WO1996022811A1 - Systeme de stockage d'energie a etages multiples pour defibrillateur implantable a synchronisation automatique - Google Patents
Systeme de stockage d'energie a etages multiples pour defibrillateur implantable a synchronisation automatique Download PDFInfo
- Publication number
- WO1996022811A1 WO1996022811A1 PCT/US1996/000763 US9600763W WO9622811A1 WO 1996022811 A1 WO1996022811 A1 WO 1996022811A1 US 9600763 W US9600763 W US 9600763W WO 9622811 A1 WO9622811 A1 WO 9622811A1
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- battery
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- energy
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- stage energy
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
- A61N1/39—Heart defibrillators
- A61N1/3956—Implantable devices for applying electric shocks to the heart, e.g. for cardioversion
-
- 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
- A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
- A61N1/39—Heart defibrillators
- A61N1/3906—Heart defibrillators characterised by the form of the shockwave
- A61N1/3912—Output circuitry therefor, e.g. switches
-
- 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
- A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
- A61N1/39—Heart defibrillators
- A61N1/3975—Power supply
Definitions
- This invention relates to the energy storage systems for implantable biomedical devices, and more particularly, to the energy storage systems for implantable cardioverter-defibrillators employing high voltage capacitive discharge outputs.
- Implantable biomedical devices typically do not have large current requirements so as to maximize the overall useful battery life and minimize the size of the battery required to power such devices.
- a good example of such a lower power biomedical device which utilizes only microwatts of power is a pacemaker. More recently, however, implantable biomedical devices have been developed which have higher power requirements, often in the milliwatts to watts range. Consequently, there has been a need to develop better energy storage systems for these devices.
- a good example of an implantable biomedical device which has a higher power output requirement is an implantable cardioverter- defibrillator.
- Cardiac defibrillation in humans using an implantable cardioverter-defibrillator requires the delivery of an electrical pulse that is several milliseconds long with peak currents as high as 25 amperes. The total energy in such a pulse can be as high as about 30 Joules.
- a high voltage defibrillation capacitor system is charged up to a voltage on the order of about 750 volts using a transformer powered by a low voltage battery. Once charged, the capacitor system is ten selectively discharged through at least a pair of implantable electrodes in the form of a defibrillation /cardioversion countershock.
- a staged energy storage system provides electrical energy to an implantable cardioverter-defibrillator device by using the combination of a first stage energy source and a second stage energy concentration system.
- the second stage energy concentration system allows for either a lower density and /or lower voltage energy source to be used as the first stage energy source, thereby decreasing the battery cost, size and weight, or, alternatively, for multiple closely spaced countershock pulses to be delivered.
- the second stage energy concentration system comprises a rechargeable battery.
- the second stage energy capacitor system comprises a high energy density capacitor system.
- a staged energy storage system for an implantable cardioverter-defibrillator.
- the implantable cardioverter-defibrillator is comprised of a biocompatible housing containing a sensing system for sensing cardiac dysrhythmias, a high voltage discharge capacitor system, a transformer and a control system for selectively charging the capacitor system and then discharging the capacitor system through a plurality of implantable electrodes in response to the sensing of a cardiac dysrhythmia.
- the staged energy storage system provides low-voltage energy to the transformer and is characterized in that the staged energy storage system includes: a first stage energy source means for providing a low-voltage electrical current; a second stage energy concentration means for storing the electrical current delivered from the first stage energy source means; and means for selectively discharging the electrical current in the second stage energy concentration means to the transformer as at least one short-term, low- voltage, high-current discharge of greater than 0.5 A.
- the first stage energy source means comprises a low-current battery having an output current of less than 10 mA
- the second stage energy source means is rechargeable so as to eliminate the need for a non-rechargeable, high-current battery.
- the first stage energy source means comprises a non-rechargeable, high current battery having an output current of at least 1A
- the second stage energy source means is rechargeable so as to allow for the delivery of multiple closely spaced electrical countershocks within one second of each other.
- Figure 1 is a simplified circuit diagram of a prior art implantable defibrillator circuit.
- Figure 2 is a simplified schematic circuit diagram of a staged energy concentration circuit.
- Figure 3 is a simplified schematic circuit diagram of an alternate embodiment staged energy concentration circuit.
