CN114886546B - Synchronous bipolar short pulse tumor ablation method and system - Google Patents
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00613—Irreversible electroporation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/126—Generators therefor characterised by the output polarity bipolar
Abstract
The application discloses a synchronous bipolar short pulse tumor ablation method and a system, wherein the method comprises the following steps: diagnosing the position, shape and size of a tumor focus, setting and adjusting a high-voltage pulse waveform, and determining electrode selection; disposing a pair or set of high voltage electrodes with partial insulation into or around a tumor lesion; positive and negative high voltage pulses are synchronously applied to the electrodes, respectively. Pulse current is input into tumor focus from positive high voltage electrode, and output from negative high voltage electrode, and high voltage pulse electric field is generated between positive and negative electrodes to unbalance cell inside and outside. The application can cause irreversible electroporation to tumor cells and death by the electric field formed by synchronous bipolar high-voltage pulse, and is a non-heating physical tumor ablation method.
Description
Technical Field
The application relates to the field of biological tissue ablation, in particular to a synchronous bipolar short pulse tumor ablation method and system.
Background
Patients with cancer are difficult to treat, early symptoms are hidden, the patients are often metastasized when in consultation, and radical surgery cannot be realized. In addition, the pancreatic cancer wraps the important vascular structures such as superior mesenteric artery, vein and celiac artery, and the surgical operation is very difficult. In fact, the operation is very traumatic and has a lot of complications, and the operation is easy to relapse after the operation. Traditional physical tumor ablation is based on microwave, radio frequency, ultrasound or laser heating or cryoablation therapy, and due to the lack of selectivity to tissue structures, ablation lesions can lead to complications that damage surrounding vital tissue structures.
Irreversible electroporation, also known as nanoknives, has been clinically used as a new technique for tumor treatment. The main principle of the nanometer knife is that a unipolar or alternating high-voltage pulse is applied between a grounding electrode and a high-voltage electrode to break down cell membranes to form irreversible pore channels, and a lipid bilayer of the cell membranes is damaged, so that the internal and external environments of the cells are unbalanced. Compared with radio frequency, microwave and cryoablation methods, the nano-knife does not cause serious damage to structures such as blood vessels and the like, and has unique advantages.
The main published patent in the domestic nanometer knife field is described as follows.
The patent of 'a method capable of efficiently promoting nano particles to enter cells based on nanosecond pulse electric field' (CN 105903014A) discloses an ablation technology with a pulse width of 10-500 ns; the patent of 'steep pulse tumor treatment device and method' (CN 101019779A) discloses an ablation technology with voltage of 0-1000V, pulse width of 100ns-100 mu s, level 6 adjustable and frequency of 1-10 kHz; the 'unrecoverable electroporation system' (CN 105055015A) patent discloses an ablation technique with a voltage of 0-3500V, a pulse width of 30-100 mu s, and a frequency of 1Hz-100 kHz; the patent of 'a device for inducing tumor cell apoptosis by high-voltage nanosecond pulse' (CN 101085391A) discloses an ablation technology with voltage of 0-9.9kV, pulse width of 200ns-1 mu s and adjustable seven stages and frequency of 2-100 Hz; the 'irreversible electroporation tumor treating device' (CN 101972168B) patent discloses an ablation technology with 100-3000V voltage, 10-500 mu s pulse width and 1-10Hz frequency, and the pulse characteristics are square wave pulses; the patent of high-voltage pulse discharge biological tissue ablation method (CN 104665924A) discloses an ablation technology with voltage of 175-330V and frequency of 100 KHz; the patent of 'high-voltage pulse discharge biological tissue ablation device' (CN 10466592A) discloses an ablation technology adopting silver plating electrodes with voltage of 175-330V and frequency of 100 KHz; the patent of an isolated square wave irreversible electroporation instrument (CN 106388929A) discloses an ablation technology of 0-3kV for