JPS62167557A - Cauterizing probe apparatus - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Application Field] The present invention relates to an ablation probe device used to cauterize to stop bleeding or sterilize.

[Prior art] In recent years, by inserting an elongated insertion section into a body cavity,
BACKGROUND OF THE INVENTION Endoscopes that can perform diagnostic or therapeutic procedures within body cavities without requiring incisions from the body surface are widely used.゛This endoscope generally has a hollow channel in the observation means through which various treatment instruments are inserted, and the operator can visually observe the symptoms with the treatment instrument inserted through the channel. Various therapeutic procedures can be performed under observation.

By the way, there are laser treatment devices that irradiate laser beams to coagulate blood as a means to stop the bleeding of wounds such as those removed from tumors or ulcers in body cavities, but at present, the laser beam irradiation requires skill. However, there are also problems in that the cost is high.

For this reason, a device has been proposed that uses an ablation probe that can be inserted through the channel of an endoscope and energizes a heating coil installed at the tip of the ablation probe to coagulate the pressed hemostatic area. .

However, with this heating coil type device, the responsiveness of the rise in temperature when blood coagulates and the fall of temperature after it stops is low, so it takes a long time to avoid coagulation.
Alternatively, there is a problem in that during the time until the solidification occurs, the surrounding tissue other than the target area (wound) may be necrotized due to heat conduction to the surrounding tissue. .

Therefore, in Japanese Unexamined Patent Application Publication No. 58-69556P3, there is an article titled ``Chi1'' of endoscopes. An ablation probe 1 that can be inserted into a tunnel is an ablation probe capable of generating heat at high speed using a heating element with good heating and cooling responsiveness. In this conventional example, a semiconductor chip as a heat generating element is fixed in the tip of a sheath with a 11' solder, and a heating current is applied to the semiconductor chip to generate heat. The heat is transmitted through the tip of the tip to which the semiconductor chip is attached to the affected area against which the tip of the tip is pressed.

[Problems to be Solved by the Invention 4] However, in the conventional example described in -, the semiconductor chip as a heat generating element is fixed to the tip gap member by soldering, which does not involve heat conduction polishing. The function of quickly transmitting the heat of the chip to the tip cap member side is insufficient, and there is a tendency for heat to be accumulated in the semiconductor chip. Therefore, a semiconductor chip with a small heat capacity is heated to an excessively high temperature, and the characteristics of the semiconductor chip may change or deteriorate, or even be destroyed.

The present invention has been made in view of the above-mentioned points, and provides an ablation probe device that can improve heat conduction between the heating element and the tip cap member and prevent the heating element from deteriorating or being destroyed. The porpose is to do.

[Means and effects for solving the problem] The present invention interposes a highly thermally conductive resin between the heating element and the tip cap member, and allows the heat of the heating element to pass through the resin.
By forming a heat transfer path from top to bottom, heat conduction is improved and property deterioration and destruction of the heating element can be prevented.

[Example 1 Hereinafter, the present invention will be specifically explained with reference to the drawings.

FIGS. 1 to 5 relate to the first embodiment of the present invention.
The figure shows the distal end side of the cautery probe device of the first embodiment, FIG. 2 shows the appearance of the entire cautery and hemostasis device, FIG. The proximal connector section is shown, and FIG. 5 shows the electrical connector section.

The cautery hemostasis device 1 equipped with the first embodiment includes a power supply box 3 with an operation panel 2 on the front surface, and a power supply box 3 with an operation panel 2 on the front.
The ablation device 6 of the first embodiment is detachably connected to the electrical connector 4 and the water supply connector 5, and the power supply box 3 is detachably connected to the connector 8 provided on the cable 7. The cleaning water tank 1 is removably attached to the side of the power supply box 3.
0, a power supply section (not shown) housed in the power supply box 3, and a water supply section.

The above-mentioned cauterizing probe device 6 includes an elongated and flexible sheath 11, an ablating probe 12 connected to the tip of the sheath 11, and 1! of the sheath 11. - Consisting of the electrical connector 4 and water supply connector 5 provided on the base side, the sheath 11 and the cautery probe 12 at its tip can be inserted into a treatment tool channel of an endoscope (not shown), and the cautery is carried out through this channel X7. A probe 12 is adapted to be introduced into the body cavity.

