CN113893030A - Miniaturized nanosecond pulse generation system for tumor ablation - Google Patents
Miniaturized nanosecond pulse generation system for tumor ablation Download PDFInfo
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- CN113893030A CN113893030A CN202111495485.2A CN202111495485A CN113893030A CN 113893030 A CN113893030 A CN 113893030A CN 202111495485 A CN202111495485 A CN 202111495485A CN 113893030 A CN113893030 A CN 113893030A
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- 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
- A61B2018/00577—Ablation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- 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
- A61B2018/128—Generators therefor generating two or more frequencies
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Abstract
The application discloses a miniaturized nanosecond pulse generation system for tumor ablation, which comprises a main control unit, a driving circuit, a high-voltage switch, a high-voltage power supply, a high-voltage pulse energy storage, an isolation transformer and an electrode array, wherein the high-voltage power supply is connected with the high-voltage pulse energy storage; the high-voltage power supply, the high-voltage pulse energy storage and the primary side of the isolation transformer form a charging loop; the high-voltage switch, the high-voltage pulse energy storage and the secondary side of the isolation transformer form a discharge loop, and the secondary side of the isolation transformer is connected with the electrode array and outputs nanosecond pulses; the main control unit triggers the high-voltage switch to be conducted through controlling the driving circuit; the high-voltage pulse energy storage adopts an LC network to replace a transmission line for transmitting electromagnetic energy for impedance matching, and the miniaturization of a nanosecond pulse generation system is realized.
Description
Technical Field
The application relates to the field of medical equipment, in particular to a miniaturized nanosecond pulse generation system for tumor ablation.
Background
With the continuous development of the bioelectromagnetic technology, the technology of treating tumors by using high-voltage electric pulses is gradually accepted and accepted. High voltage electrical pulse therapy techniques include microsecond pulses and nanosecond pulses. The microsecond pulse electric field kills tumor cells based on the cell membrane electroporation principle, while the nanosecond pulse electric field is introduced into cell nucleus through transmembrane by relying on higher density of external electric field energy, so that the piezoelectric effect is caused in the cell, and the cell nucleus, the nuclear membrane, mitochondria and other organelle membranes generate various tumor apoptosis effects in sequence. In particular, nanosecond pulsed tumor ablation systems are capable of producing extremely high power, nanosecond pulse widths, and high electric field strengths of 10 KV/cm. The nanosecond pulse technology is derived from the military technology, and the implementation method of a high-voltage transmission line of the nanosecond pulse technology requires a long insulation distance and a large space, but in medical instruments, the space of an operating room is limited, particularly the space of the operating room in an outpatient day is smaller, so that the requirement on the size of the operating instrument is tighter, and therefore, the commonly used nanosecond pulse technology cannot be directly applied to tumor ablation treatment in the medical field.
Disclosure of Invention
The purpose of this application is providing a miniaturized nanosecond impulse generation system for tumour is ablated, has realized the miniaturization that nanosecond impulse technology realized, on the basis of guaranteeing safe insulation, has dwindled the size greatly.
The application discloses a miniaturized nanosecond pulse generation system for tumor ablation, which comprises a main control unit, a driving circuit, a high-voltage switch, a high-voltage power supply, a high-voltage pulse energy storage, an isolation transformer and an electrode array, wherein the high-voltage power supply is connected with the high-voltage pulse energy storage; the high-voltage power supply, the high-voltage pulse energy storage and the primary side of the isolation transformer form a charging loop; the high-voltage switch, the high-voltage pulse energy storage and the secondary side of the isolation transformer form a discharge loop, and the secondary side of the isolation transformer is connected with the electrode array and outputs nanosecond pulses; the main control unit triggers the high-voltage switch to be conducted through controlling the driving circuit; the high-voltage pulse energy storage adopts an LC network to replace a transmission line for transmitting electromagnetic energy for impedance matching, and the miniaturization of a nanosecond pulse generation system is realized.
