles.

In accordance with another improvement of the in-' vention the basic stimulating frequency, that is to say the predetermined period X, is increased in a temporary manner. Y'may also be diminished simultaneously to adapt it to this new period X. These alternatives may be selected in dependence on various factors as will be seen from the following.

Thus, if it is found that, despite the variation in the waiting period Y, too large a number of spontaneous systoles are produced, these spontaneous systoles are automatically counted, and when, for a predetermined number of systoles one has counted too large a number of spontaneous systoles, the base period X is automatically decreased.

In another alternative, this base period varies as a function of the intramyocardial pressure detected, as will be hereinafter described. It is also possible to detect by suitable pick-up means the hemodynamic characteristics so as to regulate the rhythm and shape of the stimulating pulses and to the waiting period.

GENERAL DESCRIPTION OF THE APPARATUS The invention alsorelates to a device for carrying out i the aforesaid process and comprises stimulating means controlled by a time base to deliver at a predetermined frequency electricalpulses for stimulating the cardiac muscle through at least one preferably cardiac elecmost equal to the predetermined waiting period, means for detecting spontaneous cardiac systoles comprising at least one preferably cardiac electrode and for conducting electrical pulses corresponding to the spontaneous systoles detected to said time delay means to initiate said waiting period, which corresponds to the state in which the delay means are found at this instant, and means to shift said time delay means successively from one of said states into the other as a function of the time which has elapsed since tht last stimulating pulse. Said stimulating means may be any conventional means adapted to transmit a stimulating pulse so at least one electrode when actuated by'said time base, or by said time delay means, at the end of the waiting period.

The time base may also be of a conventional type. It is thus possible to use as a time base, for example, a capacitance which charges itself periodically through a load resistance and actuates, when charged to a sufficiently high potential, a device such as a programmable unijunction transistor. It is also possible to use an astable switch or multi-vibrator which periodically initiates the stimulation. It is also possible, as an alternative, to use as a time base a pulse generator operating at a given frequency'and associated with any suitable counting means, for example, a flip-flop counter or step-by-step integrator. This counter when the number of predeter mined pulses has been counted, causes the emission of a stimulating pulse.

The delay means are responsive to the spontaneous systole pulses coming from the detecting means and may be in either'of two'different states, so as to initiate the waiting period corresponding to their state at the moment at which they are actuated, and actuate said stimulating means at the end of said waiting period. It is thus possible to use as delay means two condensers (i.e., capacitors), each comprising a charging resistor, and both connected to trigger means such, for example, as a programmable unijunction transistor, with one of g the condensers charging from an initial potential slightly higherthan the initial potential of the other condenser, but increasing in potential more slowly the other condenser, so that the potential of this other condenser in time overtakes thepotential of the first condenser, thus actuating a device such as the unijunction transistorpThe later the second condenser starts charging after the first condenser has begun to charge, the longer the time which will be required for it to overtake the potential of the first condenser. In this embodiment, the state of the delay means is thus determined by the potential which has beenattained by the said first condenser at the moment at which a spontaneous systolic pulse occurs to initiate charging of the second condenser. Of course, instead of using the charging periods of the condensers, it is possible to use their discharge periods.

In another embodiment of the invention, said delay means may consist of a single condenser associated with a discharge resistance. This condenser is charged through a charging resistance which may be the same as the discharge resistance, but which is preferably different. When a spontaneous systolic pulse takes place the charging of the condenser is interrupted and the condenser discharges through the discharge resistance up to the point at which the potential reaches a fixed value from which, through appropriate means, it causes a stimulating pulse to beproduced. It will be appreciated that the higher the charging potential is when this I pulse takes place, the longer the discharge to the fixed charged during the occurrence of a spontaneous systole.

In another embodiment of the invention said time delay means comprise several monostable multivibrators having different periods in the unstable state, at least one of which is less than said predetermined waiting period. These different multivibrators are connected to a electronic actuated rotary switch directing the spontaneous successive systolic pulses as a function of time to the different monostable multivibrators. The state of these time delay means is thus determined by the position of the rotary electronic switch.