- Figure 4 is a simplified schematic circuit diagram of an alternate embodiment staged energy concentration circuit.
- Figure 5 is a simplified schematic circuit diagram of a staged energy concentration circuit using a concentration capacitor system.
- Figure 6 is a schematic circuit diagram of a staged energy concentration system for delivery of a rapid pulse sequence.
- Figure 7 is a schematic circuit diagram of an alternate embodiment of a staged energy concentration system for delivery of a rapid pulse sequence.
- FIG. 1 is a simplified circuit diagram of a known implantable defibrillator circuit 10.
- Circuit 10 comprises a high current defibrillation battery 13, which is typically a low energy density lithium silver vanadium oxide (SVO) battery.
- a high voltage transformer 15 comprises a transistor switch 18 which drives the primary 21.
- the oscillator driving switch 18 provides an alternating current through the primary of transformer 15.
- the secondary 25 of transformer 15 produces a significantly higher voltage which is rectified by diode 27 and stored in high voltage defibrillation capacitor 30.
- the semiconductor switch 32 is activated to complete the circuit which delivers the charge of high voltage defibrillation capacitor 30 to the cardiac electrodes 35 for defibrillation or cardioversion of the heart.
- a configuration which is similar to the above circuit comprises substitution of a H-bridge in place of switch 32. This permits delivery of the current from high voltage defibrillation capacitor 30 in either polarity, which allows delivery of a biphasic pulse. It will be appreciated that numerous variations to the monitoring, control and capacitor configurations of circuit 10 are known in the art and are equally possible with the present invention, as shown for example in U.S. Patents Nos. 5,199,429, 5,306,291, 5,312,443, 5,334,219 and 5,372,605.
- circuit 10 works well in cardiac defibrillators; however, the SVO batteries have an energy storage density of only 500 joules per gram (J/g). This is due to the tradeoff between energy storage capability and current delivery capability.
- the battery chemistry of the well known Lithium Iodide (Lil) pacemaker battery has approximately twice the energy storage density of the SVO battery, or about 1000 J/g. This means that implantable defibrillator devices using a SVO battery are utilizing a battery with a mass that is twice the mass required if a Lil pacemaker battery were used.
- Circuit 40 comprises a first embodiment of an improved staged energy concentration means designed for replacing that portion of circuit 10 denoted as primary sub-circuit 42 in Figure 1.
- Circuit 40 preferably comprises a first stage of energy concentration comprising a non- rechargeable battery, such as a high energy density pacing battery 45, configured for applying a small microampere current to the trickle charge control circuitry 48.
- a second stage of energy concentration comprising either a rechargeable battery 50 as discussed in reference to Figure 2, or a low voltage, high energy density second stage concentration capacitor system 69 as discussed in reference to Figure 5.
- the rechargeable battery system preferably comprises a rechargeable defibrillator battery 50 that is maintained fully charged by the pacing battery 45.
- Rechargeable defibrillator battery 50 is used to drive primary 21 of the high voltage transformer, or similar power transfer means, through a switch 18 in a manner similar to conventional circuits, such as circuit 10.
- the staged energy concentration configuration of circuit 40 permits use of high density pacing batteries to store energy in combination with a very small rechargeable defibrillator battery to deliver a high current for somewhere between about 5 shocks. A typical defibrillator will deliver about 200 defibrillator shocks.
- Li-CFx battery capable of storing up 1600 J of energy per gram of battery mass may be used as the second stage system. Using such a battery, is possible to store the needed 8000 J of energy in a mass of only about 5 grams, along with the additional 1-2 crams of mass needed for the lower density rechargeable batterv.
- Table 1 A comparison of the characteristics of Li-CF X batteries relative to Lil batteries is presented below in Table 1.
- Pulse Amplitude (typical) 20 mA 100 ⁇ A
- the total mass of the staged energy storage system of the present invention including the mass of the first stage energy storage (8 grams) and the mass of the second stage energy concentrator (1-2 grams), is almost one-half the mass of a conventional single stage energy storage system (16 grams).
- the total mass of such a system would be on the order of 7 grams, including 5 grams for the Li-CFx battery, and 1-2 grams for the second stage concentrator, resulting in a savings of over half of the mass of current systems.
