CN112510805A - Defibrillation energy storage capacitor and charging circuit - Google Patents
Defibrillation energy storage capacitor and charging circuit Download PDFInfo
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- CN112510805A CN112510805A CN202011444008.9A CN202011444008A CN112510805A CN 112510805 A CN112510805 A CN 112510805A CN 202011444008 A CN202011444008 A CN 202011444008A CN 112510805 A CN112510805 A CN 112510805A
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- 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
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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
- A61N1/3975—Power supply
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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
- A61N1/3975—Power supply
- A61N1/3981—High voltage charging circuitry
-
- 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
-
- 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
- H02J7/342—The other DC source being a battery actively interacting with the first one, i.e. battery to battery charging
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Power Engineering (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Heart & Thoracic Surgery (AREA)
- Biomedical Technology (AREA)
- Cardiology (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
The invention relates to a defibrillation energy storage capacitor and a charging circuit, wherein a storage battery is sequentially connected with the charging circuit and a low-voltage energy storage capacitor; the 1 st interface of a PWM chip IC1, a resistor R2 and a 14 th interface of an IC1 of the charging circuit are connected in series, the 1 st interface of an IC1, a capacitor C1, a resistor R1 and a 12 th interface of an IC1 are connected in series, a 13 th interface of an IC1 is connected between the C1 and the R1 in series, a 10 th interface of an IC1 is connected behind a capacitor C2 in series, the ground is connected in series, a 9 th interface of the IC1 is connected with a 6 th interface of an IC1 in series, a capacitor C3 is connected with the ground in series, a 3 rd interface of a dual operational amplifier IC2 is connected in series, an 8 th interface of the IC1 is connected with a 1 st interface of an IC2, a 4 th interface of an IC2 is grounded, an 8 th interface of an IC2 is connected with 12V, a 4 th interface of the IC2 is connected with a resistor R4 and a resistor R5, and a 4. The safety is ensured, waiting is not needed, stable and repeated charging and discharging can be realized, the economic effect is good, and the power consumption is reduced.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a defibrillation energy storage capacitor and a charging circuit which are safe, do not need to wait, can be stably and repeatedly charged and discharged, have good economic effect and reduce power consumption.
Background
The defibrillator uses the pulse heavy current to act on the heart, eliminates arrhythmia, and restores the heart to sinus rhythm, and has the advantages of high curative effect, quick action, simple operation, and the like. Since the end of 1962, bernard laonen invented a dc defibrillator and was successfully used in the clinic, and this dc defibrillation method has been used until now. In order to achieve high current output, a high-voltage energy storage capacitor is charged by direct current firstly, and then the high-voltage energy storage capacitor is rapidly discharged on the chest of a patient through an electrode after reaching a higher voltage, and the method is used up to now.
High voltage energy storage capacitors are important components of defibrillators, and are designed specifically to meet the reliability requirements of class III medical devices. The field reliability requirement is 100%. Defibrillators are typically measured in energy, and the electric field energy stored by a capacitor is proportional to the capacitance and the square of the voltage. To ensure defibrillation measurement accuracy, a high-precision capacitor needs to be used. The high-voltage energy storage capacitor requires withstand voltage of more than 2000V, capacity of about 120uF and pulse current as high as 40A. Other requirements include small size, low impedance, long lifetime, fast charge and fast discharge capacitance. Only a few countries of the world can manufacture. Not only is the price very high, but also the product is generally limited to supply.
The high-voltage energy storage capacitor needs to be charged before defibrillation every time, and the high-voltage energy storage capacitor needs to be discharged after defibrillation. In order to ensure the safety of medical staff and maintenance personnel, the national standard GB 9706.1-2007 general requirements for medical and electrical safety stipulates that the residual voltage on an internal energy storage element (e.g. a capacitor) must not exceed 60Vdc in a standby state. The charging time is required to be not more than 15s, and the charging can be carried out for about 3 times per minute. This not only misses the gold moment for rescuing the patient, but also wastes energy in the battery.
There is a need for a defibrillation energy storage capacitor and a charging circuit that are safe, do not need to wait, can be stably and repeatedly charged and discharged, have good economic effects, and reduce power consumption.
