WO2016149617A1 - Novel biphasic or multiphasic pulse generator and method - Google Patents
Novel biphasic or multiphasic pulse generator and method Download PDFInfo
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- WO2016149617A1 WO2016149617A1 PCT/US2016/023129 US2016023129W WO2016149617A1 WO 2016149617 A1 WO2016149617 A1 WO 2016149617A1 US 2016023129 W US2016023129 W US 2016023129W WO 2016149617 A1 WO2016149617 A1 WO 2016149617A1
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- phase
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- energy
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/38—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
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
- A61N1/3603—Control systems
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/36128—Control systems
- A61N1/36146—Control systems specified by the stimulation parameters
- A61N1/36167—Timing, e.g. stimulation onset
- A61N1/36175—Pulse width or duty cycle
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/362—Heart stimulators
- A61N1/37—Monitoring; Protecting
- A61N1/3702—Physiological parameters
- A61N1/3704—Circuits specially adapted therefor, e.g. for sensitivity control
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
- A61N1/36125—Details of circuitry or electric components
-
- 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
Definitions
- the disclosure relates to medical devices and in particular to devices and methods that generate and deliver therapeutic treatment pulses used in medical devices, such as cardioverters and defibrillators, neuro-stimulators, musculo-skeletal stimulators, organ stimulators and nerve stimulators. More specifically the disclosure relates to the generation by such medical devices of a new and innovatively shaped biphasic or multiphasic pulse waveform.
- a signal having a waveform may have a therapeutic benefit when the signal is applied to a patient.
- the therapeutic benefit to a patient may be a treatment that is provided to the patient.
- the therapeutic benefit or therapeutic treatment may include stimulation of a part of the body of the patient or treatment of a sudden cardiac arrest of the patient.
- Existing systems that apply a signal with a waveform to the patient often generate and apply a well-known signal waveform and do not provide much, or any, adjustability or variability of the signal waveform.
- the second (or Negative) phase of the Biphasic waveform is currently characterized by a lower amplitude starting point than the first (or Positive) phase of the Biphasic waveform, as shown in Figure 4. This is due to the partial draining of the high-energy reservoir during delivery of the initial Positive phase and then, after inverting the polarity of the waveform so that the Negative phase is able to be delivered, there is only the same partially drained amount of energy remaining in the energy reservoir. This lower amplitude starting point constrains and causes the lower initial amplitude of the Negative phase of the waveform.
- the typical exponential decay discharge is shown by the Positive phase of the waveform shown in Figure 4.
- the standard biphasic pulse waveform has been in common usage in manual
- defibrillators and in AEDs since the mid-1990s, and still results in energy levels of anywhere from 120 to 200 joules or more being delivered to the patient in order to be efficacious.
- WCDs generally need to deliver shocks of 150-200 joules in order to be efficacious, and this creates a lower limit on the size of the electrical components and the batteries required, and hence impacts the overall size of the device and the comfort levels for the patient wearing it.
- ICDs given that they are implanted within the body of patients, have to be able to last for as many years as possible before their batteries are exhausted and they have to be surgically replaced with a new unit.
- ICDs deliver biphasic shocks of up to a maximum of 30-45 joules, lower than is needed for effective external defibrillation as the devices are in direct contact with the heart tissue of the patient.
- Subcutaneous ICDs differ slightly in that they are not in direct contact with the heart of the patient, and these generally deliver biphasic shocks of 65- 80 joules in order to be efficacious. Even at these lower energy levels there is significant pain caused to the patient if a shock is delivered in error by the device.
- Most existing devices are designed to last for between 5-10 years before their batteries are depleted and they need to be replaced.
- FIG. 9 illustrates a conventional AED 800, which includes a base unit 802 and two pads 804. Sometimes paddles with handles are used instead of the pads 804. The pads 804 are connected to the base unit 802 using electrical cables 806.
