CN218793573U

CN218793573U - External defibrillator

Info

Publication number: CN218793573U
Application number: CN202221752838.2U
Authority: CN
Inventors: 李萍; 单纯玉
Original assignee: Shanghai University of Medicine and Health Sciences
Current assignee: Shanghai University of Medicine and Health Sciences
Priority date: 2022-07-08
Filing date: 2022-07-08
Publication date: 2023-04-07
Anticipated expiration: 2032-07-08

Abstract

The utility model belongs to the technical field of medical instrument, concretely relates to external defibrillator. An external defibrillator comprising a DC power source and a pair of defibrillation electrodes; still include the consecutive connection between DC power supply and a pair of defibrillation electrode: the resistance reducing loop is connected with the direct current power supply and reduces the internal resistance of the direct current power supply to a preset internal resistance of the power supply; the impedance matching loop is connected with the resistance reducing circuit, matches the internal resistance of the power supply with the transthoracic impedance of the human body and is provided with a defibrillation voltage output end; and the electrode switching loop is respectively connected with the defibrillation voltage output end or the defibrillation electrode, and switches the connection relation between the impedance matching loop and the defibrillation electrode. The utility model discloses need not to measure through chest impedance, can be according to the electric current of defibrillating through chest impedance adjustment, indirect compensation is through heart electric current, makes through heart electric current reach the expectation value, is fit for kind of defibrillation electrode, has reduced the complexity of design.

Description

External defibrillator

Technical Field

The utility model belongs to the technical field of medical instrument, concretely relates to external defibrillator.

Background

External defibrillators apply electrical pulses to the skin of a patient via electrodes (external electrodes), thereby implementing a device for electrically defibrillating the heart. The first aid is used for emergency treatment of patients with ventricular fibrillation, ventricular tachycardia and suspected cardiac arrest.

The principle of defibrillation is to apply a strong electrical pulse to the heart within a very short time, causing most of the cardiogenic cells to depolarize simultaneously within a short time, inactivating all of the reentrant channels that may be present, allowing the sinoatrial node to return to dominantly controlling the heart beat, and restoring sinus rhythm.

International guidelines for cardiopulmonary resuscitation and cardiovascular first aid 2000 state that "defibrillation" relies on the successful selection of appropriate energy to produce an effective current through the heart (via cardiac current) to achieve defibrillation while causing minimal electrical damage to the heart. If the energy and current are too small, a shock cannot terminate the arrhythmia; whereas if the energy and current are too large, functional or morphological damage to the heart may occur. Selecting the appropriate current also reduces the number of repetitive shocks, thereby reducing myocardial damage. "

The key factor in defibrillation success is cardioversion, and energy is only the means by which current is generated. The average cardiogenic current is an effective component for defibrillation, and the higher the average cardiogenic current is, the higher the defibrillation success rate is. The peak cardiocirculatory current is the main component of the damaged cardiac muscle function, and the higher the peak cardiocirculatory current or the larger the average cardiocirculatory current, the more serious the cardiac muscle damage degree.

The defibrillation waveform is a key factor influencing the defibrillation success rate and mainly comprises the time phase, the shape, the pulse width, the peak-to-average ratio and the like of the waveform. The two-phase wave has two time phases in sequence: the first phase is a positive phase, and the current flows from the positive electrode to the negative electrode; the second phase is a negative phase and current flows in the opposite direction between the positive and negative electrodes. The first phase residual charge is cleared by the second phase current in the opposite direction, so that the recurrence rate of ventricular fibrillation after defibrillation can be reduced.

Recent research data indicate that: "the effective time of the current for stopping ventricular fibrillation is not more than 12 milliseconds, and the current more than 12 milliseconds has no significance for improving the defibrillation effect, but can increase the damage degree of myocardial function and cause the recurrence of ventricular fibrillation. "

The impedance compensation technology is that the defibrillator adjusts parameters in the discharge process according to the measured transthoracic impedance of a patient so as to improve the success rate of defibrillation and realize individualized defibrillation. The main problems with this approach are: 1. the measurement of the transthoracic impedance must be completed during defibrillation charging, so that the electrode plate is only suitable for defibrillation electrode plates and is not suitable for defibrillation electrode plates, and the defibrillation electrode plates are still the most popular defibrillation mode. 2. The transthoracic impedance measurement and defibrillation pulse delivery are performed in a time-sharing manner, and the real-time performance is poor. 3. The transthoracic impedance needs to be measured, increasing the complexity of the circuit, the more complex the circuit the less reliable it is.