Disclosure of Invention
The invention aims to provide a defibrillation energy storage capacitor and a charging circuit which are safe, do not need to wait, can be stably and repeatedly charged and discharged, have good economic effect and reduce power consumption.
A defibrillation storage capacitor and charging circuit comprising:
the storage battery is sequentially connected with the charging circuit and the low-voltage energy storage capacitor;
the 1 st interface of a PWM chip IC1, the 14 th interfaces of resistors R2 and IC1 of the charging circuit are connected in series, the 1 st interface of an IC1, the capacitor C1, the resistor R1 and the 12 th interface of an IC1 are connected in series, the 13 th interface of the IC1 is connected between C1 and R1 in series, the 10 th interface of the IC1 is connected after being connected with the capacitor C1 in series, the ground is connected in series, the 9 th interface of the IC1 is connected with the 6 th interface of the IC1 in series, the capacitor C1 is connected with the ground in series, the 3 rd interface of the dual operational amplifier IC1 is connected in series, the 8 th interface of the IC1 is connected with the 1 st interface of the IC1, the 4 th interface of the IC1 is connected with the ground, the 4 th interface of the IC1 is connected with the resistor R1 and the gate field effect transistor Q1, the gate 1 is connected between the 5 th interface of the IC1 and the IC1, the drain electrode of Q1 connects 12V behind transformer T1, the 7 th interface of IC1 is connected all the way to the source electrode of Q1, connect diode D1 behind the T1 all the way connection, connect R5 all the way, connect electric capacity C4 with ground connection respectively all the way, C4 and R4 are connected respectively to D1, connect the 60V interface between C4 and the R4.
The low-voltage energy storage capacitor is formed by connecting a super capacitor, an electrolytic capacitor and a multilayer ceramic chip capacitor in parallel.
The voltage of the storage battery is 12V.
The storage battery is sequentially connected with the charging circuit and the low-voltage energy storage capacitor; the 1 st interface of a PWM chip IC1, a resistor R2 and a 14 th interface of an IC1 of the charging circuit are connected in series, the 1 st interface of the IC1, a capacitor C1, a resistor R1 and a 12 th interface of the IC1 are connected in series, a 13 th interface of the IC1 is connected between the C1 and the R1 in one way, a 10 th interface of the IC1 is connected after the capacitor C1 is connected in one way, the ground is connected in one way, a 9 th interface of the IC1 is connected with a 6 th interface of the IC1 in one way, the capacitor C1 is connected with the ground in one way, a 3 rd interface of the dual operational amplifier IC1 is connected in one way, an 8 th interface of the IC1 is connected with the 1 st interface of the IC1, a 4 th interface of the IC1 is connected with the ground, an 8 th interface of the IC1 is connected with a 12V, a 4 th interface of the IC1 is connected with the resistor R1 and the R1, a 5 th interface of the IC1 is connected with the 7 th interface of the IC1 in series, a field effect transistor Q1 is connected with the gate 1 and the transistor Q1. The source of Q1 is connected with the 7 th interface of IC1 all the way, and all the way is connected with diode D1 behind T1, and all the way is connected with R5, and all the way is ground connection respectively and is connected electric capacity C4, and D1 is connected C4 and R4 respectively, connect the 60V interface between C4 and the R4. The safety is ensured, waiting is not needed, stable and repeated charging and discharging can be realized, the economic effect is good, and the power consumption is reduced.