- the second stage of energy concentration is relatively small, always less than 1000 J and typically less than 500 J, the second stage must be able to deliver a fairly high current of at least 0.5 A, and preferably about 1-2 A.
- Representative rechargeable battery chemistries having single battery cells that are capable of meeting these specifications for high current delivery are shown in Table 2.
- FIG. 3 discloses another embodiment of the staged energy concentration invention.
- Circuit 60 discloses a single cell pacing batter y 63 which is used to power a voltage doubler circuit 67.
- This doubler circuit 67 which comprises numerous embodiments as described, for example, in 5,372,605, may be configured to produce an output of approximately 6 volts for charging a rechargeable defibrillation battery, such as battery 70.
- FIG 4 Another embodiment of a staged energy concentration defibrillator circuit is shown in Figure 4, in which circuit 76 comprises first stage battery 80.
- Battery 80 is a low voltage, for example a 2.8 volt, Lil single cell battery which charges two second stage batteries 83 and 84.
- Batteries 83, 84 are preferably Lithium Titanium Disulfide (LiTiS ) batteries.
- battery 84 is charged through diode 86
- battery 83 is charged through diode 87
- resistor 89 is used with a preferred value of 10K ohms.
- Field effect transistor switch 92 is off during this time. It is recognized that this schematic circuit is further simplified because there is optimal trickle charge current limiting between battery 80 and the two diodes 86, 87, however, that detail is not considered important to this depiction of the invention.
- a multi-stage energy storage system provides great savings in both volume and weight of an implantable biomedical device.
- the existing defibrillator battery chemistry has about half the density of the pacing battery, it is possible to reduce the total battery weight of an implantable cardioverter-defibrillator by greater than about 50'!.) by allowing tor the use of a higher energy density battery as the primary energy storage system and relying on the second stage energy concentration as taught by the present invention to actually charge the defibrillation capacitors of the implantable cardioverter-defibrillator.
- This provides dramatic improvement in the manufacture, implantation, and operation of the defibrillator, particularly in view of the restricted size of desired pectoral implant sites.
- a low voltage, high energy density second stage concentration capacitor system 69 is used in place of rechargeable defibrillation battery 50 as shown in Figure 2.
- Second stage concentration capacitor system 69 is used to drive the primary coil 21 of high voltage transformer 15 through the use of oscillator driven switch 18.
- the secondary side 25 of high voltage transformer 15 charges defibrillation capacitor 30 through the rectifying diode 27.
- the remaining portion of circuit 40 operates in a manner similar to circuit 10 as described in Figure 1.
- a trickle charge control circuit 48 controls the charging of concentrations capacitor system 69 from non-rechargeable battery 45.
- Trickle charge control circuit 48 is of conventional design and may include a voltage step-up feature as described for example, in U.S. Patent No. 5,372,605.
- the voltage step-up feature is preferably included to counteract a decrease in the efficiency of high voltage transformer 15 at lower voltages as concentration capacitor system 69 discharges.
- non-rechargeable battery 45 is a 2.2 V Lil batter ⁇ '
- trickle charge control circuit 48 would include a 5x1 voltage step-up to yield a total of 11 V across concentration capacitor system 69.
- concentration capacitor system 69 75% of the energy transfer from concentration capacitor system 69 to high voltage transformer 15 will occur at a voltage of 5.5 V or higher.
- a single SVO 3.0 V cell could be used with a 4x1 voltage step-up, for example.
- the resulting energy storage system would have more total stored energy (8000 J), but would take several hours to fully recharge concentration capacitor system 69 after delivery of a complete set of countershocks.
- the resulting energy storage system would have less total stored energy (4000 J), but would be able to quickly recharge concentration capacitor system 69 in less than a minute.
- the concentration capacitor system 69 would serve as buffer to maintain optimum transfer characteristics across high voltage transformer 15, the later example would have the significant advantage of saving the cost of a second SVO cell, as compared to energy storage systems for existing implantable cardioverter-defibrillators.
- concentration capacitor system 69 would be used together with the SVO battery and the 4x1 voltage step up to jointly produce the voltage across primary coil 21 of high voltage transformer 15. It would be possible, for example, to make a single cell SVO battery arrangement more efficient if, instead of trying to take all 30 J from the SVO cell, 15 J was taken from the SVO cell through the step up circuit and the other 15 J was taken from 30 J stored in two dual layer capacitors. Total net energy requirements for such a system would be 8 grams for the SVO cell and 4 grams for the dual layer caps occupying only an additional 3 cc.