- a typical protocol for using the AED 800 is as follows. Initially, the person who has suffered from sudden cardiac arrest is placed on the floor. Clothing is removed to reveal the person's chest 808. The pads 804 are applied to appropriate locations on the chest 808, as illustrated in Figure 9. The electrical system within the base unit 802 generates a high voltage between the two pads 804, which delivers an electrical shock to the person. Ideally, the shock restores a normal cardiac rhythm. In some cases, multiple shocks are required.
- Figure 1 illustrates a medical device having a biphasic or multiphasic waveform generator
- Figure 2 illustrates a defibrillator medical device with a multiphasic waveform generator with a plurality of independent subsystems each with its own energy reservoir and energy source;
- Figure 3 illustrates a defibrillator medical device with a biphasic waveform generator with two independent subsystems each with its own energy reservoir and energy source;
- Figure 4 illustrates a standard biphasic pulse waveform where the second (negative) phase of the waveform is smaller in amplitude than that of the first (positive) phase of the waveform;
- Figures 5A, 5B and 5C illustrate different examples of a novel biphasic or multiphasic pulse waveform generated by the biphasic or multiphasic waveform generator where the second (negative) phase of the waveform is larger in amplitude than the amplitude of the first (positive) phase of the waveform;
- Figure 6 illustrates an embodiment of a biphasic/multiphasic waveform generator with a single circuit containing multiple energy reservoirs which can be dynamically charged separately from a single energy source and then discharged through the H-bridge;
- Figure 7 illustrates a biphasic/multiphasic waveform generator with a single circuit containing multiple energy reservoirs which can be dynamically charged separately and then discharged through an H-bridge;
- Figure 8 illustrates a circuit for adjusting the biphasic or multiphasic waveform generator system's capacitance
- Figure 9 diagrammatically illustrates an example of a conventional external defibrillator
- Figure 10 illustrates a circuit for adjusting the waveform generator system's
- the disclosure is applicable to various medical devices including all defibrillator types: external (manual, semi-automated, and fully automated), wearable, implantable and
- the medical device may also be cardioverters and external/internal pacers, as well as other types of electrical stimulation medical devices, such as: neuro-stimulators, musculo-skeletal stimulators, organ stimulators and nerve/peripheral nerve stimulators, whether the devices are external or implantable.
- the novel biphasic or multiphasic waveform generator may be particularly useful for any type of defibrillator and examples of the novel biphasic or multiphasic waveform generator system will be described in the context of a defibrillator for illustration purposes.
- novel biphasic or multiphasic waveform generator may generate and deliver a much wider range of waveforms than has previously been possible in the art (or as shown in the examples) including a new generation/family of novel biphasic or multiphasic waveforms, as shown in Figure 5A, Figure 5B and Figure 5C.
- the novel biphasic or multiphasic waveform generator has greater utility to existing devices since it may be used to generate one or more of this family of novel lower energy biphasic pulses.
- the novel biphasic or multiphasic waveform generator may be configured to generate and deliver a wide range of the new low energy biphasic or multiphasic waveforms with varying pulse timings, phase tilts and amplitudes.
- Such waveforms can be used in the various medical devices described above.
- the pulse generator system may be used to generate therapeutic treatment pulses and then provide the pulses to a patient using paddles or pads or other suitable forms of electrodes.
- novel biphasic or multiphasic waveform generator can be embodied in a number of different ways, constituting a range of different potential circuit designs all of which are within the scope of this disclosure since any of the circuit designs would be able to generate and deliver a wide range of biphasic and/or multiphasic waveforms including the new family/generation of low energy biphasic and/or multiphasic waveforms where the first phase of the waveform has a lower amplitude than the second phase of the waveform.
- Figure 1 illustrates a medical device system 100 having a novel biphasic or multiphasic waveform generator 104.
- the medical device system may be any type of defibrillator system or any of the other types of medical devices described above.
- the medical device system 100 may include a medical device 102 that generates and delivers a novel biphasic or multiphasic pulse waveform 110 to a patient 112.