SUMMERY OF THE UTILITY MODEL

The utility model discloses need survey among the prior art through the technical problem that chest impedance adjusted the parameter of the in-process of discharging, aim at provides one kind and need not to measure the external defibrillator that just can realize dynamic adjustment through chest impedance.

An external defibrillator comprising a DC power source and a pair of defibrillation electrodes;

the direct current power supply and the pair of defibrillation electrodes are sequentially connected:

the resistance reducing loop is connected with the direct current power supply and reduces the internal resistance of the direct current power supply to a preset internal resistance of the power supply;

the impedance matching loop is connected with the resistance reducing circuit, matches the internal resistance of the power supply with the transthoracic impedance of the human body and is provided with a defibrillation voltage output end;

and the electrode switching loop is respectively connected with the defibrillation voltage output end or the defibrillation electrode and switches the connection relation between the impedance matching loop and the defibrillation electrode.

Preferably, the direct current power supply adopts a 15V disposable battery.

As a preferred scheme, the resistance reducing loop adopts a resistance reducing capacitor;

the direct current power supply is grounded through the resistance reducing capacitor.

Preferably, the resistance reducing capacitor is formed by connecting at least one of a high-frequency low-resistance capacitor or a super capacitor in parallel.

Preferably, the impedance matching circuit includes:

a switch compensation signal terminal;

an oscillator, two output ends are switch pulses with phase difference of 180 degrees;

at least one set of impedance matching components, each set of impedance matching components comprising:

two input ends of the double-path driver are respectively connected with two output ends of the oscillator, and two enabling ends of the double-path driver are both connected with the switch compensation signal end;

the primary side of the transformer is provided with a primary side tap, and the primary side tap is connected with the direct-current power supply;

the grid electrode of the first NMOS tube is connected with one output end of the double-path driver, the source electrode of the first NMOS tube is grounded, and the drain electrode of the first NMOS tube is connected with one primary side end of the transformer;

the grid electrode of the second NMOS tube is connected with the other output end of the double-path driver, the source electrode of the second NMOS tube is grounded, and the drain electrode of the second NMOS tube is connected with the other end of the primary side of the transformer;

and secondary sides of the transformers in the impedance matching assemblies are connected in series and then are connected with the defibrillation voltage output end through a voltage doubling rectifying circuit.

As a preferred scheme, the first NMOS transistor and the second NMOS transistor are N-channel insulated gate field effect transistors having a drain-source on-resistance smaller than 1m Ω.

Preferably, the voltage-doubling rectifying circuit is a voltage-doubling rectifying circuit formed by a plurality of rectifying capacitors and a plurality of rectifying diodes;

and the rectifier capacitor adopts a patch capacitor.

Preferably, the oscillator includes:

the two output ends of the power switch driver are respectively connected with the two input ends of the two-way driver;

one end of the timing capacitor is grounded, and the other end of the timing capacitor is connected with the input end of the timing capacitor of the power switch driver;

one end of the first timing resistor is connected with the input end of the power supply, and the other end of the first timing resistor is connected with the discharge end of the timing capacitor of the power switch driver;

and one end of the second timing resistor is connected with the input end of the timing capacitor, and the other end of the second timing resistor is connected with the discharge end of the timing capacitor.

Preferably, the power switch driver adopts a push-pull MOSFET power switch driver with an oscillator and a dead time compensation function, and the power switch driver adopts a power switch driver with an oscillation frequency of 200kHz and a dead time of 150 ns.

Preferably, the electrode switching loop adopts two single-pole double-throw electronic switches, and one single-pole double-throw electronic switch corresponds to one defibrillation electrode;

the common end of the single-pole double-throw electronic switch is connected with the corresponding defibrillation electrode, the normally closed end of the single-pole double-throw electronic switch is grounded, and the normally open end of the single-pole double-throw electronic switch is connected with the defibrillation voltage output end.

As a preferred scheme, the power switch driver adopts a PWM controller chip;

the external defibrillator further includes a closed loop compensation circuit, the closed loop compensation circuit comprising:

one end of the two defibrillation voltage sampling resistors is connected with the defibrillation voltage output end after being connected in series, and the other end of the two defibrillation voltage sampling resistors is grounded;

the defibrillation current sampling resistor is connected with a load resistor in series, and the load resistor is the equivalent resistor of the human body;

the non-inverting input end of the first voltage follower is connected with the common end of the two defibrillation voltage sampling resistors, and the inverting input end of the first voltage follower is connected with the output end;

the non-inverting input end of the second voltage follower is connected with one end of the defibrillation current sampling resistor, and the inverting input end of the second voltage follower is connected with the output end;

the in-phase adder is characterized in that the in-phase input end of the in-phase adder is connected with the output end of the first voltage follower through a third resistor, the in-phase input end of the in-phase adder is connected with the output end of the second voltage follower through a fourth resistor, the reverse phase input end of the in-phase adder is connected with the output end through a fifth resistor, the reverse phase input end of the in-phase adder is grounded through a sixth resistor, and the third resistor, the fourth resistor, the fifth resistor and the sixth resistor have the same resistance value;

and the non-inverting input end of the error amplifier is connected with a preset voltage end, the inverting input end of the error amplifier is connected with the output end of the non-inverting adder, and the output end of the error amplifier is connected with the error signal input end of the PWM controller chip.

