CN116212242A - High-frequency alternating-current wave defibrillator - Google Patents
High-frequency alternating-current wave defibrillator Download PDFInfo
- Publication number
- CN116212242A CN116212242A CN202310338477.XA CN202310338477A CN116212242A CN 116212242 A CN116212242 A CN 116212242A CN 202310338477 A CN202310338477 A CN 202310338477A CN 116212242 A CN116212242 A CN 116212242A
- Authority
- CN
- China
- Prior art keywords
- direct current
- conversion module
- defibrillator
- voltage
- defibrillation
- Prior art date
- Legal status (The legal status 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 status listed.)
- Pending
Links
Images
Classifications
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
- H02J7/00—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
- H02J7/34—Parallel operation in networks using both storage and other dc sources, e.g. providing buffering
- H02J7/345—Parallel operation in networks using both storage and other dc sources, e.g. providing buffering using capacitors as storage or buffering devices
-
- 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
- A61N1/3906—Heart defibrillators characterised by the form of the shockwave
-
- 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
-
- 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
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02M—APPARATUS FOR CONVERSION BETWEEN AC AND AC, BETWEEN AC AND DC, OR BETWEEN DC AND DC, AND FOR USE WITH MAINS OR SIMILAR POWER SUPPLY SYSTEMS; CONVERSION OF DC OR AC INPUT POWER INTO SURGE OUTPUT POWER; CONTROL OR REGULATION THEREOF
- H02M3/00—Conversion of dc power input into dc power output
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02M—APPARATUS FOR CONVERSION BETWEEN AC AND AC, BETWEEN AC AND DC, OR BETWEEN DC AND DC, AND FOR USE WITH MAINS OR SIMILAR POWER SUPPLY SYSTEMS; CONVERSION OF DC OR AC INPUT POWER INTO SURGE OUTPUT POWER; CONTROL OR REGULATION THEREOF
- H02M7/00—Conversion of ac power input into dc power output; Conversion of dc power input into ac power output
- H02M7/42—Conversion of dc power input into ac power output without possibility of reversal
- H02M7/44—Conversion of dc power input into ac power output without possibility of reversal by static converters
-
- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
- H02J2207/00—Indexing scheme relating to details of circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
- H02J2207/50—Charging of capacitors, supercapacitors, ultra-capacitors or double layer capacitors
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02B—CLIMATE CHANGE MITIGATION TECHNOLOGIES RELATED TO BUILDINGS, e.g. HOUSING, HOUSE APPLIANCES OR RELATED END-USER APPLICATIONS
- Y02B70/00—Technologies for an efficient end-user side electric power management and consumption
- Y02B70/10—Technologies improving the efficiency by using switched-mode power supplies [SMPS], i.e. efficient power electronics conversion e.g. power factor correction or reduction of losses in power supplies or efficient standby modes
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Cardiology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Heart & Thoracic Surgery (AREA)
- Biomedical Technology (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)
- Power Engineering (AREA)
- Electrotherapy Devices (AREA)
Abstract
The invention belongs to the technical field of medical appliances, and particularly relates to a high-frequency alternating-current wave defibrillator. A high-frequency alternating-current wave defibrillator comprises a direct-current power supply and a defibrillation electrode, and further comprises a plurality of components which are sequentially connected: the power input end of the energy storage capacitor is connected with a direct current power supply, and the energy storage capacitor is charged through the direct current power supply; the direct current/direct current conversion module is used for converting the low-voltage direct current output by the energy storage capacitor into high-voltage direct current; and the output end of the direct current-alternating current conversion module is connected with the defibrillation electrode, and the high-voltage direct current output by the direct current-direct current conversion module is converted into alternating current with preset frequency and is supplied to the defibrillation electrode. The invention adopts high-frequency biphasic wave defibrillation, has higher defibrillation efficiency, smaller myocardial injury, adopts direct-current capacitor energy storage design, has small volume, light weight and convenient carrying, solves the problem of poor usability of the alternating-current defibrillator, has no high voltage in the machine, is safer for patients and users, is convenient for production and maintenance, and has lower cost.