- the novel biphasic or multiphasic pulse waveform 110 may be a therapeutic pulse, a defibrillation pulse and the like.
- the medical device 102 may include a novel multiphasic or biphasic waveform generator 104, an energy source 106 and a control logic 108.
- the novel multiphasic or biphasic waveform generator 104 may generate a novel biphasic or multiphasic pulse waveform 110 using the energy stored/generated by the energy source 106.
- the novel biphasic or multiphasic pulse waveform 110 may have one or more first phases and one or more second phases wherein the first and second phases may be opposite polarities.
- the first phase may be a positive phase
- the second phase may be a negative phase
- the second phase of the waveform may be larger in amplitude than the amplitude of the first phase of the waveform as shown in Figures 5A and 5B.
- a novel multiphasic pulse waveform that may be generated by the multiphasic or biphasic waveform generator 104 is shown in which the biphasic or multiphasic pulse waveform 110 has more than one first phases and more than one second phases of the pulse waveform.
- each first phase has a positive polarity and each second phase has a negative polarity.
- the amplitude of the second phase may be less than 2500 volts and the first phase would be smaller than the second phase.
- the multiphasic or biphasic waveform generator 104 may deliver an energy of between 0.1 to 200 joules of energy to a patient during the first phase and second phase of the generated pulse waveform and an inter- pulse period between the first and second phases.
- the multiphasic or biphasic waveform generator 104 may deliver the waveform to the patient during a 2ms to 20ms time period.
- the control logic unit 108 may be coupled to and/or electrically connected to the multiphasic or biphasic waveform generator 104 and the energy source 106 to control each of those components to generate various version of the biphasic or multiphasic pulse waveform 110.
- the energy source 106 may be one or more power sources and one or more energy reservoirs.
- the control logic unit 108 may be implemented in hardware.
- the control logic unit 108 may be a plurality of lines of computer code that may be executed by a processor that is part of the medical device. The plurality of lines of computer code may be executed by the processor so that the processor is configured to control the multiphasic or biphasic waveform generator 104 and the energy source 106 to generate the biphasic or multiphasic pulse waveform 110.
- control logic unit 108 may be a programmable logic device, application specific integrated circuit, a state machine, a microcontroller that then controls the multiphasic or biphasic waveform generator 104 and the energy source 106 to generate the biphasic or multiphasic pulse waveform 110.
- the control logic unit may also include analog or digital switching circuitry when the high voltage switching component 109 is part of the control logic unit 108.
- the biphasic or multiphasic pulse waveform 110 may be delivered to the patient 112 using one or more patient contact devices.
- the one or more patient contact devices may be, for example, an electrode, a wire, a paddle, a pad or anything else that is capable of delivering the biphasic or multiphasic pulse waveform 110 to the patient 112.
- an example of a defibrillator that has the multiphasic or biphasic waveform generator 104 and the energy source 106 is now described in further detail.
- Figure 2 illustrates a defibrillator medical device 10 with a multiphasic waveform generator with a plurality of independent subsystems each with its own energy reservoir and energy source
- Figure 3 illustrates a defibrillator medical device 10 with a biphasic waveform generator with two independent subsystems each with its own energy reservoir and energy source.
- the components may use two or more physically and electrically distinct subsytems 12, 14 in which each subsystem has the waveform generator 104, the energy source 106 and the control logic 108 as shown in Figures 2-3.
- the reservoirs of stored electrical energy may be in two or more different circuits (see Figure 2 and Figure 3) that function together in a coordinated fashion in order to generate and deliver the pulse waveform where each phase of the waveform is produced from a separate reservoir of the stored energy.
- the reservoirs of energy may be of the same size/quantity or else of widely different sizes and may be supplied by one or more energy sources.
- the energy source 106 is not limited to any particular number of energy reservoirs (such as capacitors) or energy sources (such as batteries).
