CN212416681U - Wireless charging circuit, wireless charger and active implantable medical system - Google Patents

Abstract

The utility model provides a wireless charging circuit, wireless charger and active implanted medical system, it is mainly by first PMOS pipe, the second PMOS pipe, the full-bridge drive circuit that first NMOS pipe and second NMOS pipe were built and are formed, can drive the resonance circuit that charges under first control signal and second control signal's control and produce the resonance, this full-bridge drive circuit is because of mainly constituting by the MOS pipe, parasitic parameter is little, consequently, can greatly reduce power supply circuit's energy transfer to the loss of the resonance circuit that charges, self loss when having reduced this wireless charging circuit resonance, the charging efficiency of this wireless charging circuit self has been promoted, and can promote the efficiency that the wireless magnetic energy that this wireless charging circuit launched pierces through the titanium shell of implanted medical equipment, then can provide the wireless effect of charging of farther distance and lower consumption.

Description

Wireless charging circuit, wireless charger and active implantable medical system

Technical Field

The utility model relates to an active implanted medical technology field, in particular to wireless charging circuit, wireless charger and active implanted medical system.

Background

With the development of brain surgery technology and neuroelectronic science technology, the Deep Brain Stimulation (DBS) technology becomes the first choice treatment means for the advanced parkinson disease worldwide by virtue of its clinical effects superior to the destructive surgery, minimally invasive surgery process without damaging brain tissue, and reversibility of treatment schemes. The existing DBS system mainly comprises a pulse generator (IPG) implanted in a body, a stimulation electrode (Lead), an in-vivo Extension Lead (Extension), an in-vitro program control device (program & Remoter), and a related Surgical tool (Surgical tool).

In an Active Implantable Medical Device (AIMD) system, such as the DBS system described above, wireless communication (i.e., long-range communication) with an implanted Active Implantable Medical Device (e.g., a pulse generator of the DBS system) is the only means for monitoring the operating state of the Active Implantable Medical Device, because the causes and conditions of the user are different, and different Active Implantable Medical devices installed in different users generally have different operating states, which are reflected in many aspects, such as battery voltage, operating time, power, and current level and frequency, of the Active Implantable Medical Device. Therefore, the success rate of wireless communication (i.e., long-range communication) is critical to ensure better therapeutic efficacy and higher reliability of the active implantable medical device.

SUMMERY OF THE UTILITY MODEL

An object of the utility model is to provide a remote charging circuit can reduce the consumption, promotes the wireless charging efficiency of external machine to active implanted medical equipment.

In order to solve the above technical problem, the present invention provides a wireless charging circuit for wirelessly charging an implantable medical device, wherein the implantable medical device has a powered resonant circuit, the wireless charging circuit includes a power circuit, a full-bridge driving circuit and a charging resonant circuit, the charging resonant circuit is configured to generate resonance under the driving of the full-bridge driving circuit, so as to transmit wireless electromagnetic energy to the powered resonant circuit, and the powered resonant circuit can pick up the wireless electromagnetic energy through electromagnetic coupling; the full-bridge driving circuit comprises a first PMOS tube, a second PMOS tube, a first NMOS tube and a second NMOS tube, the source electrodes of the first PMOS tube and the second PMOS tube are both connected with the positive output end of the power supply circuit, the source electrodes of the first NMOS tube and the second NMOS tube are both connected with the negative output end of the power circuit and grounded, the grids of the first PMOS tube and the first NMOS tube are both connected with a first control signal, the grids of the second PMOS tube and the second NMOS tube are both connected with a second control signal, the drain electrode of the first PMOS tube is connected with the drain electrode of the first NMOS tube and is used as one output end of the full-bridge driving circuit, and the drain electrode of the second PMOS tube is connected with the drain electrode of the second NMOS tube and is used as the other output end of the full-bridge driving circuit, and is connected to the other input end of the charging resonance circuit.

Optionally, the charging resonant circuit includes a charging coil and a charging resonant capacitor, two ends of the charging coil are respectively two input ends of the charging resonant circuit, and the charging resonant capacitor is connected in series or in parallel with the charging coil.