Description
Technical Field
The invention belongs to the technical field of medical appliances, and particularly relates to a high-frequency alternating-current wave defibrillator.
Background
Ventricular fibrillation refers to the disordered activation of the ventricles, resulting in the loss of regular orderly activation and contractile function of the ventricles, both of which are functional cardiac arrest, meaning that the human heart has stopped pumping blood, a lethal arrhythmia. Ventricular fibrillation is an extremely chaotic manifestation of cardiac electrical activity and is generally difficult to self-terminate. Shock defibrillation is the only effective method that can clinically terminate ventricular fibrillation at present. The method is to interrupt various foldback paths through the electric pulse with certain energy and then to perform simultaneous depolarization, and the method uses the instantaneous high-energy electric pulse to depolarize all cardiac muscle cells simultaneously so as to eliminate all ectopic rhythm points and boundary currents and interrupt all foldback, thereby stopping ventricular fibrillation and restoring sinus rhythm. It is desirable to reduce the peak voltage as much as possible while achieving defibrillation, thereby reducing the damage to the patient from defibrillation currents.
One of the mechanisms by which electrical shock causes myocardial damage is the electroporation effect, i.e., the formation of holes in the membrane of the myocardial cell. Since electroporation can cause a large number of ion-transmembrane exchanges, the transmembrane action potential can continue to be zero for a period of time, thereby producing electrical paralysis. The defibrillation effect is not achieved, and even the irreversible damage to the myocardial cells is caused. The higher the peak voltage and the higher the peak current, the stronger the electroporation effect and the more serious the damage to the myocardium.
The basic requirements for defibrillator design are convenience, safety, and efficiency. Early defibrillators used a 50Hz mains frequency power supply to obtain high voltage through a transformer, producing defibrillation currents. The pulse voltage is 1000V peak voltage, with duration of 250ms,12 cycle sine wave voltage, but the use is very inconvenient. The latter monophase wave defibrillator uses capacitive energy to solve the convenience problem, the peak voltage is 4000V, the duration is 4-10 ms, and the pulse is a direct current pulse. Modern biphasic wave defibrillators change the direction of current once during the shock defibrillation process, and their peak voltage drops to 2000V for a duration of 10-30 ms. It can be seen that the voltage required for defibrillation can be reduced and the damage to the patient's cardiomyocytes can be reduced by changing the direction of the defibrillation current. Studies have shown that during shock defibrillation, after current enters the cell, the cell end nearest the cathode depolarizes, and the anode hyperpolarizes. The high resistance of the cell gap junctions on the cell membrane forces the current to pass preferentially through the cell membrane. Alternating current can be transmitted to deep tissues in a zigzag mode along the high-resistance cell bundles, so that all myocardial cells are depolarized at the same time. And the high frequency shock induced sawtooth pattern helps to maintain tissue polarization and refractory period.
Disclosure of Invention
The invention aims at solving the technical problem that the prior defibrillator still has overhigh peak voltage and is easy to damage myocardial cells of a patient when in use, and provides a high-frequency alternating current wave defibrillator.
A high-frequency alternating-current wave defibrillator comprises a defibrillation electrode and further comprises a plurality of electrodes which are sequentially connected:
a DC power supply for supplying power to the high frequency AC wave defibrillator;
the energy storage capacitor is charged by the direct-current power supply;
the direct current/direct current conversion module is used for converting the low-voltage direct current output by the energy storage capacitor into high-voltage direct current;
and the output end of the direct current-alternating current conversion module is connected with the defibrillation electrode, and the high-voltage direct current output by the direct current-direct current conversion module is converted into alternating current with preset frequency and is supplied to the defibrillation electrode.
Preferably, the direct current power supply adopts a direct current power supply of 12-24V.
Preferably, the energy storage capacitor is formed by connecting a plurality of electrolytic capacitors in parallel.
