JPH02161938A - Burning bleeding stopping device - Google Patents

Abstract

PURPOSE:To afford a water supplying function sufficient for washing an organism, to control a temperature with high accuracy, and to minimize heat capacity by controlling the temperature of a platinum resistance element having a characteristic to change according to the temperature through a temperature detecting part. CONSTITUTION:In a sheath 21, a coaxial cable 31 is inserted in an axial directional center and supplies power to a thin metallic film resistor 32 to compose a heat generating element provided in a burning probe 22 at the tip of the sheath 21. Noises 33, 33, and 33 formed for a thin and long shaped body 57 of the thin metallic film resistor 32 provided for the inside of the burning probe 22 at the tip of the flexible sheath 21 and a cap 53 are formed into a groove shape in the axial direction of an outer circumference, and their rear edge sides are communicated with a water supplying path in the sheath 21. A non- adhesive coating material 60 is applied to the cap 53, the material 60 prevents the sticking of the cap 53 to a tissue after bleeding stopping processing and rebleeding caused by the sticking. Thus, a heating body having a constant resistance value with extremely small dispersion can be realized by composing the heat generating element of the thin metallic film resistor 32.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to a cautery hemostasis device in which a heating element within a probe is composed of a platinum resistance element.

[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. In addition to the observation means, this endoscope is generally equipped with a hollow channel through which various treatment instruments are inserted. Various therapeutic treatments can be performed under visual observation.

By the way, as a means for hemostasis of a wound such as an excised tumor or an ulcer in a body cavity, there is a method constructed using a cautery hemostasis probe that can be inserted through the channel of an endoscope.

For example, instead of using a platinum wire resistor as a heating (heating) element as shown in Japanese Utility Model Publication No. 61-2571, an ablation electrode using a thin film of a semiconductor such as tantalum nitride has been devised.

Also, Japanese Patent Application Publication No. 58-69556, Japanese Patent Application No. 59-251
There is a device, such as No. 234, which uses a semiconductor element (Zener diode) as a heat generating element and performs temperature control using voltage changes across both ends of the heat generating element.

A heating element using the semiconductor described above has a function of sending water into a body cavity for the purpose of cleaning a bleeding site.

Further, in order to control the temperature of the heating element, WO3010
As shown in Japanese Patent Publication No. 2108, a device equipped with a heating element and a temperature sensor is known, and as shown in Japanese Patent Publication No. 452,232, a device equipped with a heating element and a thermal lightning pair is known.

[Problems that the invention seeks to solve
When the semiconductor element shown in No. 4 and JP-A-58-69556 is used as a heating element, S
Due to the temperature resistance of the materials such as i, internal impedance and changes in voltage generated at both ends vary from element to element.
It was difficult to accurately control the temperature.

On the other hand, in order to perform accurate temperature control, WO301021
As shown in No. 08 and Japanese Patent Publication No. 45-2232, there are some devices that have a built-in temperature sensor etc. in the heat generating part, but heating and cooling fJj to prevent necrosis of non-bleeding surrounding tissue due to increased heat capacity. Thermal responsiveness decreases.

In addition, the number of signal lines connecting the temperature sensor and the control circuit increases, and in particular, in the configuration of Japanese Patent Application No. 59-251234, which passes water through the channel of the endoscope and sends water into the living body, the effective cross-sectional area of the probe for water delivery increases. As a result, sufficient tissue cleaning cannot be performed.

The present invention has been made in view of the above-mentioned points, and aims to provide a cautery and hemostasis device that has a water supply function sufficient to clean a living body, is capable of highly accurate temperature control, and has a small heat capacity. .

[Means and effects for solving and overcoming the problems] The present invention, as shown in the conceptual diagram shown in FIG. This platinum resistance element 1
The temperature is controlled by a control section 4 via a temperature detection section 3.

Electric power is supplied from the power source section 2 under the control of the control section 4 to the platinum resistor element 1, and heat is generated. Further, this platinum resistance element 1 is used as a temperature sensor, and its output is detected by a temperature detection section 3, and a control section 4 controls the electric power from the power supply section 2 so as to maintain a predetermined temperature. In this invention, since the platinum resistance element 1 is used both as a heat generating cord and a temperature sensor, it can be miniaturized, and since the platinum resistance element 1 has stable characteristics with little variation, it is possible to control the temperature with high precision. becomes possible.

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

2 to 11 relate to the first embodiment of the present invention, FIG. 2 is a perspective view of the first embodiment, FIG. 3 is a sectional view without showing the distal end side of the ablation probe device, and FIG. 4 is a sectional view of the ablation probe device. 3 shows a cross-sectional view taken along the line A-A, and FIG. 5 shows a metal thin film resistor; FIG. 6 and 7 show the pump, FIG. 6(b) is a side view, FIG. 8(C) is a bottom view, FIG. FIG. 9 is a diagram showing the principle of temperature measurement using the four-wire system and the three-wire system, FIG. 10 is a diagram showing the principle of temperature measurement using the two-wire system, and FIG. 11 is a characteristic diagram showing the state of heating current.