- Second stage concentration capacitor system 69 is preferably comprised of one or more double layer capacitors having no permanent dielectric, although it would be possible to use an electrolytic capacitor, provided the electrolytic capacitor had a sufficient energy density rating.
- Currently available capacitor technology is capable of producing a double layer capacitor with a maximum voltage rating of 11 volts and a maximum energy density of around 10.7 J/cc.
- a double layer capacitor is the Panasonic SG.
- Other possible dual layer capacitors useful with the present invention include the Ruthenium Oxide (RO) dual layer capacitor developed by Pinnacle Research Co.
- RO Ruthenium Oxide
- New manufacturing technologies and materials are being introduced for double layer capacitors which have the potential to increase the capacitance and voltage ratings of these devices. These improvements involve new materials with increased surface areas (which directly relates to capacitance), and new manufacturing techniques to reduce the space between the plates which decreases both the overall resistance and the overall size of the capacitor.
- the implantable cardioverter-defibrillator must be capable of delivering 5 countershocks, each of 30J.
- E de ⁇ is the desired maximum energy to be delivered by a countershock
- L tran is the 1 /transformer efficiency
- L] ac i is 1/loss due to load matching
- N is the desired number of countershocks in a therapy regimen.
- n ( 2 * E de i ) / ( C * V2 ) (6)
- n ( 2 * N * E d ,, ) / ( L tt , ⁇ n * L 1(llld * C * V2 ) (7)
- the minimum number (n) of such dual layer capacitors required would be 27. While this large number of capacitors for existing dual layer capacitors does not make such an arrangement a particularly attractive alternative to energy supply systems for existing implantable devices, there are other arrangements which do make the concentration capacitor system 69 an attractive alternative. For example, when a SVO battery is used, the number of countershocks in a therapy regimen can be reduced to 1 because the battery can recharge concentration capacitor system 69 between countershocks. As such, the total number of such capacitors required would be only 6, a realistic tradeoff even with existing dual layer capacitor technology to reduce the cost of the implantable device.
- An excellent example of a potential use of the staged energy concentration power supply system of the present invention is for a prophylactic implantable cardioverter-defibrillator similar to that described in U.S. Patent No. 5,439,482.
- a prophylactic implantable defibrillator with a total energy budget of 4000 J could be provided with a three-shock therapy regimen for a budgeted number of 50 regimen cycles, each of the countershocks in a therapy regimen cycle having a maximum delivered energy of 10 J, 10 J and 20 J, respectively.
- the total energy required to be stored in concentration capacitor system 69 would be about 105 J, an energy level which can be achieved by 7 individual dual layer capacitors utilizing existing capacitor technology, that together would occupy about 9.75 cc and weigh about 14 grams.
- the overall volume of the energy storage system for this prophylactic defibrillator (total volume ⁇ 13 cc) is somewhat less than existing volumes of 16 cc for dual cell SVO battery systems, and the mass (total mass ⁇ 18 grams) is almost one-half of the mass for a 32 gram dual cell SVO battery system.
- the cost of such an energy storage system for an implantable device will decrease from almost $1000 to less than $50.
- staged energy concentration power supply system of the present invention is for the delivery of multiple closely spaced countershock pulses.
- Current medically accepted practice requires a minimum amount of energy for each countershock pulse delivered by a implantable cardioverter- defibrillators on the order of about 20-30 Joules.
- electrical countershocks consisting of multiple pulse waveforms delivered closely together have been proposed which would likely lower the total defibrillation threshold by about 50 percent, cutting the 30 Joule accepted limit to about 15 Joules per pulse.
- such a system requires multiple sizeable main energy delivery capacitors.
- the present invention teaches means for overcoming the impediments of such theoretical multiple pulse systems.
- the invention also discloses novel means for providing a rapid pulse power system for use with conventional ICD circuits to permit optional prompt transition from a widely spaced defibrillation pulse sequence to a closely spaced defibrillation pulse sequence.
