CN219048797U

CN219048797U - Ablation system for lung passages

Info

Publication number: CN219048797U
Application number: CN202223605037.6U
Authority: CN
Inventors: 衷兴华; 刘红梅; 马剑豪
Original assignee: Hangzhou Vena Anke Medical Technology Co ltd
Current assignee: Hangzhou Vena Anke Medical Technology Co ltd
Priority date: 2022-12-30
Filing date: 2022-12-30
Publication date: 2023-05-23
Anticipated expiration: 2032-12-30

Abstract

An ablation system for a lung passageway is disclosed. An ablation system for a lung passageway comprising: a pulse electric signal generator for generating a pulse electric signal; an ablation device coupled to the pulsed electrical signal generator, at least a portion of the ablation device being extendable toward tissue such that the ablation device is capable of delivering the pulsed electrical signal to the tissue, wherein the pulsed electrical signal comprises at least one high voltage narrow pulse having a magnitude greater than a magnitude of the low voltage wide pulse and at least one low voltage wide pulse having a pulse width less than a pulse width of the low voltage wide pulse. According to the ablation system for the lung channel, which is disclosed by the embodiment of the utility model, in the process of performing ablation by adopting the specific pulse electric signals, the action potential distribution to peripheral tissues can be reduced, the contraction of muscles can be reduced or even avoided, and the uncomfortable feeling of an ablated main body is reduced.

Description

Ablation system for lung passages

Technical Field

The utility model relates to the field of ablation, in particular to an ablation system for a lung channel.

Background

Irreversible electroporation (irreversible electroporation, IRE) is a tissue ablation technique that produces perforations in the cell membrane by extremely short but powerful electric fields, which is capable of inducing apoptosis or necrosis.

When the ablation system is used for tissue ablation in the related technology, the tissue is easy to stimulate to cause muscle contraction, so that a main body to be ablated generates stronger uncomfortable feeling, and the ablation effect is influenced.

Disclosure of Invention

The utility model provides an ablation system for a lung channel, which reduces tissue muscle contraction caused during ablation and reduces uncomfortable feeling of an ablated body.

An embodiment of the present utility model provides an ablation system for a lung passageway, the ablation system for a lung passageway comprising: a pulse electric signal generator for generating a pulse electric signal; an ablation device coupled to the pulsed electrical signal generator, at least a portion of the ablation device being extendable toward tissue such that the ablation device is capable of delivering the pulsed electrical signal to the tissue, wherein the pulsed electrical signal comprises at least one high voltage narrow pulse having a magnitude greater than a magnitude of the low voltage wide pulse and at least one low voltage wide pulse having a pulse width less than a pulse width of the low voltage wide pulse.

According to the foregoing embodiment of the present utility model, the pulsed electrical signal is a unipolar pulsed electrical signal; or the pulse electric signal is a bipolar pulse electric signal, wherein the bipolar pulse electric signal comprises at least one pair of the high-voltage narrow pulse and the low-voltage wide pulse with opposite polarities.

According to any one of the foregoing embodiments of the present utility model, a pulse width of each of the high-voltage narrow pulses is in a range of 0.5ns or more and less than 1000 ns; the pulse width of each of the low-voltage wide pulses is in the range of 1us or more and 100us or less.

According to any of the foregoing embodiments of the present utility model, the amplitude of each of the high-voltage narrow pulses is in a range of 5kV/cm or more and 50kV/cm or less; the amplitude of each of the low-voltage wide pulses is in a range of 0.5kV/cm or more and less than 5 kV/cm.

According to any of the preceding embodiments of the present utility model, the number of the high voltage narrow pulses in the pulsed electrical signal is 1 to 4000; the number of the low-voltage wide pulses in the pulsed electrical signal is 1 to 4000.

According to any of the preceding embodiments of the utility model, the pulsed electrical signal has a total duration of 1us to 4800s.

According to any one of the preceding embodiments of the present utility model, in the pulsed electrical signal, an interval time of 1us or more is provided between the adjacent high-voltage narrow pulse and the low-voltage wide pulse.

According to any of the foregoing embodiments of the present utility model, the pulsed electrical signal includes a third pulse group formed by at least one first pulse group and at least one second pulse group arranged in sequence, where the first pulse group and the second pulse group respectively include at least two pulses, and a pulse sequence of the first pulse group is different from a pulse sequence of the second pulse group.