Optionally, the power receiving resonant circuit includes a power receiving coil and a power receiving resonant capacitor, when the charging resonant capacitor is connected in series with the charging coil, the power receiving resonant capacitor is connected in series with the power receiving coil, and when the charging resonant capacitor is connected in parallel with the charging coil, the power receiving resonant capacitor is connected in parallel with the power receiving coil.

Optionally, a turns ratio of the charging coil and the receiving coil is not less than 2.

Based on same utility model the design, the utility model also provides a wireless charger for carry out wireless charging to implanted medical equipment, wireless charger includes as the utility model discloses wireless charging circuit.

The utility model also provides an implanted medical equipment, including casing and the power receiving resonance circuit and the pulse generating circuit that set up in the casing and connect gradually, just implanted medical equipment passes through as the wireless charging circuit carry out wireless charging.

Optionally, the implantable medical device further has a rectifying and filtering circuit, and the rectifying and filtering circuit is a half-wave rectifying circuit or a full-wave rectifying circuit.

Based on same utility model the design, the utility model discloses still provide an active implanted medical system, including implanted medical equipment and if wireless charging circuit, implanted medical equipment has the power receiving resonance circuit, wireless charging circuit be used for to power receiving resonance circuit transmission wireless electromagnetic energy, and then make power receiving resonance circuit can pick up through electromagnetic coupling wireless electromagnetic energy, in order to realize wireless charging circuit is right implanted medical equipment's wireless charging.

Compared with the prior art, the technical scheme of the utility model following beneficial effect has:

1. mainly by first PMOS pipe, the second PMOS pipe, the full-bridge drive circuit that first NMOS pipe and second NMOS pipe were built and are formed, can drive the resonance circuit that charges under first control signal and second control signal's control and produce the resonance, this full-bridge drive circuit is because of mainly being constituteed by the MOS pipe, parasitic parameter is little, consequently, can greatly reduce power supply circuit's energy transfer to the loss of the resonance circuit that charges, self loss when having reduced this wireless charging circuit resonance, the charging efficiency of this wireless charging circuit self has been promoted.

2. The resonance frequency can be reduced by reasonably selecting the parameters of the electronic elements in the charging resonance circuit, so that the efficiency of the wireless electromagnetic energy transmitted by the wireless charging circuit penetrating through the titanium shell of the implantable medical equipment can be improved, and finally the charging efficiency of the wireless charging circuit can be further improved.

3. Because low frequency resonance and full-bridge drive can reduce the wireless consumption when charging, promote the efficiency that the wireless electromagnetic energy of transmission pierces through the titanium shell, consequently, the technical scheme of the utility model in the aspect of implantable medical equipment's wireless charging, can also provide the wireless effect of charging of farther distance and lower consumption.

Drawings

Fig. 1 is a schematic diagram illustrating a charging principle of an active implantable medical system according to an embodiment of the present invention;

fig. 2 is a schematic structural diagram of a wireless charging circuit according to an embodiment of the present invention;

fig. 3 is a schematic diagram of an exemplary structure of a charging resonant circuit in a wireless charging circuit according to an embodiment of the present invention;

fig. 4 is a schematic structural diagram of another example of a charging resonant circuit in a wireless charging circuit according to an embodiment of the present invention;

fig. 5 is a schematic diagram of an exemplary structure of a rectifying and filtering circuit of an implantable medical device according to an embodiment of the present invention;

fig. 6 is a schematic diagram of another exemplary structure of a rectifying and filtering circuit of an implantable medical device according to an embodiment of the present invention;

fig. 7 is a schematic diagram of an example structure of an active implantable medical system according to an embodiment of the present invention.

Detailed Description

The technical solution provided by the present invention will be further described in detail with reference to the accompanying drawings and specific embodiments. The advantages and features of the present invention will become more apparent from the following description. It should be noted that the drawings are in simplified form and are not to precise scale, and are provided for convenience and clarity in order to facilitate the description of the embodiments of the present invention.

Referring to fig. 1 and 2, an embodiment of the present invention provides a wireless charging circuit 1 and an implantable medical device 2, wherein the wireless charging circuit 1 is located outside a living body (including a human body) and is used for wirelessly charging the implantable medical device 2 implanted inside the living body (including the human body).

