WO2010067373A2 - Chargeur pour défibrillateur - Google Patents

Chargeur pour défibrillateur Download PDF

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Publication number
WO2010067373A2
WO2010067373A2 PCT/IL2009/001186 IL2009001186W WO2010067373A2 WO 2010067373 A2 WO2010067373 A2 WO 2010067373A2 IL 2009001186 W IL2009001186 W IL 2009001186W WO 2010067373 A2 WO2010067373 A2 WO 2010067373A2
Authority
WO
WIPO (PCT)
Prior art keywords
defibrillator
charging circuit
flyback
charging
phases
Prior art date
Application number
PCT/IL2009/001186
Other languages
English (en)
Other versions
WO2010067373A3 (fr
Inventor
Miki Raviv
Original Assignee
Poems Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Poems Ltd. filed Critical Poems Ltd.
Publication of WO2010067373A2 publication Critical patent/WO2010067373A2/fr
Publication of WO2010067373A3 publication Critical patent/WO2010067373A3/fr

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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
    • A61N1/3904—External heart defibrillators [EHD]
    • 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
    • A61N1/3968—Constructional arrangements, e.g. casings
    • 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
    • A61N1/3981—High voltage charging circuitry
    • 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
    • A61N1/3993—User interfaces for automatic external defibrillators

