JPH02104348A - High frequency cautery device - Google Patents

Abstract

PURPOSE:To measure the electric characteristic of a diseased part before and after cauterizing by allowing a selecting means to constitute a circuit between an electric characteristic measuring means and a probe at the same time as the circuit formed by a high frequency generating means and the probe is opened by the selecting means. CONSTITUTION:Electrical continuity is formed with an external electrode 14 through a spherical electrode 17 and a vital structure 26, while the internal electrode 11 is connected with an analyzer 7 via a common contact 4a and a normally closed contact 4c, to provide measurability for electric characteristics. A relay driver circuit 8 is actuated to change over a high frequency coaxial relay 4, and the common contact 4a is connected with a normally open contact 4c. Through a coaxial cable 19 a high frequency signal from a high frequency generating device 6 is fed to a vital structure 26 by the electrodes 11, 14 via the normally closed contact 4b and common contact 4a, and the diseased part undergoes cauterizing. If the relay driver circuit 8 is deactuated after this cauterizing, the high frequency coaxial relay 4 is changed over again to the normally closed contact 4c side, and the analyzer 7 measures the electric characteristic of the vital structure 26 after cauterizing. This permits knowing whether cauterizing has been made with good performance with appropriate value according to the electric characteristic.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] - The present invention relates to a radiofrequency ablation device used with an endoscope.

[Prior Art and Problems to be Solved by the Invention] A high-frequency ablation device called an electric scalpel has been developed, which cauterizes an affected area by passing a high-frequency current through the affected area. If the affected area is inside a body cavity, a treatment instrument is inserted into the treatment instrument channel of the endoscope, and the polyp inside the body cavity is removed endoscopically.
The bleeding is stopped and the lime and affected tissues are killed.

Furthermore, Japanese Patent Application Laid-Open No. 57-75645 discloses a technique in which the impedance of a living tissue is measured using an ablation treatment tool and the ablation current is changed depending on the impedance.

However, adding the function of measuring the impedance of biological tissues as described above to conventionally used devices required significant improvements, and furthermore, it was only possible to measure impedance as the electrical property of tissues. More detailed information about the electrical properties of the tissue could not be obtained.

The present invention has been made in view of the above-mentioned circumstances, and does not require any major improvements to conventionally used devices, can be easily configured, and can be used to more precisely determine the state of tissue due to the electrical properties of living tissue. The purpose of the present invention is to provide a high-frequency ablation device capable of knowing the following.

[Means for Solving the Problems] The high-frequency ablation device of the present invention is provided with a switching means that simultaneously cuts off the circuit formed between the high-frequency generating means and the probe and forms a circuit between the electrical property measuring means and the probe. It is.

[Operation] In the present invention, the switching means disconnects the circuit C formed by the high frequency generating means and the probe. At the same time as the circuit formed by the high frequency generating means and the probe is cut off, the switching means forms a circuit between the electrical characteristic measuring means and the probe.

This allows the electrical characteristics of the affected area to be measured before and after cauterization.

[Example] Hereinafter, the present invention will be described in detail with reference to the drawings.

Figures 1 to 3 relate to the first embodiment of the present invention.
FIG. 2 is a perspective view illustrating the shape of the tip of the probe body, and FIG. 3 is a two-dimensional view of the tip of the probe body in use.

The high-frequency cautery bag M1 of this embodiment includes a probe body 3 inserted into an endoscope 2, a high-frequency coaxial relay 4 as a switching means to which the rear end of the probe body 3 is connected, and a high-frequency coaxial relay 4 as a switching means. an impedance/gain phase analyzer 7 (hereinafter abbreviated as "analyzer") as a means for measuring electrical characteristics; and a relay drive connected to the high frequency coaxial relay 4. It consists of a circuit 8 and a foot switch 9 connected to the high frequency generator 6.

The tip of the probe body 3 has a coaxial structure as shown in FIG. 2<a>, and the inner electrode 11 is inserted through the center thereof. The tip of this inner electrode 11 protrudes from the tip surface of the probe body 3 and forms a needle-like electrode 12. The outer periphery of the inner electrode 11 is covered with an insulating layer 13, and an outer electrode 14 is disposed so as to cover the outer periphery of the insulating layer 13. It is designed to match the tip surface of the

Further, the outer periphery of the outer electrode 14 is covered with an insulating coating 16 so as to expose the outer circumferential surface of the tip.