The invention has the beneficial effects that:
1. the safety of medical staff and maintenance staff is ensured by adopting the low-voltage energy storage capacitor with the voltage less than 60V;
2. the energy in the energy storage capacitor is directly converted into pulse current by using a high-power pulse generator, the energy in the energy storage capacitor is enough to transmit defibrillation pulses for three times, and the pulse transmission for each time does not need to wait;
3. the characteristic change of the super capacitor is very small, the charge-discharge efficiency of the super capacitor is high, the super capacitor has certain bearing capacity on overcharge and overdischarge, and the super capacitor can be stably and repeatedly charged and discharged;
4. the electrolytic capacitor is mainly used for providing energy for patients, has overwhelming advantages in price compared with other types, and is widely applied;
5. the MLCC is used for providing instant heavy current for the converter, and has the advantages of large capacity, low equivalent resistance, excellent noise absorption, better pulse resistance, small overall dimension, high insulation resistance, better impedance temperature characteristic and frequency characteristic; the self-sealing electrode has good self-sealing property, can effectively avoid the inner electrode from being affected with damp and polluted, and obviously improves the flashover voltage and the breakdown voltage;
6. the invention has no leakage current, the load is light, and the charger works in an intermittent mode to reduce the static power consumption of the circuit.
Drawings
FIG. 1 is a schematic structural view of the present invention;
FIG. 2 is a schematic diagram of a charging circuit according to the present invention;
in the figure: 1. the device comprises a storage battery, 2, a charging circuit, 3 and a low-voltage energy storage capacitor.
Detailed Description
The invention is further described below with reference to the following figures and specific examples.
A defibrillation storage capacitor and charging circuit comprising:
the storage battery 1, the storage battery 1 connects charging circuit 2, low-voltage energy-storage capacitor 3 sequentially; a 1 st interface of a PWM chip IC1, a 14 th interface of a resistor R2 and an IC1 of the charging circuit 2 are connected in series, a 1 st interface of the IC1, a capacitor C1, a resistor R1 and a 12 th interface of the IC1 are connected in series, a 13 th interface of the IC1 is connected between the C1 and the R1 in series, a 10 th interface of the IC1 is connected after the capacitor C1 is connected in series, a ground is connected after the capacitor C1 is connected, a 6 th interface of the IC1 is connected after the capacitor C1 is connected in series, a 3 rd interface of the dual operational amplifier IC1 is connected in series, an 8 th interface of the IC1 is connected with the 1 st interface of the IC1, a 4 th interface of the IC1 is connected with the ground, an 8 th interface of the IC1 is connected with the 6 th interface of the IC1 in series, a 4 th interface of the IC1 is connected with the resistor R1 and the gate 1, a field effect transistor Q1 is connected between the 5 th interface of the IC1 and the gate 1, the drain electrode of Q1 connects 12V behind transformer T1, the 7 th interface of IC1 is connected all the way to the source electrode of Q1, connect diode D1 behind the T1 all the way connection, connect R5 all the way, connect electric capacity C4 with ground connection respectively all the way, C4 and R4 are connected respectively to D1, connect the 60V interface between C4 and the R4.
The low-voltage energy storage capacitor 3 is formed by connecting a super capacitor, an electrolytic capacitor and a multilayer ceramic chip capacitor in parallel. The voltage of the battery 1 is 12V.
The invention adopts a low-voltage energy storage capacitor with the voltage less than 60V, and the energy in the storage battery 1 is stored in the low-voltage energy storage capacitor 3 by a charging circuit 2 in advance. When in defibrillation, the energy in the low-voltage energy storage capacitor 3 is directly converted into pulse current by using a high-power pulse generator. The energy in the low voltage energy storage capacitor 3 is sufficient to fire three defibrillation pulses. So that each time a pulse is transmitted there is no need to wait. Pulses of voltage 2000V, current 40A were output according to the law of conservation of energy. Input voltage 60V, input current 1330A. The storage capacitor should be capable of supplying a large current instantaneously.
The low-voltage energy storage capacitor 3 adopts a super capacitor, an electrolytic capacitor and a multilayer ceramic chip capacitor (MLCC) which are connected in parallel. To meet the above requirements. For this purpose, a supercapacitor, an electrolytic capacitor and a multilayer ceramic chip capacitor (MLCC) are connected in parallel.
Compared with the traditional capacitor, the super capacitor has larger capacity and energy density and long cycle life. After 50-100 ten thousand cycles of high-speed deep charge-discharge in a few seconds, the characteristic change of the super capacitor is small, the charge-discharge efficiency of the super capacitor is high, the super capacitor has certain bearing capacity for overcharging and overdischarging, and the super capacitor can be stably and repeatedly charged and discharged. However, the super capacitor has a large internal resistance and a poor ability of instantly outputting a large current. The energy stored by the super capacitor is used primarily for second and third defibrillation.