Definitions

  • the present invention relates to defibrillators and defibrillating systems in general and to defibrillators and defibrillating systems comprising an efficient charger to energize the defibrillator prior to delivering electrical energy to a patient in particular, as well as to other applications of such an efficient charger for portable devices.
  • SCA Sudden cardiac arrest
  • SCA typically results from a disruption in the heart's electrical activity. During SCA the heart generally stops beating and blood circulation is interrupted. If help is not received in time this condition may leave the brain and other vital organs without sufficient oxygen, which may result in their permanent damage, and in most cases, death.
  • VT and VF are attributed to faults in the electrical activity of the heart, which interferes with the normal rhythmic contraction of the heart. Such interferences are generally known as arrhythmia.
  • VT is an arrhythmic condition in which the heart suddenly beats at relatively high rates, usually in the range of 100 - 200 beats per minute.
  • VF is an arrhythmic condition in which the ventricles of the heart flutter, contracting in a rapid, unsynchronized manner. When this occurs the heart stops pumping blood.
  • a pulse-less VT and VF recognition are used as criteria to determine whether the heart's electrophysiological state is reversible by applying electrical energy.
  • Restoring normal functioning of an arrhythmic heart is usually done by stimulating the heart, either by electrical means using a defibrillator, and/or by mechanical means using CPR (cardio-pulmonary resuscitation).
  • a defibrillator is adapted to provide electrical energy or stimulus to the heart generally in an attempt to restore normal electrical activity in the heart.
  • CPR comprises chest compression - ventilations technique that is generally adapted to assist the heart in delivering blood to the coronary arteries and to the brain.
  • Defibrillators typically comprise two types of devices, internal defibrillators and external defibrillators.
  • Internal defibrillators are implanted directly in a person's body much like a pacemaker, and are often in direct contact with the heart.
  • They are designed to actively monitor heart activity and to apply an electrical stimulus to the heart following detection of a condition associated with VF.
  • External defibrillators are electronic devices typically comprising a unit from which extend two electrical leads with an electrode at the end of each cable.
  • the electrodes usually comprise a metal paddle with an insulated handle, or optionally, removable attachable, self adhered defibrillation pads, which are placed on the victim's thorax prior to administering defibrillation.
  • An automatic external defibrillator is typically used to administer defibrillation to out-of-hospital victims suffering from SCA.
  • AEDs are generally, but not necessarily, designed for use by untrained personnel, referred to hereinafter as a "rescuer” or “caregiver” possessing no prior experience using defibrillators.
  • the caregiver is only required to connect the defibrillation pads (also referred to as the: “defibrillator electrodes", “electrode” or “electrodes”) to the victim and to activate the AED, whereas, the other functions are generally pre- programmed into the device.
  • AEDs today are adapted to monitor the electrical activity of the heart and to automatically administer the electrical stimulus when abnormal electrical activity is detected. Optionally, they are adapted to prevent administering the electrical stimulus if normal electrical activity is detected.
  • AED's One of the greatest advantages of AED' s is the fact that it is made available to the greater public in non clinical and public setting such as shopping malls, airports or the like.
  • the public availability of AED's is a great asset to the greater public as SCA can occur anywhere, in uncontrolled, non clinical settings. In such settings the AED can serve as the initial and sometimes the most crucial form of initial emergency care.
  • the AED In order to make the AED readily available to the public it must be able to function in a non clinical setting, without medical personnel intervention, be user friendly to an untrained layperson, small, mobile and perhaps most importantly be operational in the shortest period of time.
  • the mobility of an AED is depicted by many factors including its size and weight. Both of these factors are generally dependent on the type of power supply used. Mobility is generally achieved by using rechargeable batteries however their size and weight are limiting in terms of their electrical output. Specifically a battery's size is directly proportional to its electrical output where a large battery provides higher electrical energy output than would a smaller sized battery. Furthermore, the energy required to energize or charge a defibrillator is large therefore a problem exist in optimizing the battery size with the energy required to energize the AED to become operational.
  • defibrillator comprising optimized and efficient capacitor charging mechanism by readily controlling the output of the defibrillator power supply.
  • the present invention overcomes the deficiencies of the background by providing an optimized and efficient power source utilization charging circuit most preferably able to generate sufficient electrical energy to charge a defibrillator's capacitor in an efficient and optimized manner.
  • such optimized and efficient provision of power and of the charging circuit may lead to reduced capacitor charging time by, for example, at least about 50% of the charging time of current state of the art defibrillators, without wishing to be limited in any way.
  • Optimized charging provides a defibrillator that may be quickly and efficiently recharged rendering it fully operational far more rapidly than for current state of the art defibrillators.
