|Número de publicación||US3614955 A|
|Tipo de publicación||Concesión|
|Fecha de publicación||26 Oct 1971|
|Fecha de presentación||9 Feb 1970|
|Fecha de prioridad||9 Feb 1970|
|También publicado como||CA981338A, CA981338A1|
|Número de publicación||US 3614955 A, US 3614955A, US-A-3614955, US3614955 A, US3614955A|
|Cesionario original||Medtronic Inc|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citada por (116), Clasificaciones (11)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
Oct. 26; 1971 M WROWSK. ETAL 3,614,955
STANDBY DEFIBRILLATOR AND METHOD OF OPERATION Filed Feb. 9, 1970 2 Sheets-Shoot 1 All m2;
HSVJJOA INVENTOR MIECZYSLAW MIROWSKI BY 5 0/ I a J 7 ATTORNEYS Oct. 26, M, M|ROWSK| ETAL 3,614,955
STANDBY DEFIBRILLATOR AND METHOD OF OPERATION Filed Feb. 9. 1970 2 Sheets-Shoot I! R I K I lllll IIWWV. llll m m WMQOEFOMJU OF P l m M \bh w A L S Y- Z c n E M BY /z i Z ATTORNEYS nited States 3,fil4,955 Patented Oct. 26, 1971 3,614,955 STANDBY DEFIBRILLATOR AND METHOD OF OPERATEON Mieczyslaw Mirowski, Baltimore, Md., assignor to Medtronic, Inc., Minneapolis, Minn. Filed Feb. 9, 1970, Ser. No. 9335 Int. Cl. A61n 1/34 U.S. Cl. 128-419 D 6 Claims ABSTRACT OF THE DISCLOSURE A method and means for automatically defibrillating a malfunctioning heart. With the present invention, the heart function is continuously monitored. When the function becomes abnormal, the malfunctioning heart is automatically shocked by a voltage of substantial size. If the heart does not return to its normal functions after a given interval, then it is again shocked. Normal heart activity ensures that the shocking mechanism remains inert.
BACKGROUND OF THE INVENTION During the past several decades, coronary heart disease has come to occupy the first position among the causes of death in the developed areas of the world. In the United States, for example, this disease is responsible for over one-half million deaths yearly. And of this number, more than half occur suddenly, outside the hospital, and therefore before the patient is able to obtain the necessary medical assistance. Although the precise cause of sudden death in coronary heart disease has not yet been entirely clarified, the available evidence permits the medical field to ascribe death in the majority of these cases to grave disturbances in cardiac electrical activity resulting in ventricular fibrillation.
Recent experience has clearly demonstrated that ventricular fibrillation and its frequent precursor, ventricular tachycardia, are reversible phenomena when prompt defibrillation of the heart is instituted. Under such circumstances, cardiac function can frequently be restored to normal without the patient suffering from residual disability. Unfortunately, however, the state of the art makes defibrillation very much dependent upon a highly specialized medical environment, thus limiting such treatment to elaborately equipped modern hospitals.
At the present, therefore, a great need exists for a defibrillator which could be carried by those who are prone to having one of the many life threatening arrhythmias generally discussed above. Thus, in some patients having coronary heart disease, a fatal outcome from ventricular tachycardia or ventricular fibrillation could be avoided, even in the absence of immediate medical assistance. The first step, of course, is the detection of those prone to suffering from cardiac malfunctions leading to ventricular tachycardia or ventricular fibrillation.
While it is not possible to predict with unerring exactness which patient suffering from coronary heart disease will be the victim of sudden death, several high risk groups of patients can be recognized. For example, patients who have experienced myocardial infarction, even though they may be surviving in good health, run a substantial risk of dying suddenly, a risk several times greater than that associated with the general population. Further, if patients with myocardial infarction have a history of serious ventricular arrhythmias and/or of cardiac arrest, or if evidence of persistent myocardial irritability is present, it may be logically assumed that the risk of sudden death is increased substantially. Patients like those described above would greatly benefit if an automatic, standby or demand defibrillator were available.
Also, such an automatic defibrillator would be an asset to those hospital patients Who have suifered myocardial infarction and who have been discharged from the wellequipped coronary care unit. Under such circumstances, the defibrillator could be implanted temporarily for the remainder of the expected hospital stay; or the defibrillator could be permanently implanted for use both in the hospital and after discharge. And another recognizable class of patients particularly in need of an automatic defibrillator is the class composed of those who have not shown prior histories of myocardial infarction but who show severe symptoms of coronary heart disease, such as ventricular arrhythmias resistant to medical treatment or angina pectoris.
From the brief discussion above, there should be little doubt that the possible applications for an automatic defibrillator are numerous. And, as previously noted, there is at present no known device which meets the need. It is toward filling this gap in medical instrumentation that the present invention is directed.