- the energy generation problem is appreciated more fully by calculating the charging power required of a representative main energy delivery capacitor system in an ICD device. Assuming a conventional single pulse defibrillator which is designed to deliver a 30 Joule pulse, a 10 second delay for capacitor charging is considered acceptable after fibrillation is detected.
- the charging power is described by simple calculation of 30 Joules divided by 10 seconds, which yields 3 watts. This 3 watt level of power is available from high quality defibrillation primary cells, such as lithium silver vanadium pentoxide cells, although others may be suitable.
- the main energy delivery capacitor could be designed to store only 15 Joules and could be made of only half the size of present capacitors.
- the main energy delivery capacitor has 10 seconds to charge in order to create the first pulse by use of present circuitry, the main energy delivery capacitor then must be quickly recharged to provide the second pulse.
- the amount of time required to quickly recharge is the same time as that required for optimum spacing between the two pulses, which is about 0.25 seconds. Therefore, the charging power must be equal to 15 Joules divided by 0.25 seconds. This requires a 60 watt power source.
- there is no functional implantable battery which is capable of providing such power output.
- Figure 6 discloses the essential circuit elements of one embodiment of the present invention in which circuit 167 uses both a primary battery and an intermediate power intensifying system, with the latter comprising a very high power output system to provide the high charging power between capacitor pulses which can be either a power intensify battery or a power intensifying capacitor system.
- battery 170 is a low amperage primary defibrillation cell, which is preferably a lithium silver vanadium pentoxide type, although other materials are feasible.
- battery 170 is used to quickly charge a intermediate power intensifying system 174 which is capable of very high power output. This is preferably accomplished through the use of transistor switch 176.
- Power intensifying system 174 is preferably selected from a list of possible high power, rechargeable batteries, such as lithium titanium disulfide, lithium sulfur dioxide, or other suitable for producing the desired power in a rechargeable configuration, or from a list of possible high energy density capacitors, such as dual layer capacitors.
- the capacitors are preferably comprised of one or more double layer capacitors having no permanent dielectric.
- Currently available capacitor technology is capable of producing a double layer capacitor with a maximum voltage rating of 11 volts and a maximum energy density of around 10.7 J/cc.
- Examples of such a double layer capacitor are the Panasonic SG and NEC FE capacitors.
- Other possible dual layer capacitors useful with the present invention include the Ruthenium Oxide (RO) dual layer capacitor developed by Pinnacle Research Co.
- RO Ruthenium Oxide
- New manufacturing technologies and materials are being introduced for double layer capacitors which have the potential to increase the capacitance and voltage ratings of these devices. These improvements involve new materials with increased surface areas (which directly relates to capacitance), and new manufacturing techniques to reduce the space between the plates which decreases both the overall resistance and the overall size of the power intensifying capacitor.
- Low impedance dual layer capacitors for example, are the subject of intensive research and development in providing power supply systems for electrical cars and the advantages gained in that area could be applied to create a custom made optimized device for use in connection with the present invention.
- the critical value of the dual layer capacitor system is the power transfer capability of the system.
- power intensifying system 174 In order to deliver the second 10 1 "half" of a total 20 J countershock, for example, power intensifying system 174 must be capable of transferring 13.3 J to the primary coil 121 of transformer 115 within less than 250 ms, assuming that the transformer has a 75% transfer efficiency. With these time and energy constraints, the power required of power intensifying system 174 is equal to:
- the NEC FE dual layer capacitor for example, has ratings of
- a preferred dual layer capacitor system ideally suitable for use with the present invention would consist of a dual layer capacitor having ratings of:
- the difference between the capacitor charging circuitry of Figure 6 and Figure 1 is an approximately 18:1 - 20:1 charging power ratio of 54 - 60 watts rather than 3 watts.
- the charging circuitry shown as schematic circuit 167 provides power means for recharging the capacitor of the related ICD device, after an initial discharge, between subsequent multiple pulses. This eliminates the need for additional main energy delivery capacitors and eliminates about half of the capacitor volume of known ICD devices. The invention also results in significant improvement in size and operation of an ICD device.
- circuit 190 also comprises high power output (approximately 1-3 amperes) intermediate power concentration system 197.
- a preferred power intensify system 197 would comprise a rechargeable battery, such as lithium titanium di-sulfide battery or other lithium batteries, alkaline batteries, NiCad batteries or lead acid batteries, or a conventional high impedance dual layer capacitor.