As a preferred scheme, the PWM controller chip controls the voltage at the output terminal of the in-phase adder to be equal to the preset voltage provided by the preset voltage terminal;

the compensation mode of the closed loop compensation circuit adopts the following formula:

V _SET ＝(kV _DF +R _S I _DF )

wherein R is ₁ And R ₂ For two of said defibrillation voltage sampling resistors, R _S Sampling resistance, V, for the defibrillation current _SET A predetermined voltage, V, provided to said predetermined voltage terminal _DF A defibrillation voltage, I, provided to the defibrillation voltage output terminal _DF A defibrillation current;

at k and R _S After fixing, by varying the preset voltage V _SET To change the defibrillation current I _DF 。

The utility model discloses an actively advance the effect and lie in: the utility model discloses an external defibrillator has following advantage:

1. the defibrillation current is adjusted according to the transthoracic impedance, and the transcardial current is indirectly compensated to reach the expected value. The defibrillation current is appropriately increased when the transthoracic impedance is low and decreased when the transthoracic impedance is high to ensure that sufficient current flows through the heart. The utility model discloses need not to measure through chest impedance, real-time dynamic adjustment's purpose is fit for kind of defibrillation electrode, has reduced the complexity of design.

2. The direct current power supply provides a low-voltage power supply to provide energy for the defibrillator; the resistance reduction loop reduces the internal resistance of the low-voltage power supply to a microohm level; the impedance matching loop matches the internal resistance of the power supply with the transthoracic impedance of the human body, so that the defibrillation current flows through the transthoracic impedance of the human body; the electrode switching circuit switches the connection relation between the impedance matching circuit and the defibrillation electrode, and the obtained defibrillation waveform is a fixed pulse width biphasic wave.

3. The utility model discloses an external defibrillator simple structure, small, light in weight are fit for once only defibrillating and use and wearable defibrillate and use.

Drawings

Fig. 1 is a schematic connection diagram of the present invention;

fig. 2 is a schematic diagram of an open loop compensation circuit according to the present invention;

fig. 3 is a graph of a compensation signal and a defibrillation waveform corresponding to the circuit schematic of fig. 2;

FIG. 4 is a graph of defibrillation current versus transthoracic impedance;

FIG. 5 is a graph of defibrillation voltage versus transthoracic impedance;

FIG. 6 is a graph of defibrillation power versus transthoracic impedance;

fig. 7 is a schematic diagram of a closed-loop compensation circuit according to the present invention.

Detailed Description

In order to make the technical means, creation features, achievement purposes and functions of the present invention easy to understand, the present invention will be further explained with reference to the specific drawings.

In the utility model, when describing the external defibrillator:

1. the defibrillation current refers to a current flowing through the defibrillation electrode when discharging a cardiac shock.

2. Cardiotomy current is the current flowing through the heart when discharging a shock to the heart.

3. The defibrillation voltage refers to the potential difference between the two defibrillation electrodes when discharging a cardiac shock.

4. The defibrillation waveform refers to a curve of defibrillation current changing with time when discharging a cardiac shock.

5. Transthoracic impedance refers to the equivalent impedance between two defibrillation electrodes. Transthoracic impedance is equivalent to electrical resistance, since the capacitive reactance component is very small. The transthoracic impedance ranges from 25 Ω to 175 Ω. Factors that determine transthoracic electrical impedance include: electrode pad size, defibrillator-skin interface, defibrillation count and interval, respiration phase, distance between electrodes (determined by the size of the thorax), and the pressure with which the defibrillator is placed on the skin. Transthoracic impedance is the only variable for defibrillation.

Referring to fig. 1, an external defibrillator includes a dc power supply 1, a resistance reduction circuit 2, an impedance matching circuit 3, an electrode switching circuit 4, and a pair of defibrillation electrodes 5, which are connected in sequence.

DC power supply 1 provides the low voltage power supply, the utility model discloses a DC power supply 1 preferably adopts 15V disposable battery. Because the internal resistance of the disposable battery is in the ohm level, the instant current of the ampere level can be provided.