A coaxial cable 13 is inserted into the sheath 11 in the axial direction to energize a heating element 14 formed of a semiconductor chip installed inside the ablation probe 12 at the tip. Coaxial cable 13 in 11
In the outer coaxial direction, there is a water supply channel 16 for pumping cleaning water to a plurality of nozzles 15 formed on the outer periphery of the ablation probe 12.
is formed. Then, the electric connector 4 and the water supply connector 5 on the base side of this ablation probe device 6 are connected to the power supply box 3, and the foot switch 9 also connects the connector 8 of the cable 7 to the power supply box 3. Turn on the main switch 3a and select and set the heating amount and washing water amount setting buttons 2a and 2b provided on the operation panel 2, and then turn on the foot switch 9.
By pressing the cleaning water supply side switch 9a,
The water pump installed in the power supply box 3 is activated to direct the cleaning water in the cleaning water tank 10 through the water supply channel 16 in the sheath 11 to the nozzle 15 on the outer periphery of the cautery probe 12 at the tip and towards the affected area in the body cavity. By supplying water to wash away blood, etc. from the affected area, or by pressing the heating switch 9b side of the foot switch 9, electricity is applied to the heating element 14 in the ablation probe 12 at the tip via the coaxial cable 13 in the sheath 11 to maintain a predetermined temperature. It can be heated to.

The power supply box 3 has a configuration in which an electric system equipped with a cauterization power source and a water supply system for supplying cleaning water are installed in the same box, for example, in the upper and lower parts of the box 3, or The left and right sides are separated by an isolation chassis, and the electrical system and water supply system are separated to ensure safety, and can be completed by separating and assembling each prefecture and then assembling both. Even the manufacturing process is easy to perform.

The details of the ablation probe 12 on the distal end side of the ablation probe device 6 are constructed as shown in FIGS. 1 and 3.

That is, a main body 18 is connected and fixed to the distal end of an elongated flexible sheath 11, for example, a Teflon sheath, and the through hole 17 in the solid axial direction is connected to the main body 18, and the distal end is pressed against the wound on the outer periphery of the main body 18. heat transfer surface 19 that cauterizes and solidifies the wound.
A hollow cylindrical cap (member) 19 having a hemispherical surface (arc surface) and having good heat transfer is attached and fixed as a. A concave portion 17a connected to the through hole 17 is formed on the distal end side of the main body 18, in which the distal end of the coaxial cable 13 inserted from the sheath 11 side is located, and the inner wall of the cap 19 facing the hemispherical heat transfer surface 19a is located. heating element 1
A semiconductor chip such as a Zener diode as 4 is in close contact with one side thereof, and a large thermally conductive resin (for example, a thermally conductive epoxy resin) 20, which is the main part of the first embodiment, is coated around its periphery. It is interposed and fixed.

A power transmission coil 21 is interposed on the outer periphery of the inner conductor at the tip of the coaxial cable 13, and the coil 21 electrically connects the other surface of the heating element 14 and the inner conductor. Further, the heating element 14 has one end connected to the through hole 17 of the main body 18 via an insulating tube 22, for example, a glass duplex.
Cap 19 with coil spring 23 in contact with the inner wall
biased toward the side. This is because when the heat generating element 14 is heated, the temperature reaches approximately 250°C, so even if the resin 20 bonding the heat generating element 14 thermally expands or the adhesive fixing force changes, the heat generating element 14 can be heated. The heat generating element 1 is securely held in a crimped state on the cap 19 side as the tip member.
4 can be quickly transferred to the cap 19 side. Also, in this way, the heating element 14 is pressed against the cap 19 by the coil spring 23, one surface (for example, the anode surface) of the heating element 14 is pressed against the cap 19, and this surface is pressed through the cap 19 and the main body 18. A power transmission coil 21 that is constantly electrically connected to the outer conductor of the coaxial cable 13 and presses the other surface (cathode surface).
This surface is electrically connected to the inner conductor of the coaxial cable 13 via.

Cap 19 having a hemispherical heat transfer surface 19a at the tip
The outer periphery of the cap 19 is coated with a non-adhesive coating 24, such as a Teflon coating (Silpers 1 Hoen-Ting), to prevent the cap 19 from sticking to tissue. This includes cap 19, ablation probe 1
2 is heated by the heat generated by the internally installed heating element 14 to cauterize and coagulate the bleeding part of the wound to stop the bleeding, and because it comes into direct contact with the tissue, there is no risk of sticking to the tissue and the resulting This prevents rebleeding. In addition, a non-adhesive coating 24 on the outer peripheral surface of the ablation probe 12, a main body 1
Since the cap 19 is formed separately from the heat generating element 14 and the main body 18, the cap 19 is attached to the heating element 14 and the main body 18 after a non-adhesive coating 2/l is applied to the cap 19. Therefore, there is no risk of destroying or deteriorating the heating element 14, such as a Zener diode.