  • the defibrillator according to the present invention is more readily available to treat a person experiencing heart failure.
  • An embodiment of the present invention provides for an efficient and optimized power supply charging circuit able to efficiently charge the defibrillator's capacitor.
  • the optimized charging circuit according to an embodiment of the present invention comprises a multiphase flyback topology, with a plurality of phases, optimizing and reducing current stress on the defibrillator power supply.
  • the flyback topology features three phases.
  • the defibrillator power supply for example includes but is not limited to a mains power supply or a battery or the like power source.
  • the efficient and optimized charging circuitry provides a boost to the battery's low DC input voltage, thus providing a defibrillator capacitor with a required sufficiently high voltage level to allow a caregiver to defibrillate a patient.
  • capacitor as used herein includes a single capacitor, a plurality of capacitors or an array of a plurality of capacitors.
  • a multiphase AC/DC flyback circuitry is utilized with a mains power source to boost the defibrillator's capacitor to the required high voltage level.
  • the power supply charging circuitry utilizing a multiphase flyback topology is controllable.
  • the charge signal utilized is optimized based on a patient's cardio-physiological state.
  • a controller determines the charging signal characteristics specifically required to optimize the charging time required to fully charge the capacitor rendering the defibrillator operational and ready to discharge its electrical energy onto the patient.
  • the power supply charging circuitry provides a multiphase efficient charger able to controllably determine the number of phases utilized in charging the defibrillator capacitor, capacitors or capacitors array.
  • a three phase power signal is produced by the power supply charging circuit to efficiently charge the capacitor.
  • a two phase power signal may be utilized.
  • the number of phases utilized is determined by the defibrillator controller based on at least one or more parameters for example including but not limited to the number of phases available, the energy required to defibrillate a patient, the available energy in the power source, the energy level stored within the capacitor, or the like parameters associated with the power source, power sink (capacitor), patient and the charging circuit.
  • the efficient power supply charging circuitry comprises a power source, a controller and a capacitor.
  • the controller controls the charging signal, interfacing between the power supply providing the electrical energy and the capacitor that is receiving the electrical energy and is being charged.
  • the controller maintains and controls the electrical properties of both the power supply as well as the capacitor.
  • the controller controls at least one and more preferably a plurality of parameters associated with the power supply and capacitor for example including but not limited to voltage slope, input voltage, output voltage and time, or the like.
  • power optimization is accomplished utilizing a pulse modulator to generate a modulated signal such as a Pulse Width Modulation (PWM).
  • PWM Pulse Width Modulation
  • a modulated signal such as a Pulse Width Modulation (PWM).
  • PWM Pulse Width Modulation
  • a three phase signal is produced to charge the defibrillator's capacitor, therein optimizing the charging time.
  • the three phase shifted signal comprises three separate signals preferably having the same frequency and duty-cycle (D) and are phase shifted from each other by about 120 degrees.
  • the optimized and efficient charging circuitry according to the present invention is particularly adapted to power and energize an electrically operated device with an electrical energy retaining component most preferably including but not limited to a defibrillator.
  • charging circuitry allows an efficient and quick charging of electrical energy retaining components, such as but not limited to electrolyte capacitors.
  • the energy retaining components may be charged from either a DC power source such as a battery, or converted to DC from AC mains power outlet. Regardless of the power source type, the charging time is shortened compared to prior art.
  • the merit for incorporating the charging circuitry of the present invention in devices or systems that are optimized while performing fast and repeated charging of electrical energy is desired. Examples of such devices include but in no way are limited to: camera flashes, stun guns, cordless power tools, wireless devices, cordless telephones, vehicle engine starter, toys, portable devices, or the like.
  • such charging circuitry may be incorporated in portable compact devices, for example devices having a size of up to 30 cm by 30 cm by 15 cm.
  • portable compact devices for example devices having a size of up to 30 cm by 30 cm by 15 cm.
  • the merit of incorporating said charging circuitry in such devices is that it allows the use of compact integral power source such as batteries, and the use of compact charging components such as transformers.
  • the charging circuitry is incorporated in defibrillators having a size of up to 30 cm by 30 cm by 15 cm.
  • An optional embodiment of the present invention provides for a multiphase flyback topology charging circuitry that may optionally be incorporated and integrated with a plurality of devices requiring a surge of quick energy that is quickly available upon demand and recharges in an efficient and optimized manner. It is known in the art that every resuscitation treatment requires cardiopulmonary massage, and most resuscitation require defibrillation. It is thereby established that cardiopulmonary massage and defibrillation are complementary treatments and are performed in adjunct. Further to that, researchers suggest that performance of cardiopulmonary massage in conjunction with defibrillation, and even more preferably prior to first defibrillation, improves the effectiveness of defibrillation.