high voltage and 0-3kV for low voltage, and the pulse characteristics are square wave pulses; the patent of a synergistic pulse irreversible electroporation device (CN 107681916A) discloses an ablation technology with high voltage of 0-3kV, low voltage of 0-3kV, pulse width of 0.2-100 mu s and period of 0.1-10 s; the 'irreversible electroporation equipment' (CN 106388932B) patent discloses an ablation technology with the electric field intensity of 1.5kV/cm-3kV/cm and the pulse width of 5-50 mu s, and the pulse characteristics are square wave pulses; the patent of 'targeted ablation cell device, method, medium and electronic equipment' (CN 109171947A) discloses an ablation technology with electric field strength of 1kV/cm-1000kV/cm, pulse width of 1ns-1000ns and frequency of 500kHz-20 GHz; the patent of a nanometer knife tumor ablation control device and a control method thereof (CN 108095820A) discloses an ablation technology with the voltage of 3kV, the current of 50A and the pulse width of 20-1000 mu s; the patent of a high-frequency irreversible electroporation instrument (CN 206992984U) discloses an ablation technology with voltage of +/-4 kV, current of 50A and pulse width of 100-1000 mu s; the patent of a high-frequency irreversible electroporation tumor treatment system (CN 113440247A) discloses an ablation technology with the voltage of 500V-10kV, the pulse width of 10ns-100 mu s and the frequency of <500 kHz; the patent of an all-solid-state nanosecond pulse generator (CN 111082784A) based on double-path Marx tangent discloses an ablation technology with voltage of 5kV and pulse width of 10-30ns, and the pulse characteristics are exponential wave pulses; the patent of 'ablation therapeutic instrument in prostate tissue' (CN 1198920A) discloses an ablation technology with voltage of 0-150V and frequency of 250k-300kHz, which is verified on prostate ablation; the 'pulse generator for irreversible electroporation' (CN 111227926A) patent discloses an ablation technique with voltage IRE 200V+RF 10-200V, pulse width 20 μs, frequency 350KHz-500KHz (RF); the patent of 'a cervical ablation device' (CN 213758519U) discloses an ablation technology which adopts a flexible spiral catheter and 24 electrodes, has the voltage of 0-10kV and the pulse width of 300ns, and is verified on cervical ablation; the generation and interleaving of irreversible electroporation and radio frequency ablation (ire_rfa) waveforms (CN 111265295A) patent discloses an ablation technique of voltage ± 2kV, which is validated on cardiac ablation; the patent of 'multimode high-voltage pulse electric field generation system and application thereof in high-voltage pulse electric field treatment system' (CN 107425827A) discloses an ablation technology with voltage nanosecond 0-6 kV+microsecond 0-3kV (single and double poles), pulse width 10-1000ns+1-500 mu s and frequency nanosecond 0-100 kHz+microsecond 1 kHz; the patent of portable charging micro-second pulse power supply (CN 106899060B) discloses an ablation technology with voltage of 0-25kV, power of <100W, pulse duty ratio of 0-20% and frequency of 0-10 kHz; the patent of a treatment system (CN 111529050A) for ablating cancerous tissues/irregular cells by a nanosecond-microsecond pulse sequence discloses an ablation technology with a voltage of 5kV/cm-50kV/cm, a microsecond of 0.5kV/cm-5kV/cm and a pulse width of 20-1000ns+1 mu s-100 mu s; the patent of 'full-time period high-voltage steep pulse cancer treatment device and method' (CN 103446667A) discloses an ablation technology with voltage of 0-10kV, pulse width of 200-1000ns and frequency of 1-1000 Hz; the patent of 'surgical therapeutic instrument for treating human liver tumor by high-voltage nanosecond pulse' (CN 101912301A) discloses an ablation technology which adopts four-needle electrodes, has a pulse width of 100ns and a frequency of 10Hz, and the technology is verified on liver ablation.
In the clinical application of nano knife tumor ablation, symptoms such as pain and discomfort caused by muscle contraction of a patient, respiratory arrest and the like occur frequently after the patient injects a muscle relaxant. In addition, strong retroperitoneal or diaphragmatic and abdominal muscle stimulatory contractions may cause displacement of the target organ, causing trauma to the target organ. The prior nanometer knife technology can not be adopted for patients with serious arrhythmia, epileptic history, cardiac pacemaker and excessive myocardial infarction, heart lung and kidney insufficiency or general anesthesia without tolerance of trachea cannula.
The main reason for these problems is that the current nanoknives are operated with low voltage (1-3 kV), low field strength (1-3 kV/cm), medium current (10-50A), long pulse width (70 us-90 us) designs based on traditional cell perforation assumptions, corresponding to high single pulse energy (5-20J/pulse), and failure to accurately apply electrical pulses in absolute refractory periods in coordination with electrocardio. The prolonged high energy discharge can cause bioelectric disturbance, induced arrhythmia, muscle contraction and epileptic seizure of the human body, and side effects such as bubbles may be generated near the treatment area.
Disclosure of Invention
Aiming at the prior art, the application provides a synchronous bipolar short pulse tumor ablation method and a system, which can solve the problems of discomfort and side effects of human bioelectricity disorder, arrhythmia, muscle contraction and the like caused by irreversible electroporation oxidation apoptosis of tumor cells under a high-voltage pulse electric field.
In order to achieve the above purpose, the present application is realized by the following technical scheme:
in a first aspect, a synchronous bipolar short pulse tumor ablation method is provided, comprising the steps of:
diagnosing the position, shape and size of a tumor focus, setting and adjusting a high-voltage pulse waveform, and determining electrode selection;
placing a pair or a group of positive and negative high voltage electrodes in or around the tumor lesion;
positive and negative high voltage pulses are synchronously and respectively applied to the positive and negative high voltage electrodes.
The position, shape and size of the tumor focus are diagnosed by conventional or three-dimensional CT or PET/CT, and the synchronous double-pulse high-voltage waveform and double-electrode type selection are analyzed and optimized according to the focus image after CT diagnosis.
Positive and negative high voltage pulses refer to the simultaneous application of a positive high voltage pulse to the positive high voltage electrode and a negative high voltage pulse to the negative high voltage electrode. Pulse current is input into the tumor focus from the positive high-voltage electrode, and flows back to the high-voltage power supply from the negative high-voltage electrode, and an electric field is generated between the positive electrode and the negative electrode.
In an alternative embodiment of the first aspect, the pulse shape of the positive and negative high voltage pulses is one of a unipolar square wave, a triangular wave, a fundamental wave superimposed high frequency oscillating wave, a pulsed alternating wave, the positive and negative pulses being of opposite polarity but of symmetrical waveform and amplitude, the synchronization time difference not exceeding 10 nanoseconds. The duration of the pulse is between tens of nanoseconds and microseconds, the peak-to-peak value of the voltage is between 10kV and 40kV, the repetition frequency of the voltage is not higher than 50Hz (or PPS (pulse per second)), the single pulse energy is not higher than 1J/pulse, the peak current is between 100A and 400A, and the average electric field intensity between electrodes exceeds 5kV/cm.
In an alternative embodiment of the first aspect, the electrocardiographic image or signal is acquired in real time before and during the start of ablation, and the absolute refractory period trigger time is set accordingly, and the high voltage pulse is triggered by the electrocardiographic signal.
In alternative embodiments of the first aspect, the tumor comprises liver cancer, lung cancer, brain tumor, breast cancer, pancreatic cancer, melanoma, renal cancer, intestinal tract, heart, thyroid, parotitis, blood cancer, vascular and vascular intima, tumor bone metastasis, sciatic nerve, and the like.
Further, positive and negative high voltage pulse ablation can be integrated with tumor therapeutic drugs, including local anesthesia, injection of nano tumor therapeutic drugs in focus attachment, and the like.
In a second aspect, a synchronous bipolar short pulse tumor ablation system is provided, comprising:
the power supply module supplies power to the system and synchronously outputs positive and negative high-voltage pulse currents to the discharge module;
the control module displays and controls various parameters of the output pulse;
the sampling module is used for acquiring electrocardiosignals or electrocardiosignals in real time and transmitting the electrocardiosignals or electrocardiosignals to the trigger circuit;
and the discharging module outputs high-voltage pulse current to the tumor focus to realize ablation.
In an alternative embodiment of the second aspect, the discharge module is a pair or set of positive and negative high voltage electrodes with partial insulation, the positive and negative high voltage electrodes being placed in or around the tumor lesion and connected to the power supply module by high voltage transmission lines. One end of the electrode connected with the high-voltage transmission line is wrapped by an insulating material and isolated from human tissues; the other end is used for releasing high-voltage pulse current to the tumor focus.
Further, the positive and negative high voltage electrodes are one of rigid solid metal electrodes, hollow metal electrodes, flexible metal electrodes and semiconductor material electrodes. The electrode is one of a round, square and triangular tip electrode. The positive and negative high voltage electrodes can be identical, can also be different in diameter and length or shape, and can be inserted into the focus in parallel or non-parallel.
In an alternative embodiment of the second aspect, one, two or more auxiliary zero potential electrodes are added in the discharge module near the positive and negative high voltage electrodes, so that part of the current can flow back to the high voltage power supply through the zero potential electrodes, the outflow of the current is reduced, and the surrounding tissues and the heart of the tumor focus are protected.
In an alternative embodiment of the second aspect, the control module comprises a pulse current voltage oscilloscope and a low-voltage control display, so that visual display of various parameters of pulse output can be realized and adjustment is convenient.
In an alternative embodiment of the second aspect, the power supply module comprises: pulse charging, high voltage transformers, AC/DC converters, high voltage switches, pulse energy storage capacitors or energy storage pulse forming lines. The two pulse energy storage capacitors are respectively connected with the positive and negative high-voltage electrodes through transmission lines, and are synchronously charged in saturation in several or more than ten microseconds, the high-voltage switch is not turned on during the period, and after charging, one switch is automatically conducted due to the coupling between the magnetic material-carrying cables, so that the two switches are synchronously output in several nanoseconds, and positive and negative high-voltage pulses are synchronously output in the positive and negative high-voltage coaxial cables. Nanosecond pulse formation can be realized by boosting and waveform shaping of a pulse transformer after generation at a low-voltage end, and can also be formed by directly utilizing a high-voltage switch at a high-voltage end to form line discharge through an energy storage capacitor or an energy storage pulse. The high-voltage switch is one of a semiconductor solid switch, a gas and liquid high-voltage spark switch, a vacuum discharge switch and a magnetic switch, and two or more high-voltage switches are used in series-parallel. The high-voltage capacitor can be a simple noninductive capacitor or a linear or nonlinear pulse forming line, and the positive and negative capacitors have equal general capacitance and charging voltage, electric quantity and energy.
In an alternative embodiment of the second aspect, the sampling module is comprised of an electrocardiographic monitoring device and a power supply external trigger circuit. An electrocardiographic monitoring device, such as an electrocardiograph monitor, acquires electrocardiographic signals or images of a patient in real time before and during the initiation of ablation. The trigger circuit comprises a trigger circuit in the power supply module and an external trigger circuit, the external trigger circuit is connected with electrocardiograph monitoring equipment such as an electrocardiograph monitor, and the absolute refractory period trigger time is set according to the acquired electrocardiograph image or electrocardiograph signal.
The technical scheme provided by the application has the beneficial effects that:
the method comprises the steps of firstly carrying out nanosecond pulse discharge treatment on cytoplasm and a cell membrane primary nano hole of a tumor cell by fast steep pulse (rise time <10 ns), high field intensity (average field intensity >5 kV/cm), high current (peak current 100-400A) and low-energy short pulse (< 1J/pulse) synchronous bipolar pulse, simultaneously increasing a cell membrane primary pore channel and generating strong active oxidation free radicals, and then treating the cell at hundreds of nanoseconds or microseconds and low field intensity (< 5 kV/cm) to unbalance inside and outside the cell, so that the tumor cell is oxidized and withered and dead under irreversible electroporation to realize tumor ablation.
Additional aspects and advantages of the application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the application.
Drawings
For a clearer description of the technical solutions of the embodiments of the present application, the drawings that are needed in the description of the embodiments will be briefly introduced below, it being obvious that the drawings in the description below are only some embodiments of the present application, and that other drawings can be obtained according to these drawings without inventive effort for a person skilled in the art, wherein:
FIG. 1 is a schematic flow chart of a synchronous bipolar short pulse tumor ablation method according to an embodiment of the present application;
FIG. 2 is a side view of a tumor lesion treatment in a synchronous bipolar short pulse tumor ablation method according to an embodiment of the present application;
FIG. 3 is a schematic diagram of waveforms of synchronous bipolar short pulse voltages with time in a synchronous bipolar short pulse tumor ablation method according to an embodiment of the present application;
FIG. 4 is a conventional electrocardiogram of a synchronous bipolar short pulse tumor ablation method according to another embodiment of the present application;
FIG. 5 is a partial circuit diagram of a synchronous bipolar short pulse tumor ablation system according to another embodiment of the present application;
fig. 6 is a top view of a discharge module and a tumor lesion in a synchronous bipolar short pulse tumor ablation system according to another embodiment of the present application.
Detailed Description
The following description of the embodiments of the present application will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the application. All other embodiments, which can be made by those skilled in the art based on the embodiments of the application without making any inventive effort, are intended to be within the scope of the application.
In the first embodiment, the position, shape, size and the like of a tumor focus are diagnosed by using conventional or three-dimensional CT or PET/CT, and the synchronous double-pulse high-voltage waveform and the double-electrode type selection are analyzed and optimized according to the focus image after CT diagnosis.
For example, as shown in FIG. 2, if the length, width and height of the lesion are about2.0cmX1.5cmX2.0cm and a volume of about 6.0cm 3 . According to the size of the focus, the distance between the two electrodes is 2.0cm, the effective length of the discharge electrode is 2.0cm, and the diameters of the electrodes are 1.1mm. The direct current resistance between the two electrodes is about 100 omega, and is close to the series impedance of 100 omega of the two output cables, so that the power supply and the focus load can be well matched. According to the focal volume of 6cm 3 Setting the total energy intensity of optimized ablation to be 15J/cm 3 The total energy of ablation is calculated to be about 90J. In order to ensure that the peak electric field intensity at the edge and inside of the focus is higher than 8kV/cm, the positive and negative peak voltages are set to be 15kV. As shown in fig. 5, the pulse capacitors 10 and 11 are both 8nF and the single pulse energy is 0.45J, so that 200 bipolar synchronous electric pulses are required for ablation in total, and the peak average electric field intensity is 15kV/cm.
After confirming the focus position and adjusting the synchronous double pulse high voltage waveform and double electrode type selection, the positive and negative electrodes are inserted into the position shown in figure 2 in sequence by utilizing ultrasonic positioning guidance under local anesthesia. 1 is a positive high-voltage electrode applying positive high-voltage pulse voltage Vp (t), 2 is a negative high-voltage electrode applying negative high-voltage pulse voltage Vn (t), 3 is an insulating material on the surface of the positive electrode and the negative electrode, 4 is a positive high-voltage electrode discharge end, 5 is a negative high-voltage electrode discharge end, and 6 is a tumor focus.
After the safety inspection of the device, a high-voltage pulse power supply is turned on, a positive high-voltage pulse voltage Vp (t) is applied to the positive high-voltage electrode 1, a negative high-voltage pulse voltage Vn (t) is applied to the negative high-voltage electrode 2, and fig. 3 is a waveform diagram showing the change of the pulse voltages of the two electrodes with time. The pulse current is input into the tumor focus 6 from the positive high-voltage electrode discharge end 4, is output from the negative high-voltage electrode discharge end 5, generates an electric field between the positive electrode and the negative electrode, and flows back to the high-voltage pulse power supply through the transmission line. The high voltage power source automatically stops the pulse emission after the set total pulse number is emitted. The power supply of the pulse power supply is turned off, the high-voltage electrode is disconnected with the cable, and the two electrodes are pulled out in sequence.
In the second embodiment, based on the first embodiment, the pulse current is triggered by the electrocardiographic signal. Before the high-voltage pulse power supply is started, an electrocardio trigger signal of a related monitoring device such as an electrocardio monitor is connected with the high-voltage power supply, the electrocardio monitor automatically samples electrocardio images for 1-10 minutes, an electrocardio graph R wave crest value is about 1.4-1.5mV, a refractory period ST section is arranged between a QRS section and a T section, the duration is about 100ms, and the RR wave interval is the reciprocal or period of heartbeat frequency. The pulse peak voltage, single pulse energy, total pulse number and total ablation time are optimized according to the size of the lesion 6 and the acquired electrocardiographic waveform. And analyzing the characteristics of the ST segment according to the acquired electrocardio images, and setting the absolute refractory period triggering time.
After the high-voltage pulse power supply is started, the electrocardiograph monitor collects electrocardiograph signals in real time, and the electrocardiograph signals are transmitted into a trigger circuit of the high-voltage pulse power supply. The high voltage pulse power supply triggers double pulses at about the ST middle position, namely the section 7, and the process from triggering to single pulse ablation is completed after about 10 microseconds. In the ablation process, the pulse current adjusts the triggering of the pulse according to the real-time electrocardiosignal.
The embodiment can monitor the change of the heart rhythm of a patient in real time, and can accurately apply pulse current in an absolute refractory period according to the triggering of the electrocardiosignal adjustment pulse, so that adverse reaction of a human body can be reduced.
Embodiment three, fig. 5 is a partial circuit diagram of a power supply module and a discharge module of the synchronous bipolar short pulse tumor ablation system according to this embodiment. The embodiment comprises a power supply module, a control module, a sampling module and a discharging module.
The control module comprises a low-voltage control display and a pulse current voltage oscilloscope and is used for displaying and controlling various parameters of output pulses. The sampling module comprises an electrocardio monitoring device and an external trigger circuit, wherein the electrocardio monitoring device, such as an electrocardio monitor, acquires electrocardio images or electrocardio signals in real time, and the external trigger circuit transmits the electrocardio images or electrocardio signals to the trigger circuit in the power supply module to trigger high-voltage pulses. The discharging module 8 comprises a positive high-voltage electrode 1 and a negative high-voltage electrode 2, and performs pulse discharging on tumor lesions to realize tumor ablation.
The power supply module comprises positive and negative high-voltage discharging energy storage capacitors 10 and 11, positive and negative high-voltage switches 12 and 13, 14 and 15 are used for charging diodes and inductors for the positive high-voltage capacitor 10, and 16 and 17 are used for charging diodes and inductors for the negative high-voltage capacitor 11; 18 and 19 are respectively positive and negative high voltage switch trigger circuits, 25 and 26 are positive and negative high voltage pulse output coaxial cables, and the lengths of the two cables are completely the same, the characteristic impedance and the like; 20 and 21 are respectively positive and negative high-voltage pulse cable external magnetic shielding materials, and 27 and 24 are respectively high-voltage pulse power supply metal shells and grounding points thereof; arrows in regions 22 and 23 indicate the direction of current flow on the power supply housing inner and outer positive and negative coaxial cable ground electrodes, respectively.
The pulse energy storage capacitors 10 and 11 are synchronously charged in saturation in several or more than ten microseconds, the high-voltage switches 12 and 13 are not turned on during the period, after the charging, one of the switches 12 or 13 is turned on in several or more than ten microseconds, the other switch is automatically turned on due to coupling between the magnetic material-carrying cables, the two switches are synchronously output in several nanoseconds, positive and negative high-voltage pulses are synchronously output in positive and negative high-voltage coaxial cables, the positive high-voltage pulse capacitor 10 is discharged to the positive high-voltage cable 25 through the high-voltage switch 12 and outputs positive high-voltage pulse voltage to the positive high-voltage electrode 1, and current flows back to the negative high-voltage electrode 2, the cable 26, the high-voltage switch 13, the negative high-voltage capacitor 11 and the positive high-voltage capacitor 10 after flowing through the treatment tissue 8 to form a current closed loop. The two zero potential sections of the positive and negative high-voltage pulse cables 25 and 26 are connected with each other to realize current matching coupling between the two groups of pulse transmission lines. The rise time of the output voltage waveform is mainly dependent on the on time of the switches 12 and 13, the peak current is taken to be the charging voltage and the characteristic impedance of the coaxial cables 25 and 26, and the duration of the pulse voltage is mainly dependent on the product of the storage capacitance and the characteristic impedance of the cables.
Preferably, the characteristic impedance between electrodes 1 and 2 is equal to the series impedance of cables 25 and 26, and the voltage waveforms between the positive and negative electrodes are as shown in fig. 3. If the voltage and the current are not matched, voltage and current oscillation occurs, and the processing efficiency is reduced.
Preferably, the high voltage capacitors 10 and 11 are one of simple non-inductive capacitors and linear or nonlinear pulse forming lines, the positive and negative capacitors being generally equal in capacitance and their charge voltages, amounts of electricity and energies.
Preferably, the high voltage switches 12 and 13 are one or more of semiconductor solid state switches, gas, liquid high voltage spark switches, vacuum discharge switches, magnetic switches used in series-parallel.
Preferably, the positive and negative high voltage electrodes 1 and 2 are one of rigid solid, hollow metal electrodes, flexible metal or semiconductor material electrodes.
Preferably, the positive and negative high voltage electrodes 1 and 2 are one of circular, square or triangular in shape.
In a fourth embodiment, fig. 6 is a top view of the discharge module and tumor lesion according to the embodiment. Based on the third embodiment, which adds one, two or more zero potential electrodes 28 near the positive and negative high voltage electrodes 1 and 2, the one end of the zero potential electrode 28 contacts the tumor lesion, the evaluation is performed according to the lesion shape size. Part of the current can also flow back to the high-voltage power supply through the zero-potential electrode 28, so that the outflow of the current is reduced, and the tissue and the heart around the focus are protected. The zero potential electrode 28 may be identical to the positive and negative high voltage electrodes 1 and 2, may be different in diameter and length or shape, and may be inserted into a tumor lesion in parallel or non-parallel with the positive and negative high voltage electrodes 1 and 2.
The foregoing description is only illustrative of the present application and is not intended to limit the scope of the application, and all equivalent structures or equivalent processes or direct or indirect application in other related technical fields are included in the scope of the present application.
Claims (4)
1. A synchronous bipolar short pulse tumor ablation system, comprising:
the power supply module comprises a pulse charging module, a high-voltage transformer, an AC/DC converter, a high-voltage switch, a pulse energy storage capacitor or an energy storage pulse forming line, and triggers the high-voltage pulse in an absolute refractory period and synchronously outputs positive and negative high-voltage pulse currents to the discharge module;
the control module comprises a pulse current voltage oscilloscope and a low-voltage control display, and displays and controls various parameters of output pulses;
the sampling module comprises electrocardio monitoring equipment and a power supply external trigger circuit, acquires electrocardio signals or electrocardio images in real time, and transmits the electrocardio signals to the trigger circuit in the power supply module;
the discharging module is connected with the power supply module through a positive and negative high-voltage pulse transmission line and synchronously outputs positive and negative high-voltage pulse current to the tumor focus to realize ablation;
the discharging module comprises positive and negative high-voltage electrodes, wherein the positive high-voltage electrodes apply positive high-voltage pulse voltage through a positive high-voltage pulse transmission line, and the negative high-voltage electrodes apply negative high-voltage pulse voltage through a negative high-voltage pulse transmission line.
2. The system of claim 1, wherein the positive and negative high voltage electrodes are a pair or a set of positive and negative high voltage electrodes with partial insulation, the electrodes connected to one end of the high voltage transmission line are covered with insulating material, and the other end contacts the tumor lesion.
3. The system of claim 2, wherein the positive and negative high voltage electrodes are one of rigid solid metal electrodes, hollow metal electrodes, flexible metal electrodes, and semiconductor material electrodes.
4. The system of claim 2, wherein the discharge module includes one, two or more auxiliary zero potential electrodes disposed adjacent to the positive and negative high voltage electrodes.
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