CN211934277U - Radio frequency energy generation device and radio frequency ablation system - Google Patents

Abstract

The application provides a radio frequency energy generation device and a radio frequency ablation system. The radio frequency energy generating device comprises a power supply module, a first isolation conversion device and a second isolation conversion device. The first isolation conversion device receives the input voltage provided by the power module, performs voltage reduction processing and electrical isolation, and outputs a first voltage. The second isolation conversion device converts the first voltage output by the first isolation conversion device into a radio frequency signal, electrically isolates the radio frequency signal and outputs the radio frequency signal to the ablation device. The ablation device carries out radiofrequency ablation on a part to be ablated by using the radiofrequency energy of the radiofrequency signal. The radio frequency energy generating device increases creepage distance and reduces generation of leakage current through the two isolating devices before generating the radio frequency energy, so that double isolation of input voltage in a radio frequency loop is realized, the electric shock prevention grade of the radio frequency energy generating device can be improved, and the treatment effect and the safety of radio frequency ablation are ensured.

Description

Radio frequency energy generation device and radio frequency ablation system

Technical Field

The application relates to the technical field of medical instruments, in particular to a radio frequency energy generating device and a radio frequency ablation system.

Background

Currently, radio frequency ablation technology has been applied in the treatment of tumor diseases, neurological diseases, etc., as an emerging technology in the medical field. The main mechanism of the radio frequency ablation is a thermal effect, when a radio frequency ablation operation is carried out, the radio frequency ablation device transmits radio frequency energy to a diseased part, such as a diseased tissue of a heart or other diseased tissues, by means of an ablation electrode, the radiofrequency energy ablates the diseased part, protein in diseased cells of the diseased tissue is denatured under the action of the radiofrequency energy, water inside and outside the cells is lost, and coagulative necrosis of the diseased tissue occurs, so that the treatment purpose is achieved.

With the popularization and application of the radio frequency ablation, higher requirements are put forward on the safety and the effectiveness of the radio frequency ablation equipment. However, the safety and effectiveness of the conventional rf ablation device are not satisfactory for the current rf ablation procedure, especially for cardiac diseases. Therefore, how to improve the safety of the rf ablation device is one of the important directions for the researchers in the present technology.

SUMMERY OF THE UTILITY MODEL

In order to solve the above technical problems, the present application provides a radio frequency energy generating device and a radio frequency ablation system.

In a first aspect, the present application provides a radio frequency energy generating apparatus comprising a power module, a first isolation switching device, and a second isolation switching device. The first isolation conversion device is electrically connected with the power supply module and used for receiving the input voltage provided by the power supply module, and outputting a first voltage after performing voltage reduction processing and electrical isolation on the input voltage. The second isolation conversion device is electrically connected with the first isolation conversion device and is used for converting the first voltage output by the first isolation conversion device into a radio frequency signal, electrically isolating the radio frequency signal and outputting the radio frequency signal to an ablation device, wherein the ablation device is used for receiving the radio frequency signal and performing radio frequency ablation on a part to be ablated by using radio frequency energy of the radio frequency signal.

In a second aspect, the present application provides a radiofrequency ablation system comprising an ablation device and a radiofrequency energy generation device as described above. The ablation device comprises an ablation needle assembly which is electrically connected with the radio frequency energy generating device and is used for receiving the radio frequency energy output by the radio frequency energy generating device and releasing the radio frequency energy to the part to be ablated so as to perform radio frequency ablation on the part to be ablated.

The radio frequency energy generating device uses the first isolation conversion device to perform voltage reduction processing and electrical isolation on input voltage in a radio frequency loop, and uses the second isolation conversion device to convert output voltage of the first isolation conversion device into a radio frequency signal and electrical isolation to generate radio frequency energy, so that before the radio frequency energy is generated, creepage distance is increased and generation of leakage current is reduced through the first isolation conversion device and the second isolation conversion device, double isolation of the input voltage in the radio frequency loop is realized, electric shock prevention grade of the radio frequency energy generating device can be improved, the radio frequency energy generating device has a good isolation effect, and when the radio frequency energy generating device is applied to treatment of heart diseases, treatment effect and safety of radio frequency ablation can be guaranteed.