- Power intensifying system 101 comprises a very high amperage (10-30 amps) battery, or a high power, low impedance dual layer capacitor.
- circuit 190 allows continuous trickle charge from battery 193 to power concentration system 197. This maintains power concentration system 197 in a substantially fully charged configuration until detection of fibrillation. After detection of fibrillation, power concentration system 197 simultaneously charges the main energy delivery capacitor 132 within sub- section 182 and power intensifying system 101, via switch 105.
- Capacitor 132 then discharges and is again re-charged with power concentration system 197.
- power concentration system 197 is not normally able to fully charge capacitor 132 in less than at least about 5 seconds.
- circuit 190 eiiscloses use of power intensifying system 101 to provide high amperage high power means for charging a main energy delivery capacitor for countershock pulses after the initial countershock/pulse.
Abstract
Un système (40) de stockage d'énergie à étages multiples alimente en énergie électrique un défibrillateur implantable à synchronisation automatique au moyen d'un premier étage qui comprend une source d'énergie (45), associé à un deuxième étage qui comprend un système de concentration d'énergie (50). Le système (50) de concentration d'énergie du deuxième étage permet d'utiliser une source d'énergie de basse densité et/ou de basse tension comme source d'énergie (45) du premier étage, et permet donc de réduire le coût, les dimensions et le poids de la batterie ou permet d'appliquer des impulsions de contrechoc multiples et rapprochées. Dans un mode de réalisation, le système de concentration d'énergie (50) du deuxième étage comprend une batterie rechargeable (50). Dans un autre mode de réalisation, le système condensateur d'énergie (50) du deuxième étage comprend un système condensateur d'énergie de haute densité.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP96903577A EP0751805A4 (fr) | 1995-01-23 | 1996-01-19 | Systeme de stockage d'energie a etages multiples pour defibrillateur implantable a synchronisation automatique |
Applications Claiming Priority (6)
Application Number | Priority Date | Filing Date | Title |
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US37737595A | 1995-01-23 | 1995-01-23 | |
US08/377,375 | 1995-01-23 | ||
US08/376,353 | 1995-01-23 | ||
US08/376,353 US5620464A (en) | 1992-12-18 | 1995-01-23 | System and method for delivering multiple closely spaced defibrillation pulses |
US08/486,760 | 1995-06-07 | ||
US08/486,760 US5674248A (en) | 1995-01-23 | 1995-06-07 | Staged energy concentration for an implantable biomedical device |
Publications (1)
Publication Number | Publication Date |
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WO1996022811A1 true WO1996022811A1 (fr) | 1996-08-01 |
Family
ID=27409294
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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PCT/US1996/000763 WO1996022811A1 (fr) | 1995-01-23 | 1996-01-19 | Systeme de stockage d'energie a etages multiples pour defibrillateur implantable a synchronisation automatique |
Country Status (2)
Country | Link |
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EP (1) | EP0751805A4 (fr) |
WO (1) | WO1996022811A1 (fr) |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
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DE10016520A1 (de) * | 2000-04-03 | 2001-10-11 | Implex Hear Tech Ag | Implantierbare Energiespeicheranordnung für ein medizinisches Implantat sowie Betriebsverfahren dafür |
WO2003035175A1 (fr) * | 2001-10-26 | 2003-05-01 | Medtronic Physio-Control Corp. | Source d'alimentation de defibrillateur dotee de blocs d'alimentation remplaçables et rechargeables |
WO2002074387A3 (fr) * | 2001-03-20 | 2003-05-22 | Koninkl Philips Electronics Nv | Defibrillateur utilisant un condensateur a double couche, a capacitance elevee et a faible impedance |
US6873133B1 (en) | 2002-09-11 | 2005-03-29 | Medtronic Physio-Control Manufacturing Corporation | Defibrillator with a reconfigurable battery module |