Referring to fig. 1 and 2, the wireless charging circuit 1 includes a power circuit 11, a full-bridge driving circuit 12, and a charging resonant circuit 13. The power circuit 11 is mainly used for providing the full-bridge driving circuit 12 with the direct current DC, the first control signal Vdrive + and the second control signal Vdrive-. The power supply circuit 11 may be a battery device, or may be a circuit capable of converting ac to DC, and includes a rectifier bridge (not shown) capable of rectifying ac power of 220V or the like and smoothing the ac power to output DC power, a transformer (not shown) capable of converting DC power output from the rectifier bridge to low-voltage DC power of 12V, 9V, 5V or the like, and a constant current/constant voltage output module (not shown) capable of outputting DC power of constant current or constant voltage. The first control signal Vdrive + and the second control signal Vdrive-are related to parameters of the first PMOS transistor V1, the second PMOS transistor V2, the first NMOS transistor V3 and the second NMOS transistor V4 in the full-bridge driving circuit 12, for example, when the first PMOS transistor V1, the second PMOS transistor V2, the first NMOS transistor V3 and the second NMOS transistor V4 are two sets of N-P fets with symmetric parameters, the first control signal Vdrive + and the second control signal Vdrive-are two square wave signals with identical period frequency, identical amplitude and 180 ° phase difference, and the period frequency of the two square wave signals is equal to the driving frequency of the full-bridge driving circuit 12, that is, equal to the resonant frequency of the charging resonant circuit 13.

Referring to fig. 1 and fig. 2, the full-bridge driving circuit 12 includes a first PMOS transistor V1, a second PMOS transistor V2, a first NMOS transistor V3, and a second NMOS transistor V4. The sources of the first PMOS transistor V1 and the second PMOS transistor V2 are both connected to the positive output end (+) of the power circuit 11. The sources of the first NMOS transistor V3 and the second NMOS transistor V4 are both connected to the negative output terminal (-) of the power circuit 11 and grounded. The grid of first PMOS pipe V1 and the grid of first NMOS pipe V3 all connect first control signal Vdrive +, the grid of second PMOS pipe V2 and the grid of second NMOS pipe V4 all connect second control signal Vdrive-, the drain-source resistance of first PMOS pipe V1 with the drain-source resistance of first NMOS pipe V3 link up and as an output of full-bridge drive circuit 12, and be connected to an input of charging resonant circuit 13, the drain-source resistance of second PMOS pipe V2 link up and as another output of full-bridge drive circuit 12 with the drain-source resistance of second NMOS pipe V4, and be connected to another input of charging resonant circuit 13.

The charging resonant circuit 13 is configured to generate resonance under the driving of the full-bridge driving circuit 12 to transmit wireless electromagnetic energy to the powered resonant circuit 21 of the implantable medical device 2, and the powered resonant circuit 21 of the implantable medical device 2 can pick up the wireless electromagnetic energy through electromagnetic coupling. Referring to fig. 3, as an example, the charging resonant circuit 13 includes a charging coil L1 and a charging resonant capacitor C0, two ends of the charging coil L1 are respectively two input ends of the charging resonant circuit 13, and the charging resonant capacitor C0 is connected in series with the charging coil L1, that is, the charging resonant capacitor C0 is connected in series between one end of the charging coil L1 and one output end of the full bridge driving circuit 12; accordingly, the power receiving resonant circuit 21 of the implantable medical device includes a power receiving coil L2 and a power receiving resonant capacitor C1, and the power receiving resonant capacitor C1 is connected in series with the power receiving coil L2, that is, the power receiving resonant capacitor C1 is connected in series between one end of the power receiving coil L2 and one input end of the rectifying and filtering circuit 22 of the implantable medical device 2. Referring to fig. 4, as another example, the charging resonant circuit 13 includes a charging coil L1 and a charging resonant capacitor C0, two ends of the charging coil L1 are respectively two input ends of the charging resonant circuit 13, and the charging resonant capacitor C0 is connected in parallel with the charging coil L1, that is, the charging resonant capacitor C0 is connected between two ends of the charging coil L1; accordingly, the power receiving resonant circuit 21 of the implantable medical device includes a power receiving coil L2 and a power receiving resonant capacitor C1, and the power receiving resonant capacitor C1 is connected in parallel with the power receiving coil L2, that is, the power receiving resonant capacitor C1 is connected between two ends of the power receiving coil L2.