In another embodiment of the invention, the delay means comprises a digital pulse counter. Said pulse counter counts a certain number of pulses from a pulse generator and, when it has counted the last of these pulses, actuates the stimulating means. The number of pulses which said counter must count is for example, determined by another number of pulses which has been previously counted, the state of said delay means being thus determined by the number of pulses previously counted and thus by the state of the counter.

This means for changing the state of one of said delay means as a function of the time elapsed since the last stimulating pulse may also be made in various ways. Thus they may comprise a source of potential and a charging resistance associated with a capacitance. The charging of said capacitance starts at the moment at which an electrical stimulating pulse takes place, or, as an alternative, at a predetermined time after such a pulse. The potential attained by said capacitance at the moment at which a spontaneous systole is detected thus determines thestate of the associated delay means, for example, a discharge resistance associated with the capacitance.

Thus when the delay means comprises two condensers, the means for changing the delay means from one state to another comprise a source of energy and the charging resistance of the slower condenser. The same is true of the variation utilizing only a single condenser.

In the variation in which said delay means comprises several monostable multivibrators which are made successively responsive, said means for changing the state -of one of these delay means comprises means advancing the rotary electronic switch at a predetermined speed from an initial position corresponding to the occurrence of a stimulating pulse. The means for changing the time delay means from one state to another may also comprise digital means including a pulse generator and a counter, for example one which is automatically reset to zero at each stimulating pulse. Beginning when a stimulating electrical pulse takes place, the counter recommences to count the pulses which it receives from the pulse generator. When a spontaneous systole occurs, the state of the time delay means is determined by the number of pulses counted. When the time delay means also comprise a counter, this second counter counts a number of pulses determined by the number of pulses which has previously been counted up to that time by the first counter. The number of pulses counted by the second counter may be, for example, the same as the number previously counted, in which case the waiting period may be equal to or different from the interval of time separating a spontaneous systole from the artificial electrosystole immediately preceding it. Of course, in all embodiments, it is advantageously possible to use common electrical or electronic components, for example for the time base, and/or delay means, and/or means for changing the state of any of the delay means.

The means for detecting spontaneous systoles comprises at least one detecting electrode, which may be the same as the stimulating electrode, and which is adapted to detect cardiac electrical phenomena. Preferably, temporary cut-off means are provided to avoid detection of the cardiac systole directly provoked by an articifical electrostimulation ES. Cut-off means may also be provided to prevent the detection of any cardiac electrical phenomena during a fixed time which follows a stimulating pulse ES, so as to avoid taking into account phenomena which take place during the refractory periods of the cardiac muscle. Finally, said detecting means may comprise different selecting means making it possible to insure the transmission to the delay means of only these pulses received from particular systoles, either as a function of the moment at which such a systole takes place, or as a function of its origin (auricular or ventricular). This is made possible by utilizing two electrodes and determining the position of the electrode which first detected the electrical phenomenon of this systole, or by using means responsive to a characteristic of the electrical systolic pulse, such as its shape, length, amplitude, etc.

The device which has been described may take several forms. It may be that a spontaneous systole detected which has triggered the time delay means will be followed by a second spontaneous systole before the end of the waiting period. In a first embodiment of the invention means are provided to return the different electronic components of the device to their original state so that a second systole is considered by the device exactly like an artificial stimulating pulse.

In another variation of the invention however, means may be provided to again trigger the time delay means to provide a waiting period corresponding to the state in which said provide a waiting period corresponding to the state in which said time delay means is found at the moment at which the second systole takes place. In this case said time delay means are preferably divided into two parts as will be hereinafter seen.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS A. FIRST EMBODIMENT This first embodiment relates to a device comprising two condensers which are charged at two different speeds, the potential of one condenser being adapted to overtake the potential of the other condensenThis device is described with reference to FIGS. 2, 3, 4, 5

and 6.