SUMMARY OF THE INVENTION The present invention relates to a standby defibrillator, an electronic system which, after detecting one of the above-noted life threatening arrhythmias, automatically defibrillates the heart of the user. The system of the present invention may be installed in patients particularly prone to develop ventricular tachycardia and/or ventricular fibrillation, either on a temporary or a permanent basis. And, because of its small size, the device of the present invention may be entirely implanted under the skin of the patient, or alternatively, may be carried externally, save for the sensing electrode and one shock-applying electrode.
More particularly, the present invention relates to a device for reliably sensing the differences between a properly functioning heart and one which has suddenly developed ventricular fibrillation, and which then delivers a defibrillating shock to the heart in fibrillation. The device is adapted to continue delivering intermittent shocks to the heart in the event that the heart fails to return to its normal behavior pattern, and has the ability of automatically regaining sensing control over a functional heart thereby ensuring that further shocks are inhibited after successful defibrillation has taken place.
The standby defibrillator of the present invention has as its basic element, a capacitor capable of storing electrical energy in an amount suflicient to depolarize the human heart (on the order of 50 joules). Upon discharge of this capacitor, a shock is delivered to the heart through two stimulating electrodes. One of these electrodes is positioned within the right ventricle, thereby forming the distal tip of an intracardiac catheter. This electrode is introduced through a peripheral vein. The second stimulating electrode is positioned either on the surface of the chest, or is sutured under the skin of the anterior chest wall or directly to the ventricular myocardium.
The capacitor is associated with a sensing circuit connected to the proximal end of the intracardiac catheter and is adapted to respond to a signal recorded at the dis tal end of the catheter. The signal sensed by the catheter must, of course, be inherently related to some distinctive characteristic of ventricular tachycardia or ventricular fibrillation; and in a specific embodiment of the present invention, the pressure in the right ventricle is sensed. When this pressure falls below a given value, on the order of 10 to 15 mm. Hg, the heart is malfunctioning and, therefore, the capacitor is discharged into the heart.
Between the sensing circuit and the capacitor, means are provided for delaying the repetition of depolarizing discharges for a preset period of time (on the order of 20 to 30 seconds). This delay is essential to give the heart the opportunity to convert spontaneously to a normal cardiac rhythm, and also to ensure that the abnormal heart conditions are, in fact, critical. Only in the absence of a successful conversion is a subsequent shock delivered to the heart. In a particular embodiment of the present invention, the time delay is brought about with the aid of a sawtooth generator, a relay and the charge time of the storage capacitor.
Accordingly, it is the main object of the present invention to provide a compact and automatic standby d..- fibrillator which lies dormant during normal heart activity but which applies a shock to the heart when the heart functions become abnormal.
It is another object of the present invention to provide a standby defibrillator which reliably senses the difference between a normally functioning heart and one that has suddenly developed abnormal function, and which then automatically delivers a defibrillating shock to the heart.
It is a further object of the present invention to provide a standby defibrillator which is capable of delivering multiple shocks in the event that the heart is not successfully cardioverted by the initial shock.
It is yet a further object of the invention to provide a standby defibrillator which automatically regains sensing control over a functioning heart, thereby inhibiting further shocks after successful defibrillation.
It is still another object of the invention to provide a device employing a heart-implanted catheter which may sense both for defibrillation and for pacing the heart if required.
It is still another object of the present invention to provide a standby defibrillator which is extremely compact and which is therefore totally implantable in the body of a patient.
It is still another object of the invention to provide a method of operating a standby defibrillator.
These and other objects of the invention, as well as many of the attendant advantages thereof, will become more readily apparent when reference is made to the following description taken in conjunction with the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a side view of the combination sensing probe and shock-applying probe forming a part of the present invention;
FIG. 2 illustrates a typical pressure curve for the right ventricle of a normally functioning heart;
FIG. 3 is a circuit schematic of the electronics comprising the standby defibrillator of the present invention; and
FIG. 4 is a graph of voltage versus time illustrating the operation of the sawtooth generator forming a part of the present invention.
DETAILED DESCRIPTION OF THE INVENTION With reference first to FIG. 1, the sensing and shock delivering probes will be described. The sensing probe is shown generally at and comprises a main body portion 12 and a pressure sensitive bulb 14. Electrical connections to the bulb 14 are made at junction box 16. One of the shock delivering probes is shown generally at 18 and comprises a main body portion 20, a first ring electrode 22 and a second ring electrode 24. As will be explained below, the electrodes 22 and 24 are short-circuited together during the operation of the device, forming a composite electrode shown at 26. The main body 12 of the sensing probe 10 is in the shape of a fiat ribbon, and the body of the bulb 14 is spherical. The shock delivering probe 18 is substantially cylindrical.
As noted previously, the combination sensing probe 10 and shock delivering probe 18 is, during operation, positioned in the right ventricle of the heart. These probes are introduced into the heart through a peripheral vein by means of surgery very similar to that involved in the implantation of a pacemaker probe.