A plurality of nozzles 15 on the outer periphery of the ablation probe 12 are formed in a straight portion of the main body 18 and one gap. This nozzle 15... is formed in the shape of a groove in the direction of the outer circumferential axis, and the rear *v1: side communicates linearly with the water supply channel 16 formed inside the sheath 11, while the output side directly communicates with It rises in a gentle arc shape from the top, and the output angle is O.
is formed at 15 to 16 degrees. Also, nozzle output O
The distance of W to the tip of the probe 12 is set to be greater than or equal to the radius of curvature of the hemispherical heat transfer surface 19a of the probe 12.

By forming the nozzles 15 in this way, the cleaning water emitted from the nozzles 15 flows in a -C straight line along the outer circumferential axis direction of the ablation probe 12, and forwards the probe 12. Water can be conveyed in a straight line, which makes it easy to target the area to be cleaned, and also prevents the conveyed cleaning water from going around the '-1' spherical heat transfer surface 19a. Note that a heat radiation groove 188 for cooling is formed in the main body 18.

The electrical connector 4 and water supply connector 5 on the base side of the ablation probe device 6 are constructed as shown in FIGS. 4 and 5. That is, a water supply tube connecting member 25 is connected to the rear end of the sheath 11, and an electrical connection member 25 is connected to the rear end of the connecting member 25.
The connector 4 is connected, and a water supply duplex 26 is connected to the side □ of the connection member 25, and the electrical system and waterway system are separated at this part, and the coaxial cable 1 is inserted into the sheath 11, respectively.
3 and the water supply channel 16 are inserted. The main body 27 of the connecting member 25 is connected to the sheath 11 with the through hole 28 to the right in the direction of the central axis.
The i11+ cable 13 extending from the side is passed through and extends in the direction of the electrical connector 4 at the rear.

Further, this main body 27 has a connecting cap 29 having a tapered outer periphery protruding forward, and the rear end of the sheath 11 is fitted into this cap 29. A screw thread is formed on the rear outer periphery of the cap 29 of the main body 7, and a retaining ring 30 having a tapered depression restraining ring 30a on the inner periphery is screwed into the male thread portion to fit into the cap 29. The rear end of the sheath 11 is pressed and fixed by a taper depression ring 30a. Also, retaining ring 30
A tapered presser ring 30a and a locking ring 3 installed on the inner circumference of the
There is an annular fitting groove 30b between the inner circumferential surface of
The rear end of a fold-preventing duplex 31, which is externally mounted on the base side of the sheath 11, is fitted and fixed into the inside of the sheath 11. A recess 32 connected to the through hole 28 is formed on the rear end side of the connecting portion main body 27, and a female thread is formed on the inner periphery of the recess 32, and an electrical connector 4 having a male thread at the tip is screwed into the recess 32 for connection. Roughly speaking, this connection body 27 has a two-stage recess 33 on the side that communicates with the through hole 28, and a female thread is formed inside the small diameter recess 33a of this recess 33, so that the water supply duplex 26 has a male thread. The joints 1 to 34 on the right side are screwed together, and the flange 34 protruding from the middle of the outer periphery of the joints 1 to 34 is screwed together.
An O-ring 35 is interposed between a and the bottom surface of the outer large-diameter recess 33b to ensure watertightness. This sea urchin water supply Chicove 26
is to join 1 through 34 to connection body 270 through hole 2
The water supply channel 16 is connected between the outer periphery of the coaxial cable 13 inserted into the through hole 28 and the inner periphery of the through hole 28.
a, and communicates with the water supply channel 16 of the sheath 11 which is fitted and connected to the connecting portion main body 27. Further, a female screw is formed on the inner periphery of the deep part of the recess 32 of the connection part main body 27, and a presser screw 36 is screwed into the coaxial cable through hole 36a. An O-ring 37 is interposed between the through-hole 28 and the outer periphery of the coaxial cable 13, and the O-ring 37 is pressed with a retaining screw 36 to ensure watertightness between the water supply channel 16a side and the rear electrical connector 4 side. , the electrical system and waterway system are separated.

The joints 1 to 3/I of the water supply cove 26 are connected and fixed by tapered screws 37. The connector 5 provided on the rear end side of the water supply duplex 26 has a socket 38 with a locking mechanism on the right side, and can be detachably connected to a water supply plug 39 of the power supply box 3.

