JP2542060B2 - Induction cauterization device - Google Patents

Description

TECHNICAL FIELD The present invention relates to an induction cauterization device used with an endoscope.

[Problems to be Solved by Conventional Techniques and Inventions] A high-frequency ablation device called a so-called electric scalpel has been developed, in which a high-frequency current is applied to the affected part to cauterize the affected part. If the affected part is inside the body cavity, the treatment tool is inserted into the treatment tool channel of the endoscope, and endoscopically endoscopically removes the polyp in the body cavity, hemostasis of the bleeding part, incision and death of the affected part tissue. Have been implemented.

Further, Japanese Patent Application Laid-Open No. 57-75645 discloses a technique of measuring the impedance of a living tissue using a cauterizing treatment tool and changing the cauterizing current depending on its size.

However, adding the function of measuring the impedance of the biological tissue as described above to a device that has been conventionally used requires a significant improvement, and furthermore, as the electrical characteristics of the tissue, only impedance can be measured. No further information was available on the electrical properties of the tissue.

The present invention has been made in view of the above circumstances, does not require a significant improvement in the conventionally used device, can be easily configured, and from the electrical characteristics of the biological tissue, the tissue state in more detail It is an object to provide a high-frequency ablation device that can be known.

[Means for Solving the Problems] The high frequency ablation device of the present invention is provided with a switching means for disconnecting the circuit formed by the high frequency generating means and the probe and at the same time for forming a circuit between the electrical characteristic measuring means and the probe. Is.

[Operation] In the present invention, the circuit formed by the high frequency generating means and the probe is disconnected by the switching means. At the same time that the circuit formed by the high frequency generating means and the probe is disconnected, the switching means forms a circuit between the electrical characteristic measuring means and the probe.
In this way, the electrical characteristics of the affected area before and after cauterization are measured.

Embodiments Embodiments of the present invention will be described below with reference to the drawings.

1 to 3 relate to the first embodiment of the present invention, FIG. 1 is an explanatory view of the overall configuration of an induction cauterization device, FIG. 2 is a perspective view for explaining the shape of the tip portion of the probe main body, and FIG. The figure is an explanatory view of a usage state of the tip portion of the probe body.

The high frequency ablation device 1 of the present embodiment has a probe main body 3 inserted through an endoscope 2, a high frequency coaxial relay 4 as a switching means to which a rear end portion of the probe main body 3 is connected, and the high frequency coaxial relay 4 A high frequency generator 6 as a high frequency generating means, an impedance / gain phase analyzer 7 (hereinafter abbreviated as an analyzer) as an electric characteristic measuring means, and a relay drive connected to the high frequency coaxial relay 4. It is composed of a circuit 8 and a foot switch 9 connected to the high frequency generator 6.

The tip portion 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 portion. The tip of this inner electrode 11 is the probe body 3
Projecting from the tip surface of the, and forming a needle electrode 12. The outer circumference of the inner electrode 11 is covered with the insulating layer 13, and the outer electrode 14 is arranged so as to cover the outer circumference of the insulating layer 13. The tip surface of the outer electrode 14 is adapted to coincide with the tip surface of the insulating layer 13. Further, the outer periphery of the outer electrode 14 is covered with an insulating coating so that the outer peripheral surface of the tip is exposed.
It is covered by 16.

The spherical electrode 17 may be formed by forming the protrusion of the inner electrode 11 into a spherical shape as shown in FIG.

The inner electrode 11 is inserted through the probe body 3 and connected to the common contact 4a of the high frequency coaxial relay 4. The normally open contact 4b of the high frequency coaxial relay 4 is connected to the coaxial cable 19. This coaxial cable 19 is a high frequency generator 6
It is connected to the. The normally closed contact 4c of the high frequency coaxial relay 4 is connected to the coaxial cable 21, and the coaxial cable 21 is connected to the analyzer 7. The analyzer 7 is connected to the high-frequency generator 6 by a signal line 27, and can transmit a control signal for giving the high-frequency generator 6 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 the 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 wire (not shown) of the coaxial cables 19 and 21.