The shock delivering electrodes are two in number. The first electrode is the composite electrode 26 and is carried by the shock delivering probe 18. The second electrode is shown at 28 and, in the preferred embodiment of this invention, is a flat plate either placed on the surface of the chest, sutured under the skin of the anterior chest wall or applied directly to the ventricular myocardium.
When the sensing probe 10 and the shock delivering probe 18 are inserted into the heart, the electrodes 22 and 24 are independent of one another. At this time, conventional pacemaking signals are applied between the electrodes 22 and 24. Since the heart responds favorably to the pacemaking signals only if the probe 18 is properly positioned, this method is suitable for checking the position of the probes 10 and 18. The probe location may, of course, be recognized by other methods such as, for example, fiuoroscopy or pressure recordings. Once it is determined that the probes 10 and 18 are properly located, they are secured in place and the pacemaking electronics are disconnected. Then, the electrodes 22 and 24 are externally short-circuited together, and the electronic circuit associated with the standby defibrillator of the present invention is then connected to the probes 10 and 18 and the electrode 28. If a pacemaking function is also to be carried out, the pacer electronics will remain connected and the step of shorting together the electrodes 22 and 24 will be eliminated.
With reference now to FIG. 2, there is illustrated a right ventricular pressure curve for a normally functioning heart. Pulses 30 and 32 are illustrated but, as is well known, these pulses repeat at the rate of approximately 60 to 70 per minute in a normally functioning heart. FIG. 2 clearly shows that each pulse has a peak and that these peaks rise above a preset pressure indicated by the dotted line 38. This dotted line corresponds to the threshold between a healthy heart and one which is in need of defibrillation. When the height of the peaks 34 and 36 fall below the pressure indicated by line 38, the malfunction is sensed by probe 10 which, as will be described immediately below, initiates the defibrillation of the heart.
With reference then to FIG. 3, the electronics associated with the standby defibrillator will be described. The electronic circuitry of FIG. 3 may conveniently be broken down into several component parts. The first part is a pressure transducer shown at 40, this pressure transducer being directly associated with the pressure sensing probe 10 shown in FIG. 1. The next state of the electronics is an amplifier shown at 42 and adapted to amplify the signals received from the pressure transducer 40. The amplified signal from the amplifier 42 is then passed to a sawtooth generator shown at 44, which generator, in turn feeds its output signal to the base of a transistor associated with the relay stage shown at 46. The relay 46 is normally in its open state condition but, when it is closed, a DC signal is impressed upon a DC/DC converter stage 48. The DC/DC converter 48 boosts the input voltage from approximately 15 volts to approximately 2,500 volts. The 2,500 volt DC signal from the converter 48 is then fed to a storage capacitor 70 which is associated with a firing circuit, the entire combination shown at 50. When the firing circuit 50 allows the capacitor 70 to discharge, the 2,500-volt signal is applied to the electrodes 26 and 28 illustrated in FIG. 1. Therefore, when the pressure sensing probe It) recognizes a malfunction in the heart, the capacitor, after a predetermined time delay, shocks the heart with approximately 2,500 volts. This voltage corresponds to approximately 50 joules of power, enough power to cause most hearts to defibrillate.
Still referring to FIG. 3, but in greater detail, the circuitry associated with the present invention functions as follows. The pressure transducer 40 takes the form of a resistive bridge, one resistor of which is defined by the pressure sensor 14 on the tip of the probe 10. The remaining legs in the bridge are defined by resistors housed in the junction box 16 shown in FIG. 1. The pressure trans ducer 40 is arranged so that the pressure sensed by element 14 is converted to an electrical signal, the amplitude of which is directly proportional to the pressure sensed by the element 14.
The output from the pressure transducer 40 is fed to a conventional amplifier 42 which amplifies the received pulses and which then feeds these amplified pulses to the sawtooth generator 44. The trimming potentiometer 52 seems to balance the inputs to the associated amplifier.
With reference now to FIGS. 2 through 4, the operation of the sawtooth generator 44 will be described. The sawtooth generator 44, if unafi'ected by the external environment, will have an output curve such as that shown at 54 in FIG. 4. However, if a signal is fed to the sawtooth generator, via lead 56, and if the signal is at least of a predeterminded amplitude, then the output voltage of the generator will immediately drop to zero and then again begin to climb. Therefore, if the sawtooth generator receives repetitious pulses of at least the predetermined voltage, then its output will be similar to that of curve 58 shown in FIG. 4.
If the heart functions sensed by the pressure transducer 40 are normal, following the curve shown in FIG. 2, then the amplified signal corresponding to a pulse in the right ventricular pressure will cause the output of the sawtooth generator 44 to drop to zero. The threshold signal reaching the generator via lead 56, can be adjusted by adjusting the amplification factor of the signal amplifier 42. This threshold is adjusted so that the generator 44 activates the relay 64 only after approximately six seconds of heart malfunction. If, then, the ventricular pressure falls lower than that value indicated by the dotted line 38, and so remains for the preset time interval, the amplified voltage reaching the generator 44, via lead 56, will be insuflicient to cause the generator output to drop to zero. Rather, the generator output will follow the curve shown at 54 in FIG. 4. Trimming potentiometer 60 is provided to balance the inputs to the associated amplifier.