US6909915B2 (en) | 2003-01-24 | 2005-06-21 | Gentcorp Ltd. | Hybrid battery power source for implantable medical use |
US6931278B1 (en) | 2002-12-06 | 2005-08-16 | Pacesetter, Inc. | Implantable cardioverter defibrillator having fast action operation |
US7020519B2 (en) | 2003-01-24 | 2006-03-28 | Gentcorp Ltd | Hybrid battery power source for implantable medical use |
US7079893B2 (en) | 2003-01-24 | 2006-07-18 | Gentcorp Ltd. | Hybrid battery power source for implantable medical use |
US7203547B1 (en) | 2004-01-20 | 2007-04-10 | Pacesetter, Inc. | System and method of implementing a prophylactic pacer/defibrillator |
US7203546B1 (en) | 2004-01-20 | 2007-04-10 | Pacesetter, Inc. | System and method of implementing a prophylactic pacer/defibrillator |
US7616995B2 (en) | 2006-04-28 | 2009-11-10 | Medtronic, Inc. | Variable recharge determination for an implantable medical device and method therefore |
CN113713260A (zh) * | 2021-07-26 | 2021-11-30 | 上海健康医学院 | 超短脉冲除颤器 |
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1996
- 1996-01-19 WO PCT/US1996/000763 patent/WO1996022811A1/fr not_active Application Discontinuation
- 1996-01-19 EP EP96903577A patent/EP0751805A4/fr not_active Withdrawn
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US5383907A (en) * | 1992-12-18 | 1995-01-24 | Angeion Corporation | System and method for delivering multiple closely spaced defibrillation pulses |
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Cited By (17)
Publication number | Priority date | Publication date | Assignee | Title |
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DE10016520A1 (de) * | 2000-04-03 | 2001-10-11 | Implex Hear Tech Ag | Implantierbare Energiespeicheranordnung für ein medizinisches Implantat sowie Betriebsverfahren dafür |
WO2002074387A3 (fr) * | 2001-03-20 | 2003-05-22 | Koninkl Philips Electronics Nv | Defibrillateur utilisant un condensateur a double couche, a capacitance elevee et a faible impedance |
US6580945B2 (en) | 2001-03-20 | 2003-06-17 | Koninklijke Philips Electronics N.V. | Defibrillator using low impedance high capacitance double layer capacitor |
WO2003035175A1 (fr) * | 2001-10-26 | 2003-05-01 | Medtronic Physio-Control Corp. | Source d'alimentation de defibrillateur dotee de blocs d'alimentation remplaçables et rechargeables |
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US7095210B2 (en) | 2001-10-26 | 2006-08-22 | Medtronic Emergency Response Systems, Inc. | Defibrillator power source with replaceable and rechargeable power packs |
US6873133B1 (en) | 2002-09-11 | 2005-03-29 | Medtronic Physio-Control Manufacturing Corporation | Defibrillator with a reconfigurable battery module |
US6931278B1 (en) | 2002-12-06 | 2005-08-16 | Pacesetter, Inc. | Implantable cardioverter defibrillator having fast action operation |
US7020519B2 (en) | 2003-01-24 | 2006-03-28 | Gentcorp Ltd | Hybrid battery power source for implantable medical use |
US7079893B2 (en) | 2003-01-24 | 2006-07-18 | Gentcorp Ltd. | Hybrid battery power source for implantable medical use |
US6909915B2 (en) | 2003-01-24 | 2005-06-21 | Gentcorp Ltd. | Hybrid battery power source for implantable medical use |
US7136701B2 (en) | 2003-01-24 | 2006-11-14 | Gentcorp Ltd. | Hybrid battery power source for implantable medical use |
AU2004207413B2 (en) * | 2003-01-24 | 2007-01-04 | Gentcorp Ltd. | Improved hybrid battery power source for implantable medical device |
US7203547B1 (en) | 2004-01-20 | 2007-04-10 | Pacesetter, Inc. | System and method of implementing a prophylactic pacer/defibrillator |
US7203546B1 (en) | 2004-01-20 | 2007-04-10 | Pacesetter, Inc. | System and method of implementing a prophylactic pacer/defibrillator |
US7616995B2 (en) | 2006-04-28 | 2009-11-10 | Medtronic, Inc. | Variable recharge determination for an implantable medical device and method therefore |
CN113713260A (zh) * | 2021-07-26 | 2021-11-30 | 上海健康医学院 | 超短脉冲除颤器 |
Also Published As
Publication number | Publication date |
---|---|
EP0751805A4 (fr) | 1998-11-11 |
EP0751805A1 (fr) | 1997-01-08 |
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