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

The alanizer 7 is calibrated while the inner electrode 11 and the outer electrode 14 are not in contact with the biological tissue 26. As a result, the electrical characteristics of the coaxial cable 21, the high-frequency coaxial relay 4, and the probe body 3 do not affect the measurement of the electrical characteristics of the living tissue 26.

Next, the needle-shaped electrode 12 provided at the tip of the probe body 3
Is inserted into the living tissue 26 as shown in FIG. The needle electrode 12 is electrically connected to the outer electrode 14 through the living tissue 26.
Further, when the inner electrode 11 has a shape as shown in FIG. 2B, the spherical electrode 17 is brought into contact with the living tissue 26, and the outer electrode 14 is electrically connected through the spherical electrode 17 and the living tissue 26. Inner electrode
Reference numeral 11 is connected to the analyzer 7 via the common electrode 4a and the normally closed contact 4c, and the electrical characteristics can be measured. By operating the keyboard 24 of the analyzer 7, measurement results of electrical characteristics such as impedance and admittance are displayed on the monitor 23 as a graph or numerical values. If the probe main body 3 is properly inserted into or in contact with the living tissue 26, the electrical characteristics specific to the living tissue 26 are 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 electrodes 11 and 14 of the probe body 3 are correctly inserted or contacted to the living tissue 26.

If it is determined that the electrodes 11 and 14 are correctly inserted or contacted to the living tissue 26, the analyzer 7 generates a high frequency signal via the signal line 27 to the high frequency generator 6 by the external I / O function of the analyzer 7. Send a control signal that gives permission. The measurement of the electric characteristics of the living tissue 26, the determination of the measured value, and the generation of the control signal are performed according to a program preset by the program function of the analyzer 7.

Next, the relay drive circuit 8 is operated to switch the high frequency coaxial relay 4 to connect the common contact 4 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 transmitted through the coaxial cable 19, the normally open contact 4b and the common contact 4a to the electrode 1
It is supplied to the living tissue 26 by 1, 14 and cauterizes this part.

When the drive of the relay drive circuit 8 is stopped after cauterization,
The high frequency coaxial relay 4 is switched to the normally closed contact 4c side again, and the electrical characteristics of the living tissue 26 after cauterization are measured by the analyzer 7. Before and after cauterization, the impedance increases due to the evaporation of water contained in the biological tissue 26, and other electrical characteristics also change. Therefore, it is possible to confirm whether or not the cauterization has been performed favorably based on the value of the electrical characteristic.

According to the present embodiment, the cauterization of the biological tissue and the measurement of the electrical characteristics can be performed by the same probe by opening the high-frequency coaxial relay 4 and connecting the analyzer 7 without making a significant improvement in the device used. You can

Therefore, it is possible to determine whether the electrodes 11 and 14 are inserted or contact the living tissue 26, and it is possible to know the degree of tissue degeneration due to cauterization from the difference in the electrical characteristics of the tissue before and after cauterization.

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

Further, since the measuring instrument used for measuring the electrical characteristics can measure not only the impedance but also characteristics such as admittance and their frequency characteristics over many items, more detailed measurement and diagnosis of the tissue are possible.

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

In the present embodiment, the foot switch for generating a high frequency in the high frequency generator 6 is a double switch so that the relay drive circuit 8 can also be operated.

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. Also, contact 29c and contact 29d of foot switch 29
Is connected to the power supply circuit of the high frequency generator, and the contact 29c and the contact 29d are connected to form a power supply circuit. By stepping on the foot switch 29, the contacts 29a and 29b and the contacts 29c and 29d can be simultaneously connected.

 Other configurations are similar to those of the first embodiment.