As a preferable scheme, the electrolytic capacitor adopts a 50V 6800 mu F high-frequency low-resistance electrolytic capacitor.
Preferably, the peak value of the energy storage voltage of the energy storage capacitor is 50V.
Preferably, the direct current power supply charges the energy storage capacitor through a flyback boost circuit.
Preferably, the working frequency of the direct current-direct current conversion module is 100 kHz-300 kHz.
As a preferable scheme, the direct current-direct current conversion module adopts a push-pull topological structure based on voltage boosting of a transformer.
As a preferable scheme, the primary coil of the transformer is wound by a plurality of enameled wires in parallel, and the alternating voltage output by the secondary coil of the transformer is rectified by voltage doubling to generate direct current output.
Preferably, the peak voltage output by the direct current-alternating current conversion module is 1000V, and the highest frequency is 1000Hz.
Preferably, the direct current-alternating current conversion module adopts an H-bridge circuit formed by four switches.
Preferably, the switch is formed by a 1200V series MOSFET switch or IGBT and a driver.
Preferably, the high-frequency ac wave defibrillator further includes:
and the detection and control system is used for respectively measuring the voltages on the direct current power supply and the energy storage capacitor, measuring the connection condition of the defibrillation electrode and respectively connecting with the direct current-direct current conversion module and the direct current-alternating current conversion module.
As a preferable scheme, the direct-current power supply charges the energy storage capacitor, the direct-current power supply supplies power to other modules, when the energy storage capacitor reaches a voltage preset value, the charging is considered to be completed, and the energy storage capacitor sends a charging completion signal to the detection and control system;
the detection and control system judges whether the voltage on the energy storage capacitor reaches a voltage preset value, if not, the detection and control system considers that the abnormality exists, otherwise, the detection and control system considers that the abnormality exists;
the detection and control system detects whether the contact quality of the defibrillation electrode is in a preset range, if not, the defibrillation electrode is considered to be abnormal, otherwise, the defibrillation electrode is considered to be normal;
when an abnormality exists, the detection and control system sends an abnormality signal to inform an operator to process, and when the abnormality is considered normal, a defibrillation instruction sent by the operator is waited to be acquired;
after a defibrillation command is received, the detection and control system starts the direct current-direct current conversion module and the direct current-alternating current conversion module, defibrillation pulse is output through the defibrillation electrode, and after a preset time is reached, the detection and control system closes the direct current-direct current conversion module and the direct current-alternating current conversion module, and defibrillation is finished.
The invention has the positive progress effects that: the invention adopts the high-frequency alternating current wave defibrillator and has the following advantages:
1. the direct current-alternating current conversion module outputs high-frequency alternating current to the defibrillation electrode so as to realize high-frequency biphasic wave defibrillation, and has higher defibrillation efficiency and smaller myocardial damage;
2. the direct-current power supply is adopted to charge the energy storage capacitor, and the direct-current capacitor energy storage design is adopted, so that the portable electric defibrillator has the advantages of small volume, light weight and portability, and solves the problem of poor usability of the alternating-current defibrillator;
3. compared with the existing defibrillator, the defibrillator provided by the invention has the advantages that lower voltage and lower current are adopted for defibrillation, and the damage to cardiac muscle is lower;
4. compared with low-frequency electric shock defibrillation with the frequency of 50Hz, the defibrillation effect is better at the frequency of about 1000Hz, the defibrillation success rate is higher, and the required energy is lower.
5. The invention has no high pressure in the machine, is safer for patients and users, is convenient for production and maintenance, and has lower cost.
Drawings
FIG. 1 is a block diagram of one connection of the present invention;
fig. 2 is a defibrillation waveform of the present invention.
Detailed Description
In order that the manner in which the invention is practiced, as well as the features and objects and functions thereof, will be readily understood and appreciated, the invention will be further described in connection with the accompanying drawings.
Referring to fig. 1, the present invention provides a high-frequency ac wave defibrillator, which includes a dc power supply 1, a storage capacitor 2, a dc-dc conversion module 3, a dc-ac conversion module 4, and defibrillation electrodes 5, which are sequentially connected.