  • a device that incorporates both defibrillation and cardiac massage, and more preferably is designed for automated synchronized operation of these treatments may has advantage over separate devices (defibrillators and cardiac massage devices. It is further established that due to the portable nature of resuscitation devices that may be used in ambulatory and in out-of-hospital settings, compactness of the device is considered a merit as it enhances portability. Therefore, incorporating compact and fast charging circuitry as provided in accordance with the present invention provides for such an integrated system (e.g. cardiac massage plus defibrillator).
  • An embodiment of such an integrated system will include means for delivering cardiac massage compressions, for example but not limited to, a mechanical plunger actuated by a DC motor and a controller controlling the operation of said DC motor (hereafter: “CMD module”).
  • CMD module a mechanical plunger actuated by a DC motor and a controller controlling the operation of said DC motor
  • the system will incorporate an electrical energy storage component, such as a capacitor or capacitors array, a charging circuitry used for charging said electrical energy storage component, and a controller for controlling the charging and discharging of said capacitor or capacitors array (hereafter: "Defibrillator module”).
  • said integrated system includes a CMD module together with a defibrillator module.
  • the CMD module and the defibrillator module are communicating with each other via a physical cord or by a cordless connection such as, RF, Bluetooth or similar communication connections.
  • the CPR module and the defibrillator module are integrated into a joint housing.
  • the CMD module and the defibrillator module are controlled by a common controller, and preferably but not necessarily, share the same power source. Such embodiments facilitate for an integrated and thus effective treatment of a patient.
  • Implementation of the systems of the present invention involves performing or completing certain selected tasks or steps manually, automatically, or a combination thereof.
  • several selected steps could be implemented by hardware or by software on any operating system of any firmware or a combination thereof.
  • selected steps of the invention could be implemented as a chip or a circuit.
  • selected steps of the invention could be implemented as a plurality of software instructions being executed by a computer using any suitable operating system.
  • selected steps of the method and system of the invention could be described as being performed by a data processor, such as a computing platform for executing a plurality of instructions.
  • FIG. IA is a schematic block diagram of an exemplary defibrillator according to the present invention.
  • Figure IB is a schematic circuit diagram of an exemplary flyback circuit specifically showing an exemplary DC/DC flyback circuit that may be incorporated into a charging circuitry of the present invention.
  • FIG. 2 is an illustration of an optional multiphase charging signal used according to the present invention.
  • FIG. 3 is a flowchart of an exemplary method according to the present invention.
  • FIG. 4 is an isometric illustration of a functionally and physically integrated system comprising a cardiac massage module and a defibrillator module.
  • the integrated system is viewed from the rear with defibrillation pads connected to enable the system to function also as a defibrillator.
  • the present invention is aimed to provide a defibrillator comprising a power source, a charging circuit comprising a plurality of phases for receiving power from said power source, and a controller for controlling said charging circuit.
  • the power supply may be a battery or mains power.
  • the charging circuit of said defibrillator comprises a multiphase flyback DC/DC converter.
  • the multiphase flyback DC/DC converter comprises at least two flyback DC/DC converters. More preferably, the multiphase flyback DC/DC converter comprises three flyback DC/DC converters.
  • the controller of the defibrillator controls the multiphase flyback DC/DC converter based on at least one parameter selected from the group consisting of the number of phases available, the energy level set to defibrillate a patient, the available energy in the power source, the energy level stored within said capacitor array, or any combination thereof.
  • the defibrillator of the present invention may further comprise at least one capacitor adapted to be reloaded with an electric charge via said charging circuit upon command from said controller.
  • the defibrillator may be integrated with a cardiac massage device.
  • the defibrillator of the present invention is adapted to communicate with an external resuscitation device.
  • a further aim of the present invention is to provide an electrically operated device comprising an energy retaining component, a charging circuit having a plurality of phases for charging said energy retaining component and a controller for controlling said charging circuit.
  • T electrically operated device may be a camera flash, stun gun, power tools, wireless devices, telephones, satellite telephones, vehicle engine starter and toys.
  • the present invention is also directed to a charging circuit for electrically operated device, wherein said charging circuit is electrically connected to a power source and comprises a plurality of phases.
  • the plurality of phases is three phases.
  • the three phases are arranged in a DC/DC flyback topology.