The resistance reducing loop 2 is connected with the direct current power supply 1, the resistance reducing loop 2 reduces the internal resistance of the direct current power supply 1 to a preset internal resistance of the power supply, for example, to a microohm level, and the low-voltage power supply can provide an instant current of a kiloampere level after passing through the resistance reducing loop 2.

Referring to fig. 2, the resistance reducing circuit 2 employs a resistance reducing capacitor C1, and the dc power supply 1 is grounded via the resistance reducing capacitor C1. The resistance reducing capacitor C1 is preferably formed by at least one of a high-frequency low-resistance capacitor or a super capacitor connected in parallel. The high frequency low resistance capacitor functions to reduce the internal resistance of the dc power supply 1 and the supercapacitor functions to provide sufficient charge during the discharge pulse. The larger the resistance reducing capacitor C1 is, the smaller the voltage drop on the resistance reducing capacitor C1 in the discharging process is, the smaller the peak-to-average ratio of defibrillation current is, the better the defibrillation effect is, and the smaller the myocardial damage is.

The impedance matching circuit 3 is connected with the resistance reducing circuit, the impedance matching circuit 3 matches the internal resistance of the power supply with the transthoracic impedance of the human body to enable the transthoracic impedance of the human body to flow defibrillation current, the impedance matching circuit 3 is provided with a defibrillation voltage output end, and the defibrillation voltage output end outputs defibrillation voltage V _DF 。

Referring to fig. 2, the impedance matching circuit 3 is preferably composed of a transformer and its auxiliary circuit, which is an element except for the resistance-reducing capacitor C1 in fig. 2. Specifically, the impedance matching circuit 3 includes a switch compensation signal terminal, an oscillator, and at least one set of impedance matching components.

The switch compensation signal terminal is an ON/OFF terminal in fig. 2, the ON/OFF terminal provides a high-level ON signal or a low-level OFF signal, defibrillation current is provided when the ON terminal is turned ON, and defibrillation is finished when the OFF terminal is turned OFF. The ON/OFF terminal is controlled and provided by an external timer, and an operator can output a high-level opening signal by pressing a defibrillation switch of the defibrillator and then the timer. Since the discharge time is in millisecond level and the pressing of the switch may last for several seconds, when the discharge time reaches 10 milliseconds as preset, and the hand of the operator pressing the defibrillation switch is not lifted, the timer will automatically change the signal at the ON/OFF end into the low-level OFF signal, and the discharge is finished.

The two output ends of the oscillator are switching pulses with a phase difference of 180 degrees. Referring to fig. 2, the oscillator preferably includes a power switch driver IC1, a timing capacitor C2, a first timing resistor R7, and a second timing resistor R8.

Two output ends of the power switch driver IC1 are respectively connected to two input ends of each dual driver in the impedance matching module. As shown in fig. 2, there are two sets of impedance matching assemblies, each set of impedance matching assemblies has a dual driver, which is a dual driver IC2 and a dual driver IC3, respectively, then one output terminal (OUTA terminal) of the power switch driver IC1 is connected to one input terminal (INA terminal) of the dual driver IC2 and one input terminal (INA terminal) of the dual driver IC3, respectively, and the other output terminal (OUTB terminal) of the power switch driver IC1 is connected to the other input terminal (INB terminal) of the dual driver IC2 and the other input terminal (INB terminal) of the dual driver IC3, respectively. The voltage input terminal (VDD terminal) of the power switch driver IC1 is connected to a power supply input terminal, which supplies +12V dc power. The ground terminal (GND terminal) and the current sampling input terminal (CS terminal) of the power switch driver IC1 are both grounded.

One end of the timing capacitor C2 is grounded, and the other end of the timing capacitor C2 is connected to a timing capacitor input terminal (CT terminal) of the power switch driver IC1.

One end of the first timing resistor R7 is connected to a power supply input terminal, the power supply input terminal provides a +12V dc power supply, and the other end of the first timing resistor R7 is connected to a timing capacitor discharge terminal (DIS terminal) of the power switch driver IC1.

One end of the second timing resistor R8 is connected with the input end (CT end) of the timing capacitor, and the other end of the second timing resistor R8 is connected with the discharge end (DIS end) of the timing capacitor.

The utility model discloses a power switch driver IC1, timing electric capacity C2, first timing resistance R7 and second timing resistance R8 constitute the oscillator, and wherein power switch driver IC1 adopts the push-pull MOSFET power switch driver IC1 who has the oscillator certainly of dead time compensation function. The power switch driver IC1 is preferably a UCC28089 chip. The series of chips are push-pull MOSFET power switch drivers with own oscillators and with dead time compensation functions, and the driving capacity of the power switch drivers is 0.5A. The UCC28089 chip has a low start-up current.