According to any of the foregoing embodiments of the present utility model, the first pulse group includes a first high-voltage narrow pulse and a first low-voltage wide pulse having the same polarity, and the second pulse group includes a second high-voltage narrow pulse and a second low-voltage wide pulse having the same polarity, and the first high-voltage narrow pulse and the second high-voltage narrow pulse have opposite polarities.

According to any of the foregoing embodiments of the present utility model, the first high-voltage narrow pulse and the second high-voltage narrow pulse have the same amplitude and pulse width, and the first low-voltage wide pulse and the second low-voltage wide pulse have the same amplitude and pulse width.

According to any of the preceding embodiments of the utility model, the first pulse group comprises a first high voltage narrow pulse and a second high voltage narrow pulse of opposite polarity, and the second pulse group comprises a first low voltage wide pulse and a second low voltage wide pulse of opposite polarity.

According to any of the preceding embodiments of the utility model, the amplitude and/or pulse width between the first high voltage narrow pulse and the second high voltage narrow pulse is different, and the amplitude and/or pulse width between the first low voltage wide pulse and the second low voltage wide pulse is different.

According to any of the preceding embodiments of the utility model, the first pulse group and the second pulse group have an interval time therebetween of 50ns or more.

According to any of the preceding embodiments of the utility model, the pulsed electrical signal comprises a fourth pulse set comprising at least two of the third pulse sets.

According to any of the foregoing embodiments of the utility model, the ablation device comprises at least one ablation electrode having an electrode ablation end or at least one ablation catheter having an ablation head end, the electrode ablation end, the ablation head end being extendable toward the tissue.

An ablation system for a lung passageway according to an embodiment of the present utility model includes a pulsed electrical signal generator for generating a pulsed electrical signal, wherein the pulsed electrical signal includes at least one high voltage narrow pulse having a magnitude greater than a magnitude of the low voltage wide pulse and at least one low voltage wide pulse having a pulse width less than a pulse width of the low voltage wide pulse, and an ablation device. The ablation device can deliver the specific pulse electric signals to tissues so as to induce apoptosis or necrosis and realize the removal of abnormal functional cells in a target area. In the process of ablation by adopting the specific pulse electric signals, the action potential distribution to peripheral tissues can be reduced, the contraction of muscles can be reduced or even avoided, and the uncomfortable feeling of an ablated main body is reduced.

Drawings

In order to more clearly illustrate the embodiments of the present utility model or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described, and it is obvious that the drawings in the following description are only some embodiments of the present utility model, and other drawings may be obtained according to the structures shown in these drawings without inventive effort for a person skilled in the art.

FIG. 1 is a block diagram of a first embodiment of an ablation system for a lung passageway according to the present utility model;

FIG. 2 is a schematic illustration of an ablation device in a first embodiment of an ablation system for a lung passageway in accordance with the present utility model;

FIG. 3 is a timing diagram of a pulsed electrical signal in a first embodiment of an ablation system for a pulmonary tract according to the present utility model;

FIG. 4 is a timing diagram of a pulsed electrical signal in a second embodiment of an ablation system for a pulmonary tract in accordance with the present utility model;

FIG. 5 is a timing diagram of a pulsed electrical signal in a third embodiment of an ablation system for a pulmonary tract in accordance with the present utility model;

FIG. 6 is a timing diagram of a pulsed electrical signal in a fourth embodiment of an ablation system for pulmonary passages in accordance with the present utility model;

FIG. 7 is a timing diagram of a pulsed electrical signal in a fifth embodiment of an ablation system for pulmonary passages in accordance with the present utility model;

FIG. 8 is a timing diagram of a pulsed electrical signal in a sixth embodiment of an ablation system for pulmonary passages in accordance with the present utility model;

FIG. 9 is a flow chart of one embodiment of a control method of the present utility model for an ablation system for a lung passageway;

fig. 10 is a schematic hardware configuration of an embodiment of a control device of the ablation system for lung passages according to the present utility model.

Reference numerals illustrate:

110-an electrical signal generator; 120-an ablation device; 121-ablating the head end;

210-memory; 220-a processor; 230-a communication interface; 240-bus.

The achievement of the objects, functional features and advantages of the present utility model will be further described with reference to the accompanying drawings, in conjunction with the embodiments.

Detailed Description

The following description of the embodiments of the present utility model 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 utility model. All other embodiments, which can be made by those skilled in the art based on the embodiments of the utility model without making any inventive effort, are intended to be within the scope of the utility model.

It should be noted that all directional indicators (such as up, down, left, right, front, and rear … …) in the embodiments of the present utility model are merely used to explain the relative positional relationship, movement, etc. between the components in a particular posture (as shown in the drawings), and if the particular posture is changed, the directional indicator is changed accordingly.

Furthermore, the description of "first," "second," etc. in this disclosure is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be considered to be absent and not within the scope of protection claimed in the present utility model.

The embodiment of the utility model provides an ablation system for a lung channel. The ablation system for lung passages may be used for chronic obstructive pulmonary disease (chronic obstructive pulmonary disease, COPD). Fig. 1 is a block diagram of a first embodiment of an ablation system for a lung passageway according to the present utility model, including a pulsed electrical signal generator 110 and an ablation device 120. The pulse electric signal generator 110 is used for generating a pulse electric signal. Ablation device 120 is coupled to pulsed electrical signal generator 110 such that at least a portion of ablation device 120 is capable of extending toward tissue such that ablation device 120 is capable of delivering pulsed electrical signals to tissue.

In some embodiments, the ablation device 120 includes at least one ablation electrode or at least one ablation catheter. Fig. 2 is a schematic structural view of an ablation device in a first embodiment of an ablation system for a lung passageway according to the present utility model, wherein the ablation device 120 includes an ablation catheter having an ablation head 121, the ablation head 121 being capable of extending toward tissue. In other embodiments, the ablation device 120 includes at least one ablation electrode having an electrode ablation tip or at least one ablation catheter having an ablation tip, the electrode ablation tip, the ablation tip being extendable toward tissue.

Fig. 3 is a timing diagram of a pulsed electrical signal in a first embodiment of an ablation system for a lung passageway according to the present utility model.

The pulsed electrical signal comprises at least one high voltage narrow pulse HN and at least one low voltage wide pulse LW, the amplitude of the high voltage narrow pulse HN being greater than the amplitude of the low voltage wide pulse LW, the pulse width of the high voltage narrow pulse HN being less than the pulse width of the low voltage wide pulse LW.

The high-voltage narrow pulse HN is, for example, a nanosecond pulse, and the low-voltage wide pulse LW is, for example, a microsecond pulse.

In some embodiments, the pulse width of each high-voltage narrow pulse HN is in the range of 0.5ns (nanosecond) or more and less than 1000 ns. For example, the pulse width of the high voltage narrow pulse HN may be 0.5ns, 1ns, 8ns, 60ns, 700ns, 980ns. In some embodiments, the pulse width of each low-voltage wide pulse LW is in the range of 1us (microseconds) or more and 100us or less. For example, the pulse width of the low voltage wide pulse LW may be 1us, 5us, 20us, 90us, 100us.

In some embodiments, the amplitude of each high voltage narrow pulse HN is in the range of 5kV/cm or more and 50kV/cm or less. For example, the amplitude of the high voltage narrow pulse HN may be 5kV/cm, 30kV/cm, 50kV/cm. In some embodiments, the amplitude of each low voltage wide pulse LW is in the range of greater than or equal to 0.5kV/cm and less than 5 kV/cm. For example, the amplitude of the low voltage broad pulse LW may be 0.5kV/cm, 1kV/cm, 4kV/cm.

In some embodiments, the number of high voltage narrow pulses HN in the pulsed electrical signal is 1 to 4000; the number of low voltage wide pulses LW in the pulsed electrical signal is 1 to 4000. The number of high voltage narrow pulses HN in the pulsed electrical signal may be the same as or different from the number of low voltage wide pulses LW. For example, in one example, the pulsed electrical signal comprises 80 high voltage narrow pulses HN and 80 low voltage wide pulses LW, and in another example, the pulsed electrical signal comprises 50 high voltage narrow pulses HN and 60 low voltage wide pulses LW.

In some embodiments, the pulsed electrical signal has a total duration of 1us to 4800s.

In some embodiments, the pulsed electrical signal has a separation time of 1us or more between adjacent high voltage narrow pulses HN and low voltage wide pulses LW. For example, one pair of adjacent high voltage narrow pulses HN and low voltage wide pulses LW has a 1us separation time therebetween, for example, the other pair of adjacent high voltage narrow pulses HN and low voltage wide pulses LW has a 2.5us separation time therebetween.

In this embodiment, the pulsed electrical signal is a unipolar pulsed electrical signal. In other embodiments, the pulsed electrical signal may be a bipolar pulsed electrical signal.

Fig. 4 is a timing diagram of a pulsed electrical signal in a second embodiment of an ablation system for a pulmonary tract in accordance with the present utility model. In a second embodiment, the pulsed electrical signal is a bipolar pulsed electrical signal, wherein the bipolar pulsed electrical signal comprises at least a pair of high voltage narrow pulses HN and low voltage wide pulses LW of opposite polarity.

Fig. 5 is a timing diagram of a pulsed electrical signal in a third embodiment of an ablation system for a pulmonary tract in accordance with the present utility model. In the third embodiment, the pulse electric signal includes a third pulse group M3 formed by at least one first pulse group M1 and at least one second pulse group M2 arranged in sequence, where the first pulse group M1 and the second pulse group M2 respectively include at least two pulses, and the pulse sequence of the first pulse group M1 is different from the pulse sequence of the second pulse group M2.

As shown in fig. 5, in the third embodiment, the first pulse group M1 includes a first high-voltage narrow pulse HN1 and a first low-voltage wide pulse LW1 with the same polarity, the second pulse group M2 includes a second high-voltage narrow pulse HN2 and a second low-voltage wide pulse LW2 with the same polarity, and the first high-voltage narrow pulse HN1 and the second high-voltage narrow pulse HN2 are opposite in polarity.

As shown in fig. 5, in the third embodiment, the first high-voltage narrow pulse HN1 and the second high-voltage narrow pulse HN2 have the same amplitude and pulse width, and the first low-voltage wide pulse LW1 and the second low-voltage wide pulse LW2 have the same amplitude and pulse width.

Fig. 6 is a timing diagram of a pulsed electrical signal in a fourth embodiment of an ablation system for pulmonary passages in accordance with the present utility model. In the fourth embodiment, the pulse electric signal includes a third pulse group M3 formed by at least one first pulse group M1 and at least one second pulse group M2 arranged in sequence, where the first pulse group M1 and the second pulse group M2 respectively include at least two pulses, and the pulse sequence of the first pulse group M1 is different from the pulse sequence of the second pulse group M2. The first pulse group M1 includes first high-voltage narrow pulses HN1 and second high-voltage narrow pulses HN2 having opposite polarities, and the second pulse group M2 includes first low-voltage wide pulses LW1 and second low-voltage wide pulses LW2 having opposite polarities.

As shown in fig. 6, in the fourth embodiment, the first high-voltage narrow pulse HN1 and the second high-voltage narrow pulse HN2 have the same amplitude and pulse width, and the first low-voltage wide pulse LW1 and the second low-voltage wide pulse LW2 have the same amplitude and pulse width.

Fig. 7 is a timing diagram of a pulsed electrical signal in a fifth embodiment of an ablation system for pulmonary passages in accordance with the present utility model. In the fifth embodiment, the pulse electric signal includes a third pulse group M3 formed by at least one first pulse group M1 and at least one second pulse group M2 arranged in sequence, where the first pulse group M1 and the second pulse group M2 respectively include at least two pulses, and the pulse sequence of the first pulse group M1 is different from the pulse sequence of the second pulse group M2. The first pulse group M1 includes first high-voltage narrow pulses HN1 and second high-voltage narrow pulses HN2 having opposite polarities, and the second pulse group M2 includes first low-voltage wide pulses LW1 and second low-voltage wide pulses LW2 having opposite polarities. In the fifth embodiment, the amplitude and/or pulse width between the first high-voltage narrow pulse HN1 and the second high-voltage narrow pulse HN2 are different, and the amplitude and/or pulse width between the first low-voltage wide pulse LW1 and the second low-voltage wide pulse LW2 are different.

In some embodiments, the first pulse set and the second pulse set have an interval time therebetween of 50ns or more. In one example, there is a 50ns separation time between the first pulse set and the second pulse set, and in another example, there is an 80ns separation time between the first pulse set and the second pulse set.

In some embodiments, the pulsed electrical signal may further comprise a fourth pulse set comprising at least two third pulse sets M3. For example, fig. 8 is a timing diagram of a pulsed electrical signal in a sixth embodiment of an ablation system for pulmonary passages according to the present utility model, where the pulsed electrical signal includes a fourth pulse set M4, such as the third pulse set M3 including at least two of the foregoing fifth embodiments. In other embodiments, the fourth pulse group M4 may include other types of third pulse groups M3, for example, the third pulse groups M3 of the third and fourth embodiments may be included.

An ablation system for a lung passageway according to an embodiment of the present utility model includes a pulse electrical signal generator 110 and an ablation device 120, the pulse electrical signal generator 110 being configured to generate a pulse electrical signal, wherein the pulse electrical signal includes at least one high voltage narrow pulse HN and at least one low voltage wide pulse LW, the amplitude of the high voltage narrow pulse HN is greater than the amplitude of the low voltage wide pulse LW, and the pulse width of the high voltage narrow pulse HN is less than the pulse width of the low voltage wide pulse LW. The ablation device 120 is capable of delivering the specific pulsed electrical signals to tissue to induce apoptosis or necrosis to effect removal of abnormal functional cells from the targeted area. In the process of ablation by adopting the specific pulse electric signals, the action potential distribution to peripheral tissues can be reduced, the contraction of muscles can be reduced or even avoided, and the uncomfortable feeling of an ablated main body is reduced.

In some of the embodiments described above, the pulsed electrical signal is applied to the biological tissue via ablation device 120 for a specific duration and manner of application, thereby inducing apoptosis or necrosis. In some embodiments, the pulsed electrical signal may act on the cell membrane structure, disrupting the lipid bilayer of the cell membrane, causing the intracellular and extracellular balance to break and die. In some embodiments, the pulsed electrical signal may also act on the inside of the cell, inducing functional damage to the organelles within the cell, initiating a death signaling pathway, causing apoptotic death.

The ablation system for the lung channel can be used for COPD, and in the process of ablation by adopting the specific pulse electric signals, the pulse electric signals can be transmitted to the airway wall to remove abnormal functional cells in the targeted area. In the process of ablation using the specific pulsed electrical signals described above, the pulsed electrical signals may preserve extracellular matrix structure and adjacent critical conduit structural integrity while damaging abnormal cells. After the ablation process is completed, normal and newly generated healthy cells or healthy tissues replace abnormal functional cells cleared by the ablation process.

The embodiment of the utility model also provides a control method of the ablation system for the lung channel, which is used for controlling the ablation system for the lung channel in any of the previous embodiments.

Fig. 9 is a flow chart of one embodiment of a control method of the ablation system for a lung passageway of the present utility model. The control method includes steps S110 to S130.

In step S110, the pulse electric signal generator is controlled to generate a pulse electric signal.

In step S120, the pulsed electrical signal is configured to include at least one high voltage narrow pulse and at least one low voltage wide pulse, the amplitude of the high voltage narrow pulse being greater than the amplitude of the low voltage wide pulse, the pulse width of the high voltage narrow pulse being less than the pulse width of the low voltage wide pulse.

In step S130, the ablation device is controlled to deliver a pulsed electrical signal to the tissue.

In some embodiments, the pulsed electrical signal is a unipolar pulsed electrical signal. In some embodiments, the pulsed electrical signal is a bipolar pulsed electrical signal, wherein the bipolar pulsed electrical signal comprises at least one pair of high voltage narrow pulses and low voltage wide pulses of opposite polarity.

In some embodiments, the pulse width of each high voltage narrow pulse is in the range of 0.5ns or more and less than 1000 ns. The pulse width of each low-voltage wide pulse is in the range of 1us or more and 100us or less.

In some embodiments, the amplitude of each high voltage narrow pulse is in the range of greater than or equal to 5kV/cm and less than or equal to 50kV/cm. The amplitude of each low-voltage wide pulse is in the range of 0.5kV/cm or more and less than 5 kV/cm.

In some embodiments, the number of high voltage narrow pulses in the pulsed electrical signal is 1 to 4000; the number of low voltage wide pulses in the pulsed electrical signal is 1 to 4000. In some embodiments, the pulsed electrical signal has a total duration of 1us to 4800s. In some embodiments, the pulsed electrical signal has a separation time of 1us or more between adjacent high voltage narrow pulses and low voltage wide pulses.

In some embodiments, in step S120, the pulsed electrical signal is configured to include a third pulse group comprising at least one first pulse group and at least one second pulse group arranged in sequence, where the first pulse group and the second pulse group respectively include at least two pulses, and a pulse sequence of the first pulse group is different from a pulse sequence of the second pulse group.

In some embodiments, in step S120, the first pulse group includes a first high voltage narrow pulse and a first low voltage wide pulse with the same polarity, and the second pulse group includes a second high voltage narrow pulse and a second low voltage wide pulse with the same polarity, and the first high voltage narrow pulse and the second high voltage narrow pulse are opposite in polarity.

Optionally, in step S120, the amplitudes and pulse widths of the first high-voltage narrow pulse and the second high-voltage narrow pulse are the same, and the amplitudes and pulse widths of the first low-voltage wide pulse and the second low-voltage wide pulse are the same.

Optionally, in step S120, the first pulse group includes a first high-voltage narrow pulse and a second high-voltage narrow pulse with opposite polarities, and the second pulse group includes a first low-voltage wide pulse and a second low-voltage wide pulse with opposite polarities.

Optionally, in step S120, the amplitude and/or pulse width between the first high voltage narrow pulse and the second high voltage narrow pulse is different, and the amplitude and/or pulse width between the first low voltage wide pulse and the second low voltage wide pulse is different.

In some embodiments, the first pulse set and the second pulse set have an interval time therebetween of 50ns or more.

In some embodiments, in step S120, the pulsed electrical signal is configured to include a fourth pulse set comprising at least two third pulse sets. The fourth pulse set may comprise the third pulse set of any of the preceding embodiments.

According to the control method for the lung channel ablation system, the pulse electric signal generator can be controlled to generate the pulse electric signal, and the pulse electric signal is configured to comprise at least one high-voltage narrow pulse and at least one low-voltage wide pulse, wherein the amplitude of the high-voltage narrow pulse is larger than that of the low-voltage wide pulse, and the pulse width of the high-voltage narrow pulse is smaller than that of the low-voltage wide pulse. The ablation device is controlled to deliver the pulse electric signals to the tissues, so that apoptosis or necrosis of cells can be induced, and abnormal functional cells in the target area can be cleared. In the process of ablation by adopting the specific pulse electric signals, the action potential distribution to peripheral tissues can be reduced, the contraction of muscles can be reduced or even avoided, and the uncomfortable feeling of an ablated main body is reduced.

In some of the embodiments described above, the pulsed electrical signal is configured to have a specific duration and manner of application, and is applied to biological tissue via the ablation device, thereby inducing apoptosis or necrosis. In some embodiments, the pulsed electrical signal may act on the cell membrane structure, disrupting the lipid bilayer of the cell membrane, causing the intracellular and extracellular balance to break and die. In some embodiments, the pulsed electrical signal may also act on the inside of the cell, inducing functional damage to the organelles within the cell, initiating a death signaling pathway, causing apoptotic death.

The control method of the ablation system for the lung channel can be used for COPD, and in the process of ablation by adopting the specific pulse electric signals, the pulse electric signals can be transmitted to the airway wall to remove abnormal functional cells in the targeted area. In the process of ablation using the specific pulsed electrical signals described above, the pulsed electrical signals may preserve extracellular matrix structure and adjacent critical conduit structural integrity while damaging abnormal cells. After the ablation process is completed, normal and newly generated healthy cells or healthy tissues replace abnormal functional cells cleared by the ablation process.

The embodiment of the utility model also provides a control device for the ablation system of the lung channel. Fig. 10 is a schematic hardware configuration of an embodiment of a control device of the ablation system for lung passages according to the present utility model. The control device comprises a memory 210 and at least one processor 220, the memory 210 having instructions stored therein, the at least one processor 220 invoking the instructions in the memory 210, causing the control device to perform a control method for an ablation system for a lung passageway according to any of the preceding embodiments of the utility model.

The control method comprises the following steps: controlling a pulse electric signal generator to generate a pulse electric signal; configuring the pulsed electrical signal to include at least one high voltage narrow pulse and at least one low voltage wide pulse, the amplitude of the high voltage narrow pulse being greater than the amplitude of the low voltage wide pulse, the pulse width of the high voltage narrow pulse being less than the pulse width of the low voltage wide pulse; the ablation device is controlled to deliver pulsed electrical signals to tissue.

In particular, the processor 220 may comprise a Central Processing Unit (CPU), or an application specific integrated circuit (Application Specific Integrated Circuit, ASIC), or may be configured as one or more integrated circuits that implement embodiments of the present utility model.

Memory 210 may include mass storage 210 for data or instructions. By way of example, and not limitation, memory 210 may include a Hard Disk Drive (HDD), floppy Disk Drive, flash memory, optical Disk, magneto-optical Disk, magnetic tape, or universal serial bus (Universal Serial Bus, USB) Drive, or a combination of two or more of the above. Memory 210 may include removable or non-removable (or fixed) media, where appropriate. Memory 210 may be internal or external to the integrated gateway disaster recovery device, where appropriate. In a particular embodiment, the memory 210 is a non-volatile solid-state memory. In particular embodiments, memory 210 includes Read Only Memory (ROM). The ROM may be mask programmed ROM, programmable ROM (PROM), erasable PROM (EPROM), electrically Erasable PROM (EEPROM), electrically rewritable ROM (EAROM), or flash memory, or a combination of two or more of these, where appropriate.

In one example, the control device may also include a communication interface 230 and a bus 240. The processor 220, memory 210, and communication interface 230 are coupled to and communicate with each other via a bus 240.

The communication interface 230 is primarily used to implement communication between modules, devices, units, and/or apparatuses in an embodiment of the present utility model.

Bus 240 includes hardware, software, or both, that couple the components of the online data flow billing device to each other. By way of example, and not limitation, the buses may include an Accelerated Graphics Port (AGP) or other graphics bus, an Enhanced Industry Standard Architecture (EISA) bus, a Front Side Bus (FSB), a HyperTransport (HT) interconnect, an Industry Standard Architecture (ISA) bus, an infiniband interconnect, a Low Pin Count (LPC) bus, a memory 210 bus, a micro channel architecture (MCa) bus, a Peripheral Component Interconnect (PCI) bus, a PCI-Express (PCI-X) bus, a Serial Advanced Technology Attachment (SATA) bus, a video electronics standards association local (VLB) bus, or other suitable bus, or a combination of two or more of the above. Bus 240 may include one or more buses, where appropriate. Although embodiments of the utility model have been described and illustrated with respect to a particular bus, the utility model contemplates any suitable bus or interconnect.

In addition, in combination with the control method of the ablation system for lung passages in the above embodiments, embodiments of the present utility model may be implemented by providing a computer-readable storage medium. The computer readable storage medium has stored thereon instructions which, when executed by a processor, implement a method of controlling an ablation system for a lung passageway according to any of the above embodiments.

The present utility model is not limited to the specific configurations and processes described above and shown in the drawings. For the sake of brevity, a detailed description of known methods is omitted here. In the above embodiments, several specific steps are described and shown as examples. However, the method processes of the present utility model are not limited to the specific steps described and shown, and those skilled in the art can make various changes, modifications and additions, or change the order between steps, after appreciating the spirit of the present utility model.

The functional blocks shown in the above block diagrams may be implemented in hardware, software, firmware, or a combination thereof. When implemented in hardware, it may be, for example, an electronic circuit, an Application Specific Integrated Circuit (ASIC), suitable firmware, a plug-in, a function card, or the like. When implemented in software, the elements of the utility model are the programs or code segments used to perform the required tasks. The program or code segments may be stored in a machine readable medium or transmitted over transmission media or communication links by a data signal carried in a carrier wave. A "machine-readable medium" may include any medium that can store or transfer information. Examples of machine-readable media include electronic circuitry, semiconductor memory devices, ROM, flash memory, erasable ROM (EROM), floppy disks, CD-ROMs, optical disks, hard disks, fiber optic media, radio Frequency (RF) links, and the like. The code segments may be downloaded via computer networks such as the internet, intranets, etc.

It should also be noted that the exemplary embodiments mentioned in this disclosure describe some methods or systems based on a series of steps or devices. However, the present utility model is not limited to the order of the above-described steps, that is, the steps may be performed in the order mentioned in the embodiments, or may be performed in a different order from the order in the embodiments, or several steps may be performed simultaneously.

In the foregoing, only the specific embodiments of the present utility model are described, and it will be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working processes of the systems, modules and units described above may refer to the corresponding processes in the foregoing method embodiments, which are not repeated herein. It should be understood that the scope of the present utility model is not limited thereto, and any equivalent modifications or substitutions can be easily made by those skilled in the art within the technical scope of the present utility model, and they should be included in the scope of the present utility model.

Claims

1. An ablation system for a lung passageway, comprising:

a pulse electric signal generator for generating a pulse electric signal;

an ablation device coupled to the pulsed electrical signal generator, at least a portion of the ablation device being capable of reaching tissue such that the ablation device is capable of delivering the pulsed electrical signal to the tissue,

the pulse electric signal comprises at least one high-voltage narrow pulse and at least one low-voltage wide pulse, the amplitude of the high-voltage narrow pulse is larger than that of the low-voltage wide pulse, and the pulse width of the high-voltage narrow pulse is smaller than that of the low-voltage wide pulse.

2. The ablation system for a pulmonary tract of claim 1, wherein the pulsed electrical signal is a unipolar pulsed electrical signal; or alternatively

The pulsed electrical signal is a bipolar pulsed electrical signal, wherein the bipolar pulsed electrical signal comprises at least one pair of the high voltage narrow pulse and the low voltage wide pulse with opposite polarities.

3. The ablation system for a pulmonary tract of claim 1, wherein a pulse width of each of the high voltage narrow pulses is in a range of 0.5ns or more and less than 1000 ns;

the pulse width of each of the low-voltage wide pulses is in the range of 1us or more and 100us or less.

4. The ablation system for a pulmonary tract of claim 1, wherein the amplitude of each of the high voltage narrow pulses is in a range of 5kV/cm or more and 50kV/cm or less;

the amplitude of each of the low-voltage wide pulses is in a range of 0.5kV/cm or more and less than 5 kV/cm.

5. The ablation system for a pulmonary tract of claim 1, wherein the number of the high voltage narrow pulses in the pulsed electrical signal is 1 to 4000;

the number of the low-voltage wide pulses in the pulsed electrical signal is 1 to 4000.

6. The ablation system for a lung passageway according to claim 1 wherein the pulsed electrical signal has a total duration of 1us to 4800s.

7. The ablation system for a pulmonary tract of claim 1, wherein the pulsed electrical signal has a separation time of 1us or more between adjacent ones of the high voltage narrow pulses and the low voltage wide pulses.

8. The ablation system for a pulmonary tract according to claim 1, wherein the pulsed electrical signal comprises a third pulse set comprising at least one first pulse set and at least one second pulse set arranged in succession, the first pulse set and the second pulse set each comprising at least two pulses, the pulse sequence of the first pulse set being different from the pulse sequence of the second pulse set.

9. The ablation system for a pulmonary tract of claim 8, wherein the first pulse set includes a first high voltage narrow pulse and a first low voltage wide pulse of the same polarity, the second pulse set includes a second high voltage narrow pulse and a second low voltage wide pulse of the same polarity, and the first high voltage narrow pulse is of opposite polarity to the second high voltage narrow pulse.

10. The ablation system for a pulmonary tract of claim 9, wherein the first high voltage narrow pulse is the same as the second high voltage narrow pulse in amplitude and pulse width, and the first low voltage wide pulse is the same as the second low voltage wide pulse in amplitude and pulse width.

11. The ablation system for a pulmonary tract of claim 8, wherein the first pulse set includes first high voltage narrow pulses and second high voltage narrow pulses of opposite polarity, and the second pulse set includes first low voltage wide pulses and second low voltage wide pulses of opposite polarity.

12. The ablation system for a pulmonary tract of claim 11, wherein the first high voltage narrow pulse is the same as the second high voltage narrow pulse in amplitude and pulse width, and the first low voltage wide pulse is the same as the second low voltage wide pulse in amplitude and pulse width.

13. The ablation system for a pulmonary channel of claim 11, wherein the first high voltage narrow pulse and the second high voltage narrow pulse differ in amplitude and/or pulse width, and the first low voltage wide pulse and the second low voltage wide pulse differ in amplitude and/or pulse width.

14. The ablation system for a pulmonary tract of claim 8, wherein the first pulse set and the second pulse set have a separation time greater than or equal to 50 ns.

15. The ablation system for a pulmonary channel of claim 8, wherein the pulsed electrical signal includes a fourth pulse set including at least two of the third pulse sets.

16. The ablation system for a lung passageway according to claim 1 wherein the ablation device comprises at least one ablation electrode having an electrode ablation end or at least one ablation catheter having an ablation tip, the electrode ablation end, the ablation tip being extendable toward the tissue.