The output from the sawtooth generator 44 is fed to the relay circuit 46. The relay contacts shown generally at 64 are initially set in the open-circuit condition, thereby isolating the 15-volt source from the D-C/DC converter 48. Further, the relay 64 is set to close only after the current passing through coil 66 reaches a predetermined value. With reference to FIG. 4, the voltage output of the sawtooth generator 44 must be at the level 68 before the current in the coil 66 is sufficient to switch the relay 64 into its closed-circuit state.
When the relay 64 closes, then the l5-volt source is connected directly to the DC/ DC converter 48. From FIGS. 2 through 4, it should be evident that approximately six seconds must elapse, with the heart continuously malfunctioning, before the relay 64 switches from its opencircuit mode to its closed-circuit mode. This will be apparent when one realizes that each tooth of the curve 58 corresponds to one peak of the right ventricular pressure curve and, as noted above, the peaks of the pressure curve repeat at approximately 60 to 70 per minute. Therefore, the heart pressure must be below the threshold level for approximately six seconds before input voltage is fed to the DC/ DC converter 48. If the heart returns to its normal function at any time during that Six seconds, then the sawtooth generator output response would drop to zero and the six second cycle would begin again.
With the relay 64 closed and a 15-volt DC signal being impressed upon the converter 48, an output of 2,500 volts appears at the output terminals of the converter 48. This voltage is fed directly to storage capacitor 70. Simultaneously, the 2,500-volt signal is fed to a resistive chain and finally to the base of transistor 72 via a neon tube 74. A silicon controlled rectifier (SCR) is triggered on when transistor 72 becomes conductive.
The operation of the firing circuit 50 is as follows: the 2,5 00-volt signal from the converter 48 is fed to the capacitor 70. When the capacitor 70 is fully charged, the transistor 72 becomes conductive, due to the now-conducting neon tube 74. The resistor chains and the tube 74 are interconnected in such a manner that when the voltage across the capacitor 70 reaches the full 2,500 volts, then the tube 74 becomes conductive. When the tube 74 conducts, so too does transistor 72 and, therefore, SCR 76. Then, the full 2,500 volts pass through electrodes 26 and 28 thus shocking the heart with a voltage sufiicient to cause defibrillation.
As above noted, it is important that a time period elapse between the detection of a heart malfunction and the delivery of the defibrillating shock to the heart. As also noted above, approximately six seconds of delay occur between the first detection of a malfunction and the closing of the relay 64. There is an additional delay, on the order of fifteen seconds, which is brought about by the charge time of the capacitor 70. That is, when the relay 64 closes, six seconds after the initial malfunction, the capacitor first begins to charge. The capacitor employed in the preferred embodiment charges in approximately fifteen seconds. Therefore, approximately twenty-one seconds elapse between the initial sensing of heart malfunction and the discharge of the capacitor into the heart. Naturally by varying the rise time of the sawtooth generator and the charge time of the capacitor, the twenty-one seconds may be enlarged or contracted as desired. And, as mentioned above, if at any time during the delay period the heart returns to normal, then the delay period automatically begins again.
Above, a specific embodiment of the present invention has been described. It should be understood, however, that this description is given for illustrative purposes only and that many alterations and modifications may be practiced without departing from the spirit and scope of the invention. Just as a few examples, it should be understood that while in the specific embodiment of the present invention, the pressure in the right ventricle is sensed as an indication of heart malfunction, other sensing arrangements may be practiced. Further, a single SCR is used as a triggering device. It is possible to substitute this device for a plurality of SCR units or, alternatively, with a vacuum relay. Still further, while the above description shows a single storage capacitor, a series of capacitors could be employed. It is, therefore, the intent that the present invention not be limited to the above but be limited only as defined in the appended claims.
What is claimed is:
1. A device for automatically cardioverting a malfunctioning heart, the device comprising: means for continually sensing the function of a heart; means associated with said sensing means for discriminating between normal heart function and abnormal heart function; means for storing electrical energy for cardioverting a malfunctioning heart; electrode means associated with said storage means for connecting the storage means directly to the heart; at least one of said electrode means adapted to be positioned within the heart; and means for automatically switching said storage means into a discharge state in response to an abnormal condition indication from said discriminating means whereby the stored energy is applied directly to the heart through said electrode means.
2. The device as set forth in claim 1, and further comprising: delay means for ensuring that a time delay exists between the sensing of the initial heart malfunction and the discharge of said storage means into the heart.
3. The device as set forth in claim 1, and further comprising: means for inhibiting the discharge of said storage means under conditions of normal heart activity.