The timing capacitor C2, the first timing resistor R7 and the second timing resistor R8 are used to determine the oscillation frequency and the dead time. The utility model discloses select oscillation frequency preferred 200kHz, the dead time is 150ns, and power switch driver IC 1's OUTA end, OUTB end output two phase differences 180 frequency are 100 kHz's switching pulse.

The impedance matching components may be provided in one or more sets, preferably in a plurality of sets, and more preferably in two sets as shown in fig. 2, as desired. Taking the two impedance matching components shown in fig. 2 as an example, the two impedance matching components include a two-way driver IC2, a two-way driver IC3, a transformer T1, a transformer T2, a first NMOS transistor Q1, a first NMOS transistor Q3, a second NMOS transistor Q2, a second NMOS transistor Q4, and a voltage-doubling rectifying circuit. Taking one of the impedance matching components as an example, the circuit connection relationship is as follows:

one input end (INA end) of the double-circuit driver IC2 is connected with one output end (OUTA end) of the oscillator, the other input end (INB end) of the double-circuit driver IC2 is connected with one output end (OUTB end) of the oscillator, and two enabling ends (ENA end and ENB end) of the double-circuit driver IC2 are connected with an ON/OFF end (switch compensation signal end). One output end (OUTA end) of the dual-channel driver IC2 is connected with the grid of the first NMOS transistor Q3, and the other output end (OUTB end) of the dual-channel driver IC2 is connected with the grid of the second NMOS transistor Q4. The voltage input (VDD terminal) of the two-way driver IC2 is connected to a power supply input terminal, which supplies +12V dc power. The ground terminal (GND terminal) of the two-way driver IC2 is grounded.

Dual driver IC2 and dual driver IC3 preferably employ UCC27528 dual drivers, and dual driver IC2 and dual driver IC3 may increase the current of the switching pulse output from the oscillator to 5A, respectively.

The primary side of the transformer T1 is provided with a primary side tap, and the primary side tap is connected with the direct current power supply 1. The secondary sides of the transformers T1 in the impedance matching assemblies are connected in series and then are connected with the defibrillation voltage output end through the voltage doubling rectifying circuit. The utility model discloses a many transformers of multiunit impedance matching subassembly, like transformer T1 and transformer T2's design, can reduce the transformation ratio of every transformer. For example, the primary side of the transformer selects 1 turn, and the voltage of each turn is 15V, so that the iron loss and the magnetic loss of the transformer can be balanced, and the distributed capacitance of the transformer is also reduced. For example, the number of turns of the secondary side of the transformer is 40, so that the secondary side has no load voltage of 600V output. Two voltage transformation secondary sides are connected in series and then output 1200V, and after voltage doubling and rectification, defibrillation voltage V is obtained _DF =2400V. The impedance of the primary output circuit includes: the internal resistance of the resistance reducing capacitor C1, the on-resistance of each switching tube and the internal resistance of the transformer are designed to ensure that the output impedance of the circuit is about 50 omega.

The grid electrode of the first NMOS pipe Q3 is connected with one output end (OUTA end) of the double-circuit driver IC2, the source electrode of the first NMOS pipe Q3 is grounded, and the drain electrode of the first NMOS pipe Q3 is connected with one primary side end of the transformer T1.

The grid electrode of the second NMOS tube Q4 is connected with the other output end (OUTB end) of the double-path driver IC2, the source electrode of the second NMOS tube Q4 is grounded, and the drain electrode of the second NMOS tube Q4 is connected with the other end of the primary side of the transformer T1.

The first NMOS tube Q3 and the second NMOS tube Q4 adopt N-channel insulated gate field effect tubes with drain-source on resistance smaller than 1m omega.

The voltage doubling rectifying circuit is a voltage doubling rectifying circuit formed by a plurality of rectifying capacitors and a plurality of rectifying diodes, and the rectifying capacitors are patch capacitors. Specifically, as shown in fig. 2, taking two sets of impedance matching components as an example, the voltage-doubler rectification circuit includes a third rectification capacitor C3, a fourth rectification capacitor C4, a fifth rectification capacitor C5, a sixth rectification capacitor C6, a first rectification diode D1, a second rectification diode D2, a third rectification diode D3, and a fourth rectification diode D4.

And after the third rectifying capacitor C3, the fourth rectifying capacitor C4, the fifth rectifying capacitor C5 and the sixth rectifying capacitor C6 are sequentially connected in series, one end of the third rectifying capacitor C is connected with the flutter voltage output end, and the other end of the third rectifying capacitor C is grounded. The first rectifier diode D1, the second rectifier diode D2, the third rectifier diode D3 and the fourth rectifier diode D4 are sequentially connected in series, then the negative end is connected with the flutter voltage output end, and the positive end is grounded.