It should be noted that the resonant frequency f of the wireless charging circuit 1 may be related to the inductance value of the charging coil L1 and the capacitance value of the charging resonant capacitor C0, and satisfy the following relation:

the resonant frequency f of the wireless charging circuit 1 may be related to the inductance value of the power receiving coil L2 and the capacitance value of the power receiving resonant capacitor C1, and satisfy the following relationship:

the turn ratio of the charging coil L1 and the power receiving coil L2 is not less than 2, so that the resonance frequency is 5 KHz-15 KHz. For example 7.12 KHz.

In addition, it should be noted that, the embodiment of the present invention has no special requirement for the model selection of the first PMOS transistor V1, the second PMOS transistor V2, the first NMOS transistor V3, and the second NMOS transistor V4, and the operating voltage, the operating current, and the operating frequency of each MOS transistor are all within the electrical general requirement range.

Referring to fig. 1 and 2, an implantable medical device 2 is a medical device that is implanted within the body of a living organism (including the human body) and is used to generate and deliver electrical stimulation to body nerves and tissues for the treatment of various biological disorders, such as: a pacemaker for treating arrhythmia; a defibrillator for treating cardiac fibrillation; a cochlear stimulator for treating hearing loss; a retinal stimulator for treating blindness; a muscle stimulator for producing coordinated limb movements; spinal cord stimulators for treating chronic pain; cortical and Deep Brain Stimulators (DBS) for the treatment of motor and psychological disorders; and other neurostimulators used to treat urinary incontinence, sleep apnea, subluxation of the shoulder, and the like. The implantable medical device 2 may include a housing (not shown, which may be a titanium housing), and a power receiving resonant circuit 21, a rectifying and filtering circuit 22, a pulse generating circuit (not shown), and the like, which are disposed in the housing and connected in sequence. The housing is typically made of a biocompatible material such as, for example, titanium. The specific circuit design of the pulse generating circuit depends on the type and function of the implantable medical device 2, and the circuit is not the innovation of the present invention, so that reference can be made to the related circuit design in the field, and details are not repeated herein. In addition, the circuit design of the power receiving resonant circuit 21 may refer to fig. 3 or fig. 4, and details thereof are not repeated.

Referring to fig. 3 and 5, as an example, the rectifying and filtering circuit 22 may be a half-wave rectifying and filtering circuit, which includes a rectifying diode D1, an anode of the rectifying diode D1 is connected to one end of the power receiving coil L2, a cathode of the rectifying diode D1 is connected to one end of the power receiving resonant capacitor C1, and outputs a dc charging voltage Vcharge, and another end of the power receiving resonant capacitor C1 is connected to one end of the power receiving coil L2 and is connected to the housing ground of the implanted medical device 2, where the power receiving resonant capacitor C1 functions as a resonant capacitor for receiving the wireless electromagnetic energy emitted by the wireless charging circuit 1 and also functions as a filter. Referring to fig. 6, as another example, the rectifying and filtering circuit 22 may also be a full-wave rectifying and filtering circuit, which includes rectifying diodes D1-D4 and a filtering capacitor C2, one end of the power receiving coil L2 is connected to the anode of the rectifying diode D1 and the cathode of the rectifying diode D3, the other end of the power receiving coil L2 is connected to the anode of the rectifying diode D2 and the cathode of the rectifying diode D4, the cathode of the rectifying diode D1 is connected to the cathode of the rectifying diode D2 and outputs a dc charging voltage Vcharge, and the anode of the rectifying diode D3 is connected to the anode of the rectifying diode D4 and connected to the housing ground of the implantable medical device 2.

It should be noted that the output end of the rectifying and filtering circuit 22 (i.e., the end outputting the dc charging voltage Vcharge) may be directly connected to the pulse generating circuit of the implantable medical device 2, so that the pulse generating circuit can operate by supplying power to the wireless charging circuit, and the output end of the rectifying and filtering circuit 22 may also be connected to the pulse generating circuit by a rechargeable battery, so that the rechargeable battery is charged by the wireless charging circuit 1, and the pulse generating circuit needs to be supplied power by the rechargeable battery.