Referring first to FIG. 2, the device according to the invention comprises three parts, A, B and C, of which only parts A and B will now be described. Part C is hereinafter described since it is not indispensable to the operation of parts A and B. Part B comprises an intracardiac catheter I which terminates in several electrodes 2, certain of which are positive, while others are negative. These electrodes 2 act both as detectors and as stimulators for the cardiac muscle. The electrodes 2

Citations de brevets
Brevet cité Date de dépôt Date de publication Déposant Titre
US3547127 *29 avr. 196815 déc. 1970Medtronic IncCardiac pacemaker with regulated power supply
US3656487 *7 janv. 197018 avr. 1972Medtronic IncElectronic demand heart pacemaker with different pacing and standby rates
US3693626 *2 nov. 197026 sept. 1972Adcole CorpDemand pacer with heart rate memory
Référencé par
Brevet citant Date de dépôt Date de publication Déposant Titre
US3995624 *19 déc. 19747 déc. 1976Siemens AktiengesellschaftInstallation for the processing of EKG signals
US4228803 *6 oct. 197821 oct. 1980Credit Du Nord International N.V.Physiologically adaptive cardiac pacemaker
US4503857 *25 oct. 198212 mars 1985Vitatron Medical B.V.Programmable cardiac pacemaker with microprocessor control of pacer rate
US4566456 *18 oct. 198428 janv. 1986Cordis CorporationApparatus and method for adjusting heart/pacer rate relative to right ventricular systolic pressure to obtain a required cardiac output
US4577633 *28 mars 198425 mars 1986Medtronic, Inc.Rate scanning demand pacemaker and method for treatment of tachycardia
US4600017 *19 juil. 198415 juil. 1986Cordis CorporationPacing lead with sensor
US4763646 *9 déc. 198716 août 1988Siemens AktiengesellschaftHeart pacemaker
US4791931 *13 août 198720 déc. 1988Pacesetter Infusion, Ltd.Demand pacemaker using an artificial baroreceptor reflex
US4867161 *17 mars 198719 sept. 1989Max SchaldachCardiac pacemaker
US4936304 *16 déc. 198726 juin 1990Thomas Jefferson UniversityPacing system and method for cardiac pacing as a function of determined myocardial contractility
US4941471 *7 sept. 198817 juil. 1990Medtronic, Inc.Rate stabilization pacemaker
US5016630 *30 janv. 198921 mai 1991Siemens AktiengesellschaftHeart pacemaker with hysteresis function
US5042480 *10 oct. 199027 août 1991Siemens AktiengesellschaftMethod and implantable medical device for stimulating tissue contractions
US5129394 *7 janv. 199114 juil. 1992Medtronic, Inc.Method and apparatus for controlling heart rate in proportion to left ventricular pressure
US5205283 *30 juil. 199127 avr. 1993Medtronic, Inc.Method and apparatus for tachyarrhythmia detection and treatment
US5213098 *26 juil. 199125 mai 1993Medtronic, Inc.Cardiac pacemaker
US5284491 *27 févr. 19928 févr. 1994Medtronic, Inc.Cardiac pacemaker with hysteresis behavior
US5305745 *2 avr. 199226 avr. 1994Fred ZacoutoDevice for protection against blood-related disorders, notably thromboses, embolisms, vascular spasms, hemorrhages, hemopathies and the presence of abnormal elements in the blood
US5306293 *21 nov. 199126 avr. 1994Fred ZacoutoDevice for the prevention of cardiac failures
US5370668 *22 juin 19936 déc. 1994Medtronic, Inc.Fault-tolerant elective replacement indication for implantable medical device
US5387228 *22 juin 19937 févr. 1995Medtronic, Inc.Cardiac pacemaker with programmable output pulse amplitude and method
US5402070 *15 juil. 199428 mars 1995Medtronic, Inc.Fault-tolerant elective replacement indication for implantable medical device