- the medical device system 10 may have a plurality or "n" number (as many as wanted) of subsystems 12, 14 that together can be utilized to generate the various multiphasic or biphasic waveforms.
- the two or more subsystems 12, 14 permit the system to shape the various characteristics of first and second phases separately from each other.
- the first phase may have a positive polarity and its characteristics may be shaped independently of the second phase that may have a negative polarity and its characteristics.
- the above described functions may be accomplished through the use of a fast switching high-energy / voltage switch system as described below.
- the fast switching high- energy / voltage switch system 109 may be part of the control logic unit 108 or the generator 104.
- Each subsystem 12, 14 of each side, as shown in Figure 2 and Figure 3, may have the control logic and heart rhythm sense component 108 (that is connected to a similar component on the other side by a digital control link 30 as shown in Figure 2 and Figure 3) that may be also coupled to a high voltage switching system component 109.
- the high voltage switching system component 109 may be implemented using either analog circuits or digital circuits or even some hybrid of the two approaches. Furthermore, the high voltage switching system component 109 may be implemented through the use of mechanical or solid-state switches or a combination of the two.
- the energy reservoir may also be coupled, by a high voltage return line 32 to the other side of the system as shown in Figure 2 and Figure 3.
- the high voltage return 32 electrically completes the circuit and is present in existing defibrillators, but in a slightly different form since in the existing style of devices it is split into two parts in the form of the two leads which go from the main defibrillator device to the internal or external surface of the patient.
- Figures 5A-5C illustrate examples of the biphasic or multiphasic waveforms that may be generated by the systems shown in Figures 2-3 as well as the systems shown in Figures 6-8.
- a first phase may be a positive polarity and the second phase may be a negative polarity.
- the biphasic or multiphasic waveforms also may have a negative polarity first pulse and a positive polarity second pulse.
- the first phase pulse amplitude may be smaller than the second phase amplitude.
- Figure 5C illustrates a multiphasic waveform in which the waveform has two or more positive polarity phases and two or more negative polarity phases.
- the system 10 makes use of two or more reservoirs of stored electrical energy 501 (such as high voltage generator and reservoir 1061, high voltage generator and reservoir 1062 and high voltage generator and reservoir 106n) that are either statically or dynamically allocated from within a single circuit 502 and that function together in a coordinated fashion in order to generate and deliver the final waveform where each phase of the waveform is produced from a separate reservoir of the stored energy.
- the reservoirs of energy 501 may be of the same size/quantity or else of widely different sizes and may be supplied by one or more energy sources.
- the system 10 may also have the high voltage switch 109 for each reservoir 501 and an H-bridge switch 110 that may be part of the control logic unit 108 or the generator 104.
- the H-bridge circuit is a known electronic circuit that enables a voltage to be applied across a load, M, in either direction using one or more switches (see
- the system makes use of at least one reservoir of stored electrical energy 601 in a configuration that is divided up and either statically or dynamically allocated into two or more portions of stored energy 602 from within a single circuit and that generates and delivers the final waveform in a coordinated fashion where each phase of the waveform is produced from a separate portion of the stored energy.
- the portions of energy 602 may be of the same size/quantity or else of widely different sizes and may be supplied by the one or more energy sources.
- this involves charging one or more group(s)/array(s) of capacitors (the number of capacitors in a statically or dynamically created group is based on the voltage and energy requirements for the phase of the waveform or waveform that is to be generated and delivered) and then discharging a select number of capacitors in a group that is configured as required to provide the desired waveform or phase of a waveform.
- the charging and discharging of capacitors in parallel and in series is well known in the art.
- switches mechanical or solid state
- Another embodiment of the system makes use of a direct current generation source in order to generate the initial phase of the waveform and then uses one or more reservoirs of stored electrical energy in order to generate the second phase of the waveform and any additional phases of the waveform.
- the energy reservoirs used may be supplied by one or more energy sources.