Note that the protruding portion of the inner electrode 11 may be formed into a spherical shape to form a spherical electrode 17 as shown in FIG. 2(b).

#i Inner electrode 11 is inserted through the probe body 3 and connected to the common contact 4a of the high frequency coaxial relay 4. A normally closed contact 4b of this high frequency coaxial relay 4 is connected to a coaxial cable 19. This coaxial cable 19 is connected to the high frequency generator 6. Further, the normally closed contact 4C of the high frequency coaxial relay 4 is connected to a coaxial cable 21, which is connected to the analyzer 7. The analyzer 7 is connected to the high frequency generator 6 by a signal line 27. The high frequency generator 6 is connected to the high frequency generator 6 so as to be able to transmit a control signal that gives permission to generate a high frequency signal.

The high frequency coaxial relay 4 is connected to the relay drive circuit 8 by a relay drive line 31, and contacts 4b and 4c are switched by a control signal from the relay drive circuit 8.

Further, the analyzer 7 is provided with a monitor 23 as a display means and a keyboard 24 as an input means.

The foot switch 9 is connected to the high frequency generator 6, and by pressing the foot switch 9, a high frequency signal can be output.

The outer electrode 14 of the probe body 3 is grounded via the high frequency coaxial relay 4 by an external conductor (not shown) of the coaxial cable 19.21.

The operation of the high-frequency ablation device 1 configured as described above will be explained.

The analyzer 7 is calibrated in a state where the inner electrode 11 and the outer electrode 14 are not in contact with the biological set #126.

As a result, the electrical characteristics of the coaxial cable 21, high frequency coaxial relay 4, and probe body 3 do not affect the measurement of the electrical characteristics of the living tissue 26.

Next, a needle electrode 12 provided at the tip of the probe body 3
As shown in Figure 3(a), the biological assembly! Insert into 26.

The needle electrode 12 communicates with the outer electrode 14 through the living tissue 26 . Further, when the inner electrode 11 has a shape as shown in FIG. 2(b), the spherical electrode 17 is brought into contact with the living tissue 26, and the spherical electrode 17 and the living tissue 26 are electrically connected to the outer electrode 14. The inner electrode 11 is the common electrode 4a and the normally closed contact 4
It is connected to the analyzer 7 via C, and electrical characteristics can be measured. By operating the keyboard 24 of the analyzer 7, the measurement results of electrical characteristics such as impedance and admittance are displayed on the monitor 23 in the form of graphs or numerical values. If the probe main body 3 is correctly inserted into or in contact with the living tissue 126, electrical characteristics specific to the living tissue 1a26 can be measured. That is, if the measurement result matches the electrical characteristics of the living tissue 26 to be cauterized, it can be considered that the probe main body 3 and 14 are correctly inserted into or in contact with the living tissue 26.

If it is determined that the electrodes 11 and 14 are correctly inserted into or in contact with the living tissue 26, the external electrode 11 held by the analyzer 7
The 0 function transmits a control signal from the analyzer 7 to the high frequency generator 6 via the signal line 27 to give permission to generate a high frequency signal. The measurement of the electrical characteristics of the living tissue 26, the judgment of the measured values, and the generation of control signals are performed according to a program set in advance by the program function of the analyzer 7.

Next, the relay drive circuit 8 is operated to switch the high frequency coaxial relay 4 and connect the common contact 4a and the normally open contact 4b. After that, the foot switch 9 is stepped on to cause the high frequency generator 6 to generate a high frequency signal. This high frequency signal is supplied to the living body assembly 126 by the electrodes 11 and 14 via the coaxial couple 19, the normally open contact 4b, and the common contact 4a to cauterize this region.

When the drive of the relay drive circuit 8 is stopped after the cauterization, the high frequency coaxial relay 4 is switched again to the normally closed contact 4C side, and the analyzer 7 detects the biological tissue after the cauterization! Measure the electrical properties of 126. Biological assembly before and after cauterization! The impedance has increased due to the evaporation of the water contained in 26, and other electrical characteristics have also changed. Therefore, it is possible to confirm whether or not cauterization has been performed satisfactorily based on the value of the electrical characteristics.