Electrolytic capacitors are primarily used to provide energy to a patient. An electrolytic capacitor includes: the capacitance per unit volume is very large, and is dozens to hundreds of times larger than other types of capacitors; the rated capacity can be very large, and tens of thousands of uF or even several F (but the capacitance ratio of the capacitor to the double electric layers) can be easily achieved; the price has overwhelming advantages compared with other types, and the application is wide, such as a switch power supply, a camera flash lamp and the like.
Multilayer ceramic chip capacitors (MLCCs), also known as monolithic capacitors, have good high frequency characteristics and are mainly used to provide instantaneous high currents to the converter. The MLCC has the advantages of large capacity, low equivalent resistance, excellent noise absorption, better pulse resistance, small overall dimension, high insulation resistance, better impedance temperature characteristic and frequency characteristic; and the self-sealing electrode has good self-sealing property, can effectively avoid the inner electrode from being affected with damp and polluted, and obviously improves the flashover voltage and the breakdown voltage.
The charging circuit 2: the control chip adopts a micro-power consumption voltage mode PWM chip UCC3581 produced by TI company, is a control chip designed for a micro-power consumption high-efficiency DC-DC converter and is mainly used for a single-ended forward flyback converter. The device is manufactured by adopting a BICMOS process, the starting current is 80 muA, the working current is 300 muA, so the device is particularly suitable for a micro-power consumption high-efficiency converter, the working frequency is up to more than 100kHz, and the frequency and the maximum duty ratio of an oscillator in UCC3581 can be changed by using two resistors and one capacitor.
The transformer T1 and the switching tube Q1 form a flyback boost converter, and the 12V direct-current input voltage is boosted to 0-60V. The converter operates in an intermittent mode when the load is light when there is no leakage current to reduce the static power consumption of the circuit.
Resistors R1, R2 and capacitor C1 constitute a set frequency of the internal oscillator of UCC3581 to 6kHz with a maximum duty cycle set to 70%. The capacitor C2 is a soft start capacitor, and the capacitor C3 is a filter capacitor for filtering out ripples on the 6 th pin of the reference voltage IC 1.
The diode D1 and the capacitor C4 form a rectifying and smoothing circuit, and convert the ac power output from the transformer T1 into dc power. And the voltage division circuit consists of resistors R4 and R5 and is used for collecting output voltage and sending the collected voltage to a pin 2 of an inverted input end pin of the error amplifier IC 2. Resistor R6 sets a voltage to pin 3 of the non-inverting input of IC2 for determining the set value of the output voltage.
The whole circuit forms a negative feedback circuit to stabilize the output voltage at the set value. When the high-voltage output voltage drops, the output voltage of the error amplifier rises, the 4 th pin output pulse of the IC1 becomes wide, the energy stored in the switch tube Q1 is increased every time the switch tube is turned on, and the output voltage rises. When the high-voltage output voltage rises, the output voltage of the error amplifier drops, the 4 th pin output pulse of the IC1 is narrowed, the energy stored in the switch tube Q1 is reduced every time the switch tube is turned on, and the output voltage drops.
The foregoing illustrates and describes the principles, general features, and advantages of the present invention. It will be understood by those skilled in the art that the present invention is not limited to the embodiments described above, which are given by way of illustration of the principles of the present invention, and that various changes and modifications may be made without departing from the spirit and scope of the invention as defined by the appended claims. The scope of the invention is defined by the appended claims and equivalents thereof.