Two ends of a secondary side of the transformer T1 are respectively connected with a common end of the third rectifying capacitor C3 and the fourth rectifying capacitor C4 and a common end of the first rectifying diode D1 and the second rectifying diode D2.

And the common end of the fourth rectifying capacitor C4 and the fifth rectifying capacitor C5 is in short circuit with the common end of the second rectifying diode D2 and the third rectifying diode D3.

Two ends of the secondary side of the transformer T2 are respectively connected with the common end of the fifth rectifying capacitor C5 and the sixth rectifying capacitor C6, and the common end of the third rectifying diode D3 and the fourth rectifying diode D4.

Since the third rectifying capacitor C3, the fourth rectifying capacitor C4, the fifth rectifying capacitor C5 and the sixth rectifying capacitor C6 are only discharged during the dead time, a small patch capacitor can be selected to reduce the size of the device.

The electrode switching circuit 4 is respectively connected with the defibrillation voltage output end or the defibrillation electrode 5, and the connection relation between the impedance matching circuit 3 and the defibrillation electrode 5 is switched.

The electrode switching circuit 4 preferably employs two single-pole double-throw electronic switches, one for each defibrillation electrode 5. The common end of the single-pole double-throw electronic switch is connected with the corresponding defibrillation electrode 5, the normally closed end of the single-pole double-throw electronic switch is grounded, and the normally open end of the single-pole double-throw electronic switch is connected with the defibrillation voltage output end so as to reduce the leakage current of a patient.

Referring to fig. 3, the two electrodes may be referred to as a first electrode and a second electrode, respectively. A first phase of the defibrillation pulse is output when the normally open switch on the first electrode is closed and the normally closed switch on the second electrode is closed. A second phase of the defibrillation pulse is output when the normally closed end of the switch on the first electrode is closed and the normally open end of the switch on the second electrode is closed.

Referring to fig. 2, after power up,the input end of the power supply provides +12V direct current power supply, and the oscillator starts to work. When the ON/OFF end is at a high level, the double-circuit driver IC2 and the double-circuit driver IC3 output signals, the first NMOS tube Q1 and the second NMOS tube Q2 are alternately switched, the first NMOS tube Q3 and the second NMOS tube Q4 are alternately switched, alternating magnetic fields are generated in the magnetic cores of the transformer T1 and the transformer T2, so that the secondary coil generates alternating voltage, and the defibrillation voltage V is output by the defibrillation voltage output end after rectification and filtering of the voltage doubling rectifying circuit _DF . Referring to fig. 3, this voltage can be used to generate a defibrillation current directly across the transthoracic impedance of the body through the electrode switching circuit 4. When the ON/OFF terminal is at low level, the defibrillation voltage V stops being output _DF Defibrillation current is zero, defibrillation is suspended or terminated.

Referring to fig. 1, the external defibrillator may further include a control circuit 6, the control circuit 6 being connected to the dc power supply 1, the impedance matching circuit 3, and the electrode switching circuit 4, respectively. The through hole control circuit 6 controls the power supply state of the dc power supply 1, and the through hole control circuit 6 controls the on/off state of the switch compensation signal of the impedance matching circuit 3 and the switching state of the electrode switching circuit 4 by the through hole control circuit 6.

Referring to fig. 4, the greater the transthoracic impedance, the smaller the defibrillation current. Referring to fig. 5, the higher the defibrillation voltage, the greater the defibrillation current. Referring to fig. 6, the relationship between defibrillation current, defibrillation voltage, and transthoracic impedance follows ohm's law.

The relationship between defibrillation current, cardiogenic current and transthoracic impedance is that after the transthoracic impedance shunts the defibrillation current, the remaining current is cardiogenic current. The smaller the transthoracic impedance, the more shunted, and the smaller the cardioelectric current. The greater the transthoracic impedance, the less shunt and the greater the cardiogenic current. Only about 5% of the defibrillation current can pass through the heart to form a transardial current due to the shunting effect of transthoracic impedance.

The utility model discloses compensate current of defibrillating according to transthoracic impedance, indirect compensation is through the heart electric current, makes through the heart electric current reach the expectation value. Specifically, the low transthoracic impedance shunts more, increases the defibrillation current appropriately, and the high transthoracic impedance shunts less, decreases the defibrillation current appropriately. For example, the defibrillation current compensation is at 30A at a transthoracic impedance of 25 Ω and at 10A at a transthoracic impedance of 175 Ω. The compensation relationship is then:

wherein, I _DF For defibrillation current, unit a; v _SET Is a preset voltage, unit V; k is a transthoracic resistance compensation factor, and is dimensionless; r _TTI Transthoracic impedance in Ω; r _S The resistance is sampled for defibrillation current in Ω.