The direct current power supply 1 of the present invention provides energy to the defibrillator of the present invention, and the energy storage capacitor 2 is charged by the direct current power supply 1. Although the defibrillation pulse power of the invention is very high, the average power is very small due to the adoption of a slow charge and fast discharge capacitive energy storage method, so that the direct current power supply 1 can be used as a power supply of the defibrillator by using a battery or mains supply.
Preferably, the DC power supply 1 is a 12V to 24V DC power supply 1.
The storage capacitor 2 of the present invention is used to provide a discharge such that the discharge power meets defibrillation requirements. In order to avoid excessive drop in the amplitude of the defibrillation pulse during discharge, sufficient charge must be stored in the storage capacitor 2.
Preferably, the energy storage capacitor 2 is formed by connecting a plurality of high-frequency low-resistance electrolytic capacitors in parallel so as to reduce the volume of the defibrillator.
Preferably, the electrolytic capacitor is a 50V,6800 mu F high-frequency low-resistance electrolytic capacitor, and the internal resistance of the electrolytic capacitor is 15mΩ. If 30 electrolytic capacitors are adopted, the energy can be stored for 8.5J after the 30 electrolytic capacitors are connected in parallel, 255J can be stored, and the internal resistance is 0.5mΩ.
Preferably, the peak value of the storage voltage of the storage capacitor 2 is 50V, so that the storage voltage is in the safe very low voltage range. Therefore, the energy storage capacitor 2 can be charged immediately upon power-up. After defibrillation is completed, the remaining energy does not have to be discharged.
Preferably, in design, the storage voltage of the storage capacitor 2 is not too high compared with the dc power supply 1, for example, the storage voltage of 50V is close to the dc power supply 1 of 12V-24V, so that the dc power supply 1 can charge the storage capacitor 2 through a flyback boost circuit such as LM2587, and the charging of the storage capacitor 2 can be completed.
The direct current-direct current conversion module 3 of the present invention converts the low voltage direct current output from the storage capacitor 2 into high voltage direct current. The low voltage in the low voltage direct current is referred to the high voltage in the high voltage direct current, namely, the voltage of the low voltage direct current is lower than the voltage of the high voltage direct current, and the specific voltage value of the low voltage direct current is the output voltage of the energy storage capacitor 2. The voltage of the high-voltage direct current is determined according to the voltage required to be provided for the defibrillation electrode 5, and when the peak voltage required to be provided for the defibrillation electrode 5 is 1000V alternating current, the high-voltage direct current is 1000V direct current. When the energy storage voltage of the energy storage capacitor 2 is 50V, the direct current-direct current conversion module 3 boosts the 50V energy storage voltage output by the energy storage capacitor 2 to 1000V direct current.
The dc-dc conversion module 3 has a certain output resistance for automatically adjusting the amplitude of the defibrillation current according to the transthoracic impedance of the patient.
Preferably, the operating frequency of the DC-DC conversion module 3 is 100 kHz-300 kHz. For example, the 50V storage voltage is boosted to 1000V by using a dc-dc conversion module 3 with an operating frequency of 200 kHz.
Preferably, the direct current-direct current conversion module 3 adopts a push-pull topology structure based on transformer boosting so as to realize the boosting by the transformer.
Preferably, in order to maintain the magnetic balance of the transformer, the primary coil of the transformer is wound in parallel by a plurality of enameled wires. In order to solve the problem of large variation range of load resistance (human body resistance), the transformation ratio of the transformer is reduced, the efficiency is improved, and the AC voltage output by the secondary coil of the transformer is rectified by voltage doubling to generate DC output.
The direct current-alternating current conversion module 4 converts the high-voltage direct current output by the direct current-direct current conversion module 3 into high-voltage alternating current with preset frequency and provides the high-voltage alternating current for the defibrillation electrode 5. The voltage values of the high-voltage alternating current and the high-voltage direct current are preferably the same.