4. The method of automatically sensing and cardioverting a malfunctioning heart, the method comprising the steps of: continually sensing the function of the heart; discriminating between normal heart function and abnormal heart function; automatically starting a cycle for shocking the heart, in response to the sensing of abnormal 7 heart function, shocking the heart to cause cardioversion; and positively inhibiting the heart shocking cycle under conditions of normal heart function.
5. A device for automatically cardioverting a malfunctioning heart, the device comprising: means for continually sensing the function of a heart; means associated with said sensing means for discriminating between normal heart function and abnormal heart function; means for storing electrical energy for cardioverting a malfunctioning heart; electrode means associated with said storage means for connecting the storage means directly to the heart; means for automatically switching said storage means into a discharge state whereby the stored energy is applied directly to the heart through said electrode means; delay means for ensuring that a time delay exists between the sensing of the initial heart malfunction and the discharge of said storage means into the heart; and means UNITED STATES PATENTS 3,135,264 6/1964 Tischler et al 1284l9 D 3,236,239 2/1966 Berkovits 128419 D 3,358,690 12/1967 Cohen l28419 D 3,481,341 12/1969 Siedband 1284l9 D WILLIAM E. KAMM, Primary Examiner US. Cl. X.R. l28-2.05 P, 2.06 A
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3738370 *||18 Ene 1971||12 Jun 1973||Charms B||Method of defibrillating a malfunctioning heart by means of electrodes located within the atrium|
|US3815611 *||26 Nov 1971||11 Jun 1974||Medtronic Inc||Muscle stimulation and/or contraction detection device|
|US4026302 *||30 Abr 1975||31 May 1977||Joseph Grayzel||Method of implanting a permanent pacemaker bipolar lead apparatus and an implantable permanent pacemaker bipolar lead apparatus|
|US4289134 *||23 Jul 1979||15 Sep 1981||Electro-Catheter Corporation||Tripolar catheter apparatus|
|US4440172 *||11 Dic 1980||3 Abr 1984||Mieczyslaw Mirowski||Apparatus for combining pacing and cardioverting functions in a single implanted device|
|US4475551 *||2 Sep 1982||9 Oct 1984||Mieczyslaw Mirowski||Arrhythmia detection and defibrillation system and method|
|US4574807 *||2 Mar 1984||11 Mar 1986||Carl Hewson||Method and apparatus for pacing the heart employing external and internal electrodes|
|US4683890 *||2 Oct 1986||4 Ago 1987||Brunswick Manufacturing Co., Inc.||Method and apparatus for controlled breathing employing internal and external electrodes|
|US4693253 *||23 Mar 1981||15 Sep 1987||Medtronic, Inc.||Automatic implantable defibrillator and pacer|
|US4708145 *||11 Sep 1985||24 Nov 1987||Medtronic, Inc.||Sequential-pulse, multiple pathway defibrillation method|
|US4768512 *||13 May 1986||6 Sep 1988||Mieczyslaw Mirowski||Cardioverting system and method with high-frequency pulse delivery|
|US4825871 *||18 May 1987||2 May 1989||Societe Anonyme Dite: Atesys||Defibrillating or cardioverting electric shock system including electrodes|
|US4834100 *||12 May 1986||30 May 1989||Charms Bernard L||Apparatus and method of defibrillation|
|US5083562 *||28 Ago 1990||28 Ene 1992||Telectronics Pacing Systems, Inc.||Method and apparatus for applying asymmetric biphasic truncated exponential countershocks|
|US5083563 *||16 Feb 1990||28 Ene 1992||Telectronics Pacing Systems, Inc.||Implantable automatic and haemodynamically responsive cardioverting/defibrillating pacemaker|
|US5105810 *||24 Jul 1990||21 Abr 1992||Telectronics Pacing Systems, Inc.||Implantable automatic and haemodynamically responsive cardioverting/defibrillating pacemaker with means for minimizing bradycardia support pacing voltages|
|US5156148 *||13 May 1991||20 Oct 1992||Leonard Bloom||System for treating a malfunctioning heart|
|US5184614 *||19 Oct 1990||9 Feb 1993||Telectronics Pacing Systems, Inc.||Implantable haemodynamically responsive cardioverting/defibrillating pacemaker|
|US5282837 *||12 Abr 1991||1 Feb 1994||Incontrol, Inc.||Atrial defibrillator and method|
|US5342403 *||9 Abr 1993||30 Ago 1994||Hewlett-Packard Corporation||Integrated defibrillator/monitor architecture with defibrillator-only fail-safe mode of operation|