US5674257 *5 mars 19967 oct. 1997Medtronic, Inc.Pacemaker adapted to prefer underlying sinus rhythm over other rate responsive indicator
US5713929 *3 mai 19963 févr. 1998Medtronic, Inc.Arrhythmia and fibrillation prevention pacemaker using ratchet up and decay modes of operation
US5741310 *26 oct. 199521 avr. 1998Medtronic, Inc.System and method for hemodynamic pacing in ventricular tachycardia
US5919210 *10 avr. 19976 juil. 1999Pharmatarget, Inc.Device and method for detection and treatment of syncope
US6078834 *25 févr. 199920 juin 2000Pharmatarget, Inc.Device and method for detection and treatment of syncope
US6078836 *14 mai 199820 juin 2000Ela Medical S.A.Active implantable medical device for the reduction of cardiac arrhythmias by modifying the escape interval and methods therefor
US6128527 *3 déc. 19973 oct. 2000University Of Iowa Research FoundationApparatus and method of analyzing electrical brain activity
US6241682 *16 août 20005 juin 2001Nihon Kohden CorporationPatient monitoring apparatus
US628590721 mai 19994 sept. 2001Cardiac Pacemakers, Inc.System providing ventricular pacing and biventricular coordination
US635166921 mai 199926 févr. 2002Cardiac Pacemakers, Inc.Cardiac rhythm management system promoting atrial pacing
US635375920 oct. 20005 mars 2002Cardiac Pacemakers, Inc.Cardiac rhythm management system promoting a trial pacing
US641184818 avr. 200125 juin 2002Cardiac Pacemakers, Inc.System providing ventricular pacing and biventricular coordination
US643043821 mai 19996 août 2002Cardiac Pacemakers, Inc.Cardiac rhythm management system with atrial shock timing optimization
US643840828 déc. 200020 août 2002Medtronic, Inc.Implantable medical device for monitoring congestive heart failure
US650198826 déc. 200031 déc. 2002Cardiac Pacemakers Inc.Apparatus and method for ventricular rate regularization with biventricular sensing
US668754130 déc. 20023 févr. 2004Cardiac Pacemakers, Inc.Method for delivering atrial defibrillation therapy
US6738665 *5 juin 200118 mai 2004Ela Medical S.A.Detection of late atrial extrasystoles in an active implantable medical device such as pacemaker defibrillator, cardiovertor and/or multisite device
US673866728 déc. 200018 mai 2004Medtronic, Inc.Implantable medical device for treating cardiac mechanical dysfunction by electrical stimulation
US684526828 févr. 200218 janv. 2005Medtronic, Inc.Rate stabilization with maintenance of intrinsic ventricular response
US695710026 déc. 200018 oct. 2005Cardiac Pacemakers, Inc.Method and system for display of cardiac event intervals in a resynchronization pacemaker
US698800225 nov. 200217 janv. 2006Cardiac Pacemakers, Inc.Apparatus and method for ventricular rate regularization with biventricular sensing
US703946113 mai 20002 mai 2006Cardiac Pacemakers, Inc.Cardiac pacing system for prevention of ventricular fibrillation and ventricular tachycardia episode
US70470663 mars 200416 mai 2006Cardiac Pacemakers, Inc.Method and system for display of cardiac event intervals in a resynchronization pacemaker
US705845022 avr. 20026 juin 2006Medtronic, Inc.Organizing data according to cardiac rhythm type
US706232521 mai 199913 juin 2006Cardiac Pacemakers IncMethod and apparatus for treating irregular ventricular contractions such as during atrial arrhythmia
US706907727 nov. 200227 juin 2006Cardiac Pacemakers, Inc.Rate smoothing control
US7117746 *13 août 200110 oct. 2006Michael YehDigital pressure gauge