  • the electrically operated device comprises a defibrillator.
  • the electrically operated device may be selected from the group consisting of camera flash, stun gun, power tools, wireless devices, telephones, satellite telephones, vehicle engine starter and toys.
  • FIG. IA shows a battery powered defibrillator 100 according to the present invention.
  • Defibrillator 100 comprises battery 102, charging circuit 104, capacitor 106 and controller 110 (which may for example be a digital signal processor (DSP)), which may in turn comprise a PWM 112 and at least one digital outputs 114.
  • DSP digital signal processor
  • defibrillator 100 is rendered operational once capacitor 106 is fully charged and ready to discharge the required electrical energy onto a patient (not shown) via electrodes 118 and 120.
  • capacitor 106 is charged from a power source for example including but not limited to mains power (not shown) or battery 102 that is most preferably optimized and made efficient with charging circuit 104 according to the present invention.
  • charging circuit 104 is controllable through controller 110, preferably comprising PWM 112 that modulates the energy stream from the power source, most preferably to produce a charging sequence that is optimized both in terms of battery 102 use, and time period needed to charge the capacitor with the energy required to defibrillate a patient (not shown).
  • controller 110 determines the energy level required in capacitor 106.
  • controller 110 preferably modulates circuit 104 to control and most preferably to optimize capacitor 106 charging capabilities.
  • circuit 104 produces a three phase signal, as shown in Figure 2, to optimize the charging time of capacitor 106 from the power source optionally battery 102 or a mains power (not shown).
  • Controller 110 determines whether capacitor 106 is to be charged or whether a defibrillating power discharge is to occur. For the latter, controller 110 switches the circuit for discharge from capacitor 106 to a bridge 108, which generates in conjugation with Digital output 114, preferably but not necessarily in conjunction with Digital output 114, a biphasic waveform for delivery to electrodes 118 and 120.
  • bridge 108 together with Digital output 114 may generate a monophasic waveform.
  • charging circuit 104 comprises a plurality of multiphase flyback DC/DC circuits, for example including three flyback DC/DC converters 122, 124 and 126.
  • a non-limiting example of a single phase flyback DC/DC topology is described with regard to US Patent No. 6118675, hereby incorporated by reference as if fully set forth herein.
  • Such a single phase flyback DC/DC converter could easily be adapted for the purposes of the present invention by one of ordinary skill in the art.
  • at least two or more flyback DC/DC converters may be incorporated.
  • Most preferably three flyback DC/DC converters 122, 124 and 126 are incorporated within circuit 104 as is shown in Figure IA.
  • converters 122-126 produce charging signals 222, 224 and 226 that are used to optimize and to efficiently charge capacitor 106 in preparation for the high energy required to defibrillate a patient.
  • a plurality of multiphase flyback AC/DC converters may be utilized with a mains power source (not shown).
  • Figure IB provides an example of flyback DC/DC converters 122, 124, 126 preferably incorporated within charging circuit 104 to produce a capacitor charging signal as depicted in Figure 2.
  • Figure IB shows only substantial electrical elements that are essential parts of a functional flyback DC/DC converter. Electrical components such as resistors, capacitors, transistors, diodes and others that may be used for controlling and regulating the charging are generally not shown.
  • the flyback converter circuitry 122 (as shown; circuitry 124, 126 are identical) comprises incoming power supply (Vin) 150, current check 152 (current sense out + and current sense out -), controller signal 154 (PWM In), control switch 155, transformer 156, and outgoing power supply (Vout) 158 that charges the capacitor 106.
  • power supply 150 may be obtained from different sources currently shown from a direct current (DC) source for example including but not limited to a battery.
  • DC direct current
  • converters 122, 124, 126 may be adjusted to accommodate alternating current power sources for example including but not limited to mains power source.
  • controller signal 154 is delivered from a controller, for example controller 110 of Figure IA, providing control for at least one and most preferably a plurality of signal parameters for example including but not limited to current duration, ramp up time, frequency, duty cycle, channel ON/OFF time, and the like parameters, to produce a controllable signal similar to that described in greater details in Figure 2.
  • a controller for example controller 110 of Figure IA
  • signal parameters for example including but not limited to current duration, ramp up time, frequency, duty cycle, channel ON/OFF time, and the like parameters
  • the step up energy conversion is provided by transformer 156 to boost the input power supply electrical energy 150 to sufficiently high electrical energy provided by the outgoing power supply 158 that charges the capacitor.
  • More preferably outgoing power supply 158 produces a charging signal, for example output power (signal) 222, 224, 226 as depicted in Figure IA, that is sufficient to charge the defibrillator capacitor or capacitors array, for example capacitor 106 of Figure IA, in accordance with the controller parameters provided by controller signal 154, preferably producing a charging signal as shown in Figure 2.
  • the charging signal 154 is further regulating the operation of Switch 155 by determining which charging signal 222, 224 or 226 is operated and what the energy level that will be transferred is.