Preferably, the peak voltage output by the dc-ac conversion module 4 is 1000V, and the highest frequency is 1000Hz.
Preferably, the dc-ac conversion module 4 adopts an H-bridge circuit formed by four switches.
Preferably, since the output peak voltage is 1000V at the time of setting, the switch can be composed of a general 1200V series MOSFET switch or an IGBT and a general driver, so as to improve the reliability of the device and reduce the cost of the device.
The defibrillation electrode 5 of the present invention applies high-voltage alternating current to the human body to perform defibrillation.
Preferably, the high-frequency ac wave defibrillator of the present invention further comprises a detection and control system 6, the detection and control system 6 measures the voltages on the dc power supply 1 and the storage capacitor 2, the detection and control system 6 measures the connection status of the defibrillation electrode 5, the detection and control system 6 is respectively connected with the dc-dc conversion module 3 and the dc-ac conversion module 4, and the detection and control system 6 is used for controlling the on-operation or off-operation of the dc-dc conversion module 3 and the dc-ac conversion module 4.
The detection and control system 6 prohibits outputting the defibrillation pulse to ensure the defibrillation effect when the voltage is too low or the contact condition of the defibrillation electrode is poor.
The detection and control system 6 may control parameters such as defibrillation pulse width and frequency. The detection and control system 6 controls the parameters by being connected to the dc-ac conversion module 4. The detection and control system 6 controls the defibrillation pulse width to be between 0.25ms and 1ms, preferably 0.5ms; the detection and control system 6 controls the defibrillation pulse frequency between 500Hz and 2000Hz, preferably 1000Hz.
Preferably, the detection and control system 6 can employ prior art measurement methods, such as impedance methods or open circuit disturbance signal methods, in measuring the connection condition of the defibrillation electrode 5.
Preferably, the detection and control system 6 is further connected to the storage capacitor 2, and the detection and control system 6 receives a charging completion signal sent by the storage capacitor 2. The storage capacitor 2 adopts the prior art that can transmit a charge completion signal.
Preferably, the detection and control system 6 is also connected to a defibrillation button for the operator to issue defibrillation instructions.
Preferably, the operator operates the high frequency ac defibrillator of the present invention in three steps: 1. starting up; 2. pasting a defibrillation electrode 5;3. the defibrillation button is pressed.
When the high-frequency alternating-current wave defibrillator of the invention is started, the internal operation steps are as follows:
(1) Charging: the direct current power supply 1 charges the energy storage capacitor 2, the direct current power supply 1 supplies power to other modules, when the energy storage capacitor 2 reaches a voltage preset value, the charging is considered to be completed, and the energy storage capacitor 2 sends a charging completion signal to the detection and control system 6.
(2) Standby: the detection and control system 6 judges whether the voltage on the energy storage capacitor 2 reaches a preset voltage value (for example, 50V), if not, the abnormality is considered, otherwise, the abnormality is considered to be normal; the detection and control system 6 detects whether the contact quality of the defibrillation electrode 5 is in a preset range, if not, the defibrillation electrode is considered to be abnormal, otherwise, the defibrillation electrode is considered to be normal; when there is an abnormality, the detection and control system 6 issues an abnormality signal to notify the operator of the processing, and when it is considered normal, waits for acquisition of a defibrillation command issued by the operator.
When the detection and control system 6 sends out an abnormal signal, the operator can be informed to process through a display, a signal lamp or a photoelectric signal lamp and other prompting devices connected with the detection and control system 6.
In this step, the detecting and controlling system 6 detects whether the connection condition of the defibrillation electrode 5 is in a preset range or not, specifically, whether the contact quality of the defibrillation electrode 5 is within a preset range. Prior art measurement methods such as impedance methods or open-circuit interference signal methods may be used.