US71204902 août 200210 oct. 2006Cardiac Pacemakers, Inc.Cardiac rhythm management system with atrial shock timing optimization
US713961311 déc. 200321 nov. 2006Medtronic, Inc.Implantable medical device communication system with pulsed power biasing
US714291513 juin 200328 nov. 2006Cardiac Pacemakers, Inc.Apparatus and method for ventricular rate regularization
US714291826 déc. 200028 nov. 2006Cardiac Pacemakers, Inc.Apparatus and method for pacing mode switching during atrial tachyarrhythmias
US716494822 avr. 200216 janv. 2007Medtronic, Inc.Cardiac output measurement using dual oxygen sensors in right and left ventricles
US718127820 mars 200320 févr. 2007Cardiac Pacemakers, Inc.Apparatus and method for ventricular rate regularization
US720979026 nov. 200324 avr. 2007Medtronic, Inc.Multi-mode programmer for medical device communication
US721286013 nov. 20031 mai 2007Cardiac Pacemakers, Inc.Apparatus and method for pacing mode switching during atrial tachyarrhythmias
US723991412 déc. 20013 juil. 2007Cardiac Pacemakers, Inc.Rate smoothing control
US728688416 janv. 200423 oct. 2007Medtronic, Inc.Implantable lead including sensor
US738308612 juil. 20043 juin 2008Cardiac Pacemakers, Inc.Ventricular conduction delay trending system and method
US746090824 mai 20042 déc. 2008Cardiac Pacemakers, Inc.System providing ventricular pacing and biventricular coordination
US754616623 avr. 20039 juin 2009Medtronic, Inc.Medical lead designs for lead placement through tissue
US76805303 mai 200616 mars 2010Cardiac Pacemakers, Inc.Method and system for display of cardiac event intervals in a resynchronization pacemaker
US774281425 avr. 200622 juin 2010Cardiac Pacemakers, Inc.Cardiac pacing system for prevention of ventricular fibrillation and ventricular tachycardia episode
US780519213 oct. 200628 sept. 2010Cardiac Pacemakers, Inc.Apparatus and method for pacing mode switching during atrial tachyarrhythmias
US785626710 avr. 200721 déc. 2010Cardiac Pacemakers, Inc.Apparatus and method for pacing mode switching during atrial tachyarrhythmias
US790415828 avr. 20058 mars 2011Medtronic, Inc.Measurement of coronary sinus parameters to optimize left ventricular performance
US79172114 mai 200629 mars 2011Medtronic Inc.Inotropic orthorhythmic cardiac stimulator
US801020721 avr. 200330 août 2011Medtronic, Inc.Implantable medical lead designs
US804606125 août 200825 oct. 2011Cardiac Pacemakers, Inc.System and method for preventing recurrence of atrial tachyarrhythmia
US806499712 juin 200622 nov. 2011Cardiac Pacemakers, Inc.Method and apparatus for treating irregular ventricular contractions such as during atrial arrhythmia
US810333417 févr. 201024 janv. 2012Cardiac Pacemakers, Inc.Method and system for display of cardiac event intervals in a resynchronization pacemaker
US810335713 sept. 200724 janv. 2012Medtronic, Inc.Implantable lead including sensor
US81265519 déc. 200828 févr. 2012Cardiac Pacemakers, Inc.AV delay features
US81354651 déc. 200813 mars 2012Cardiac Pacemakers, Inc.System providing ventricular pacing and biventricular coordination
US823902115 juin 20107 août 2012Cardiac Pacemakers, Inc.Cardiac pacing system for prevention of ventricular fibrillation and ventricular tachycardia episode
US82497039 févr. 200721 août 2012Cardiac Pacemakers, Inc.Apparatus and method for ventricular rate regularization
US835578413 mai 201115 janv. 2013Medtronic, Inc.Dynamic representation of multipolar leads in a programmer interface