Claims (3)
1. A defibrillation storage capacitor and charging circuit, comprising:
the storage battery (1), the storage battery (1) connects charging circuit (2), low-voltage energy-storage capacitor (3) sequentially;
a 1 st interface of a PWM chip IC1, a 14 th interface of a resistor R2 and an IC1 of the charging circuit (2) are connected in series, a 1 st interface of an IC1, a capacitor C1, a resistor R1 and a 12 th interface of an IC1 are connected in series, a 13 th interface of an IC1 is connected between the C1 and the R1 through a line, a 10 th interface of an IC1 is connected behind a line connecting a capacitor C2, and is connected to ground through a line, a 6 th interface of an IC1 is connected to ground through a line connecting a capacitor C1, a 3 rd interface of a dual operational amplifier IC1 is connected through a line, an 8 th interface of the IC1 is connected to a 1 st interface of the IC1, a 4 th interface of the IC1 is connected to ground, an 8 th interface of the IC1 is connected to 12V, a 4 th interface of the IC1 is connected to a resistor R1 and a resistor R1 respectively, a 5 th interface of the IC1 and a 7 th interface of the IC1 are connected to ground through a resistor R1, and a resistor R1, a resistor 36, the grid of field effect transistor Q1 is connected, 12V is connected behind the drain electrode of Q1 connection transformer T1, the 7 th interface of IC1 is connected all the way to the source electrode of Q1, connect diode D1 behind all the way connection T1, connect R5 all the way, all the way ground connection and connection electric capacity C4 respectively, C4 and R4 are connected respectively to D1, connect the 60V interface between C4 and the R4.
2. A defibrillation capacitor and charging circuit according to claim 1, characterized in that the low voltage capacitor (3) is a super capacitor, an electrolytic capacitor and a multi-layer ceramic capacitor connected in parallel.
3. A defibrillation storage capacitor and charging circuit according to claim 1, characterized in that the voltage of the battery (1) is 12V.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202011444008.9A CN112510805A (en) | 2020-12-08 | 2020-12-08 | Defibrillation energy storage capacitor and charging circuit |
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| Application Number | Priority Date | Filing Date | Title |
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| CN202011444008.9A CN112510805A (en) | 2020-12-08 | 2020-12-08 | Defibrillation energy storage capacitor and charging circuit |
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| CN112510805A true CN112510805A (en) | 2021-03-16 |
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| CN202011444008.9A Pending CN112510805A (en) | 2020-12-08 | 2020-12-08 | Defibrillation energy storage capacitor and charging circuit |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114470536A (en) * | 2022-01-30 | 2022-05-13 | 清华大学 | Pulse modulator and charging method thereof |
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| CN101564574A (en) * | 2008-04-23 | 2009-10-28 | 温立 | High-voltage pulse generating circuit suitable for extracorporeal defibrillator |
| CN203827040U (en) * | 2014-04-30 | 2014-09-10 | 刘明美 | Charging circuit for external defibrillator |
| CN205041397U (en) * | 2015-08-26 | 2016-02-24 | 深圳市理邦精密仪器股份有限公司 | PCB layer capacitance module and anti electric shock heart electrical detection circuitry |
| CN110520190A (en) * | 2017-04-27 | 2019-11-29 | 维曼急救医疗科技两合公司 | Method and apparatus for defibrillation |
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2020
- 2020-12-08 CN CN202011444008.9A patent/CN112510805A/en active Pending
Patent Citations (4)
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| CN101564574A (en) * | 2008-04-23 | 2009-10-28 | 温立 | High-voltage pulse generating circuit suitable for extracorporeal defibrillator |
| CN203827040U (en) * | 2014-04-30 | 2014-09-10 | 刘明美 | Charging circuit for external defibrillator |
| CN205041397U (en) * | 2015-08-26 | 2016-02-24 | 深圳市理邦精密仪器股份有限公司 | PCB layer capacitance module and anti electric shock heart electrical detection circuitry |
| CN110520190A (en) * | 2017-04-27 | 2019-11-29 | 维曼急救医疗科技两合公司 | Method and apparatus for defibrillation |
Non-Patent Citations (1)
| Title |
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| TEXAS INSTRUMENTS: "芯片手册Micropower Voltage Mode PWM-UCC3581", 《UNITRODE PRODUCTS FROM TEXAS INSTRUMENTS》 * |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114470536A (en) * | 2022-01-30 | 2022-05-13 | 清华大学 | Pulse modulator and charging method thereof |
| CN114470536B (en) * | 2022-01-30 | 2023-06-13 | 清华大学 | Pulse modulator and charging method thereof |
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