(3) Defibrillation: after receiving the defibrillation command, the detection and control system 6 starts the direct current-direct current conversion module 3 and the direct current-alternating current conversion module 4, outputs defibrillation pulses through the defibrillation electrodes 5, and after reaching the preset time, the detection and control system 6 closes the direct current-direct current conversion module 3 and the direct current-alternating current conversion module 4, and the defibrillation is finished.
Example 1:
a defibrillator shown in fig. 1 is used, and the defibrillator comprises a direct-current power supply 1, a storage capacitor 2, a direct-current-to-direct-current conversion module 3, a direct-current-to-alternating-current conversion module 4 and a defibrillation electrode 5 which are sequentially connected. The defibrillator also includes a detection and control system 6.
The direct current power supply 1 adopts a direct current power supply 1 with 12V to 24V, the energy storage voltage of the energy storage capacitor 2 is 50V, the direct current-direct current conversion module 3 and the direct current-alternating current conversion module 4 work together after defibrillation begins, the direct current-direct current conversion module 3 with the working frequency of 200kHz boosts the energy storage voltage of 50V to direct current of 1000V, the direct current-alternating current conversion module 4 converts 1000V direct current into 1000Hz alternating current, the peak voltage of the alternating current is 1000V, the power is up to 10kW, and the alternating current is provided for the defibrillation electrode 5 for defibrillation, and the defibrillation waveform at the moment is shown in figure 2. After the preset time, the direct current-direct current conversion module 3 and the direct current-alternating current conversion module 4 are closed, and defibrillation is finished.
The foregoing has shown and described the basic principles, principal features and advantages of the invention. It will be understood by those skilled in the art that the present invention is not limited to the embodiments described above, and that the above embodiments and descriptions are merely illustrative of the principles of the present invention, and various changes and modifications may be made without departing from the spirit and scope of the invention, which is defined in the appended claims. The scope of the invention is defined by the appended claims and equivalents thereof.
Claims (10)
1. The high-frequency alternating-current wave defibrillator comprises defibrillation electrodes and is characterized by further comprising the following components connected in sequence:
a DC power supply for supplying power to the high frequency AC wave defibrillator;
the energy storage capacitor is charged by the direct-current power supply;
the direct current/direct current conversion module is used for converting the low-voltage direct current output by the energy storage capacitor into high-voltage direct current;
and the output end of the direct current-alternating current conversion module is connected with the defibrillation electrode, and the high-voltage direct current output by the direct current-direct current conversion module is converted into alternating current with preset frequency and is supplied to the defibrillation electrode.
2. The high frequency ac defibrillator of claim 1 wherein said dc power source is a 12V to 24V dc power source.
3. The high frequency ac defibrillator of claim 1 wherein said storage capacitor is formed by a plurality of electrolytic capacitors in parallel;
the electrolytic capacitor is preferably a 50V 6800 mu F high-frequency low-resistance electrolytic capacitor;
the peak value of the storage voltage of the storage capacitor is preferably 50V.
4. The high frequency ac defibrillator of claim 1 wherein said dc power source charges said storage capacitor through a flyback boost circuit.
5. The high frequency ac defibrillator of claim 1 wherein the dc-dc conversion module operates at a frequency of 100kHz to 300kHz.
6. The high frequency ac defibrillator of claim 1 wherein said dc-dc conversion module employs a push-pull topology based on transformer boosting;
the primary coil of the transformer is preferably wound by a plurality of enameled wires, and the alternating voltage output by the secondary coil of the transformer is preferably rectified by voltage doubling to generate direct current output.
7. The high frequency ac defibrillator of claim 1 wherein the peak voltage output by said dc to ac conversion module is 1000V and the highest frequency is 1000Hz.
8. The high frequency ac defibrillator of claim 1 wherein said dc to ac conversion module is an H-bridge circuit of four switches.
9. The high frequency ac defibrillator of any one of claims 1 to 8, wherein said high frequency ac defibrillator further comprises:
and the detection and control system is used for respectively measuring the voltages on the direct current power supply and the energy storage capacitor, measuring the connection condition of the defibrillation electrode and respectively connecting with the direct current-direct current conversion module and the direct current-alternating current conversion module.