US839197420 déc. 20105 mars 2013Cardiac Pacemakers, Inc.Apparatus and method for pacing mode switching during atrial tachyarrhythmias
US839654928 avr. 200412 mars 2013Medtronic, Inc.Papillary muscle stimulation
US839656329 janv. 201012 mars 2013Medtronic, Inc.Clock synchronization in an implantable medical device system
US848382920 sept. 20129 juil. 2013Medtronic, Inc.Dynamic representation of multipolar leads in a programmer interface
US850416522 janv. 20136 août 2013Medtronic, Inc.Clock synchronization in an implantable medical device system
US850989327 oct. 201013 août 2013Medtronic, Inc.Supraventricular stimulation to control ventricular rate
US85122207 juin 200720 août 2013Cardiac Pacemakers, Inc.Rate smoothing control
US862042430 avr. 200731 déc. 2013Medtronic, Inc.Method and apparatus for providing extra systolic stimulation
US870622430 oct. 200722 avr. 2014Pacesetter, In.Systems and methods for paired/coupled pacing and dynamic overdrive/underdrive pacing
US871877021 oct. 20106 mai 2014Medtronic, Inc.Capture threshold measurement for selection of pacing vector
USRE37454 *24 oct. 199527 nov. 2001Medtronic, Inc.Cardiac pacemaker with hystersis behavior
DE2944636A1 *5 nov. 197914 mai 1980Medtronic IncImpulsgenerator fuer medizinische geraete
DE2944637A1 *5 nov. 197914 mai 1980Medtronic IncProgrammierbares medizinisches geraet
EP0178528A1 *1 oct. 198523 avr. 1986Telectronics N.V.Method for adjusting heart/pacer rate relative to right ventricular systolic pressure to obtain a required cardiac output
EP0215730A2 *17 sept. 198625 mars 1987BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro BerlinHeart stimulator
EP0222681A1 *17 sept. 198620 mai 1987BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro BerlinHeart pacemaker
EP0244446A1 *6 oct. 198611 nov. 1987Univ JeffersonMyocardial contractility-sensitive pacer.
EP0317065A2 *3 oct. 198824 mai 1989Todd J. CohenHemodynamically responsive system for treating a malfunctioning heart
EP2213729A227 oct. 20044 août 2010Fred ZacoutoInotropic orthorhythmic cardiac stimulator
WO1979000070A1 *25 juil. 197822 févr. 1979S JosephHeart stimulating apparatus
WO1986005698A1 *11 oct. 19859 oct. 1986Pacesetter SystStimulated heart interval measurement, adaptive pacer and method of operation
WO1992004076A1 *8 août 19911 mars 1992Vitatron Medical BvRate controlled pacemaker system using ar internal for rate control
WO2002053026A226 déc. 200111 juil. 2002Medtronic IncImplantable medical device for treating cardiac mechanical dysfunction by electrical stimulation
WO2002053228A127 déc. 200111 juil. 2002Medtronic IncImplantable medical device for monitoring congestive heart failure
WO2003020364A228 août 200213 mars 2003Medtronic IncImplantable medical device for treating cardiac mechanical dysfunction by electrical stimulation
WO2003037428A211 oct. 20028 mai 2003Medtronic IncImplantable medical device for monitoring cardiac blood pressure and chamber dimension
WO2005046790A227 oct. 200426 mai 2005Fred ZacoutoInotropic orthorythmic cardiac stimulator
WO2006115890A214 avr. 20062 nov. 2006Medtronic IncMulti-site pesp with fusion pacing
WO2006118713A128 mars 20069 nov. 2006Medtronic IncMeasurement of coronary sinus parameters to optimize left ventricular performance
WO2007038544A1 *26 sept. 20065 avr. 2007Medtronic IncTrans-septal anchoring system and method
Classifications
Classification aux États-Unis607/9, 607/23
Classification internationaleA61N1/05, A61N1/365
Classification coopérativeA61N1/365, A61N1/056
Classification européenneA61N1/365, A61N1/05N