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

Similar to the first embodiment, it is determined that the electrodes 11 and 14 of the probe body 3 are inserted into or contact the living tissue 26, and a control signal for permitting generation of a high frequency signal from the analyzer 7 via the signal line 27. Is transmitted, the foot switch 29 is stepped on. When the foot switch 29 is stepped on, the contacts 29a and 29b, and the contacts 29c and 29d are connected. When the contacts 29a and 29b are connected to each other, a power supply circuit of the relay drive circuit 8 is formed, whereby the common contact 4a of the high frequency coaxial relay 4 and the normally open contact 4b are connected to connect the high frequency generator 6 and the probe body 3 to each other. A circuit is formed. Further, when the contacts 29b and 29d are connected, a power supply circuit of the high frequency generator 6 is formed, and the high frequency generator 6 generates a high frequency signal. The generated high frequency signal is switched to the normally open contact 4b and the common contact 4a by the relay drive circuit 8.
Is supplied to the electrodes 11 and 14 via and to ablate the living tissue 26.

When stepping on the foot switch 29 is stopped, the contact points 29a and 29b are opened, and the contact points 29c and 29d are opened to stop the relay drive circuit 8 and the high frequency generator 6. When the relay drive circuit 8 is stopped, the high frequency coaxial relay 4 is switched, the common contact 4a and the normally closed contact 4c are connected, and the circuit of the probe body 3 and the analyzer 7 is formed. This allows the analyzer 7 to measure the electrical characteristics of the living tissue 26 after cauterization.

 Other functions are similar to those of the first embodiment.

In this embodiment, since the switching of the high frequency coaxial relay 4 and the generation of the high frequency signal in the high frequency generator 6 can be controlled simultaneously by stepping on the foot switch 29,
Compared to the first embodiment, the operability can be improved without manually operating the relay drive circuit 8.

 Other effects are similar to those of the first embodiment.

FIG. 5 relates to the third embodiment of the present invention and is an explanatory view of the main part of the high frequency ablation device.

In this embodiment, the analyzer 7 directly controls the high-frequency coaxial relay 4, 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. The analyzer 7 is also connected to a high frequency generator 6 and a signal line 27 for transmitting a control signal for permitting the generation of a high frequency signal, as well as a signal 32 for outputting a control signal indicating the end of cauterization.

 Other configurations are similar to those of the first embodiment.

In this embodiment, when it is determined that the electrodes 11 and 14 are correctly inserted or contacted with the living tissue 26, control is performed to permit the high frequency generator 6 to generate a high frequency signal from the analyzer 7 via the signal line 27. The signal is output. Simultaneously with this control 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 open contact 4b are connected. After stepping on the foot switch 9 and cauterizing the living tissue 26, when stepping on the foot switch 9 is stopped,
A control signal representing the end of cauterization is output from the high frequency generator 6 to the analyzer 7 via the signal line 32, and the analyzer 7 stops the output of 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 cauterization can be measured.

 Other functions are similar to those of the first embodiment.

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

 Other effects are similar to those of the first embodiment.

6 and 7 relate to a fourth embodiment of the present invention, FIG. 6 is an explanatory view of a high frequency coaxial relay, and FIG. 7 is an explanatory view of a tip portion of a probe main 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 thereof. The outer periphery of the first inner electrode 36 is the first insulating layer.
The first inner electrode 36 is covered with 37, and the first inner electrode 36 projects from the tip end surface of the first insulating layer 37. This protrusion forms a spherical electrode 38. This first
A second inner electrode 39 is provided on the outer periphery of the insulating layer 37, and the tip end surface of the second inner electrode 39 is the first insulating layer.
It is designed to match the tip surface of 37. The outer periphery of the second inner electrode 39 is covered with the second insulating layer 41 such that the outer peripheral surface of the tip portion is exposed. The outer periphery of the second insulating layer 41 is covered with the outer electrode 42, and the tip end surface of the outer electrode 42 coincides with the tip end surface of the second insulating layer 41. Further, the periphery of the outer electrode 42 is covered with an insulating coating 43 so that the outer peripheral surface of the tip portion is exposed.