- Another embodiment of the system makes use of a direct current generation source in order to generate the initial phase of the waveform and then uses one or more additional direct current generation sources, configured alone, together, or else in combination with reservoirs of stored electrical energy, in order to generate the second phase of the waveform and any additional phases of the waveform.
- the energy reservoirs used may be supplied by one or more energy sources.
- the pulse generator may be configured with the circuitry, processors, programming and other control mechanisms necessary to separately and individually vary the phase timings, the inter-phase pulse timing(s), the phase tilts and the phase amplitudes necessary to customize and optimize the waveform for the patient at hand and for the specific therapeutic purpose for which the waveform is being used.
- the above described functions may be accomplished through the use of a fast switching high-energy / voltage switch system 109 which can be either analog or digital in nature or even some hybrid of the two approaches as shown in Figure 2 and Figure 3.
- the switching can be accomplished through the use of mechanical or solid-state switches or a combination of the two.
- FIG. 10 Other embodiments of the system discharge part of the waveform's initial phase energy through the use of a statically or dynamically allocated group of resistive power splitters (see Figure 10), which steps the waveform's initial phase amplitude down across the group of resistors, and in this manner delivers a smaller remaining amplitude of the waveform's initial phase to the patient, while still delivering a full amplitude of the second phase (and any additional phases) to the patient.
- modules or subsystems intended to alter the RC constant of the pulse delivery circuitry for one or more of the pulse phases, and hence alter the tilt of the phase of the pulse waveform involved.
- modules or subsystems can consist of an array of capacitors or an array of resistors, or of a combination of the two (see Figure 8 and Figure 10).
- the system may provide for the recharging of individual energy reservoirs by the energy sources during times (including inter-phase pulse times) that an individual energy reservoir is not selected for discharge. This provides the opportunity to interlace equivalent amplitude initial multiphasic pulses utilizing several different high energy reservoirs.
Abstract
Description
Claims
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2017549277A JP2018508313A (en) | 2015-03-18 | 2016-03-18 | Novel two-phase or multi-phase pulse generator and method |
AU2016232837A AU2016232837B2 (en) | 2015-03-18 | 2016-03-18 | Novel biphasic or multiphasic pulse generator and method |
EP16765826.9A EP3271010A4 (en) | 2015-03-18 | 2016-03-18 | Novel biphasic or multiphasic pulse generator and method |
CN201680028694.7A CN107847753B (en) | 2015-03-18 | 2016-03-18 | Novel biphasic or multiphasic pulse generator and method |
CA2980000A CA2980000A1 (en) | 2015-03-18 | 2016-03-18 | Novel biphasic or multiphasic pulse generator and method |
KR1020177030053A KR20170129865A (en) | 2015-03-18 | 2016-03-18 | Novel odd or multiphase pulse generators and methods |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US14/661,949 | 2015-03-18 | ||
US14/661,949 US9656094B2 (en) | 2013-06-14 | 2015-03-18 | Biphasic or multiphasic pulse generator and method |
Publications (1)
Publication Number | Publication Date |
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WO2016149617A1 true WO2016149617A1 (en) | 2016-09-22 |
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ID=56919472
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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PCT/US2016/023129 WO2016149617A1 (en) | 2015-03-18 | 2016-03-18 | Novel biphasic or multiphasic pulse generator and method |
Country Status (8)
Country | Link |
---|---|
EP (1) | EP3271010A4 (en) |