On the other hand, a coaxial cable 13 is extended inside the electrical connector 4 connected to the rear end of the connection body 27, and this cable 13 is connected to a contact via a variable resistor 41 in addition to a fixed resistor 40. ing. The reason why the variable resistor 41 is inserted in this way is due to variations in the Zener voltage of the Zener diode serving as the heating element 14, or due to variations in the Zener voltage of the cable 13.
This is because it is necessary to adjust so that a constant current flows regardless of the variation in the resistance value of the i'iT variable resistor 41, which facilitates the adjustment and improves workability. It is.

According to the first embodiment configured in this way, the heating element 1
4 is in close contact with the heat-conducting knob 19 without using an intervening member, and its periphery is covered with a heat-conducting resin 20. 14 is heated, the heat is quickly transferred to one side of the kill tube. Therefore, it is possible to realize an ablation probe device with good thermal response that hardly causes necrosis of the surrounding tissue, and it is also possible to prevent the heat generating element 14 from becoming excessively high temperature due to heat accumulation, thereby preventing characteristic deterioration or destruction of the heat generating element 14. It can be prevented. Therefore, the safety and reliability of the device required as a medical device can be improved.

FIG. 6 shows the main part of a second embodiment of the present invention.

In this second embodiment, one surface of the heating element 14 is in close contact with the inner surface of the cap 19, and the other surface is a metal plate 5 with good conductivity (for example, an aluminum 1Kum plate, a silver plate, a copper plate).
A heating element 14 and a metal plate 51 are fixed to a cap 19 by applying a resin 20 having good thermal conductivity to the peripheral edge of the side part of the cap 19 in close contact with one surface of the cap 19.

Thus, this metal plate 51 is pressed toward the cap 19 by the coil spring 23 as in the first embodiment, and
It is also pressed by the power transmission coil 21 to establish electrical connection.

In this second embodiment, the heat-generating cord 14 is sandwiched between members having good thermal conductivity, and the outer periphery of these sides is also interposed with a resin 2o having good heat conductivity, so that no heat is generated. The heat of the element 14 can be quickly transferred to the chitotube 19 side.

FIG. 7 shows the main part of a third embodiment of the present invention.

In this third embodiment, each side of the heating element 14 in the second embodiment is bonded with an electrical adhesive 61 such as solder or silver solder.
Each surface is fixed to a cap 19 and a metal plate 51, respectively. The rest is the same as the second embodiment.

In this case as well, compared to the conventional example, heat is conducted on both sides, and the sides are surrounded by resin 20 with good thermal conductivity.
Since it is covered with a lining, heat can be conducted through this part. Therefore, thermal responsiveness can be improved and deterioration, destruction, etc. of the heating element can be prevented.

In the third embodiment, only one surface of the heating element 14 may be bonded with the adhesive 61.

Note that a thermistor with positive temperature characteristics may be used as the heating element.

The present invention is not limited to hemostasis treatment, but can also be applied to treatments such as sterilization with heat by pressing against an affected area or the like.

[Effects of the Invention] As described above, according to the present invention, the heating element is made of a resin with good thermal conductivity to conduct heat between it and the tip part, so that the heat of the heating element can be quickly transferred. can be transmitted to the tip member side. Therefore, thermal responsiveness can be improved, deterioration and destruction of the heating element can be prevented, and the safety and reliability of the device can be improved.

[Brief explanation of drawings]

1 to 5 relate to the first embodiment of the device of the present invention,
Figure 1 is a sectional view showing the tip side of the ablation probe device, Figure 2
The figure is a perspective view showing the overall configuration of the cautery hemostasis device, Figure 3 is a sectional view taken along the line 8-A in Figure 1, Figure 4 is a partially cutaway front view showing the electrical and water supply connectors at the base of the sheath, and Figure 5. 6 is a sectional view of the main part of the second embodiment of the present invention, and FIG. 7 is a sectional view of the main part of the third embodiment of the present invention.

Claims (1)

[Claims] A heating element formed of a semiconductor is housed in the tip of the elongated sheath, and the heat generated by energizing the heating element is transmitted to the tip cap member that covers the heating element, and the affected area is pressed against the tip cap member. In an ablation probe device for hemostasis, etc., a highly thermally conductive resin is interposed between the heating element and the tip cap member, and the heat of the heating element is transmitted to the tip cap member side via the resin. An ablation probe device characterized by forming.