According to this embodiment, by opening the high-frequency coaxial relay 4 and connecting the analyzer 7, it is possible to cauterize the living tissue and measure the electrical characteristics with the same probe without making any special major improvements to the equipment used. Can be done.

Therefore, it can be determined that the electrodes 11, 14 are inserted into or in contact with the living tissue 26, and the degree of tissue alteration due to the cauterization can be determined from the difference in the electrical characteristics of the tissue before and after the cauterization.

Further, due to the difference in electrical characteristics between the lesioned area and the normal area, only the lesioned area can be selectively cauterized.

Furthermore, since the measuring instrument used to measure electrical characteristics can measure not only impedance but also many characteristics such as admittance and their frequency characteristics, more detailed measurements and diagnosis of tissues are possible.

FIG. 4 is an explanatory diagram of the overall configuration of a high-frequency ablation device according to a second embodiment of the present invention.

In this embodiment, a 7-way switch for causing the high frequency generator 6 to generate high frequencies is used as a double switch to also operate the relay drive circuit 8.

The power supply circuit of the relay drive circuit 8 is connected to the contacts 29a and 29b of the foot switch 29, and the power supply circuit is formed by connecting the contacts 29a and 29b. Further, the contacts 29C and 29d of the foot switch 29 are connected to the power supply circuit of the high frequency generating bag, and the contact 29c and the contact 29d are connected to form a power supply circuit.

By stepping on this foot switch 29, contacts 29a and 29b and contacts 29c and 29d can be connected simultaneously.

The other configurations are the same as in the first embodiment.

The operation of the high-frequency ablation device 1 configured as described above will be explained.

As in the first embodiment, it is determined that the electrodes 11 and 14 of the probe body 3 are inserted into or in contact with the living tissue 26, and control is performed to permit generation of high-frequency signals from the analyzer 7 via the signal line 27. After the signal is transmitted, step on the foot switch 29. When the foot switch 29 is stepped on, the contacts 29a and 29b are connected, and the contacts 29c and 29d are connected. When the contacts 29a and 29b are connected, a power supply circuit for the relay drive circuit 8 is formed, and the common contact 4a and the normally closed contact 4b of the high frequency coaxial relay 4 are connected by this device, and the high frequency generator 6 and the probe body 3 are connected. A circuit is now formed.

Further, when the contacts 29b and 29d are connected, a power supply circuit for the high frequency generator 6 is formed, and the high frequency generator 6
generates a high frequency signal. The generated high-frequency signal is supplied to the electrodes 11.14 via the normally closed contact 4b and the common contact 4a switched by the relay drive circuit 8, and cauterizes the living tissue 26.

When the foot switch 29 is stopped being depressed, the contacts 29a and 29b and the contacts 29c and 29d are opened, respectively, and the relay drive circuit 8 and high frequency generator 6 are stopped. By stopping and covering the relay drive circuit 8, the high frequency coaxial relay 4 is switched, the common contact 4a and the normally closed contact 4C are connected, and a circuit between the probe body 3 and the analyzer 7 is formed. This allows the analyzer 7 to detect the body tissue 26 after cauterization.
The electrical properties of can be measured.

Other operations are similar to those in the first embodiment.

In this embodiment, by stepping on the foot switch 29, switching of the high frequency coaxial relay 4 and generation of the high frequency signal in the high frequency generator 6 can be simultaneously controlled.
Compared to the first embodiment, the relay drive circuit 8 is not operated by the f motion, and operability can be improved.

Other effects are similar to those of the first embodiment.

FIG. 5 is an explanatory diagram of the main parts of a 1τA frequency ablation device according to a third embodiment of the present invention.

In this embodiment, the high frequency coaxial relay 4 is directly connected to the analyzer 7.
, and the relay drive circuit 8 is omitted.

The high frequency coaxial relay 8 of this embodiment is connected to the analyzer 7 by a relay drive line 31. Further, the analyzer 7 is connected to the high-frequency generator 6 and a signal line 27 that transmits a control signal for permitting generation of a high-frequency signal, as well as a signal line 32 that outputs a control signal without indicating the ablation path.