Drawings

In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.

Fig. 1 is a schematic structural diagram of a radio frequency ablation system according to an embodiment of the present application.

Fig. 2 is a schematic structural diagram of a radio frequency energy generation apparatus according to an embodiment of the present disclosure.

Fig. 3 is a schematic structural diagram of an ablation device including an ablation needle and an insulating sleeve in an assembled state according to an embodiment of the present application.

Fig. 4 is a schematic structural view of the ablation needle and the insulating sleeve shown in fig. 3 in an unassembled state.

Fig. 5 is a functional block diagram of an rf energy generating device according to an embodiment of the present application.

Fig. 6 is a schematic circuit diagram of an rf loop of an rf energy generating apparatus according to an embodiment of the present disclosure.

Fig. 7 is a functional block diagram of an rf energy generating device according to another embodiment of the present application.

Fig. 8 is a schematic circuit diagram of a portion of a main control loop of the rf energy generator according to an embodiment of the present disclosure.

Fig. 9 is a schematic circuit diagram of a part of a DAC control loop of the rf energy generating apparatus according to the embodiment of the present application.

Fig. 10 is a schematic circuit diagram of a portion of a main control loop of the rf energy generator according to an embodiment of the present disclosure.

Fig. 11 is a schematic circuit diagram of a PWM control loop of the rf energy generator according to an embodiment of the present disclosure.

Description of the main elements

Radiofrequency ablation system 1000

Radio frequency energy generating device 100

Outer casing 11

Input/output interface 12

Power supply module 31

First isolated switching device 32

Second isolated switching device 33

Rectifier module 34

Filter module 35

Control unit 36

DAC module 37

PWM control module 38

Ablation parameter detection module 39

Temperature detection module 391

Voltage detection module 392

Current detection module 393

Impedance detection module 394

Second isolator 40

Display unit 41

Control assembly 42

Mechanical knob 421

Mechanical button 422

First isolator 43

Logic control circuit 44

Switch control circuit 45

Ablation device 200

Ablation needle assembly 21

Ablation needle 211

Insulating sleeve 212

Ablation handle 213

Connecting conduit 22

Reference electrode 500

Input interface J1

Output interfaces J2, J3

DC-DC converter M1

Converter T1

Inductor L1

Capacitor C11

Isolation chips U2 and U9

MOS tube driving chip U5

Logic AND gate U6, U7

DAC chip U10

Follower U11

Optocoupler U71

Logic devices U8, U91

The following detailed description will further illustrate the present application in conjunction with the above-described figures.

Detailed Description

The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application. The drawings are for illustration purposes only and are merely schematic representations, not intended to limit the present application.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. The terminology used in the description herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.

Please refer to fig. 1, which is a schematic structural diagram of a radio frequency ablation system according to an embodiment of the present application. The radiofrequency ablation system 1000 includes a radiofrequency energy generation device 100 and an ablation device 200. As shown in fig. 2, the rf energy generating apparatus 100 may include a housing 11 and a plurality of input/output interfaces 12 disposed on the housing 11. The input/output interface 12 may be used to interface with devices such as the ablation device 200. The rf energy generating device 100 is used as an rf energy generating and controlling device for providing rf energy required for rf ablation during rf ablation and controlling the output of the rf energy according to ablation parameters of the site to be ablated. The site to be ablated is a diseased site, such as diseased tissue of the heart or other diseased tissue.

Accordingly, as shown in fig. 3 and 4, the ablation device 200 includes at least an ablation needle assembly 21 and a plurality of connecting catheters 22. Wherein the plurality of connecting conduits 22 are used for connecting the ablation device 200 with the radiofrequency energy generation device 100 or a coolant conduit (not shown) or the like.