Let V _SET ＝5V，R _TTI ＝25Ω，I _DF ＝30A；R _TTI ＝175Ω，I _DF And (5) 10A, into formula (1). Can find k and R _S The value is obtained. k =1/450,R _S ＝1/9Ω。

Then the process of the first step is carried out,

wherein, V _DF For defibrillation voltage, unit V; r _O To compensate for the resistance, the unit Ω.

Defibrillation discharge time constant τ = (R) _TTI +R _O ) C, compensation resistance R _O The time constant is increased and the peak-to-average ratio of the defibrillation current is decreased.

As can be seen from formula (2): as long as the defibrillation voltage is set at V _DF ＝2250V，R _O The above object can be achieved by 50 Ω.

Practically equivalent to an internal resistance of R _O Open circuit voltage of V _DF Voltage source of, regulation V _DF I.e. adjustable in proportion I _DF Changing R _O I.e. can change _DF And V _DF And R _TTI The relationship between the three is changed. This method has no feedback during discharge and is therefore open loop compensation.

Will be provided with

Substituting the formula (1) to obtain:

V _SET ＝kV _DF +R _S I _DF (3)

when k =0, the defibrillation voltage has no effect on the defibrillation current, and the defibrillation current is in a constant current state. When k is greater than 0, the defibrillation voltage affects the defibrillation current, and the higher the defibrillation voltage, the smaller the defibrillation current. At low transthoracic impedance, the defibrillation voltage is low and the defibrillation current increases. The defibrillation current is automatically adjusted with the transthoracic impedance according to a desired law, the above equation lacks the term transthoracic impedance, and therefore the transthoracic impedance need not be measured.

The utility model discloses an external defibrillator uses above-mentioned principle as the basis, through setting up like the circuit connection picture of fig. 1 and fig. 2, realizes need not to detect the open loop compensation method through chest impedance, as shown in fig. 3, through chest impedance's scope when 25 omega ~ 175 omega, can be according to the different current of defibrillating through chest impedance regulation, indirect compensation is through heart current, makes through heart current reach the expectation value.

In the above open-loop compensation type formula (3), k and R _S After fixing, change V _SET The defibrillation current I can be changed _DF 。V _SET The time period for delivering the defibrillation pulse is constant, and can be automatically given by the defibrillator or set by the user. This method has negative feedback during discharge and is therefore a closed loop compensation.

Since equation (3) above is only a summation relationship, real-time dynamic adjustment of the defibrillation current is easily achieved with analog circuitry, and the circuit schematic of the closed-loop compensation is shown in fig. 7.

When power switch driver IC1 adopts the PWM controller chip, if adopt UC3825 controller chip, the utility model discloses can realize a closed loop compensation method. At this moment, the utility model discloses still include closed loop compensation circuit, refer to figure 7, closed loop compensation circuit is including defibrillation voltage sampling resistor R1, defibrillation voltage sampling resistor R2, current sampling resistor R defibrillates _S The voltage-controlled oscillator comprises a first voltage follower U1, a second voltage follower U2, an in-phase adder U3, a third resistor R3, a fourth resistor R4, a fifth resistor R5, a sixth resistor R6, an error amplifier U4 and a preset voltage end.

The defibrillation voltage sampling resistor R1 and the defibrillation voltage sampling resistor R2 are connected in series, and the defibrillation voltage samplingThe non-common end of the resistor R1 is connected with a defibrillation voltage output end which outputs defibrillation voltage V _DF The non-common terminal of the defibrillation voltage sampling resistor R2 is grounded. The voltage at the common end of the defibrillation voltage sampling resistor R1 and the defibrillation voltage sampling resistor R2 is V1.

Defibrillation current sampling resistor R _S And the load resistor is connected in series with the load resistor, and the load resistor is the equivalent resistance of the human body. Sampling resistor R for defibrillation current flowing through _S Is the defibrillation current I _DF . Defibrillation current sampling resistor R _S Is V3.

The non-inverting input end of the first voltage follower U1 is connected with the common end of the defibrillation voltage sampling resistor R1 and the defibrillation voltage sampling resistor R2, and the inverting input end of the first voltage follower U1 is connected with the output end of the first voltage follower U1. The voltage at the output of the first voltage follower U1 is V2.

The non-inverting input end of the second voltage follower U2 is connected with the defibrillation current sampling resistor R _S And the inverting input terminal of the second voltage follower U2 is connected to the output terminal of the second voltage follower U2. The voltage at the output of the second voltage follower U2 is V4.