|US5389069 *||17 Sep 1993||14 Feb 1995||Massachusetts Institute Of Technology||Method and apparatus for in vivo electroporation of remote cells and tissue|
|US5391187 *||22 Feb 1994||21 Feb 1995||Zmd Corporation||Semiautomatic defibrillator with heart rate alarm driven by shock advisory algorithm|
|US5409009 *||18 Mar 1994||25 Abr 1995||Medtronic, Inc.||Methods for measurement of arterial blood flow|
|US5433729 *||24 Mar 1992||18 Jul 1995||Incontrol, Inc.||Atrial defibrillator, lead systems, and method|
|US5507778 *||22 Feb 1994||16 Abr 1996||Zmd Corporation||Semiautomatic defibrillator with synchronized shock delivery|
|US5547467 *||23 Jul 1993||20 Ago 1996||Massachusettes Institute Of Technology||Method for rapid temporal control of molecular transport across tissue|
|US5667491 *||7 Jun 1995||16 Sep 1997||Massachusetts Institute Of Technology||Method for rapid temporal control of molecular transport across tissue|
|US5738105 *||24 Oct 1995||14 Abr 1998||Angeion Corporation||Method and apparatus for sensing R-waves using both near field and far field sensing simultaneously|
|US5749847 *||6 Jun 1995||12 May 1998||Massachusetts Institute Of Technology||Delivery of nucleotides into organisms by electroporation|
|US5911223 *||9 Ago 1996||15 Jun 1999||Massachusetts Institute Of Technology||Introduction of modifying agents into skin by electroporation|
|US5913887 *||27 Feb 1997||22 Jun 1999||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter including three coil electrodes|
|US5916238 *||4 Nov 1997||29 Jun 1999||Cardiac Pacemakers, Inc.||Implantable intravenous cardiac stimulation system with pulse generator housing serving as optional additional electrode|
|US5983131 *||9 Ago 1996||9 Nov 1999||Massachusetts Institute Of Technology||Apparatus and method for electroporation of tissue|
|US6041256 *||9 Jun 1999||21 Mar 2000||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter|
|US6085115 *||22 May 1998||4 Jul 2000||Massachusetts Institite Of Technology||Biopotential measurement including electroporation of tissue surface|
|US6085119 *||22 Jul 1998||4 Jul 2000||Cardiac Pacemakers, Inc.||Single pass endocardial lead for multi-site atrial pacing|
|US6152954 *||22 Jul 1998||28 Nov 2000||Cardiac Pacemakers, Inc.||Single pass lead having retractable, actively attached electrode for pacing and sensing|
|US6157860 *||28 Jun 1999||5 Dic 2000||Cardiac Pacemakers, Inc.||Implantable intravenous cardiac stimulation system with pulse generator housing serving as optional additional electrode|
|US6212434||22 Jul 1998||3 Abr 2001||Cardiac Pacemakers, Inc.||Single pass lead system|
|US6280462||12 Oct 2000||28 Ago 2001||Cardiac Pacemakers, Inc.||Implantable intravenous cardiac stimulation system with pulse generator housing serving as optional additional electrode|
|US6321122||22 Jul 1998||20 Nov 2001||Cardiac Pacemakers, Inc.||Single pass defibrillation/pacing lead with passively attached electrode for pacing and sensing|
|US6345204||14 Sep 2000||5 Feb 2002||Cardiac Pacemakers, Inc.||Single pass lead having retractable, actively attached electrode for pacing and sensing|
|US6438416||20 Mar 2000||20 Ago 2002||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter including three coil electrodes|
|US6463334||22 Jul 1999||8 Oct 2002||Cardiac Pacemakers, Inc.||Extendable and retractable lead|
|US6501990||23 Dic 1999||31 Dic 2002||Cardiac Pacemakers, Inc.||Extendable and retractable lead having a snap-fit terminal connector|
|US6501994||22 Jul 1998||31 Dic 2002||Cardiac Pacemakers, Inc.||High impedance electrode tip|
|US6505082||21 Ago 2000||7 Ene 2003||Cardiac Pacemakers, Inc.||Single pass lead system|
|US6741894||3 Dic 2001||25 May 2004||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter|
|US6915169||4 Oct 2002||5 Jul 2005||Cardiac Pacemakers, Inc.||Extendable and retractable lead having a snap-fit terminal connector|
|US6983185||31 Jul 2002||3 Ene 2006||Cardiac Pacemakers, Inc.||Lead with terminal connector assembly|
|US6999814||19 Jun 2001||14 Feb 2006||Cardiac Pacemakers, Inc.|
|US7239915||16 Nov 2004||3 Jul 2007||Medtronic, Inc.||Hemodynamic optimization system for biventricular implants|
|US7245973||23 Dic 2003||17 Jul 2007||Cardiac Pacemakers, Inc.||His bundle mapping, pacing, and injection lead|