The probe body 34 may be configured as shown in FIG. 7 (b).

In FIG. 7B, the first inner electrode 36 is inserted through the center of the probe main body 34 having the coaxial structure. The outer periphery of the first inner electrode 36 is covered with a first insulating layer 37, and the first inner electrode 36 projects from the tip surface of the first insulating layer 37. This protrusion forms the needle electrode 44. The outer circumference of the first insulating layer 37 is the second
Inner electrode 39 of the second inner electrode 39
The outer periphery of is covered with the second insulating layer 41. Furthermore, the outer periphery of the second insulating layer 41 is covered with the outer electrode 42, and each of the outer electrode 42, the second insulating layer 41, the second inner electrode 39, and the first insulating layer 37 is covered. The tip surfaces are designed to match. 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 connected to a contact 46a forming a normally open switch 46 of the high frequency coaxial relay 45, and the second inner electrode 39 is connected to a contact 47a forming a normally closed switch 47. The contact 46b of the normally open switch 46 is connected to the high frequency generator 6 by the coaxial cable 19 described in the first embodiment, and the contact 47b of the normally closed switch 47 is similarly connected to the analyzer 7 by the coaxial cable 21. Has been done.

The outer electrode 42 is connected to the external conductors of the coaxial cables 19 and 21 via a high frequency coaxial relay 45.

 Other configurations are similar to those of the first embodiment.

In the above embodiment, the probe body of FIG.
When 34 is used, the biological tissue 26 is contacted with the spherical electrode 38, the second inner electrode 39, and the outer electrode. Further, when the probe main body 34 shown in FIG.
The needle electrode 44 is inserted into the second inner electrode 39 and the outer electrode 42.
And are brought into contact with the biological tissue 26. After that, 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 is closed and the normally closed switch 47 is opened. As a result, the high frequency signal generated by the high frequency generator 6 is transmitted to the first inner electrode 36.
Between the outer electrode 42 and the outer electrode 42 to cauterize between the electrodes 36, 42.

When the relay drive signal is stopped after cauterization, the normally open switch 46 opens and the normally closed switch 47 closes. As a result, a circuit including the second inner electrode 39 and the analyzer 7 is formed, and the electrical characteristics of the ablation site are measured.

 Other functions are similar to those of the first embodiment.

In this embodiment, the ablation includes a first inner electrode 36 and an outer electrode 42,
Since the electrodes are separated like the second inner electrode 39 and the outer electrode 42 for the measurement of the electrical characteristics, even when the biological tissue 26 is seized on the first inner electrode 36 which is the ablation electrode,
The electrical characteristics can be measured accurately.

 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 the electrical characteristics of the living tissue are considered. ,
The state of the organization can be known in more detail.

[Brief description of drawings]

1 to 3 relate to a first embodiment of the present invention.
FIG. 2 is an explanatory view of the overall configuration of the high-frequency ablation device, FIG. 2 is a perspective view illustrating the shape of the tip of the probe main body, FIG. 3 is an illustration of the usage state of the tip of the probe main body, and FIG. FIG. 5 is an explanatory view of the overall configuration of an induction cauterization apparatus according to the second embodiment, FIG. 5 is an explanatory view of the main parts of the induction cauterization apparatus according to the third embodiment of the present invention, and FIGS. FIG. 6 is an explanatory view of a high-frequency simultaneous relay according to a fourth embodiment of the invention.
FIG. 7 is an illustration 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

Claims (1)

(57) [Claims] 1. A high frequency ablation device having an ablation probe for cauterizing an affected area, a high frequency generating means for outputting a high frequency signal to the ablation probe, and an electrical characteristic measuring means for measuring an electrical characteristic of the affected area cauterized by the probe. In the above, switching means for forming a circuit between the electric characteristic measuring means and the probe is provided at the same time when the circuit formed by the high frequency generating means and the probe is cut off, and the electric characteristic measuring means and the 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 cauterization.