In this embodiment, the ablation needle assembly 21 is electrically connected to the radiofrequency energy generator 100, and the ablation needle assembly 21 is inserted into the site to be ablated when performing radiofrequency ablation, receives radiofrequency energy output by the radiofrequency energy generator 100, and releases the radiofrequency energy to the site to be ablated, so as to perform radiofrequency ablation on the site to be ablated, thereby achieving the purpose of treating diseased tissue. Wherein, the part to be ablated is a pathological change part in a living body. Taking hypertrophic cardiomyopathy as an example, the ablation needle assembly 21 is inserted into the heart of a patient through an apical approach, and radio frequency ablation operation is performed on hypertrophic interventricular myocardium to treat hypertrophic cardiomyopathy.

Fig. 5 is a functional block diagram of an rf energy generating device according to an embodiment of the present application. In this embodiment, as shown in fig. 5, the rf energy generating apparatus 100 further includes a power module 31, a first isolation converter 32, and a second isolation converter 33. The power module 31 is a power input terminal. The first isolation switching device 32 is electrically connected to the power module 31, and is configured to receive an input voltage provided by the power module 31, perform voltage reduction processing on the input voltage, and output a first voltage after electrical isolation.

In the present embodiment, the power input terminal is used for electrical connection with an AC power source (commercial power) to obtain an input AC high voltage. In this embodiment, the radio frequency energy generating apparatus 100 may further include a rectifying module 34, where the rectifying module 34 is electrically connected between the power module 31 and the first isolation switching device 32, and is configured to rectify and filter the input voltage provided by the power module 31 and output a dc high voltage to the first isolation switching device 32.

In the present application, the first isolation switching device 32 may perform a voltage reduction process on the input voltage provided by the power module 31, so as to adjust the output power of the rf energy generating apparatus 100; meanwhile, the input voltage can be isolated and output, so that the generation of leakage current is reduced.

The second isolation transformer 33 is electrically connected to the first isolation transformer 32, and is configured to convert the first voltage output by the first isolation transformer 32 into a radio frequency signal, electrically isolate the radio frequency signal, and output the radio frequency signal to the ablation apparatus 200. Wherein the ablation device 200 is configured to receive the radio frequency signal and perform radio frequency ablation on the portion to be ablated by using radio frequency energy of the radio frequency signal.

In the present application, the frequency conversion of the first voltage, i.e. converting a direct current voltage signal into an alternating current radio frequency signal (DC to AC), can be accomplished by the second isolation conversion device 33; meanwhile, the radio frequency signal can be isolated and output, so that the generation of leakage current is reduced.

In this embodiment, the output end of the second isolation conversion device 33 is further electrically connected to a reference electrode 500, and the reference electrode 500 is attached to the target object where the to-be-ablated part is located in the rf ablation process. Wherein the reference electrode 500 is generally configured as a patch electrode, and is attached to the body surface of the target object.

In this embodiment, the power module 31, the first isolation switching device 32, the second isolation switching device 33, the ablation device 200, the reference electrode 500 and the target object together form a radio frequency loop during a radio frequency ablation process. It will be appreciated that the reference electrode 500 and the ablation needle 211 (shown in fig. 3 and 4) included in the ablation device 200 constitute two poles of the rf circuit.

In one embodiment, for example, as shown in fig. 6, the power module 31 may correspond to an input interface J1 in circuit structure and may correspond to one of the input and output interfaces 12 of the casing 11 of the rf energy generating device 100 shown in fig. 2 in appearance structure.

The first isolation switching device 32 may correspond to a DC-DC converter M1 having an electrical isolation performance, and the second isolation switching device 33 may correspond to a converter T1. The DC-DC converter M1 is configured to convert the DC high voltage output by the rectifier module 34 into a DC low voltage, and simultaneously isolate the converted DC low voltage from the utility power. Namely, the first voltage is a direct current low voltage. It is understood that the operation principle of the voltage conversion and the electrical isolation of the DC-DC converter M1 is known in the art and will not be described in detail herein.

The rf energy generating apparatus 100 may further include a filtering module 35 electrically connected between the DC-DC converter M1 and the converter T1, wherein the filtering module 35 is configured to filter the first voltage output by the DC-DC converter M1, i.e., the DC low voltage, so as to stabilize the voltage signal entering the converter T1. In this embodiment, the filtering module 35 is an LC filtering circuit, and includes an inductor L1 and a capacitor C11.

The input terminal TM2 of the primary side of the transformer T1 receives the first voltage filtered by the filtering module 35, and the secondary side of the transformer T1, i.e., the output terminals TM4 and TM5, can output the rf signal through an output interface J2. Meanwhile, a first voltage is received by the primary coil of the transformer T1, and the radio frequency signal is output by the secondary coil of the transformer T1, so that the radio frequency signal is isolated from the first voltage. The output interface J2 may correspond in appearance structure to one of the input and output interfaces 12 provided on the housing 11 of the rf energy generating device 100 shown in fig. 2.

The radio frequency energy generating device 100 of the present application uses the first isolation switching device 32(DC-DC converter M1) to perform voltage reduction and electrical isolation on the input voltage in the radio frequency loop, and uses the second isolation switching device 33 (converter T1) to convert the output voltage of the first isolation switching device 32 into a radio frequency signal and to electrically isolate the radio frequency signal to generate radio frequency energy, so that before the radio frequency energy is generated, the first isolation switching device 32(DC-DC converter M1) and the second isolation switching device 33 (converter T1) are used to increase the creepage distance and reduce the generation of leakage current, so as to achieve double isolation on the input voltage in the radio frequency loop, thereby improving the anti-electric shock level of the radio frequency energy generating device 100, and enabling the radio frequency energy generating device 100 to have a better isolation effect. Because the allowable current leakage value of the heart is far smaller than the allowable current leakage values of other tissues and organs, when the radio frequency ablation is applied to the treatment of heart diseases, compared with the ablation of tumors and the like, the higher the safety level is to be met, and the corresponding requirement on electric shock prevention is higher.

Referring again to fig. 5, the rf energy generating apparatus 100 further includes a control unit 36 and a DAC module 37. Wherein the DAC module 37 is electrically connected to the first isolation switching device 32, and the control unit 36 is electrically connected to the DAC module 37. The control unit 36 is configured to control the DAC module 37 to output an adjustment signal to adjust a voltage value of the first voltage output by the first isolation switching device 32, so as to adjust the output power of the radio frequency energy generation apparatus 100.

In one embodiment, as shown in fig. 7, the rf energy generating apparatus 100 may further include a first isolator 43, and the control unit 36 is electrically connected to the DAC module 37 through the first isolator 43.

Specifically, in some embodiments, referring to fig. 8 and 9, the control unit 36 may correspond to a master MCU, the DAC module 37 may correspond to a DAC chip U10, and the first isolator 43 may correspond to an isolation chip U2. As shown in fig. 8, the master MCU outputs a digital signal SPI to the DAC chip U10 through an isolation chip U2 and an output interface J3.

As shown in fig. 9, the DAC chip U10 outputs the adjustment signal according to the received digital signal SPI. After the adjusting signal comes out from the pin 8 of the DAC chip U10, the adjusting signal enters the DC-DC converter M1, i.e., the first isolation conversion device 32, through the follower U11, so as to adjust the voltage value of the first voltage output by the DC-DC converter M1. In this embodiment, the adjustment signal is an analog voltage signal. The voltage value of the input and output voltage of the DC-DC converter M1 is not limited, for example, the DC high voltage entering the DC-DC converter M1 may be 300V, and the voltage value of the first voltage output from the DC-DC converter M1 may range from 0 to 48V.

In this embodiment, the master MCU may also control the output state of the DAC chip U10. Wherein, the output state can comprise two states of output and off. Specifically, as shown in fig. 8, the master MCU may further output a first switch signal SW _ DAC to the enable pin 5 of the DAC chip U10 through the isolation chip U2, the output interface J3 and an isolation chip U9, so as to control the output state of the DAC chip U10.

In this embodiment, the master MCU may also control the output state of the DC-DC converter M1. Wherein, the output state can comprise two states of output and off. Specifically, as shown in fig. 8, the master MCU may output a second switch signal SW _ PC _ M1 through the isolation chip U2 and the output interface J3. As shown in fig. 10, the second switch signal SW _ PC _ M1 can be transmitted to pin 2 of the DC-DC converter M1 through a logic device U91 (logic and gate) and an optical coupler device U71 to enter the DC-DC converter M1, so as to control the output state of the DC-DC converter M1.

It can be understood that the rf energy generating device 100 of the present application can further improve the safety of the rf energy generating device 100 by using the first isolator 43 to isolate the output digital signal SPI and the control signals, such as the first switch signal SW _ DAC and the second switch signal SW _ PC _ M1.

In this embodiment, the second isolated switching device 33 may be a fixed duty cycle push-pull converter. It is understood that the operation principles of voltage conversion and electrical isolation of the fixed duty push-pull converter are known in the art and are not specifically described herein.

Referring to fig. 5 again, the rf energy generating apparatus 100 further includes a Pulse Width Modulation (PWM) control module 38 electrically connected to the second isolation switching device 33, wherein the PWM control module 38 is configured to output a PWM signal to control the second isolation switching device 33 to output an rf signal.

In one embodiment, referring to fig. 11, the PWM control module 38 is a PWM signal generator U4, and the PWM signal generator U4 controls the on/off frequency of the primary of the inverter T1 by outputting two complementary PWM signals to control the inverter T1 to output an ac rf signal.

Specifically, in this embodiment, the PWM signal generator U4 is electrically connected to the primary side of the inverter T1 through a logic control circuit 44 and a switch control circuit 45, the PWM signal generator U4 outputs the PWM signal to the logic control circuit 44, and the logic control circuit 44 logically combines the PWM signals and outputs a logic control signal to the switch control circuit 45 to control the switching state of the switch control circuit 45, so as to control the on-off frequency of the primary side of the inverter T1, and further control the on-off frequency of the current flowing through the primary side of the inverter T1.

Wherein the primary of the converter T1 includes a first input TM1, a second input TM2, and a third input TM 3. As shown in fig. 6, the second input terminal TM2 is electrically connected to the output terminal of the DC-DC converter M1. As shown in fig. 11, the switch control circuit 45 may include a MOS transistor Q2 electrically connected to the first input terminal TM1, and a MOS transistor Q1 electrically connected to the third input terminal TM 3. The logic control circuit 44 may include logic and gates U6 and U7. One input end of the logic and gate U6 is electrically connected to the first output pin 21 of the PWM signal generator U4, and the output end of the logic and gate U6 is electrically connected to the MOS transistor Q1 through the MOS transistor driver chip U5. One input end of the logic and gate U7 is electrically connected to the second output pin 22 of the PWM signal generator U4, and the output end of the logic and gate U7 is electrically connected to the MOS transistor Q2 through the MOS transistor driver chip U5.

In this embodiment, the radio frequency signal is a sinusoidal alternating current signal. The PWM signal generator U4 controls the on-off frequency of the MOS transistors Q1 and Q2 through the logic and gates U6 and U7, thereby controlling the on-off frequency of the primary of the converter T1 to generate the sinusoidal ac signal. For example, during the conduction of the MOS transistor Q1, the inverter T1 generates the positive half-wave of the sinusoidal alternating current signal, and during the conduction of the MOS transistor Q2, the inverter T1 generates the negative half-wave of the sinusoidal alternating current signal.

In this embodiment, the main control MCU may also control the output state of the PWM signal. Specifically, the second switch signal SW _ PC _ M1 output by the main control MCU may also enter the logic and gates U6 and U7 from the other input ends of the logic and gates U6 and U7 through a logic device U8 (a logic nand gate), and respectively logically combine with the PWM signal, thereby implementing control of the output state of the PWM signal.

Referring to fig. 5 again, in this embodiment, the radiofrequency energy generation device 100 further includes an ablation parameter detection module 39, and the ablation parameter detection module 39 is electrically connected to the radiofrequency circuit and the control unit 36, and is configured to detect an electrical parameter of the to-be-ablated region in the radiofrequency ablation process and feed back the acquired electrical parameter to the control unit 36.

It is to be understood that the ablation parameter detection module 39, although logically divided as part of the rf energy generating device 100, may be provided at least in part on the ablation device 200.

For example, in the present embodiment, as shown in fig. 7, the ablation parameter detection module 39 may include a temperature detection module 391, where the temperature detection module 391 is configured to detect the ablation temperature of the site to be ablated in real time during the rf ablation. Wherein the temperature detection module 391 is disposed in the ablation device 200.

Specifically, referring to fig. 3 and 4, in one embodiment, the ablation needle assembly 21 includes an ablation needle 211, a hollow insulating sleeve 212, and an ablation handle 213 coupled to a proximal end of the ablation needle 211. The insulation sleeve 212 is movably sleeved outside the ablation needle 211 and is detachably and rotatably connected with the ablation handle 213. The distal end of the ablation needle 211 extends out of the insulating sleeve 212, and since the insulating sleeve 212 is fully insulated, the portion of the ablation needle 211 extending out of the insulating sleeve 212 performs an ablation operation. Specifically, when the ablation needle 211 is electrically connected to the radio frequency energy generating device 100, the ablation needle 211 transmits a high-frequency current to enable positive and negative ions with charges in the lesion tissue around the distal end of the ablation needle 211 to generate a high-speed oscillation motion, and the high-speed oscillation ions generate a large amount of heat due to friction, so that the temperature in the lesion tissue is increased, and finally, proteins in lesion cells are denatured, water inside and outside the cells is lost, and the lesion tissue is coagulative necrosis, thereby realizing radio frequency ablation. It will be understood that the terms "proximal" and "distal" are used herein as conventional terms in the medical field. Specifically, "distal" refers to the end of the surgical procedure that is distal from the operator, and "proximal" refers to the end of the surgical procedure that is proximal to the operator.

The temperature detection module 391 may be disposed on the insulating sleeve 212. In some embodiments, the temperature detection module 391 may be a thermocouple. Alternatively, in other embodiments, the temperature detecting module 391 may be a thermistor.

In this embodiment, the ablation parameter detection module 39 may further include a voltage detection module 392 and a current detection module 393. The voltage detection module 392 can be connected in parallel to two poles of the rf loop, and is configured to detect an ablation voltage between the two poles of the rf loop. The current detection module 393 may be connected in series in the rf loop for detecting an ablation current in the rf loop. It will be appreciated that in this embodiment, the control unit 36 may also calculate the ablation power in real time based on the received ablation voltage and ablation current.

In this embodiment, the ablation parameter detection module 39 may further include an impedance detection module 394, and the impedance detection module 394 is used for detecting the impedance of the ablation site.

Referring to fig. 5 and 7 again, in this embodiment, the rf energy generating device 100 further includes a second isolator 40, and the second isolator 40 is electrically connected between the ablation parameter detecting module 39 and the control unit 36, and is configured to electrically isolate the ablation parameter detected by the ablation parameter detecting module 39 and feed the electrically isolated ablation parameter back to the control unit 36. Wherein the second isolator 40 may comprise an optical fiber and an optical fiber driver.

In the signal acquisition process, the radio frequency energy generation device 100 uses the second isolator 40 to electrically isolate the ablation parameters detected by the ablation parameter detection module 39, namely, the input signals, so that the control unit 36 can deliver the accurate ablation parameters, and the radio frequency ablation power is regulated and controlled according to the accurate ablation parameters, thereby further improving the safety of the radio frequency energy generation device 100.

In this embodiment, as shown in fig. 2 and 5, the rf energy generating apparatus 100 may further include a display unit 41 electrically connected to the control unit 36, and the control unit 36 is further configured to control the display unit 41 to display the ablation parameters, the ablation power, and the like, so as to display a real-time ablation state.

In this embodiment, the radio frequency energy generating apparatus 100 further includes a control component 42 electrically connected to the control unit 36, wherein the control component 42 is configured to receive an input operation of a user to generate a corresponding input control signal, and the control unit 36 is configured to control the DAC module 37 to output the adjustment signal according to the input control signal, so as to adjust the output of the radio frequency energy. In this way, a medical staff such as a physician can know the condition of the ablation procedure by observing various ablation parameters displayed by the display unit 41, and adjust the output of the radio frequency energy through the control module 42, so that the ablation needle 211 performs radio frequency ablation on the lesion tissue at a preset temperature based on a set power value.

It is understood that, as shown in fig. 2, the control assembly 42 may include a physical mechanical knob 421, a mechanical button 422, or a touch button, etc. disposed on the housing 11 of the rf energy generating device 100 for operation by medical personnel, such as a physician. Optionally, the display unit 41 may also be a touch display screen, and the doctor may also perform an operation by touching a virtual key displayed in the display unit 41.

For example, before operation, a physician may set the power value of the rf signal output by the rf energy generating device 100 according to the size of the region to be ablated; in operation, a physician may adjust (for example, by touching a virtual key displayed in the display unit 41, or operating a physical mechanical knob 421 or a mechanical key 422 disposed on the housing 11, or the like) a power value of the rf signal output by the rf energy generation device 100 according to data displayed by the display unit 41 of the rf energy generation device 100, so as to make the temperature of the ablation site within a preset temperature range, and make the ablation needle 211 perform rf ablation on the lesion tissue at a preset temperature based on the set power value; after operation, when a predetermined ablation time or a predetermined ablation effect is reached, the control unit 36 may cut off the output power of the first isolating and switching device 32, so that the ablation device 200 stops ablation.

It is understood that the rf energy generating device 100 may further include a lamp panel (not shown) electrically connected to the control unit 36, and the control unit 36 may further be configured to control the lamp panel to emit light to indicate an abnormality when the ablation parameter or the ablation power is abnormal, for example, exceeds a preset range. Optionally, the rf energy generating device 100 may further include a buzzer (not shown) electrically connected to the control unit 36, and the control unit 36 may further be configured to control the buzzer to sound when the ablation parameter or the ablation power is abnormal, so as to indicate the abnormality.

It can be understood that, since the portion of the ablation needle 211 contacting the tissue transmits the rf energy to generate high temperature in the tissue, so that the tissue coagulatively necroses to achieve the therapeutic purpose, but the local high temperature may affect the normal tissue that does not need to be ablated, a cooling channel may be disposed in the ablation needle 211, and the cooling channel is used for delivering a gaseous or liquid cooling medium (e.g., cooling water) to cool down the high temperature portion to control the local temperature during the ablation operation. Wherein the cooling channel may be in communication with one of the connecting catheters 22 on the ablation device 200.

Correspondingly, the rf ablation system 1000 may further include a peristaltic pump (not shown), wherein the peristaltic pump may be externally connected to a water circulation catheter and the connection catheter 22 of the ablation device 200, and deliver a cooling medium to the cooling channel inside the ablation needle 211 through the water circulation catheter and the connection catheter 22 of the ablation device 200, and circulate in the cooling channel, so as to achieve a cooling effect.

The foregoing is a preferred embodiment of the present application, and it should be noted that, for those skilled in the art, various modifications and decorations can be made without departing from the principle of the present application, and these modifications and decorations are also regarded as the protection scope of the present application.

Claims (17)

1. A radio frequency energy generating device, comprising:

a power supply module;

the first isolation conversion device is electrically connected with the power supply module and used for receiving the input voltage provided by the power supply module, performing voltage reduction processing on the input voltage, electrically isolating the input voltage and outputting a first voltage; and

and the second isolation conversion device is electrically connected with the first isolation conversion device and is used for converting the first voltage output by the first isolation conversion device into a radio frequency signal, electrically isolating the radio frequency signal and outputting the radio frequency signal to an ablation device, wherein the ablation device is used for receiving the radio frequency signal and performing radio frequency ablation on a part to be ablated by using radio frequency energy of the radio frequency signal.

2. The rf energy generator of claim 1, wherein the output end of the second isolating and transforming device is further electrically connected to a reference electrode, and the reference electrode is attached to a target object on which the portion to be ablated is located during rf ablation;

the power module, the first isolation conversion device, the second isolation conversion device, the ablation device, the reference electrode and the target object jointly form a radio frequency loop in a radio frequency ablation process.

3. The radio frequency energy generation apparatus according to claim 1 or 2, wherein the second isolated conversion device is a fixed duty cycle push-pull converter;

the radio frequency energy generation device also comprises a PWM control module electrically connected with the second isolation conversion device, and the PWM control module is used for outputting PWM signals to control the second isolation conversion device to output radio frequency signals.

4. The radio frequency energy generation device according to claim 3, wherein the PWM control module is a PWM signal generator for outputting two-way complementary PWM signals to control the on-off frequency of the primary of the fixed-duty push-pull converter so as to control the fixed-duty push-pull converter to output an AC radio frequency signal.

5. The radio frequency energy generation apparatus according to claim 2, wherein the first isolation conversion device is a DC-DC converter having an electrical isolation property; the radio frequency energy generation apparatus further comprises:

a DAC module electrically connected with the first isolation conversion device;

a first isolator; and

and the control unit is electrically connected with the DAC module through the first isolator and is used for controlling the DAC module to output an adjusting signal so as to adjust the voltage value of the first voltage output by the first isolation conversion device, thereby realizing the adjustment of the output power of the radio frequency energy generation device.

6. The rf energy generating device according to claim 5, further comprising an ablation parameter detecting module electrically connected to the rf circuit and the control unit for detecting ablation parameters of the site to be ablated during rf ablation and feeding back the detected ablation parameters to the control unit.

7. The rf energy generating device according to claim 6, further comprising a second isolator electrically connected between the ablation parameter detecting module and the control unit for electrically isolating the ablation parameter detected by the ablation parameter detecting module and feeding the electrically isolated ablation parameter back to the control unit.

8. The radio frequency energy generation device according to claim 7, wherein the second isolator comprises an optical fiber and an optical fiber driver.

9. The rf energy generator according to any of claims 6-8, further comprising a display unit electrically connected to said control unit, said control unit further configured to control said display unit to display said ablation parameters.

10. The rf energy generating device as claimed in claim 9, further comprising a control component electrically connected to the control unit, wherein the control component is configured to receive an input operation from a user to generate a corresponding input control signal, and the control unit is configured to control the DAC module to output the adjustment signal according to the input control signal.

11. The radiofrequency energy generation device of claim 6, wherein the ablation parameter detection module comprises a temperature sensor for detecting an ablation temperature of the site to be ablated in real time during the radiofrequency ablation process;

wherein the temperature sensor is disposed in the ablation device.

12. The rf energy generation device of claim 11, wherein the ablation parameter detection module further comprises:

the voltage detection module is electrically connected to two poles of the radio frequency circuit and is used for detecting the ablation voltage between the two poles of the radio frequency circuit, wherein the reference electrode and an ablation needle included by the ablation device form the two poles of the radio frequency circuit; and

the current detection module is electrically connected to the radio frequency loop and is used for detecting the ablation current in the radio frequency loop.

13. The rf energy generator of claim 12, wherein the control unit is further configured to calculate the ablation power in real time based on the received ablation voltage and ablation current.

14. The radiofrequency energy generation device of any one of claims 11-13, wherein the ablation parameter detection module further comprises an impedance detection module for detecting an impedance of the ablation site.

15. The rf energy generating apparatus according to claim 1 or 5, further comprising a rectifying module electrically connected between the power module and the first isolating and converting device, for rectifying and filtering the input voltage provided by the power module and outputting a dc high-voltage signal to the first isolating and converting device;

the first isolation conversion device is used for converting the direct current high voltage into direct current low voltage.

16. The rf energy generator according to claim 1, further comprising a filtering module electrically connected between the first isolating transformer and the second isolating transformer, wherein the filtering module is configured to filter the first voltage output by the first isolating transformer.

17. A radio frequency ablation system comprising an ablation device and a radio frequency energy generation device as claimed in any one of claims 1 to 16, wherein the ablation device comprises an ablation needle assembly electrically connected with the radio frequency energy generation device for receiving the radio frequency energy output by the radio frequency energy generation device and releasing the radio frequency energy to the site to be ablated so as to perform radio frequency ablation on the site to be ablated.

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