|US7366574||5 Abr 2004||29 Abr 2008||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter|
|US7392095||1 Jul 2005||24 Jun 2008||Cardiac Pacemakers, Inc.||Extendable and retractable lead having a snap-fit terminal connector|
|US7522959||30 Dic 2004||21 Abr 2009||Cardiac Pacemakers, Inc.||Subcutaneous cardiac rhythm management|
|US7658196||25 Abr 2007||9 Feb 2010||Ethicon Endo-Surgery, Inc.||System and method for determining implanted device orientation|
|US7678071||10 Abr 2003||16 Mar 2010||Medtronic Minimed, Inc.||Microprocessor controlled ambulatory medical apparatus with hand held communication device|
|US7774934||8 Dic 2005||17 Ago 2010||Cardiac Pacemakers, Inc.||Method for making a terminal connector|
|US7775215||7 Mar 2006||17 Ago 2010||Ethicon Endo-Surgery, Inc.||System and method for determining implanted device positioning and obtaining pressure data|
|US7775966||7 Mar 2006||17 Ago 2010||Ethicon Endo-Surgery, Inc.||Non-invasive pressure measurement in a fluid adjustable restrictive device|
|US7831310 *||28 Jul 2004||9 Nov 2010||Medtronic Minimed, Inc.||Microprocessor controlled ambulatory medical apparatus with hand held communication device|
|US7844342||7 Feb 2008||30 Nov 2010||Ethicon Endo-Surgery, Inc.||Powering implantable restriction systems using light|
|US7927270||29 Ene 2007||19 Abr 2011||Ethicon Endo-Surgery, Inc.||External mechanical pressure sensor for gastric band pressure measurements|
|US8016744||7 Mar 2006||13 Sep 2011||Ethicon Endo-Surgery, Inc.||External pressure-based gastric band adjustment system and method|
|US8016745||6 Abr 2006||13 Sep 2011||Ethicon Endo-Surgery, Inc.||Monitoring of a food intake restriction device|
|US8034065||26 Feb 2008||11 Oct 2011||Ethicon Endo-Surgery, Inc.||Controlling pressure in adjustable restriction devices|
|US8057492||12 Feb 2008||15 Nov 2011||Ethicon Endo-Surgery, Inc.||Automatically adjusting band system with MEMS pump|
|US8066629||12 Feb 2007||29 Nov 2011||Ethicon Endo-Surgery, Inc.||Apparatus for adjustment and sensing of gastric band pressure|
|US8078287||8 Jun 2007||13 Dic 2011||Cardiac Pacemakers, Inc.||His bundle mapping, pacing, and injection lead|
|US8100870||14 Dic 2007||24 Ene 2012||Ethicon Endo-Surgery, Inc.||Adjustable height gastric restriction devices and methods|
|US8114345||8 Feb 2008||14 Feb 2012||Ethicon Endo-Surgery, Inc.||System and method of sterilizing an implantable medical device|
|US8142452||27 Dic 2007||27 Mar 2012||Ethicon Endo-Surgery, Inc.||Controlling pressure in adjustable restriction devices|
|US8152710||28 Feb 2008||10 Abr 2012||Ethicon Endo-Surgery, Inc.||Physiological parameter analysis for an implantable restriction device and a data logger|
|US8187162||6 Mar 2008||29 May 2012||Ethicon Endo-Surgery, Inc.||Reorientation port|
|US8187163||10 Dic 2007||29 May 2012||Ethicon Endo-Surgery, Inc.||Methods for implanting a gastric restriction device|
|US8192350||28 Ene 2008||5 Jun 2012||Ethicon Endo-Surgery, Inc.||Methods and devices for measuring impedance in a gastric restriction system|
|US8209035||23 Jun 2008||26 Jun 2012||Cardiac Pacemakers, Inc.||Extendable and retractable lead having a snap-fit terminal connector|
|US8221439||7 Feb 2008||17 Jul 2012||Ethicon Endo-Surgery, Inc.||Powering implantable restriction systems using kinetic motion|
|US8233995||6 Mar 2008||31 Jul 2012||Ethicon Endo-Surgery, Inc.||System and method of aligning an implantable antenna|
|US8285376||27 Mar 2009||9 Oct 2012||Cardiac Pacemakers, Inc.||Ventricular pacing|
|US8285398||7 Jul 2010||9 Oct 2012||Cardiac Pacemakers, Inc.||Lead with terminal connector assembly|
|US8290586||10 Oct 2008||16 Oct 2012||Cardiac Pacemakers, Inc.||Methods, devices and systems for single-chamber pacing using a dual-chamber pacing device|
|US8326423||26 Jun 2008||4 Dic 2012||Cardiac Pacemakers, Inc.||Devices and methods for steering electrical stimulation in cardiac rhythm management|
|US8337389||28 Ene 2008||25 Dic 2012||Ethicon Endo-Surgery, Inc.||Methods and devices for diagnosing performance of a gastric restriction system|
|US8346358||13 Dic 2005||1 Ene 2013||Cardiac Pacemakers, Inc.||Pacemaker which reestablishes or keeps the physiological electric conduction of the heart and a method of application|