Based on same utility model concept, please refer to fig. 1 to 7, an embodiment of the present invention further provides a wireless charger for wirelessly charging implanted medical equipment, the wireless charger includes as in any one of the present invention wireless charging circuit 1. Furthermore, the utility model provides an active implanted medical system, including implanted medical equipment 2 and if wireless charging circuit 1, implanted medical equipment 2 has powered resonance circuit 21, wireless charging circuit 1 be used for to powered resonance circuit 21 transmits wireless electromagnetic energy, and then makes powered resonance circuit 21 can pick up through electromagnetic coupling wireless electromagnetic energy, in order to realize wireless charging circuit 1 is right implanted medical equipment 2's wireless charging.

Referring to fig. 7, the specific circuit design and the corresponding charging principle of the wireless charging circuit 1, the wireless charger and the active implanted medical system of the present invention will be described in detail below with the charging resonant circuit 13 and the receiving resonant circuit 21 as a parallel resonant mode, the rectifying and filtering circuit 22 as a full-wave rectifying and filtering circuit, and the resonant frequency of 7.12KHz as an example.

Referring to fig. 7, the active implantable medical system in this example has a circuit including a first control signal of 7.12KHz (i.e., a square wave signal with a period frequency of 7.12KHz), Vdrive +, a second control signal of 7.12KHz (i.e., a negative square wave signal with a period frequency of 7.12KHz), Vdrive-, 12V DC power supply (DC)11, a PMOS transistor V1, a PMOS transistor V2, an NMOS transistor V3, an NMOS transistor V4, a 1mH charging coil L1 (i.e., an inductance value of 1mH), a 500nf charging resonant capacitor C0 (i.e., a capacitance value of 500nf), a 4mH receiving coil L2 (i.e., an inductance value of 4mH), a 125nf receiving resonant capacitor C1 (i.e., a capacitance value of 125nf), and rectifier diodes D1-D4. The full-bridge driving circuit 12 is composed of a PMOS tube V1, a PMOS tube V2, an NMOS tube V3 and an NMOS tube V4, the charging resonant circuit 13 is composed of a 1mH charging coil L1 and a 500nf charging resonant capacitor C0, the receiving resonant circuit 21 is composed of a 4mH receiving coil L2 and a 125nf receiving resonant capacitor C1, and the rectifying filter circuit 22 is composed of circuits composed of rectifying diodes D1-D4. The reverse withstand voltages of the rectifier diodes D1-D4 may be all 40V, or all be greater than 40V, for example, 50V, 60V, and the like, the rated forward currents may be all 1A, or all be greater than 1A, for example, 2A, 3A, and the like, and the rectifier diodes D1-D4 may be implemented by any suitable schottky diode. The PMOS transistor V1, the PMOS transistor V2, the NMOS transistor V3 and the NMOS transistor V4 can be selected from transistors having a conduction resistance of m Ω level (e.g., 12m Ω or 29m Ω), an absolute value of a turn-on voltage of 0.6V to 0.7V (e.g., 0.6V or 0.65V), an absolute value of a leakage current of 20 μ A to 30 μ A (e.g., 20 μ A or 25 μ A), and a low-frequency transconductance of 0.5s to 1.5s (e.g., 0.8s or 1.45 s).

The positive electrode of a 12V direct current power supply 11 is connected with the source electrode of a PMOS tube V1 and the source electrode of a PMOS tube V2, the drain electrode of a PMOS tube V1 is connected with the drain electrode of an NMOS tube V3, the drain electrode of a PMOS tube V2 is connected with the drain electrode of an NMOS tube V4, the source electrode of an NMOS tube V3 and the source electrode of an NMOS tube V4 are both connected with the negative electrode of the 12V direct current power supply 11 and are connected with a power ground, the grid electrode of the PMOS tube V1 and the grid electrode of the NMOS tube V3 are connected with a 7.12KHz first control signal Vdrive +, the grid electrode of the PMOS tube V2 and the grid electrode of the NMOS tube V4 are connected with a 7.12KHz second control signal Vdrive-, the drain electrode of the PMOS tube V1 and the drain electrode of the NMOS tube V3 are connected with one end of a 1mH charging coil L1, the drain electrode of the PMOS tube V4 and the drain electrode of the PMOS tube V8 and the NMOS tube V4 are connected.