The other configurations are the same as in the first embodiment.

In this embodiment, when it is determined that the electrodes 11 and 14 are correctly inserted into or in contact with the living tissue 26, the analyzer 7 controls the high-frequency generator 6 via the signal line 27 to permit the generation of high-frequency signals. A signal is output. This υJl
At the same time as the 'll signal, a relay drive signal is sent to the high frequency coaxial relay 4 via the relay drive line 31, and the common contact 4a
and the normally closed contact 4b are connected. After stepping on the foot switch 9 to cauterize the biological tissue 26, the foot switch 9 is
When the user stops stepping on the , the high-frequency generator 6 outputs a control signal indicating the ablation path to the analyzer 7 via the signal line 32, and the analyzer 7 stops outputting the relay drive signal to the high-frequency coaxial relay 4. . As a result, the high frequency coaxial relay 4 returns to the normally closed contact 4C side, and the electrical characteristics of the tissue after ablation can be measured.

Other operations are similar to those in the first embodiment.

In this embodiment, the relay drive circuit 8 can be omitted in order to drive the high frequency coaxial relay 4 using the program function of the analyzer 7 and the external 1101 function.

Other effects are similar to those of the first embodiment.

6 and 7 relate to the fourth embodiment of the present invention, and FIG.
The figure is an explanatory diagram of the high frequency coaxial relay, and FIG. 7 is an explanatory diagram of the tip of the probe body.

The high frequency coaxial relay of this embodiment is of a one-circuit, two-make type.

As shown in FIG. 7<a), the probe main body 34 of this embodiment has a coaxial structure, and the first inner electrode 36 is inserted through the center. The outer periphery of this first inner electrode 36 is covered with a first insulating layer 37.
The first inner electrode 36 protrudes from the distal end surface of the electrode.

This protrusion forms a spherical electrode 38. A second inner electrode 39 is provided on the outer periphery of the first insulating layer 37, and the tip surface of the second inner electrode 39 is aligned with the tip surface of the first absolutely rounded layer 37. It has become. The outer circumference of the second inner electrode 39 is covered with a second insulating layer 41 so that the outer circumferential surface of the tip portion is exposed. The outer periphery of this second insulating layer 41 is outer til! It is covered with an electrode 42 , and the tip end surface of this outer electrode 42 coincides with the tip end surface of the second insulating layer 41 .

Further, the periphery of this outer T1 pole 42 is covered with an insulating coating 43 so that the outer peripheral surface of the tip portion is exposed.

Note that the probe body 34 may be configured as shown in FIG. 7(b).

In FIG. 7(b), a first inner electrode 36 is inserted through the center of the probe body 34 having a coaxial structure. This first
The outer periphery of the inner electrode 36 is covered with a first insulating layer 37, and the tip of the first insulating layer 37 is
The inner electrode 36 of the inner electrode 36 protrudes. This protrusion forms a needle-like electrode 44. This first insulating layer 3
A second inner electrode 39 is provided on the outer periphery of the three second inner electrodes 7, and the outer periphery of the three second inner electrodes is covered with a second insulating layer 41. Furthermore, the outer periphery of this second insulating layer 41 is covered with an outer electrode 42, and between this outer electrode 42, the second insulating layer 41, the second inner electrode HA39, and the first insulating layer 41, the outer periphery of the second insulating layer 41 is covered. The tip surfaces of each of the 137 are made to coincide with each other. The periphery of the outer electrode 42 is covered with an insulating coating 43 so that the outer peripheral surface of the tip portion of the outer electrode 42 is exposed.

In FIG. 6, the first inner electrode 36 is a contact 46a forming a normally open switch 46 of a high frequency coaxial relay 45, and the three second inner electrodes are a contact 46a forming a normally closed switch 47.
7a. Contact 4 of normally open switch 46
6b is connected to the high frequency generator 6 by the coaxial cable 19 described in the first embodiment, and similarly, the contact 47b of the normally closed switch 47 is connected to the analyzer 7 by the coaxial cable 21.

Note that the outer electrode 42 is connected to the outer conductor of the coaxial cable 19.21 via a high frequency coaxial relay 45.

The other configurations are the same as in the first embodiment.

In the above embodiment, the probe body 3 of FIG. 7(a)
4, the spherical electrode 38, the three second inner electrodes, and the outer electrode are brought into contact with the biological tissue 26. In addition, when using the probe main body 34 shown in FIG. 3(b), the needle electrode 44 is inserted into the living tissue 26 and the second inner electrode 39 and the outer electrode 42 are connected to the living tissue &'! 26. Thereafter, a relay drive signal is input from the relay drive circuit 8 to the high frequency coaxial relay 45 via the relay drive line 31. Then, the normally open switch 46 closes and the normally closed switch 47 opens. Thereby, the high frequency signal generated by the high frequency generator 6 is supplied to the first inner electrode 36 and the outer electrode 42, and ablation is performed between the first inner electrode 36 and the outer electrode 42.

Furthermore, when the relay drive signal is stopped after cauterization, the normally open switch 46 opens and the normally closed switch 47 closes. This causes the second inner electric If! 39 and the analyzer 7 are formed to measure the electrical characteristics of the ablation site.

Other operations are similar to those in the first embodiment.

In this embodiment, ablation is performed using the first inner electrode 36 and the outer electrode 42.
, the electrical characteristics are measured using the second inner electrode 39 and the outer electrode 42.
As described above, since the electrodes are separate, even if the living tissue 26 is burned onto the first inner electrode 36, which is the cauterization electrode, the electrical characteristics can be accurately measured.

Other effects are similar to those of the first embodiment.

[Effects of the Invention] As described above, according to the present invention, by providing the switching means, it is not necessary to significantly improve the conventionally used device, the configuration is simple, and it is possible to , the state of the organization can be known in more detail.

[Brief explanation of drawings]

Figures 1 to 3 relate to the first embodiment of the present invention.
The figure is an explanatory diagram of the overall configuration of the high-frequency ablation device, Figure 2 is a perspective view illustrating the shape of the tip of the probe body, Figure 3 is an explanatory diagram of the state of use of the tip of the probe body, and Figure 4 is an illustration of the state of use of the tip of the probe body. 5 is an explanatory diagram of the overall configuration of the high-frequency ablation device according to the second embodiment, and FIG. 5 is an explanatory diagram of the main parts of the high-frequency ablation device according to the third embodiment of the present invention. Fourth invention
Regarding the embodiment, FIG. 6 is an explanatory diagram of the frequency simultaneous relay, and FIG. 7 is an explanatory diagram of the tip of the probe body. 1...High frequency ablation device 2...Endoscope 3...Probe body 4...High frequency coaxial relay 6...High frequency generator 7...Impedance/gain/phase analyzer 8...Relay drive Circuit 9...Foot switch (a
1. Display of case 1988 Patent Application No. 259916
Title (037) Olympus Optical Industry Co., Ltd. Representative Satoshi Shimoyama Department 4. Agent and drawings (Figures 6 and 7) 7. Contents of amendment As attached 1. Page 2 of the specification, line 7 The word ``lime'' in the eyes is ``
Corrected by "incision". 2. In the 6th line of page 11 of the specification, "High frequency signal"
Correct the statement to "high frequency signal." 3. "High frequency belief" on page 12, line 14 of the specification
Correct the statement to "high frequency signal." 4. Correct the statement "Probe body is 34" on page 15, line 17 of the specification to "Probe body 34." 5. In the first line of page 18 of the specification, "supply with outer electrode 42" should be corrected to "supply between outer electrode 42".

Claims (1)

[Scope of Claims] High-frequency ablation comprising: an ablation probe that cauterizes the affected area; a high-frequency generator that outputs a high-frequency signal to the ablation probe; and an electrical property measuring unit that measures the electrical properties of the affected area that has been ablated by the probe. In the apparatus, a switching means is provided for cutting off a circuit formed by the high frequency generation means and the probe and simultaneously forming a circuit between the electrical property measuring means and the probe, and the switching means switches between the electrical property measuring means and the probe. A high-frequency ablation device characterized in that a circuit is formed between the probe and the probe to measure the electrical characteristics of the affected area before and after ablation.