Furthermore, the high-voltage pulse energy storage comprises m selection switches for controlling the output level of the pulse, and the main control unit controls the on-off of the selection switches to switch the pulse widths of different levels according to different ablation requirements.
Furthermore, the high-voltage pulse energy storage comprises m groups of LC networks connected in parallel, and each group of LC networks corresponds to one pulse output level; the selection switch is arranged between the LC network and the isolation transformer.
Furthermore, the LC network includes n inductors connected in series with each other and n capacitors connected in parallel with each other, wherein a first end of a first inductor L is connected to the output end of the high voltage power supply as an input end, a second end of each inductor L is connected to a first end of a capacitor C, and second ends of the n capacitors C are connected to the selector switch and the isolation transformer in sequence.
Further, the inductance value of the inductor L is a unit length inductance value of the transmission line for transmitting electromagnetic energy, and the capacitance value of the capacitor C is a unit length capacitance value of the transmission line for transmitting electromagnetic energy.
Further, the number of stages of the LC network is determined according to the impedance of the electrode array and the turn ratio of the isolation transformer.
Further, the electrode array comprises a plurality of output electrodes connected in parallel, and each output electrode is controlled by a relay switch.
Furthermore, the input end of the electrode array is provided with a current sensor, and the current sensor is connected with the main control unit.
Furthermore, the current sensor is connected with the operational amplifier after being attenuated by the attenuation network, the signal of the operational amplifier is amplified and then transmitted to the main controller unit, and the output impedance of the current sensor is consistent with the characteristic impedance of the attenuation network.
Further, the output pulse width of the high-voltage pulse energy storage comprises 300nS \500nS \700nS \900 nS.
Has the advantages that: the impedance matching is carried out by adopting the LC network to replace a transmission line for transmitting electromagnetic energy, so that the defects that the traditional nanosecond pulse generator cannot be suitable for medical occasions due to long distance and large volume of the required transmission line are overcome, and the miniaturization of a nanosecond pulse generating system is realized; furthermore, multistage nanosecond pulse output is arranged, and the on-off of the selection switch is controlled according to different ablation requirements to switch different levels of pulse widths; different electrodes can be selected to work by controlling a relay switch, so that ablation operations of different parts are realized.
The respective technical features disclosed in the above summary, the respective technical features disclosed in the following embodiments and examples, and the respective technical features disclosed in the drawings can be freely combined with each other to constitute various new technical solutions (which should be regarded as having been described in the present specification) unless such a combination of the technical features is technically impossible. For example, in one example, the feature a + B + C is disclosed, in another example, the feature a + B + D + E is disclosed, and the features C and D are equivalent technical means for the same purpose, and technically only one feature is used, but not simultaneously employed, and the feature E can be technically combined with the feature C, then the solution of a + B + C + D should not be considered as being described because the technology is not feasible, and the solution of a + B + C + E should be considered as being described.
Drawings
FIG. 1 is a schematic diagram of a nanosecond pulse generation system according to an embodiment of the application;
FIG. 2 is a current processing circuit of the current sensor 180;
FIG. 3 is a schematic view of the electrode array 190 of FIG. 1;
fig. 4 is a schematic diagram of an LC network.
Detailed Description
In the following description, numerous technical details are set forth in order to provide a better understanding of the present application. However, it will be understood by those skilled in the art that the technical solutions claimed in the present application may be implemented without these technical details and with various changes and modifications based on the following embodiments.
To make the objects, technical solutions and advantages of the present application more clear, embodiments of the present application will be described in further detail below with reference to the accompanying drawings.
As shown in fig. 1-3, a miniaturized nanosecond pulsing system for tumor ablation comprises a main control unit 110, a driving circuit 170, a high voltage switch 162, a high voltage power supply 120, a high voltage pulse energy storage 160, an isolation transformer 164, and an electrode array 190; the high voltage power supply 120, the high voltage pulse energy storage 160 and the primary side of the isolation transformer 164 form a charging loop; the high-voltage switch 162, the high-voltage pulse energy storage 160 and the secondary side of the isolation transformer 164 form a discharge circuit, and the secondary side of the isolation transformer 164 is connected with the electrode array 190 to output nanosecond pulses. The main control unit 110 triggers the high voltage switch 162 to be turned on by controlling the driving circuit 170. A relay switch 140 is arranged between the output end of the high-voltage power supply and the high-voltage switch 162 and between the output end of the high-voltage power supply and the high-voltage pulse energy storage 160, and the on-off of a coil of the relay switch 140 is controlled through the main control unit 110, so that the conduction of a charge-discharge loop is controlled. An adjustable resistor 130 is arranged between the high-voltage power supply 130 and the relay switch 140, and the adjustable resistor 340 is a high-voltage-resistant power resistor and plays a role in limiting current.
According to the electromagnetic wave transmission theory, the maximum output energy can be achieved only by matching the characteristic impedance of the transmission medium with the impedance of the load (the electrodes of the electrode array 190 are connected with the tumor tissue or the human tissue in the human body, and the impedance range of the liver tumor is about 50-200 Ω) in the transmission process of the electromagnetic wave, the loss is minimum, and ideally, a homogeneous lossless transmission line is adopted to transmit the electromagnetic energy. Characteristic impedance of transmission line per unit length of Z0，Z0=
Pulse width t =
=l*
(ii) a Wherein L is0Is the inductance per unit length of the coaxial cable (less than 2.75X 10)-7) The unit H/m; c0Is the capacitance value per unit length of the cable (less than 1.1X 10)-10) I.e. permittivity, in units of F/m. It can be found by calculation that to realize a high voltage pulse of 200nS class, the required transmission line length is about 60 meters (l = tXv =200X 10)-9X3.0X108) The diameter of the transmission cable after being spirally wound is more than 1m, and the transmission cable is large in size, so that the transmission cable can hardly be applied in a medical environment.
In the present application, the high-voltage pulse energy storage 160 performs impedance matching by using an LC network instead of a transmission line for transmitting electromagnetic energy, and can design the characteristic impedance of the LC network according to the change of the load, thereby achieving the best impedance matching and realizing the miniaturization of the nanosecond pulse generation system. Specifically, as shown in fig. 4, the LC network packet in the present applicationComprising n inductors connected in series and n capacitors connected in parallel, L1=L2= L3=L4=L5=……=Ln=L0，C1=C2=C3=C4=C5=……=Cn=C0. The first end of the first inductor L is connected to the output end of the high voltage power supply 120 as an input end, the second end of each inductor L is connected to the first end of a capacitor C, and the second ends of the n capacitors C are sequentially connected to the selector switch and the isolation transformer 164. The inductance value of the inductor L is a unit length inductance value of the transmission line for transmitting electromagnetic energy, and the capacitance value of the capacitor C is a unit length capacitance value of the transmission line for transmitting electromagnetic energy. Characteristic impedance of LC network: z =
Pulse width of LC network: t =2n
Wherein L = L0，C=
And n is the number of LC network stages. Theoretically, the more the LC series is, the closer the LC series is to the ideal transmission line characteristic, the more the LC series is, the more the ideal transmission line characteristic is, the more the ideal LC series is, the more the ideal transmission line characteristic is, the more the ideal LC series is, the more the ideal transmission line is, the more the LC series is, the more the ideal transmission line is, the more the ideal transmission line is, the more the transmission line is, the more the transmission line is, the more. Specifically, the number of stages of the LC network is determined according to the impedance of the electrode array 190 and the turn ratio of the isolation transformer 164 so that the characteristic impedance of the LC network coincides with the impedance of the electrode array 190. For example, when the turns ratio of the isolation transformer 164 is 1:1, the characteristic impedance of the LC network should be equal to the impedance of the electrode array 190; when the turns ratio of the isolation transformer 164 is 1:2, the characteristic impedance of the LC network should be equal to 4 times the impedance of the electrode array 190. The number of stages n is then determined based on the characteristic impedance of the LC network.
In addition, the pulse generator generally outputs a pulse signal with a single pulse width, but for different ablation sites or ablation ranges or for achieving better ablation effect, the pulse signals with different pulse widths need to be switched in time or alternately. In the present application, the high-voltage pulse energy storage 160 includes m groups of LC networks connected in parallel and m selection switches for controlling pulse output levels, the selection switches are disposed between the LC networks and the isolation transformer 164, each group of LC networks corresponds to one pulse output level, and the main control unit 110 controls the on/off of the selection switches to switch the pulse widths of different levels according to different ablation requirements. In the present application, the output pulse width of the high voltage pulse energy storage 160 includes 300nS \500nS \700nS \900 nS.
Meanwhile, the electrode array 190 includes a plurality of output electrodes connected in parallel, each output electrode is controlled by a relay switch, and the main control unit 110 can select different electrodes to work by controlling the relay switches, so as to realize ablation operations at different positions. The impedance of the electrode array 190 is also different at this time.
The input end of the electrode array 190 is provided with a current sensor 180, the current sensor 180 is connected with the main control unit 110, and the current sensor 180 is used for detecting a pulse current signal output to the electrode array 190. The main control unit 110 collects the current signal of the current sensor 180, and if the current value exceeds the maximum limit value or is less than the minimum value, the high voltage power supply 120 and the driving circuit 170 are closed immediately, and the state warning information is displayed in the display system: over-current or under-current.
When nanosecond pulses are output, selection and combination of output electrodes are achieved through a relay switch in the electrode array 190 and the current sensor 180, specifically, a test voltage U is applied to the electrode array 190, a current I collected by the current sensor 180 is read, the resistance R = U/I of the current electrode is obtained, and the resistance of each electrode can be obtained in the same way. The current sensor 180 is connected with the operational amplifier after being attenuated by the attenuation network 181, the signal is transmitted to the main controller unit after being amplified by the operational amplifier, and the output impedance of the current sensor 180 is consistent with the characteristic impedance of the attenuation network 181. Specifically, the current sensor 180 converts the pulse current signal into a voltage signal according to a conversion ratio of 0.1V/a, and outputs an impedance of 50 Ω (note: the characteristic impedance of a transmission line commonly used for high-frequency electromagnetic signal transmission is 50 Ω, the characteristic impedance of the current sensor is 50 Ω, and the characteristic impedance of a circuit is also matched with 50 Ω in order to obtain a large output.) when the maximum pulse current is 180A, the output voltage is 18V, because of the limitation of the operational voltage of an operational amplifier (generally 5V), the voltage output by the current sensor 180 needs to be increased by an attenuation network 181, and considering the output impedance matching of the current sensor 180 (the characteristic impedance of a transmission medium is matched with the impedance of a load so as to achieve the maximum output energy and minimize the loss), a T-type attenuation network 181 consisting of R1, R2 and R5, an attenuation factor of 10, and a characteristic impedance of 50 are designed in the present application, and then the current signal processing is completed by sampling a high-speed differential operational amplifier U1 with wide bandwidth, low distortion, low noise and high common mode rejection ratio.
In this embodiment, the isolation transformer 164 is an oil-immersed step-up isolation transformer 164, the isolation voltage level is greater than or equal to 30KV, the turn ratio of the primary side coil and the secondary side coil ranges from 1:1 to 1:5, the isolation transformer 164 magnetic core adopts a high magnetic saturation magnetic core, and the isolation transformer 164 winding adopts a high-voltage insulated wire with a withstand voltage level of more than 30 KV. The primary and secondary windings adopt a process of cross overlapping and mutual winding of a plurality of windings, magnetic leakage is reduced, the coupling rate of magnetic inductance is increased, and energy transfer efficiency is improved. The high-voltage switch 162 is made of a hydrogen thyratron, a circulating insulating oil pipeline is adopted for heat dissipation or an air cooling design is adopted, the circulating insulating oil pipeline is made of a non-conductive material, an air cooling design fan is made of a non-conductive insulating material, and a fan conductive circuit is made of an electromagnetic shielding material.
It is noted that, in the application, relational terms such as first and second, and the like are used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Also, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, the use of the verb "comprise a" to define an element does not exclude the presence of another, same element in a process, method, article, or apparatus that comprises the element.
Further, it should be understood that various changes or modifications can be made to the present application by those skilled in the art after reading the contents of the present application, and these equivalents also fall within the scope of the claims of the present application.
Claims (10)
1. A miniaturized nanosecond pulse generation system for tumor ablation is characterized by comprising a main control unit, a driving circuit, a high-voltage switch, a high-voltage power supply, a high-voltage pulse energy storage, an isolation transformer and an electrode array;
the high-voltage power supply, the high-voltage pulse energy storage and the primary side of the isolation transformer form a charging loop; the high-voltage switch, the high-voltage pulse energy storage and the secondary side of the isolation transformer form a discharge loop, and the secondary side of the isolation transformer is connected with the electrode array and outputs nanosecond pulses; the main control unit triggers the high-voltage switch to be conducted through controlling the driving circuit;
the high-voltage pulse energy storage adopts an LC network to replace a transmission line for transmitting electromagnetic energy for impedance matching, and the miniaturization of a nanosecond pulse generation system is realized.
2. The nanosecond pulser system according to claim 1, wherein the high-voltage pulse energy storage comprises m selection switches for controlling the output level of the pulse, and the main control unit controls the selection switches to be switched on and off to switch the pulse widths of different levels according to different ablation requirements.
3. A miniaturized nanosecond pulse generation system for tumor ablation according to claim 2, wherein said high voltage pulsed energy storage comprises m sets of LC networks in parallel, each set corresponding to a pulse output level; the selection switch is arranged between the LC network and the isolation transformer.
4. The miniaturized nanosecond pulser system for tumor ablation according to claim 3, wherein the LC network comprises n inductors in series and n capacitors in parallel, wherein a first end of a first inductor L is connected as an input terminal to the high voltage power output terminal, a second end of each inductor L is connected to a first end of a capacitor C, and second ends of the n capacitors C are connected to the selector switch and the isolation transformer in sequence.
5. The miniaturized nanosecond pulser system for tumor ablation according to claim 4, wherein the inductance value of the inductor L is the inductance per unit length of the transmission line for transmitting electromagnetic energy, and the capacitance value of the capacitor C is the capacitance per unit length of the transmission line for transmitting electromagnetic energy.
6. A miniaturized nanosecond pulsing system for tumor ablation according to claim 3, wherein the number of stages of said LC network is determined by the impedance of said electrode array and the turns ratio of the isolation transformer.
7. The miniaturized nanosecond pulsing system for tumor ablation according to claim 1, wherein said electrode array comprises multiple parallel output electrodes, each output electrode being controlled by a relay switch.
8. The miniaturized nanosecond pulser system for tumor ablation according to claim 7, wherein the input end of the electrode array is provided with a current sensor, and the current sensor is connected with the main control unit.
9. The system of claim 8, wherein the current sensor is attenuated by the attenuator network and then connected to the operational amplifier, and the signal of the operational amplifier is amplified and transmitted to the main controller unit, and the output impedance of the current sensor is consistent with the characteristic impedance of the attenuator network.
10. The miniaturized nanosecond pulse generation system for tumor ablation according to claim 2, wherein the output pulse width of the high voltage pulse energy storage comprises 300nS \500nS \700nS \900 nS.
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