  • Figure 2 depicts a graphical illustration of an exemplary optimal charging signal as defined by controller 110 of Figure 1 utilizing PWM 112 to produce a three phases charging signal by charging circuit 104 as depicted in Figure IA, in which the x-axis shows degrees (Degrees) and the y-axis shows duty cycle (D).
  • Figure 2 depicts a signal having three phases each comprising the same frequency and duty cycle, however, preferably delayed by a controllable phase shift for example by 120 degrees.
  • the charging circuit may produce a three-phase signal comprising a first phase signal 222 depicted by the solid line, while a second phase signal 224 depicted by the long dot dashed line, ramps up before the first phase ramps down, while the third phase signal 226 depicted by the dashed line ramps up prior to the ramp down of the second phase signal 224.
  • the signal ramp up and or ramp down may controllably be shaped by controller 110.
  • the number of phases produced by charging circuit 104 is determined by controller 110 and is based on at least one or more parameters for example including but not limited to the number of phases available, the energy required to defibrillate a patient, the available energy in the power source, for example battery 102 of Figure IA, the energy level stored and available within capacitor 106.
  • circuit 104 and controller 110 may also provide safety measures for both, the device and the patient, by allowing the charging circuit 104 to toggle among the plurality of DC/DC flyback converters 122-126, according to the output of the current sense circuit of Fig. IB.
  • Current sense out 152 returns the potential voltage from a resistor 170 (Rsense) to controller 110 repeatedly.
  • Controller 110 calculates the current flow through Rsense 170 and adjusts the current flow to flyback 156 by PWM 154.
  • controller 110 may depict which of the available converter circuits 122-126 are operational at any point in time both for efficiency and optimization as well as safety purposes, i.e. preventing overheating, overcharging, or the like.
  • Controller 110 preferably depicts the signal waveform produced by converters 122-126 for example signal waveforms 222-226.
  • controller 110 senses over current from Current sense output 152 it can either turn off switch 155 to avoid temporary over charging or alternatively it may shorten the PWN in signal duration to reduce the current flow to thereby shorten the duty cycle of the active charging channel and thus reduce the over current to a desired level.
  • the controller 110 may act in a same manner as described above.
  • the current enters the transformer 156 (Tl) where it is converted Nl, N2 denote coils) and flows through Vout 158 to charge a capacitor such as capacitor 106 demonstrated in figure IA.
  • FIG. 3 shows a flowchart of an exemplary method of using the defibrillator according to the present invention.
  • capacitor 106 of Figure 1 is charged so as to produce sufficient electrical energy to defibrillate a patient.
  • the controller via PWM signals determines the required charging output level to be used by charging circuit 104 of Figure 1 for charging capacitor 106.
  • the charging circuit 104 of Figure 1 produces a multiphase charging signal for example a three phase charging signal as depicted in Figure 2.
  • the multiphase signal comprises three phases produced sequentially in accordance with the controller 110 of Figure 1, optionally producing a first phase signal 322 followed by a second phase signal 324 and a third phase signal 326.
  • Capacitor charging continues in stage 306 utilizing the multiphase signal produced by the multiphase flyback DC/DC topology according to a preferred embodiment of the present invention.
  • Capacitor charging continues until such a time as it is sufficiently charged in stage 308, preferably the charging period is optimized by a controller in accordance with at least one or more parameters as mentioned above.
  • stage 310 the capacitor awaits the signal to discharge the stored energy to thereby defibrillate a patient.
  • stage 312 the defibrillator is activated and electrical energy is delivered to a patient through electrodes for example electrodes 118 and 120 of Figure 1. Once capacitor discharge is completed the controller may commend to recharge the capacitor to be ready for the next defibrillation signal.
  • Fig. 4 schematically illustrates an exemplary combined device comprising a cardiac massage module 12 according to some embodiments of the present invention, and a defibrillator module 100 of FIG IA.
  • the cardiac massage module 12 comprises a DC motor 14, a plunger 62 and a battery (not shown).
  • a control unit (controller) 20 is integrated into the structure of cardiac massage module 12.
  • the control unit 20 includes an "ON 1 V 11 OFF" button 54, an LCD display 21 (which may also be a LED display or any other suitable display), and optionally a speaker (not shown) for audio feedback or guidance and a microphone (not shown).
  • Control unit 20 includes also a massage activation button (not shown) and a defibrillation shock release button (not shown).
  • Defibrillation pads 80 are attached to the CMD treated person for measuring
  • ECG signals and for delivering the defibrillation shock.
  • the ECG data is transferred via defibrillation pads 80, via cords 76 and adapter 73 to control 20 for processing and timing of dispensing either cardiac massage or defibrillations shock.
  • the timing of treatments is automatically determined by control unit 20.
  • the controller 20 synchronizes the activity of the cardiac massage plunger or the release of electric energy to the patient by the defibrillation module in an alternate manner (not shown). While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications and other applications of the invention may be made.