JP (1) | JP2018508313A (en) |
KR (1) | KR20170129865A (en) |
CN (1) | CN107847753B (en) |
AU (1) | AU2016232837B2 (en) |
CA (1) | CA2980000A1 (en) |
HK (1) | HK1253039A1 (en) |
WO (1) | WO2016149617A1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP3307381A4 (en) * | 2015-06-10 | 2019-01-23 | CardioThrive, Inc. | Multivector patient electrode system and method of use |
US11712575B2 (en) | 2013-06-14 | 2023-08-01 | Cardiothrive, Inc. | Wearable multiphasic cardioverter defibrillator system and method |
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US5733310A (en) * | 1996-12-18 | 1998-03-31 | Zmd Corporation | Electrotherapy circuit and method for producing therapeutic discharge waveform immediately following sensing pulse |
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US5824017A (en) * | 1997-03-05 | 1998-10-20 | Physio-Control Corporation | H-bridge circuit for generating a high-energy biphasic waveform in an external defibrillator |
US7065403B1 (en) * | 2001-12-03 | 2006-06-20 | Pacesetter, Inc. | System and method for measuring lead impedance in an implantable stimulation device employing pulse-train waveforms |
CN102974039B (en) * | 2012-12-20 | 2015-01-07 | 久心医疗科技(苏州)有限公司 | Defibrillator output stage with H bridge circuit and diphase sawtooth square wave defibrillation high-voltage discharge method |
CN203154608U (en) * | 2013-04-15 | 2013-08-28 | 北京瑞新康达医疗科技有限公司 | Bidirectional defibrillation waveform generating circuit |
US10279189B2 (en) * | 2013-06-14 | 2019-05-07 | Cardiothrive, Inc. | Wearable multiphasic cardioverter defibrillator system and method |
US9656094B2 (en) * | 2013-06-14 | 2017-05-23 | Cardiothrive, Inc. | Biphasic or multiphasic pulse generator and method |
-
2016
- 2016-03-18 AU AU2016232837A patent/AU2016232837B2/en active Active
- 2016-03-18 EP EP16765826.9A patent/EP3271010A4/en not_active Withdrawn
- 2016-03-18 CN CN201680028694.7A patent/CN107847753B/en active Active
- 2016-03-18 WO PCT/US2016/023129 patent/WO2016149617A1/en active Application Filing
- 2016-03-18 KR KR1020177030053A patent/KR20170129865A/en not_active Application Discontinuation
- 2016-03-18 CA CA2980000A patent/CA2980000A1/en not_active Abandoned
- 2016-03-18 JP JP2017549277A patent/JP2018508313A/en active Pending
-
2018
- 2018-09-27 HK HK18112419.8A patent/HK1253039A1/en unknown
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US5199429A (en) * | 1991-05-23 | 1993-04-06 | Angemed, Inc. | Implantable defibrillator system employing capacitor switching networks |
US5733310A (en) * | 1996-12-18 | 1998-03-31 | Zmd Corporation | Electrotherapy circuit and method for producing therapeutic discharge waveform immediately following sensing pulse |
US20010031992A1 (en) * | 1997-05-14 | 2001-10-18 | Fishler Matthew G. | System and method of generating a high efficiency biphasic defibrillation waveform for use in an implantable cardioverter/defibrillator (ICD) |
US20010051819A1 (en) * | 1997-10-27 | 2001-12-13 | Fischell Robert E. | Implantable apparatus for treating neurological disorders |
US20140371805A1 (en) * | 2013-06-14 | 2014-12-18 | Cardiothrive, Inc. | Dynamically adjustable multiphasic defibrillator pulse system and method |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11712575B2 (en) | 2013-06-14 | 2023-08-01 | Cardiothrive, Inc. | Wearable multiphasic cardioverter defibrillator system and method |
EP3307381A4 (en) * | 2015-06-10 | 2019-01-23 | CardioThrive, Inc. | Multivector patient electrode system and method of use |
Also Published As
Publication number | Publication date |
---|---|
KR20170129865A (en) | 2017-11-27 |
CA2980000A1 (en) | 2016-09-22 |
JP2018508313A (en) | 2018-03-29 |
EP3271010A1 (en) | 2018-01-24 |
CN107847753A (en) | 2018-03-27 |
HK1253039A1 (en) | 2019-06-06 |
AU2016232837A1 (en) | 2017-11-02 |
EP3271010A4 (en) | 2019-01-02 |
AU2016232837B2 (en) | 2021-01-28 |
CN107847753B (en) | 2022-02-08 |
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