10. The high frequency ac defibrillator of claim 9 wherein said dc power source charges said storage capacitor, said dc power source providing power to other modules, and wherein when said storage capacitor reaches a predetermined voltage level, said storage capacitor is considered to be charged, and wherein said storage capacitor sends a charge complete signal to said detection and control system;
the detection and control system judges whether the voltage on the energy storage capacitor reaches a voltage preset value, if not, the detection and control system considers that the abnormality exists, otherwise, the detection and control system considers that the abnormality exists;
the detection and control system detects whether the contact quality of the defibrillation electrode is in a preset range, if not, the defibrillation electrode is considered to be abnormal, otherwise, the defibrillation electrode is considered to be normal;
when an abnormality exists, the detection and control system sends an abnormality signal to inform an operator to process, and when the abnormality is considered normal, a defibrillation instruction sent by the operator is waited to be acquired;
after a defibrillation command is received, the detection and control system starts the direct current-direct current conversion module and the direct current-alternating current conversion module, defibrillation pulse is output through the defibrillation electrode, and after a preset time is reached, the detection and control system closes the direct current-direct current conversion module and the direct current-alternating current conversion module, and defibrillation is finished.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310338477.XA CN116212242A (en) | 2023-03-31 | 2023-03-31 | High-frequency alternating-current wave defibrillator |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310338477.XA CN116212242A (en) | 2023-03-31 | 2023-03-31 | High-frequency alternating-current wave defibrillator |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116212242A true CN116212242A (en) | 2023-06-06 |
Family
ID=86585726
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202310338477.XA Pending CN116212242A (en) | 2023-03-31 | 2023-03-31 | High-frequency alternating-current wave defibrillator |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116212242A (en) |
-
2023
- 2023-03-31 CN CN202310338477.XA patent/CN116212242A/en active Pending
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US8718759B2 (en) | Multi-modal electrotherapy method and apparatus | |
| EP0808639B1 (en) | Patient-worn energy delivery apparatus | |
| JP2013525084A5 (en) | ||
| CN102974039A (en) | Defibrillator output stage with H bridge circuit and diphase sawtooth square wave defibrillation high-voltage discharge method | |
| US6104953A (en) | Method and apparatus for delivering defibrillation and pacing energy from a single power source | |
| CN104661702A (en) | Therapy delivery method and system for implantable medical devices | |
| CN103816615A (en) | Discharge dose accurate control method and device applied to cardiac defibrillator | |
| WO2010067373A2 (en) | Defibrillator charger | |
| US6253105B1 (en) | Method for delivering defibrillation energy | |
| US10238884B2 (en) | Cardiac-safe electrotherapy method and apparatus | |
| CN112426627B (en) | Biphase constant-current type heart defibrillator | |
| CN113440247B (en) | High-frequency irreversible electroporation tumor treatment system | |
| CN102974038A (en) | Extended H-bridge circuit in defibrillator capable of generating biphasic sawtooth discharging waveform | |
| CN102974040A (en) | Defibrillator with extended H bridge circuit output stage and biphase sawtooth square wave high-voltage discharge method for defibrillating | |
| CN116212242A (en) | High-frequency alternating-current wave defibrillator | |
| CN112439128B (en) | Ultra-low voltage energy storage type cardiac defibrillator | |
| CN101917027B (en) | Charging system for defibrillator | |
| CN210041442U (en) | Wireless charging system of cardiac pacemaker | |
| CN203139392U (en) | Extended H-bridge circuit in defibrillator capable of realizing high-voltage discharge | |
| CN102580245A (en) | Repetitive pulse type serve magnetic-stimulation emissive source | |
| CN113521536A (en) | Defibrillation current control method and defibrillator | |
| CN219847851U (en) | Automatic external defibrillator with pacing function | |
| CN219439389U (en) | Pulsed electric field therapeutic device | |
| CN216061693U (en) | Defibrillator | |
| CN113541325A (en) | Isolated defibrillator |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |