CN113824309A

CN113824309A - Radio frequency ablation power supply and radio frequency ablation system

Info

Publication number: CN113824309A
Application number: CN202010539947.5A
Authority: CN
Inventors: 王雄志; 刘丽文; 胡芮; 刘道洋; 胡善锋; 丘信炯; 张庭超
Original assignee: Hangzhou Nuo Cheng Medical Instrument Co ltd
Current assignee: Hangzhou Nuo Cheng Medical Instrument Co ltd
Priority date: 2020-06-12
Filing date: 2020-06-12
Publication date: 2021-12-21

Abstract

The application provides a radio frequency ablation power supply and a radio frequency ablation system. The radiofrequency ablation power source includes a first control unit, a second control unit, and a radiofrequency energy generation circuit. The radio frequency energy generating circuit comprises a power supply module, a voltage reduction module and a voltage conversion module which are sequentially and electrically connected. The power supply module provides a voltage-stabilized direct-current signal. The voltage reduction module carries out voltage reduction processing on the voltage-stabilized direct current signal and outputs a low-voltage direct current signal. The voltage conversion module is electrically connected with the first control unit to receive the low-voltage direct current signal and the radio frequency control signal output by the first control unit and convert the low-voltage direct current signal into a radio frequency signal according to the radio frequency control signal. The second control unit sends a voltage adjusting signal to the voltage reduction module to control the voltage reduction module to adjust the voltage value of the currently output low-voltage direct-current electric signal. The radio frequency ablation power supply can accurately and stably control the output of the radio frequency control signal independently, so that the radio frequency signal can be ensured to be stable and reliable.

Description

Radio frequency ablation power supply and radio frequency ablation system

Technical Field

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

Background

Currently, radio frequency ablation technology has been applied in the treatment of neoplastic diseases, neurological diseases, cardiac diseases, etc., as an emerging technology in the medical field. The radiofrequency ablation is to send an ablation electrode to a diseased region, and the ablation electrode is utilized to generate an electric heating effect in diseased tissues to dry and necrose diseased cells, thereby achieving the purpose of treatment.

For example, when the rf ablation technology is applied to treat hypertrophic cardiomyopathy, the electrode needle is electrically connected to the rf ablation power supply, under the guidance of ultrasound, the electrode needle is punctured to the cardiac hypertrophy position in the ventricular septum of the heart through the apex between the ribs, and after the rf ablation power supply is started, the electrode continuously ablates the hypertrophic myocardium until the diseased myocardial cells are dehydrated and necrotic, so that the hypertrophic myocardial necrosis shrinks and thins, and the left ventricular outflow tract widens.

Control of various output parameters of the rf energy is important to ensure the safety of the ablation procedure and to achieve the desired therapeutic effect. Some existing rf ablation power supplies generally control the whole ablation process through a controller, which not only controls the frequency and waveform of the output rf signal, but also performs other controls, such as rf output switch control, rf power adjustment control, user input parameter detection and processing, rf parameter detection and processing, logic control of the rf ablation process, output interface display, etc., so that delay of processing the rf signal waveform may occur to affect generation of the rf signal waveform, and even cause distortion of the rf signal waveform. The abnormal rf signal waveform may cause instability of rf power, rf current output, etc., thereby affecting the rf ablation effect.

Disclosure of Invention

The application provides a radio frequency ablation power supply and radio frequency ablation system can carry out accurate, stable control to the output of radio frequency control signal to ensure the stability of the radio frequency signal's of radio frequency ablation power supply output wave form, thereby can make the radio frequency ablation power supply can output reliable and stable radio frequency signal, with the safety of ensureing to melt the process and can obtain anticipated ablation treatment.

In a first aspect, the present application provides a radio frequency ablation power supply comprising a first control unit, a radio frequency energy generating circuit, and a second control unit. The first control unit is used for outputting a radio frequency control signal. The radio frequency energy generating circuit comprises a power supply module, a voltage reduction module and a voltage conversion module which are sequentially and electrically connected. The power supply module is used for providing a voltage-stabilizing direct-current signal; the voltage reduction module is used for carrying out voltage reduction processing on the voltage-stabilized direct current signal so as to output a low-voltage direct current signal; the voltage conversion module is further electrically connected with the first control unit, and is used for receiving the low-voltage direct-current electric signal and the radio frequency control signal and converting the low-voltage direct-current electric signal into a radio frequency signal according to the radio frequency control signal. The second control unit is electrically connected with the voltage reduction module and used for sending a voltage regulation signal to the voltage reduction module so as to control the voltage reduction module to regulate the voltage value of the currently output low-voltage direct-current signal, and therefore the power regulation of the radio-frequency signal is realized.

In a second aspect, the present application provides a radiofrequency ablation system comprising an ablation device and a radiofrequency ablation power source as described above. The ablation device is electrically connected with the output end of the radio frequency ablation power supply and is used for receiving the radio frequency signal output by the radio frequency ablation power supply and performing radio frequency ablation on a part to be ablated by using the radio frequency energy of the radio frequency signal.

The radiofrequency ablation power supply of the application controls the radiofrequency signal by independently outputting the radiofrequency control signal through the first control unit, the second control unit is used for executing operations such as radio frequency output switch control, radio frequency power regulation control, user input parameter detection and processing, actual ablation parameter detection and processing, output interface display and the like, namely, the output control of the radio frequency control signal is separated from other control, so that the output of the radio frequency control signal can be more accurately and stably controlled, to ensure the stability of the RF control signal, avoid the waveform distortion of the RF signal caused by the interference on the output of the RF control signal, and further, the radio frequency ablation power supply can output stable and reliable radio frequency signals so as to ensure the safety of the ablation process and obtain the expected ablation treatment effect.

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 block diagram of a radio frequency ablation system according to an embodiment of the present application.

Fig. 2 is a schematic perspective view of a radio frequency ablation power supply according to an embodiment of the present application.

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

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

Fig. 5 is a functional block diagram of a rf ablation power source according to an embodiment of the present application.

Fig. 6 is a functional block diagram of a power module according to an embodiment of the present disclosure.

Fig. 7 is a schematic circuit diagram of a radio frequency energy generating circuit in the radio frequency ablation power supply according to the embodiment of the present application.

Fig. 8 is a functional block diagram of a rf ablation power supply according to another embodiment of the present application.

Fig. 9 is a schematic circuit diagram of a part of a circuit structure of a voltage regulating circuit of a voltage dropping module according to an embodiment of the present application.

Fig. 10 is a schematic structural diagram of an output state control circuit of a voltage reduction module according to an embodiment of the present application.

Fig. 11 is a schematic structural diagram of a frequency and waveform control circuit of an rf signal according to an embodiment of the present disclosure.

FIG. 12 is a timing diagram illustrating various signals associated with RF signals in an embodiment of the present application.

Description of the main elements

Radiofrequency ablation system 1000

Radiofrequency ablation power supply 100

Outer casing 11

Input/output interface 12

Ablation device 200

Ablation needle assembly 210

Ablation electrode needle 211

Insulating sleeve 212

Ablation handle 213

Connecting line 220

Radio frequency energy generating circuit 30

Power supply module 31

Power input port 311

Power output port 312

Rectifier module 313

Voltage reduction module 32

Voltage conversion module 33

Transformation module 331

Switch module 332

Filter module 34

First control unit 40

Logic control circuit 41

Second control unit 50

Ablation parameter detection module 51

Control assembly 52

Mechanical knob 521

Mechanical button 522

Display unit 53

DAC Module 54

Connectors J1, J2, J3

DC-DC transformer M1

Transformer T1

Connecting ends TM1, TM2, TM3, TM4 and TM5

MOS switches Q1, Q2

Inductor L1

Capacitors C11, C13, C14

Singlechip U4

First output port 21

Second output port 22

MOS switch driving chip U5

DAC chip U10

Follower U11

Optical coupler U71

And gates U6, U7 and U9

NAND gate U8

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.

Referring to fig. 1, a radiofrequency ablation system 1000 provided by the embodiment of the present application includes a radiofrequency ablation power source 100 and an ablation device 200 electrically connected to an output end of the radiofrequency ablation power source 100. As shown in fig. 2, the rf ablation power source 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 ablation power supply 100 is used as an rf energy generating and controlling device for generating rf energy required for rf ablation based on preset ablation parameters during rf ablation and controlling the output of the rf energy according to detected ablation parameters associated with the site to be ablated. Wherein, the part to be ablated is a pathological change part in a living body, such as pathological change tissue of a heart of a human body or other pathological change tissue.

Specifically, referring to fig. 3, the ablation device 200 at least includes an ablation needle assembly 210 and a plurality of connecting lines 220. Wherein the plurality of connecting lines 220 are used for connecting the ablation needle assembly 210 with the radiofrequency ablation power source 100, a cooling circulation device (not shown) and the like.

When the radiofrequency ablation is performed, the ablation needle assembly 210 is inserted into the part to be ablated, receives the radiofrequency energy output by the radiofrequency ablation power supply 100, and releases the radiofrequency energy to the part to be ablated so as to perform the radiofrequency ablation on the part to be ablated, thereby achieving the purpose of ablating and treating the lesion tissue. Taking hypertrophic cardiomyopathy as an example, the ablation needle assembly 210 penetrates into the heart of a patient through an intercostal transapical approach, and performs radio frequency ablation on hypertrophic interventricular myocardium to treat hypertrophic cardiomyopathy.

Referring to fig. 4, in one embodiment, the ablation needle assembly 210 includes an ablation electrode needle 211, a hollow insulating sleeve 212, and an ablation handle 213 connected to a proximal end of the ablation electrode needle 211. The insulation sleeve 212 is movably sleeved outside the ablation electrode needle 211 and detachably connected with the ablation handle 213. The distal end of the ablation electrode needle 211 extends out of the insulation sleeve 212, and since the insulation sleeve 212 is completely insulated, the part of the ablation electrode needle 211 extending out of the insulation sleeve 212 is used for performing an ablation operation. Specifically, when the ablation electrode needle 211 is electrically connected to the output end of the rf ablation power supply 100, the ablation electrode needle 211 receives and transmits a high-frequency current to enable positive and negative ions with charges in the lesion tissue around the distal end of the ablation electrode needle 211 to perform high-speed oscillation movement, and the ions oscillating at high speed generate a large amount of heat due to friction, so that the temperature in the lesion tissue is increased, and finally, proteins in the lesion cells are denatured, water inside and outside the cells is lost, and coagulation necrosis occurs in the lesion tissue, thereby achieving rf ablation and achieving the purpose of treatment. When the length of the distal end of the ablation electrode needle 211 extending out of the insulation sleeve 212 needs to be changed to adjust the effective ablation length, the insulation sleeve 212 can be driven to move towards the distal end or the proximal end by a driving structure (not shown) in the ablation handle 213. 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.

Referring to fig. 5, fig. 5 is a functional block diagram of a rf ablation power source according to an embodiment of the present application. In this embodiment, the rf ablation power source 100 includes an rf energy generating circuit 30, a first control unit 40, and a second control unit 50. The rf energy generating circuit 30 is configured to receive an input voltage from an external power source and process the input voltage, such as step-down, frequency conversion, electrical isolation, etc., to output rf energy.

In the present embodiment, the radio frequency energy generating circuit 30 includes a power supply module 31, a voltage reducing module 32, and a voltage converting module 33, which are electrically connected in sequence. The power module 31 is used for providing a regulated dc signal. Specifically, the power module 31 may receive an input voltage provided by an external power source (not shown), and perform a rectification and voltage stabilization process on the input voltage to output the stabilized dc signal.

In the present embodiment, as shown in fig. 6, the power module 31 includes a power input port 311, a power output port 312, and a rectifying module 313 electrically connected between the power input port 311 and the power output port 312. The power input port 311 is configured to be electrically connected to an external AC power source (e.g., 220 v commercial power) to receive a high-voltage AC signal input by the external power source. The rectifying module 313 is configured to perform rectification filtering on the input high-voltage ac signal, and output the regulated dc signal through the power output port 312. The regulated dc signal is a high-voltage dc signal, and may be, for example, a dc signal of about 310 v.

The voltage reducing module 32 is electrically connected to the power output port 312, and is configured to receive the voltage-stabilized dc signal output by the power module 31, and output a low-voltage dc signal after performing voltage reduction processing on the voltage-stabilized dc signal.

The first control unit 40 is electrically connected to the voltage conversion module 33, and is configured to output a radio frequency control signal to the voltage conversion module 33. The voltage conversion module 33 is configured to receive the low-voltage dc signal and the rf control signal, convert the low-voltage dc signal into an rf signal according to the rf control signal, and output the rf signal to an rf output module, such as the ablation device 200.

In this way, the frequency conversion of the low-voltage DC signal, i.e., the conversion of the DC signal into a high-frequency AC signal (DC to AC) can be accomplished by the voltage conversion module 33 and the first control unit 40. The radio frequency signal is the high-frequency alternating current signal, for example, a 480kHz high-frequency alternating current signal. In this way, the radio frequency energy generating circuit 30 can output a radio frequency signal of 480 kHz. It is understood that the frequency value of the high-frequency alternating current signal is not limited to 480kHz, and may be other frequency values, which are not limited herein.

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.

It is understood that, in other embodiments, the voltage conversion module 33 may also be disposed between the power module 31 and the voltage reduction module 32, that is, the radio frequency energy generating circuit 30 includes the power module 31, the voltage conversion module 33, and the voltage reduction module 32 which are electrically connected in sequence. Thus, the rf energy generating circuit 30 performs frequency conversion on the regulated dc signal and then performs voltage reduction processing.

The second control unit 50 is electrically connected to the voltage-reducing module 32, and the second control unit 50 is configured to send a voltage adjustment signal to the voltage-reducing module 32 to control the voltage-reducing module 32 to adjust a voltage value of a currently output low-voltage direct-current electrical signal, so as to implement power adjustment on the radio-frequency signal.

In this embodiment, the second control unit 50 can also be used to perform on-off control on the rf output state of the rf energy generating circuit 30, detect and process user input parameters, detect and process actual ablation parameters, and perform display control on an output interface, for details, see the following detailed description.

In the present embodiment, the first control unit 40 and the second control unit 50 are two electronic devices independent of each other.

In the voltage conversion process, the voltage conversion module 33 converts the dc signal into an ac signal, and the frequency of the ac signal is the same as the frequency of the rf control signal. It will be appreciated that the stability of the rf control signal directly affects the frequency and waveform stability of the rf signal. That is, the instability of the rf control signal may cause the waveform distortion of the rf signal.

The rf ablation power supply 100 of the present application controls the rf signal by outputting the rf control signal separately through the first control unit 40, the second control unit 50 is used to perform operations such as rf output switch control, rf power adjustment control, user input parameter detection and processing, actual ablation parameter detection and processing, output interface display, etc., namely, the output control of the radio frequency control signal is separated from other control, so that the output of the radio frequency control signal can be more accurately and stably controlled, to ensure the stability of the RF control signal, avoid the waveform distortion of the RF signal caused by the interference on the output of the RF control signal, further, the rf ablation power supply 100 can output stable and reliable rf signals to ensure the safety of the ablation process and obtain the desired ablation treatment effect.

The circuit configuration of the radio frequency energy generating circuit 30 will be described in detail below.

In one embodiment, such as shown in fig. 7, the power output port 312 may correspond in circuit configuration to the connector J1 and in appearance configuration to one of the plurality of input/output interfaces 12 shown in fig. 2 disposed on the housing 11 of the rf ablation power supply 100. The voltage reducing module 32 may correspond to a DC-DC transformer M1 having an electrical isolation property.

The DC-DC transformer M1 is configured to convert the high-voltage DC electrical signal output by the power output port 312 into a low-voltage DC electrical signal, and electrically isolate the converted low-voltage DC electrical signal from an external power source, so as to reduce generation of leakage current. For example, the rectifying module 313 may receive 220 v commercial power, and output a high-voltage direct-current electrical signal of about 310 v after rectifying and filtering the 220 v commercial power. The DC-DC transformer M1 can reduce the high-voltage direct-current electric signal with about 310 volts to a low-voltage direct-current electric signal with 0-48 volts. It is understood that the operation principle of the voltage conversion and the electrical isolation of the DC-DC transformer M1 is known in the art and will not be described in detail herein. The voltage values of the high-voltage dc electrical signal and the low-voltage dc electrical signal may also be other values, and are not specifically limited herein.

As shown in fig. 7, in the embodiment, the rf energy generating circuit 30 may further include a filtering module 34 electrically connected between the DC-DC transformer M1 and the voltage converting module 33, where the filtering module 34 is configured to filter the low-voltage DC signal output by the DC-DC transformer M1 to further eliminate the influence of external power and internal noise on the low-voltage DC signal, so as to stabilize the low-voltage DC signal entering the voltage converting module 33. In the one embodiment, the filter module 34 is an LC filter circuit, and includes an inductor L1 and a capacitor C11.

Referring to fig. 5 and fig. 7, the voltage converting module 33 includes a transforming module 331 and a switching module 332. The voltage transformation module 331 is electrically connected to the output end of the voltage reduction module 32 through the filter module 34, and the switch module 332 is electrically connected between the first control unit 40 and the voltage transformation module 331.

In this embodiment, the transformation module 331 may correspond to a push-pull transformer T1 with electrical isolation performance. The push-pull transformer T1 comprises two primary windings TM1-TM2 and TM2-TM3 and a secondary winding TM4-TM5, wherein one primary winding TM1-TM2 comprises two connecting ends TM1 and TM2, and the other primary winding TM2-TM3 comprises two connecting ends TM2 and TM3, namely, the two primary windings TM1-TM2 and the two primary windings TM2-TM3 share the same connecting end TM 2. The connection terminal TM2 is electrically connected to the output terminal of the voltage reduction module 32 through the filter module 34, and is configured to receive the low-voltage dc electrical signal filtered by the filter module 34.

The switch module 332 comprises MOS switches Q1 and Q2, wherein control terminals of the MOS switches Q1 and Q2 are electrically connected to the first control unit 40, respectively, to receive the rf control signal output by the first control unit 40. A connection terminal TM1 of the push-pull transformer T1 is connected to the ground terminal SGND through the MOS switch Q1, and is connected to the ground terminal SGND through a capacitor C13. A connection terminal TM3 of the push-pull transformer T1 is connected to the ground terminal SGND through the MOS switch Q2, and is connected to the ground terminal SGND through a capacitor C14. The loop of the primary winding TM1-TM2 and the capacitor C13 forms a first LC oscillating circuit, and the loop of the primary winding TM2-TM3 and the capacitor C14 forms a second LC oscillating circuit. The first control unit 40 controls the on-off frequency of the MOS switches Q1 and Q2 respectively through the radio frequency control signal, so that the first LC oscillating circuit and the second LC oscillating circuit generate sine wave signals respectively during the turn-off period of the corresponding MOS switches, the voltage values of the dc voltage signals at the two connection terminals TM1 and TM3 of the push-pull transformer T1 continuously change, and thus the ac radio frequency signals are induced by the secondary windings TM4-TM5 of the push-pull transformer T1 correspondingly, and finally the radio frequency signals can be output through an output interface, such as a connector J2.

Taking the voltage change at the connection end TM1 as an example: in an initial state, the voltage at the connection terminal TM1 is 0, the low-voltage dc signal is transmitted to the connection terminal TM2, when the MOS switch Q1 is turned off, the first LC oscillating circuit generates a sine wave signal during the turn-off of the MOS switch Q1, and therefore, the dc voltage signal at the connection terminal TM1 is a sine wave signal whose voltage value continuously changes, and the secondary windings TM4-TM5 of the push-pull transformer T1 accordingly induce a sine wave signal; when the MOS switch Q1 is turned on, the connection terminal TM1 is electrically connected to the ground terminal SGND through the turned-on MOS switch Q1, and thus, a voltage value at the connection terminal TM1 becomes 0, and the secondary windings TM4-TM5 of the push-pull transformer T1 do not generate an induced signal corresponding to the primary windings TM1-TM 2. It can be understood that the principle of the voltage change at the connection terminal TM3 is the same as that of the voltage change at the connection terminal TM1, that is, in the initial state, the voltage at the connection terminal TM3 is 0, when the MOS switch Q2 is turned off, the second LC oscillating circuit generates a sine wave signal during the turn-off of the MOS switch Q2, the direct current voltage signal at the connection terminal TM3 is a sine wave signal whose voltage value changes continuously, and the secondary windings TM4-TM5 of the push-pull transformer T1 induce a sine wave signal accordingly; when the MOS switch Q2 is turned on, the connection terminal TM3 is electrically connected to the ground terminal SGND through the turned-on MOS switch Q2, and thus, a voltage value at the connection terminal TM3 becomes 0, and the secondary windings TM4-TM5 of the push-pull transformer T1 do not generate an induced signal corresponding to the primary windings TM2-TM 3.

It can be understood that, by receiving the low-voltage dc signal through the connection terminal TM2 of the push-pull transformer T1 and inducing the rf signal through the secondary winding TM4-TM5 of the push-pull transformer T1, the rf signal can be electrically isolated from the low-voltage dc signal, so as to reduce the generation of leakage current. Wherein the connector J2 may correspond in appearance to one of the plurality of input/output interfaces 12 shown in FIG. 2 provided on the housing 11 of the RF ablation power supply 100.

The rf ablation power supply 100 of the present application uses the DC-DC transformer M1 to perform voltage reduction and electrical isolation on the input voltage in the rf energy generating circuit 30, and uses the push-pull transformer T1 to convert the low-voltage DC signal output by the DC-DC transformer M1 into an rf signal and to electrically isolate the rf signal, so as to generate the rf signal, thereby increasing the creepage distance and reducing the generation of leakage current through the DC-DC transformer M1 and the push-pull transformer T1 before generating the rf signal, so as to achieve dual electrical isolation on the input voltage in the rf energy generating circuit 30, thereby increasing the anti-electric shock level of the rf ablation power supply 100, and enabling the rf ablation power supply 100 to have good 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.

The control performed by the second control unit 50 will be described in detail below.

Referring to fig. 5 again, in the present embodiment, the rf ablation power supply 100 further includes an ablation parameter detection module 51 and a control component 52 electrically connected to the second control unit 50, respectively. The ablation parameter detection module 51 is configured to detect a relevant electrical parameter of the to-be-ablated region in real time during the rf ablation process, and feed back the detected electrical parameter to the second control unit 50. The control component 52 is configured to receive an input operation of a user to generate a corresponding input signal, and send the input signal to the second control unit 50. The second control unit 50 is configured to generate the voltage adjustment signal according to the electrical parameter fed back by the ablation parameter detection module 51 and/or the input signal sent by the control component 52, and send the voltage adjustment signal to the voltage reduction module 32, so as to control the voltage reduction module 32 to adjust the voltage value of the currently output low-voltage dc signal in real time. In this way, the second control unit 50 can perform user input parameter detection and processing, actual ablation parameter detection and processing, and rf power adjustment control.

It can be understood that, by detecting the relevant electrical parameter of the to-be-ablated region in real time and adjusting the currently output low-voltage direct current electrical signal in real time according to the detected electrical parameter, the purpose of adjusting the power of the radio frequency signal output by the radio frequency energy generating circuit 30 in real time can be achieved, so as to ensure that the radio frequency signal can generate a continuous and stable thermal effect to obtain the desired ablation treatment effect.

In particular, the electrical parameters include, but are not limited to, ablation temperature and impedance of an ablation site, and ablation voltage and ablation current applied to the ablation site. Accordingly, the ablation parameter detection module 51 may include, but is not limited to, a temperature detection module, an impedance detection module, a voltage detection module, a current detection module. The temperature detection module can be a temperature sensor, such as a thermocouple or a thermistor, and is used for detecting the ablation temperature of the to-be-ablated part in real time in the radio frequency ablation process. The impedance detection module is used for detecting the impedance of the ablation part. The voltage detection module and the current detection module may be electrically connected to the rf energy generating circuit 30, for example, to an output of the voltage conversion module 33. The voltage detection module is used for detecting the ablation voltage output by the radio frequency energy generation circuit 30, and the current detection module is used for detecting the ablation current output by the radio frequency energy generation circuit 30. It will be appreciated that the second control unit 50 may also calculate the ablation power in real time from the received ablation voltage and ablation current.

It is understood that the ablation parameter detection module 51, although logically divided as part of the rf ablation power supply 100, may be provided at least in part on the ablation device 200. For example, the temperature detection module and the impedance detection module may be disposed on the ablation electrode needle 211 of the ablation device 200.

In this embodiment, as shown in fig. 2 and 5, the rf ablation power source 100 may further include a display unit 53 electrically connected to the second control unit 50, and the second control unit 50 is further configured to control the display unit 53 to display electrical parameters related to rf ablation, the ablation power, and the like, so as to display a real-time ablation state. That is, the second control unit 50 can perform operations such as output interface display. In this way, medical staff such as a doctor can know the condition of the rf ablation operation by observing various electrical parameters displayed by the display unit 53, and adjust the output of the rf energy generating circuit 30 in time through the control component 52, so that the ablation electrode needle 211 performs rf ablation on the lesion tissue at a preset temperature based on a set power value.

As shown in fig. 2, the control assembly 52 may include a physical mechanical knob 521, a mechanical button 522, or a touch button, etc. disposed on the housing 11 of the rf ablation power supply 100 for operation by a medical staff. Optionally, the display unit 53 may also be a touch display screen, and medical personnel may also perform related operations by touching the display unit 53. For example, before an operation, a physician can set parameters such as an upper and lower limit range of ablation impedance, an upper limit value of ablation temperature, ablation time and the like according to the size of a region to be ablated; in operation, a physician may adjust (for example, by touching the display unit 53, or operating a mechanical knob 521 or a mechanical button 522 disposed on the housing 11, or the like) a power value of the rf signal output by the rf ablation power supply 100 according to data displayed by the display unit 53 of the rf ablation power supply 100, so that the temperature of the ablation site is within a preset temperature range, and the ablation electrode needle 211 performs rf ablation on the lesion tissue at a preset temperature based on the set power value; when the preset ablation time or the preset ablation effect is reached, the second control unit 50 may cut off the output voltage of the voltage reduction module 32, so that the ablation device 200 stops ablation.

Referring to fig. 8, in an embodiment, the voltage adjustment signal output by the second control unit 50 is a digital signal, and the rf ablation power supply 100 further includes a DAC module 54 electrically connected between the second control unit 50 and the voltage reduction module 32. The DAC module 54 is configured to convert the voltage adjustment signal output by the second control unit 50 from a digital signal to an analog signal, and transmit the analog signal to the voltage reduction module 32 to adjust a voltage value of the low-voltage dc signal output by the voltage reduction module 32, so as to adjust the radio frequency output power of the radio frequency ablation power supply 100.

In particular, the second control unit 50 is used as a main controller, which may be a microprocessor. Referring to fig. 9, the DAC module 54 may correspond to a DAC chip U10, and the second control unit 50 may output a digital signal SPI to the DAC chip U10 through three interfaces POWER _ CS, POWER _ SCK, POWER _ SDI of the connector J3. The DAC chip U10 can output corresponding analog signals according to the received digital signals SPI. After the analog signal comes out from the pin 8 of the DAC chip U10, the analog signal enters the DC-DC transformer M1, i.e., the voltage dropping module 32, through the follower U11, so that the second control unit 50 adjusts the voltage value of the low-voltage direct-current electrical signal output by the DC-DC transformer M1.

In the embodiment, the second control unit 50 may also control the output state of the DAC chip U10. For example, as shown in fig. 9, the second control unit 50 may output a first switch signal SW _ DAC to the enable pin 5 of the DAC chip U10 to control the output state of the DAC chip U10. Wherein, the output state can comprise two states of output and off.

In the embodiment, the second control unit 50 is further configured to output a second switching signal to control the output state of the DC-DC transformer M1, so as to realize the switching control of the rf output of the rf ablation power supply 100. Wherein, the output state can comprise two states of output and off. For example, as shown in fig. 10, the second control unit 50 may output a second switch signal SW _ PC _ M1, and transmit the second switch signal SW _ PC _ M1 to pin 2 of the DC-DC transformer M1 through an and gate U9 and an optical coupler U71, so as to control the output state of the DC-DC transformer M1. In the present embodiment, when the second switch signal SW _ PC _ M1 is at a low level, the DC-DC converter M1 is in a state of having a signal output. On the contrary, when the second switch signal SW _ PC _ M1 is at a high level, the DC-DC transformer M1 is in a state of no signal output, i.e., an off state.

The frequency and waveform control of the rf signal performed by the first control unit 40 will be described in detail below.

Referring to fig. 11, the first control unit 40 may be a single chip microcomputer U4 in terms of circuit structure. The radio frequency control signals are two paths of complementary PWM signals and comprise a first path of PWM signal PWM 1 and a second path of PWM signal PWM 2. The single chip microcomputer U4 outputs the first PWM signal PWM 1 through a first output port 21 and outputs the second PWM signal PWM 2 through a second output port 22.

The control end of the MOS switch Q1 is electrically connected with the first output port 21 of the singlechip U4 to receive the first path of PWM signal PWM 1. The control end of the MOS switch Q2 is electrically connected to the second output port 22 of the single chip microcomputer U4 to receive the second path of PWM signal PWM 2.

The single chip microcomputer U4 controls the MOS switches Q1 and Q2 to be alternatively cut off respectively by outputting the two complementary PWM signals, so that the first LC oscillating circuit and the second LC oscillating circuit respectively generate sine wave half-wave signals during the cut-off period of the corresponding MOS switches, and then the connection terminals TM1 and TM3 of the two primary windings of the push-pull transformer T1 alternately form sine wave half-wave signals, so that the secondary windings TM4-TM5 of the push-pull transformer T1 correspondingly induce the sine wave half-wave signals.

It should be noted that, in this embodiment, the two primary windings TM1-TM2 and TM2-TM3 have different terminals with the same name, so that the secondary windings TM4-TM5 of the push-pull transformer T1 induce two half-wave sine waves with opposite directions corresponding to the two primary windings TM1-TM2 and TM2-TM3 respectively during the period when the MOS switches Q1 and Q2 are turned off alternately, thereby outputting a complete half-wave sine wave signal, that is, the rf signal is a sine wave signal.

For example, during the turn-off period of the MOS switch Q1, the first LC oscillating circuit generates a sine wave half-wave signal, and accordingly, the secondary windings TM4-TM5 of the push-pull transformer T1 induce a sine wave half-wave signal; it is understood that during this time, MOS switch Q2 is turned on, and the second LC oscillating circuit does not generate a sine wave signal. While during the turn-off period of the MOS switch Q2, the second LC oscillating circuit generates a sine wave half-wave signal, and accordingly, the secondary winding TM4-TM5 of the push-pull transformer T1 induces another sine wave half-wave signal in the opposite direction; it is understood that during this time, MOS switch Q1 is turned on, and the first LC oscillating circuit does not generate a sine wave signal. Thus, the secondary windings TM4-TM5 of the push-pull transformer T1 induce a complete sine wave signal during a cycle.

The frequency of the radio frequency control signal is the same as the frequencies of the first LC oscillating circuit and the second LC oscillating circuit, and the frequency of the sine wave signal is the same as the frequencies of the first LC oscillating circuit and the second LC oscillating circuit. If the rf control signal is unstable, the waveform of the sine wave signal is distorted. This application passes through singlechip U4 comes the independent output radio frequency control signal to can prevent radio frequency control signal's output receives the influence of other control signal and the control process that main control unit needs to handle, in order to ensure radio frequency control signal's stability, and then can avoid radio frequency signal's waveform distortion.

Referring to fig. 8 and fig. 11, in this embodiment, the rf ablation power supply 100 further includes a logic control circuit 41 electrically connected between the first control unit 40 and the switch module 332, and the second control unit 50 is further electrically connected to the logic control circuit 41 and outputs the second switch signal SW _ PC _ M1 to control the output state of the logic control circuit 41, so as to control the transmission state of the two complementary PWM signals, thereby implementing the on-off control of the rf output of the rf ablation power supply 100.

Specifically, the logic control circuit 41 includes and gates U6 and U7. A first input end B of the and gate U6 is electrically connected to the first output port 21 of the single chip microcomputer U4 to receive the first PWM signal PWM 1, and an output end of the and gate U6 is electrically connected to a control end of the MOS switch Q1 through the MOS switch driving chip U5. A first input end B of the and gate U7 is electrically connected to the second output port 22 of the single chip microcomputer U4 to receive the second PWM signal PWM 2, and an output end of the and gate U7 is electrically connected to a control end of the MOS switch Q2 through the MOS switch driving chip U5.

The logic control circuit 41 may also include a nand gate U8. Both input terminals A, B of the nand gate U8 are electrically connected to the second control unit 50 for receiving the second switch signal SW _ PC _ M1. The output end of the NAND gate U8 is electrically connected with the second input ends A of the AND gates U6 and U7 respectively.

The frequency and waveform control of the rf signal is further described below in conjunction with timing diagrams of various signals associated with the rf signal.

As shown in fig. 12, S1 is a timing diagram of the second switch signal SW _ PC _ M1 output by the second control unit 50. S2 is a timing diagram of the output signal of the nand gate U8, i.e., the input signal received at the second input terminal a of the and gates U6 and U7. S3 is a timing diagram of the output signal of the and gate U6. S4 is a timing diagram of the output signal of the and gate U7. S5 is a waveform diagram of the dc voltage signal at the connection terminal TM1 of the push-pull transformer T1. S6 is a waveform diagram of the dc voltage signal at the connection terminal TM3 of the push-pull transformer T1. S7 is a waveform diagram of the RF signal induced by the secondary winding TM4-TM5 of the push-pull transformer T1.

Referring to fig. 11-12, during the rf ablation, the single-chip U4 outputs the two complementary PWM signals to the first input terminals B of the and gates U6 and U7 through the first output port 21 and the second output port 22, respectively. That is, the single chip microcomputer U4 outputs the first PWM signal PWM 1 to the first input terminal B of the and gate U6 through the first output port 21, and outputs the second PWM signal PWM 2 to the first input terminal B of the and gate U7 through the second output port 22. The frequency of the two complementary PWM signals may be, for example, 480kHz, and the voltage value may be, for example, 3.3V, which is not limited in this respect.

When the second switch signal SW _ PC _ M1 is low, both inputs a and B of the nand gate U8 receive low signals, and therefore, the nand gate U8 outputs high signals. At this time, the second input terminals a of the and gates U6 and U7 both receive the high level signal output by the nand gate U8.

The and gate U6 and the and gate U7 and the high level signal and the first PWM signal PWM 1, and the and gate U7 and the second PWM signal PWM 2, so that the output signal of the and gate U6 corresponds to the first PWM signal PWM 1 received by the first input terminal B thereof, and the output signal of the and gate U7 corresponds to the second PWM signal PWM 2 received by the first input terminal B thereof. Thus, the and gates U6 and U7 may output a second dual complementary PWM signal to the MOS switch driver chip U5. The voltage value of the second dual complementary PWM signal may be, for example, 5V, which is not limited herein.

After receiving the second dual-path complementary PWM signal, the MOS switch driving chip U5 may correspondingly output a third dual-path complementary PWM signal to respectively drive the MOS switches Q1 and Q2 to be alternately turned off, so that the first LC oscillating circuit and the second LC oscillating circuit respectively generate half-wave sine waves during the turn-off period of the corresponding MOS switches, and the dc voltage signals at the connection terminals TM1 and TM3 of the two primary windings of the push-pull transformer T1 are formed as half-wave sine waves, so that the secondary windings TM4 to TM5 of the push-pull transformer T1 respectively sense two half-wave sine waves with opposite directions corresponding to the two primary windings TM1 to TM2 and TM2 to TM3, so as to output a complete half-wave sine wave signal. Therefore, the frequency and the waveform of the radio frequency signal can be adjusted by adjusting the frequency of the two-way complementary PWM signal output by the single chip microcomputer U4. The voltage value of the third two-way complementary PWM signal may be, for example, 12V, which is not limited in this respect.

When the second switch signal SW _ PC _ M1 is at a high level, both inputs a and B of the nand gate U8 receive a high signal, and thus the nand gate U8 outputs a low signal. At this time, the second input terminals a of the and gates U6 and U7 both receive the low level signal output by the nand gate U8. It can be understood that, at this time, regardless of whether the single-chip microcomputer U4 continues to output the two-way complementary PWM signal, the and gates U6 and U7 both output low level signals, that is, the logic control circuit 41 has no signal output, and thus cannot drive the MOS switches Q1 and Q2 to be turned off, and therefore, the push-pull transformer T1 also has no signal output.

It can be seen that, in the present application, when the second switch signal SW _ PC _ M1 is at a low level, the logic control circuit 41 and the DC-DC transformer M1 are both in a state of having a signal output, so that the push-pull transformer T1 also has a signal output. On the contrary, when the second switch signal SW _ PC _ M1 is at a high level, the logic control circuit 41 and the DC-DC transformer M1 are both in a state of no signal output, so that the push-pull transformer T1 also has no signal output. That is, in the present application, the second control unit 50 can simultaneously control the output state of the DC-DC transformer M1 and the transmission state of the two-way complementary PWM signal output by the first control unit 40 by outputting the second switching signal SW _ PC _ M1, so that the radio frequency output state of the radio frequency energy generation circuit 30, that is, the radio frequency output state of the radio frequency ablation power supply 100, can be switch-controlled.

It is understood that the logic control circuit 41 and the DC-DC transformer M1 need to be in the state of signal output at the same time to make the push-pull transformer T1 in the state of signal output.

It can be understood that, since the DC-DC transformer M1 is disposed in the rf energy generating circuit 30, i.e., the main power circuit, if the logic control circuit 41 is not disposed, the main power circuit may output large power at the moment of starting to cause discomfort or even danger to living beings, such as human body. By arranging the logic control circuit 41 and simultaneously starting the logic control circuit 41 and the output of the DC-DC transformer M1, the radio frequency output power can be slowly changed from low power to high power, so that the phenomenon that the main power loop outputs high power at the starting moment to bring discomfort or danger to a human body is avoided.

It is understood that, in some embodiments, the rf ablation power supply 100 may further include a lamp panel (not shown) electrically connected to the second control unit 50, and the second control unit 50 may further be configured to control the lamp panel to emit light to indicate an abnormality when the ablation parameters or the ablation power and the like are abnormal. Optionally, the rf ablation power supply 100 may further include a buzzer (not shown) electrically connected to the second control unit 50, and the second control unit 50 may further be configured to control the buzzer to sound to indicate an abnormality when the ablation parameter or the ablation power or the like is abnormal.

It can be understood that, since the portion of the ablation electrode needle 211 contacting the tissue transmits the radio frequency energy to generate high temperature in the tissue, so that the tissue coagulatively necroses to achieve the treatment 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 electrode needle 211, and the cooling channel is used for delivering a gaseous or liquid cooling medium (e.g., cooling water) to cool the high temperature portion so as to control the local temperature during the ablation operation. Wherein the cooling channel may be in communication with one of the connecting lines 220 on the ablation device 200.

Correspondingly, the radiofrequency ablation system 1000 may further include a peristaltic pump (not shown), and a cooling medium is delivered to the cooling channel in the ablation electrode needle 211 through the connecting tube 220 by the peristaltic pump and circulates in the cooling channel 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

1. A radio frequency ablation power supply, comprising:

the first control unit is used for outputting a radio frequency control signal;

the radio frequency energy generating circuit comprises a power supply module, a voltage reduction module and a voltage conversion module which are sequentially and electrically connected, wherein the power supply module is used for providing a voltage-stabilizing direct current signal; the voltage reduction module is used for carrying out voltage reduction processing on the voltage-stabilized direct current signal so as to output a low-voltage direct current signal; the voltage conversion module is also electrically connected with the first control unit and is used for receiving the low-voltage direct current signal and the radio frequency control signal and converting the low-voltage direct current signal into a radio frequency signal according to the radio frequency control signal; and

and the second control unit is electrically connected with the voltage reduction module and used for sending a voltage regulation signal to the voltage reduction module so as to control the voltage reduction module to regulate the voltage value of the currently output low-voltage direct-current signal, thereby realizing the power regulation of the radio-frequency signal.

2. The rf ablation power supply of claim 1, further comprising a logic control circuit electrically connected between the first control unit and the voltage conversion module;

the second control unit is also electrically connected with the logic control circuit and outputs a switch signal to control the output state of the logic control circuit so as to control the transmission state of the radio frequency control signal, thereby carrying out switch control on the radio frequency output of the radio frequency ablation power supply.

3. The rf ablation power supply of claim 2, wherein the voltage conversion module comprises a voltage transformation module and a switch module;

the transformation module comprises a first primary winding, a second primary winding and a secondary winding; the first primary winding comprises a first connecting end and a second connecting end, and the second primary winding comprises the second connecting end and a third connecting end; the second connecting end is electrically connected with the output end of the voltage reduction module and used for receiving the low-voltage direct current signal; the switch module comprises a first MOS switch and a second MOS switch; the control ends of the first MOS switch and the second MOS switch are respectively and electrically connected with the first control unit so as to receive the radio frequency control signal output by the first control unit; the first connection end of the voltage transformation module is connected to a grounding end through the first MOS switch and is connected to the grounding end through a first capacitor; the third connection end of the voltage transformation module is connected to the ground end through the second MOS switch and is connected to the ground end through a second capacitor;

a loop where the first primary winding and the first capacitor are located forms a first LC oscillating circuit, and a loop where the second primary winding and the second capacitor are located forms a second LC oscillating circuit;

the first control unit controls the on-off frequency of the first MOS switch and the second MOS switch respectively through the radio frequency control signal, so that the first LC oscillating circuit generates a sine wave signal during the cut-off period of the first MOS switch, and the second LC oscillating circuit generates a sine wave signal during the cut-off period of the second MOS switch, and therefore the secondary winding of the voltage transformation module correspondingly induces an alternating current radio frequency signal.

4. The rf ablation power supply of claim 3, wherein the rf control signal is a dual-path complementary PWM signal, including a first PWM signal and a second PWM signal, and the first control unit outputs the first PWM signal through a first output port and outputs the second PWM signal through a second output port;

the control end of the first MOS switch is electrically connected with a first output port of the first control unit so as to receive the first path of PWM signals; the control end of the second MOS switch is electrically connected with the second output port of the first control unit so as to receive the second path of PWM signals;

the first control unit respectively controls the first MOS switch and the second MOS switch to be alternately turned off by outputting the two-way complementary PWM signals, so that the first LC oscillating circuit generates a sine wave half-wave signal during the turn-off period of the first MOS switch, and the second LC oscillating circuit generates a sine wave half-wave signal during the turn-off period of the second MOS switch, and therefore the secondary winding of the voltage transformation module respectively induces the sine wave half-wave signal correspondingly.

5. The rf ablation power supply of claim 4, wherein the first primary winding and the second primary winding have different ends with the same name, and the secondary winding of the transformer module induces two sine wave half-waves with opposite directions corresponding to the first primary winding and the second primary winding during the period of the first MOS switch and the second MOS switch being turned off alternately, so as to output a complete sine wave signal, wherein the rf signal is the sine wave signal.

6. The rf ablation power supply of claim 5, wherein the logic control circuit comprises:

a first input end of the first and gate is electrically connected with a first output port of the first control unit to receive the first path of PWM signal, and an output end of the first and gate is electrically connected with a control end of the first MOS switch through an MOS switch driving chip;

a first input end of the second and gate is electrically connected with a second output port of the first control unit so as to receive the second path of PWM signals, and an output end of the second and gate is electrically connected with a control end of the second MOS switch through the MOS switch driving chip; and

the two input ends of the NAND gate are electrically connected with the second control unit to receive the switching signal, and the output end of the NAND gate is electrically connected with the second input ends of the first AND gate and the second AND gate respectively;

when the switch signal is at a low level, the logic control circuit is in a state of signal output.

7. The rf ablation power supply of claim 4, wherein the first control unit is a single-chip microcomputer.

8. The rf ablation power supply of claim 3, wherein the voltage transformation module is a push-pull transformer.

9. The rf ablation power supply of claim 1, further comprising an ablation parameter detection module electrically connected to the second control unit, wherein the ablation parameter detection module is configured to detect an electrical parameter related to a site to be ablated in real time during rf ablation and feed the detected electrical parameter back to the second control unit;

the second control unit is used for generating the voltage adjusting signal according to the electric parameter fed back by the ablation parameter detection module.

10. The rf ablation power supply of claim 1, further comprising a control component electrically connected to the second control unit, the control component configured to receive an input operation from a user to generate a corresponding input signal and transmit the input signal to the second control unit;

the second control unit is used for generating the voltage regulating signal according to the input signal sent by the control component.

11. The rf ablation power supply of claim 9 or 10, wherein the voltage step-down module is a DC-DC transformer;

the second control unit is a microprocessor, and the voltage regulating signal output by the second control unit is a digital signal;

the radio frequency ablation power supply further comprises a DAC module electrically connected between the second control unit and the voltage reduction module, and the DAC module is used for converting the voltage regulation signal output by the second control unit into an analog signal and transmitting the analog signal to the voltage reduction module so as to regulate the voltage value of the low-voltage direct-current signal output by the voltage reduction module.

12. The rf ablation power supply of claim 1 or 2, wherein the second control unit is further configured to output a switching signal to control an output state of the voltage reduction module, so as to switch the rf output of the rf ablation power supply; when the switching signal is at a low level, the DC-DC transformer is in a state of signal output.

13. The rf ablation power supply of claim 1 or 10, further comprising a display unit electrically connected to the second control unit, the second control unit further configured to control the display unit to display an electrical parameter associated with rf ablation.

14. The rf ablation power supply of claim 1, wherein the power supply module comprises:

the power input port is electrically connected with an external power supply to receive a high-voltage alternating current signal input by the external power supply;

a power output port; and

and the rectification module is electrically connected between the power input port and the power output port, and is used for rectifying and filtering the high-voltage alternating current signal and outputting the voltage-stabilizing direct current signal through the power output port.

15. The rf ablation power supply of claim 1, further comprising a filtering module electrically connected between the voltage-reducing module and the voltage converting module, wherein the filtering module is configured to filter the low-voltage dc signal output by the voltage-reducing module.

16. A radio frequency ablation system, comprising an ablation device and a radio frequency ablation power supply according to any one of claims 1 to 15, wherein the ablation device is electrically connected with an output end of the radio frequency ablation power supply, and the ablation device is configured to receive a radio frequency signal output by the radio frequency ablation power supply and perform radio frequency ablation on a to-be-ablated part by using radio frequency energy of the radio frequency signal.

17. The rf ablation system of claim 16, wherein the ablation device includes an ablation needle assembly electrically connected to the output of the rf ablation power source, the ablation needle assembly including an ablation electrode needle and an insulating sleeve movably sleeved over the ablation electrode needle.