|US8377079||27 Dic 2007||19 Feb 2013||Ethicon Endo-Surgery, Inc.||Constant force mechanisms for regulating restriction devices|
|US8423139||26 Jun 2008||16 Abr 2013||Cardiac Pacemakers, Inc.||Methods, devices and systems for cardiac rhythm management using an electrode arrangement|
|US8428715||10 Oct 2008||23 Abr 2013||Cardiac Pacemakers, Inc.||Methods for treating the physiological electric conduction of the heart|
|US8437848||10 Oct 2008||7 May 2013||Cardiac Pacemakers, Inc.||Apparatus for treating the physiological electric conduction of the heart|
|US8538521||25 Ago 2011||17 Sep 2013||Cardiac Pacemakers, Inc.||Systems, devices and methods for monitoring efficiency of pacing|
|US8543203||17 Ago 2011||24 Sep 2013||Cardiac Pacemakers, Inc.||Endocardial pacing devices and methods useful for resynchronization and defibrillation|
|US8565880||26 Abr 2011||22 Oct 2013||Cardiac Pacemakers, Inc.||His-bundle capture verification and monitoring|
|US8568356||2 Mar 2011||29 Oct 2013||Medtronic Minimed, Inc.||Ambulatory medical apparatus with hand held communication device|
|US8591395||28 Ene 2008||26 Nov 2013||Ethicon Endo-Surgery, Inc.||Gastric restriction device data handling devices and methods|
|US8591532||12 Feb 2008||26 Nov 2013||Ethicon Endo-Sugery, Inc.||Automatically adjusting band system|
|US8688234||18 Dic 2009||1 Abr 2014||Cardiac Pacemakers, Inc.||Devices, methods, and systems including cardiac pacing|
|US8812106||2 May 2013||19 Ago 2014||Cardiac Pacemakers, Inc.||Apparatus for treating the physiological electric conduction of the heart|
|US8825159||29 Nov 2012||2 Sep 2014||Cardiac Pacemakers, Inc.||Devices and methods for steering electrical stimulation in cardiac rhythm management|
|US8838238||4 Oct 2012||16 Sep 2014||Cardiac Pacemakers, Inc.||Ventricular pacing|
|US8870742||28 Feb 2008||28 Oct 2014||Ethicon Endo-Surgery, Inc.||GUI for an implantable restriction device and a data logger|
|US8880169||24 Ago 2011||4 Nov 2014||Cardiac Pacemakers, Inc.||Endocardial pacing relating to conduction abnormalities|
|US8903489||12 Oct 2012||2 Dic 2014||Cardiac Pacemakers, Inc.||Methods, devices and systems for single-chamber pacing using a dual-chamber pacing device|
|US8934969||16 Sep 2013||13 Ene 2015||Cardiac Pacemakers, Inc.||Systems, devices and methods for monitoring efficiency of pacing|
|US8969353||6 Nov 2009||3 Mar 2015||Massachusetts Institute Of Technology||Aminoalcohol lipidoids and uses thereof|
|US9006487||14 Jun 2006||14 Abr 2015||Massachusetts Institute Of Technology||Amine-containing lipids and uses thereof|
|US9008768||15 Abr 2013||14 Abr 2015||Cardiac Pacemakers, Inc.||Methods, devices and systems for cardiac rhythm management using an electrode arrangement|
|US9031648||17 Sep 2013||12 May 2015||Cardiac Pacemakers, Inc.||Endocardial pacing devices and methods useful for resynchronization and defibrillation|
|US9181321||17 Jun 2014||10 Nov 2015||Shire Human Genetic Therapies, Inc.||CFTR mRNA compositions and related methods and uses|
|US9193827||26 Ago 2011||24 Nov 2015||Massachusetts Institute Of Technology||Poly(beta-amino alcohols), their preparation, and uses thereof|
|US20030176933 *||10 Abr 2003||18 Sep 2003||Medtronic Minimed, Inc.||Microprocessor controlled ambulatory medical apparatus with hand held communication device|
|US20040193240 *||5 Abr 2004||30 Sep 2004||Cardiac Pacemakers, Inc.||Device for the transvenous cardioversion of atrial fibrillation or atrial flutter|
|US20050131469 *||16 Nov 2004||16 Jun 2005||Leonard Bloom||Hemodynamic optimization system for biventricular implants|
|US20070071685 *||21 Dic 2004||29 Mar 2007||Bracco Research S.A.||Gas-filled microvesicle assembly for contrast imaging|
|DE3914662A1 *||3 May 1989||8 Nov 1990||Alt Eckhard||Vorrichtung zum uebertragen elektrischer signale zwischen einem implantierbaren medizinischen geraet und elektrisch erregbarem menschlichen gewebe|
|EP0326290A1 *||19 Ene 1989||2 Ago 1989||Telectronics N.V.||Method and apparatus for applying asymmetric biphasic truncated exponential countershocks|
|Clasificación de EE.UU.||607/6|
|Clasificación internacional||A61B5/0215, A61B5/0275, A61B5/026, A61N1/39|
|Clasificación cooperativa||A61B5/0215, A61B5/0275, A61N1/3956|
|Clasificación europea||A61B5/0215, A61B5/0275, A61N1/39M|