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

Abstract

La présente invention concerne d'une façon générale des défibrillateurs et des systèmes de défibrillation. L'invention concerne plus particulièrement des défibrillateurs et des systèmes de défibrillation comprenant un chargeur efficace servant à alimenter en énergie électrique le défibrillateur avant délivrance du choc électrique au patient.
PCT/IL2009/001186 2008-12-11 2009-12-13 Chargeur pour défibrillateur WO2010067373A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
IL195874A IL195874A0 (en) 2008-12-11 2008-12-11 Defibrillator charger
IL195874 2008-12-11

Publications (2)

Publication Number Publication Date
WO2010067373A2 true WO2010067373A2 (fr) 2010-06-17
WO2010067373A3 WO2010067373A3 (fr) 2010-08-12

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Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012085306A1 (fr) * 2010-12-24 2012-06-28 Merce Vives Salvador Dispositif d'assistance cardiaque d'urgence
US10029109B2 (en) 2016-12-12 2018-07-24 Revive Solutions, Inc. Defibrillator
US10449380B2 (en) 2016-12-12 2019-10-22 Revive Solutions, Inc. Defibrillator
US10903675B2 (en) 2016-12-12 2021-01-26 Avive Solutions, Inc. Medical device draw current regulation
US10946207B2 (en) 2017-05-27 2021-03-16 West Affum Holdings Corp. Defibrillation waveforms for a wearable cardiac defibrillator
US11607555B2 (en) 2016-12-12 2023-03-21 Avive Solutions, Inc. Defibrillator discharge control
US20230099672A1 (en) * 2021-09-24 2023-03-30 Altrix Medical, Inc. Charging circuit for a defibrillator
EP4234004A1 (fr) * 2016-12-19 2023-08-30 HeartHero, Inc. Système de défibrillateur externe automatisé

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050119706A1 (en) * 2003-12-02 2005-06-02 Ideker Raymond E. Methods, systems and computer program products to inhibit ventricular fibrillation during cardiopulmonary resuscitation
US20070032830A1 (en) * 2005-08-04 2007-02-08 Bowers Kyle R Automatic external defibrillator (AED) with wireless communications
US7298197B2 (en) * 2003-08-18 2007-11-20 Nxp B.V. Multi-phase DC-DC converter with shared control

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7298197B2 (en) * 2003-08-18 2007-11-20 Nxp B.V. Multi-phase DC-DC converter with shared control
US20050119706A1 (en) * 2003-12-02 2005-06-02 Ideker Raymond E. Methods, systems and computer program products to inhibit ventricular fibrillation during cardiopulmonary resuscitation
US20070032830A1 (en) * 2005-08-04 2007-02-08 Bowers Kyle R Automatic external defibrillator (AED) with wireless communications

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012085306A1 (fr) * 2010-12-24 2012-06-28 Merce Vives Salvador Dispositif d'assistance cardiaque d'urgence
ES2385146A1 (es) * 2010-12-24 2012-07-19 Salvador Mercé Vives Dispositivo para asistencia cardiaca de urgencia.
US10543376B2 (en) 2016-12-12 2020-01-28 Avive Solutions, Inc. Defibrillator
US10071256B2 (en) 2016-12-12 2018-09-11 Revive Solutions, Inc. Defibrillator
US10112054B2 (en) 2016-12-12 2018-10-30 Revive Solutions, Inc. Defibrillator
US10449380B2 (en) 2016-12-12 2019-10-22 Revive Solutions, Inc. Defibrillator
US10029109B2 (en) 2016-12-12 2018-07-24 Revive Solutions, Inc. Defibrillator
US10903675B2 (en) 2016-12-12 2021-01-26 Avive Solutions, Inc. Medical device draw current regulation
US10946209B2 (en) 2016-12-12 2021-03-16 Avive Solutions, Inc. Tubular, portable automated external defibrillator
US11318322B2 (en) 2016-12-12 2022-05-03 Avive Solutions, Inc. Defibrillator
US11607555B2 (en) 2016-12-12 2023-03-21 Avive Solutions, Inc. Defibrillator discharge control
EP4234004A1 (fr) * 2016-12-19 2023-08-30 HeartHero, Inc. Système de défibrillateur externe automatisé
US10946207B2 (en) 2017-05-27 2021-03-16 West Affum Holdings Corp. Defibrillation waveforms for a wearable cardiac defibrillator
US11648411B2 (en) 2017-05-27 2023-05-16 West Affum Holdings Dac Defibrillation waveforms for a wearable cardiac defibrillator
US20230099672A1 (en) * 2021-09-24 2023-03-30 Altrix Medical, Inc. Charging circuit for a defibrillator

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