The two ends of the 4mH power receiving coil L2 are connected with a 125nf power receiving resonant capacitor C1 in parallel, one end of the 4mH power receiving coil L2 is connected with the anode of a rectifier diode D1 and the cathode of a rectifier diode D3, and the other end of the 4mH power receiving coil L2 is connected with the anode of a rectifier diode D2 and the cathode of a rectifier diode D4; the cathode of the rectifier diode D1 is connected with the cathode of the rectifier diode D2 and outputs a direct-current charging voltage Vcharge, and the anode of the rectifier diode D3 is connected with the anode of the rectifier diode D4 and connected with the chassis ground of the shell of the implantable medical device.

The 7.12KHz first control signal and the 7.12KHz second control signal have the same cycle frequency and the same amplitude, but have a phase difference of 180 deg.

The resonant frequency is related to the parameters of the resonant capacitor C0 charged by the 1mH charging coils L1 and 500nf and the parameters of the resonant capacitor C1 charged by the 4mH receiving coils L2 and 125nf, and the following relations are satisfied:

the 1mH charging coil L1 and the 4mH power receiving coil L2 are not on the same circuit board, and the turns ratio of the 1mH charging coil L1 and the 4mH power receiving coil L2 is not less than 4.

The specific circuit charging principle is as follows: the first control signal Vdrive + and the second control signal Vdrive-, have the same frequency, the same amplitude and the phase difference of 180 degrees. When the first control signal Vdrive + is at a high level, the second control signal Vdrive-is at a low level, the PMOS transistor V1 is turned on, the NMOS transistor V3 is turned off, the PMOS transistor V2 is turned off, the NMOS transistor V4 is turned on, the drain of the NMOS transistor V3 outputs a dc power supply voltage value, and the drain of the NMOS transistor V4 outputs 0V; when the first control signal Vdrive + is at a low level at the next moment, the second control signal Vdrive-is at a high level, the PMOS transistor V1 is closed, the NMOS transistor V3 is opened, the PMOS transistor V2 is opened, the NMOS transistor V4 is closed, the drain of the NMOS transistor V3 outputs 0V, the drain of the PMOS transistor V4 outputs a DC power voltage value, the full-bridge driving circuit 12 converts the DC power DC into a square wave ac signal of 5KHz to 15KHz for driving the charging resonant circuit 13 (i.e., an LC resonant circuit), and the charging resonant circuit 13 is excited by the square wave ac signal output by the full-bridge driving circuit 12 and generates resonance to achieve the maximum working current. The wireless electromagnetic energy is emitted through the charging coil L1, the power receiving coil L2 of the power receiving resonant circuit 21 picks up the wireless electromagnetic energy through electromagnetic coupling, and the picked-up wireless electromagnetic energy is transmitted to the rectifier filter circuit 22 at the subsequent stage to the maximum extent through the resonance (i.e., alternating current signal generation) of the power receiving coil L2 and the power receiving resonant capacitor C1. When the amplitude of the alternating current signal generated by the power receiving coil L2 and the power receiving resonant capacitor C1 is a positive value, the rectifier diodes D1 and D4 are turned on, the rectifier diodes D2 and D3 are turned off in the reverse direction, the cathode of the rectifier diode D2 generates a positive voltage Vcharge, when the amplitude of the alternating current signal generated by the power receiving coil L2 and the power receiving resonant capacitor C1 is a negative value, the rectifier diodes D2 and D3 are turned on, the rectifier diodes D1 and D4 are turned off in the reverse direction, the cathode of the rectifier diode D2 generates a positive voltage Vcharge, so that full-waveform rectification of the alternating current signal is completed, the alternating current signal is converted into a direct current signal, and the filter capacitor C2 is used for storing, filtering and stabilizing the energy of the direct current signal Vcharge output by the cathode of.