The non-inverting input end of the non-inverting adder U3 is connected with the output end of the first voltage follower U1 through a third resistor R3, the non-inverting input end of the non-inverting adder U3 is connected with the output end of the second voltage follower U2 through a fourth resistor R4, the inverting input end of the non-inverting adder U3 is connected with the output end of the non-inverting adder U3 through a fifth resistor R5, the inverting input end of the non-inverting adder U3 is grounded through a sixth resistor R6, and the resistance values of the third resistor R3, the fourth resistor R4, the fifth resistor R5 and the sixth resistor R6 are the same. The output terminal voltage of the in-phase adder U3 is V5.

The non-inverting input end of the error amplifier U4 is connected with a preset voltage end, the inverting input end of the error amplifier U4 is connected with the output end of the non-inverting adder U3, and the output end of the error amplifier U4 is connected with the error signal input end of the PWM controller chip. The preset voltage provided by the preset voltage end is V _SET The output terminal voltage of the error amplifier U4 is V6.

Referring to FIG. 7, V _DF For defibrillation voltage, I _DF In order to achieve a defibrillation current flow,the resistor R1 and the resistor R2 are defibrillation voltage sampling resistors, and the sampling voltage V1= kV _DF Transthoracic resistance compensation factor

Resistance R _S For defibrillation current sampling resistor, voltage V3= R _S I _DF 。

The first voltage follower U1 and the second voltage follower U2 are used to reduce the effect of subsequent circuits on the samples V1 and V3.

Since the third resistor R3, the fourth resistor R4, the fifth resistor R5, and the sixth resistor R6 have the same resistance, V5= (V1 + V3) = (kV) _DF +R _S I _DF )

And V6 is an error signal used for compensating the defibrillation discharge circuit. The error signal V6 is sent to the PWM controller chip, under the control of the PWM controller chip, through the opposite trend change, the depth negative feedback compensation can lead V5= V _SET Realization of V _SET ＝(kV _DF +R _S I _DF )

At k and R _S After fixing, by varying the preset voltage V _SET To change the defibrillation current I _DF . The closed-loop compensation method does not need to measure transthoracic impedance, and realizes real-time dynamic adjustment.

The foregoing shows and describes the general principles, essential 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 above embodiments, and that the foregoing embodiments and descriptions are provided only to illustrate the principles of the present invention without departing from the spirit and scope of the present invention. The scope of the invention is defined by the appended claims and equivalents thereof.

Claims

1. An external defibrillator comprising a DC power source and a pair of defibrillation electrodes;

characterized in that, still including connecting gradually between DC power supply and a pair of defibrillation electrode:

the resistance reducing loop is connected with the direct current power supply;

the impedance matching loop is connected with the resistance reducing circuit and is provided with a defibrillation voltage output end;

2. The external defibrillator of claim 1 wherein the dc power source is a 15V disposable battery.

3. The external defibrillator of claim 1 wherein the resistance reducing circuit employs a resistance reducing capacitor;

4. The external defibrillator of claim 3 wherein the resistance reducing capacitor is comprised of at least one of a high frequency low resistance capacitor or a supercapacitor connected in parallel.

5. The external defibrillator of any one of claims 1 to 4 wherein the impedance matching circuit comprises:

a switch compensation signal terminal;

the secondary sides of the transformers in the impedance matching assemblies are connected in series and then are connected with the defibrillation voltage output end through a voltage doubling rectifying circuit.

6. The external defibrillator of claim 5 wherein the first NMOS transistor and the second NMOS transistor are N-channel insulated gate field effect transistors having a drain-source on-resistance of less than 1m Ω;

the voltage doubling rectifying circuit is a voltage doubling rectifying circuit formed by a plurality of rectifying capacitors and a plurality of rectifying diodes, and the rectifying capacitors are patch capacitors.

7. The external defibrillator of claim 5 wherein the oscillator comprises:

8. The external defibrillator of claim 7 wherein the power switch driver is a push-pull MOSFET power switch driver with an oscillator of its own having dead time compensation, the power switch driver being a power switch driver with an oscillation frequency of 200kHz and a dead time of 150 ns.

9. The external defibrillator of claim 1 wherein the electrode switching circuit employs two single pole double throw electronic switches, one for each of the defibrillation electrodes;

10. The external defibrillator of claim 7 wherein the power switch driver employs a PWM controller chip;

and the non-inverting input end of the error amplifier is connected with the preset voltage end, the inverting input end of the error amplifier is connected with the output end of the non-inverting adder, and the output end of the error amplifier is connected with the error signal input end of the PWM controller chip.