To sum up, the utility model discloses an among wireless charging circuit, wireless charger and the active implanted medical system, mainly by first PMOS pipe, the second PMOS pipe, the full-bridge drive circuit that first NMOS pipe and second NMOS pipe were built and are formed, can drive the resonance circuit that charges and produce the resonance under first control signal and second control signal's control, this full-bridge drive circuit is because of mainly constituting by the MOS pipe, parasitic parameter is little, consequently, can greatly reduce power supply circuit's energy transfer to the loss of the resonance circuit that charges, self loss when having reduced this wireless charging circuit resonance, the charge efficiency of this wireless charging circuit self has been promoted. In addition, the resonance frequency can be reduced by reasonably selecting the parameters of the electronic elements in the charging resonance circuit, so that the efficiency of the wireless electromagnetic energy transmitted by the wireless charging circuit penetrating through the titanium shell of the implantable medical device can be improved, and finally, the charging efficiency of the wireless charging circuit can be further improved. Moreover, because low frequency resonance and full-bridge drive can reduce the wireless consumption when charging, promote the efficiency that the wireless electromagnetic energy of transmission pierces through the titanium shell, consequently, the technical scheme of the utility model in the aspect of implantable medical equipment's wireless charging, can provide the wireless effect of charging of farther distance and lower consumption.

The above description is only for the preferred embodiment of the present invention and is not intended to limit the scope of the present invention, and any modification and modification made by those skilled in the art according to the above disclosure are all within the scope of the claims.

Claims (8)

1. A wireless charging circuit is used for wirelessly charging an implantable medical device, the implantable medical device is provided with a power receiving resonant circuit, the wireless charging circuit comprises a power supply circuit, a full-bridge driving circuit and a charging resonant circuit, the charging resonant circuit is used for generating resonance under the driving of the full-bridge driving circuit so as to transmit wireless electromagnetic energy to the power receiving resonant circuit, and the power receiving resonant circuit can pick up the wireless electromagnetic energy through electromagnetic coupling; the full-bridge driving circuit comprises a first PMOS tube, a second PMOS tube, a first NMOS tube and a second NMOS tube, the source electrodes of the first PMOS tube and the second PMOS tube are both connected with the positive output end of the power supply circuit, the source electrodes of the first NMOS tube and the second NMOS tube are both connected with the negative output end of the power circuit and grounded, the grids of the first PMOS tube and the first NMOS tube are both connected with a first control signal, the grids of the second PMOS tube and the second NMOS tube are both connected with a second control signal, the drain electrode of the first PMOS tube is connected with the drain electrode of the first NMOS tube and is used as one output end of the full-bridge driving circuit, and the drain electrode of the second PMOS tube is connected with the drain electrode of the second NMOS tube and is used as the other output end of the full-bridge driving circuit, and is connected to the other input end of the charging resonance circuit.

2. The wireless charging circuit according to claim 1, wherein the charging resonant circuit comprises a charging coil and a charging resonant capacitor, two ends of the charging coil are respectively two input ends of the charging resonant circuit, and the charging resonant capacitor is connected in series or in parallel with the charging coil.

3. The wireless charging circuit according to claim 2, wherein the power receiving resonant circuit comprises a power receiving coil and a power receiving resonant capacitor, the power receiving resonant capacitor is connected in series with the power receiving coil when the charging resonant capacitor is connected in series with the charging coil, and the power receiving resonant capacitor is connected in parallel with the power receiving coil when the charging resonant capacitor is connected in parallel with the charging coil.

4. The wireless charging circuit of claim 3, wherein a turns ratio of the charging coil and the receiving coil is not less than 2.

5. A wireless charger for wirelessly charging implantable medical devices, comprising the wireless charging circuit of any one of claims 1-4.

6. An implantable medical device, comprising a housing, and a power receiving resonant circuit and a pulse generating circuit which are disposed in the housing and connected in sequence, wherein the implantable medical device is charged wirelessly through the wireless charging circuit according to any one of claims 1 to 4.

7. The implantable medical device of claim 6, further comprising a rectifying and filtering circuit that is a half-wave rectifying circuit or a full-wave rectifying circuit.

8. An active implantable medical system, comprising an implantable medical device and the wireless charging circuit of any one of claims 1-4, wherein the implantable medical device has a powered resonant circuit, and the wireless charging circuit is configured to transmit wireless electromagnetic energy to the powered resonant circuit, so that the powered resonant circuit can pick up the wireless electromagnetic energy through electromagnetic coupling, thereby enabling the wireless charging circuit to wirelessly charge the implantable medical device.

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