As shown in FIG. 2, the cautery hemostasis device 11 of the first embodiment includes:
A main body part 13 having an operation panel 12 on the front surface, an ablation probe device 16 detachably connected to this main body part 13 through an electrical connector 14 and a water supply connector 15, and a cable 17 attached to the main body part 13. It is comprised of a foot switch 19 that is detachably attached to a connector 18, and a wash water tank 20 that is detachably attached to the side surface of the main body 13.

The foot switch 19 is provided with a water supply switch 19a and a heating switch 19b.

The ablation probe device 16 includes an elongated and flexible sheath 21, an ablation probe 22 connected to the tip of the sheath 21, and the electrical connector 14 and water supply connector 15 provided on the base side of the sheath 21. consisting of sheath 2
1 and the ablation probe 22 at its tip can be inserted into a channel of a treatment tool of an endoscope (not shown), and the ablation probe 22 can be inserted into the body cavity through this channel.

As shown in FIG. 3, a coaxial cable 31 is inserted into the sheath 21 in the axial direction, and the ablation probe 2 at the tip is inserted into the sheath 21.
A metal thin film resistor 32 constituting a heating element installed inside the sheath 21 is energized, and a plurality of nozzles 33 formed on the outer periphery of the ablation probe 22 are connected to the coaxial cable 31 in the sheath 21 in the axial direction. 33. ... (see Fig. 4) is formed with a water supply channel 34 for pressure-feeding wash water.

Said nozzle 33.33. Water is sent in a jet shape by...

The metal thin film resistor 32 constituting the heating element has a conductive thin film 36 on both sides of a thin film base material 35 as shown in FIG.
．． 36 is used.

Incidentally, a pump 37 as shown in FIGS. 6 and 7 is housed in the main body 13.

In this pump 37, a piston 41 reciprocates through an eccentric shaft 39 by the rotation of a motor 38, and works in cooperation with ball valves 42a and 42b constituting a check valve to open a piston chamber 43.
The water inside is pumped in a pulsating manner.

The piston 41 has a cup 4 which expands by hydraulic pressure when the volume of the piston chamber 43 decreases to improve sealing performance.
4 is provided.

In addition to this cup 44, modified shapes as shown in FIGS. 8(a) to 8(g) may be used. Here, FIG. 8(a) shows a cup 44a composed of a cylindrical rigid part and an outer thin part, and FIG. 8(b) shows a cup 44a with the rigid part in (a) screwed into the
The cup 44b is made easy to N. Figure (C) is a cup 44c with a tapered thin part, Figure (d) is a cup 44d with a chamfered rigid part, and Figure (0) is a cup 44c with a tapered part. This is a cup 44e with a rounded part. In addition, the same figure (
A cup 44f cut out in an arc shape as shown in ) has a poor ability to receive water pressure, so its ability to expand is small and its sealing performance is poor.

As shown in FIG. 3, one surface of a metal thin film resistor 32 provided within the cautery probe 22 at the tip of the elongated flexible sheath 21 is electrically connected to the core wire 51 of the coaxial cable 31. They are connected by pressure contact via the power transmission coil 52. The other part of the metal thin film resistor 32 is provided at the tip and is electrically and thermally contacted via solder 54 to a concave portion of a cap 53 provided with a hemispherical surface.
The outer line 55 is designed to allow current to flow through a cylindrical portion 56 on the rear end side of the cap 53 and a tip main body 57 to which this cylindrical portion 56 is externally fitted and fixed. In addition, l1jl li'll
The cable 31 is inserted through the through hole 57a of the main body 57, and the sheath 21 is externally fitted and fixed to the rear end of the main body 57.

The front end side of the through hole 57a is enlarged in diameter to house a coil spring 58, and the coil spring 58 presses an insulating tube (for example, a glass duplex) 59 that is in contact with the metal thin film resistor 32, thereby removing the metal thin film resistor. 3
2 is biased so as to come into pressure contact with the solder 54.

Nozzle 33 formed on the main body 57 and cap 53
．． 33. 33 is formed in a spiral shape in the axial direction of the outer periphery, and the rear end side communicates with the water supply channel within the sheath 21. Each nozzle 3
The output angle θ of No. 3 is, for example, 15 degrees to 16 degrees.

The cap 53 is coated with a non-adhesive coating 60 to prevent it from sticking to tissue after hemostatic treatment and from causing rebleeding.

When the ablation probe 22 using the metal thin film resistor 32 is used in combination with an endoscope having a large diameter channel, the dimension tl + approx.
Heating can be carried out while measuring temperature using the 4-conductor system shown in ) or the 713-fathom system shown in Figure (b).

In FIG. 9(a), a constant current source 61 connects two conductive wires ρ1.
A constant current is supplied to the metal film resistor 32 as a heating element through ρ2 to heat it. On the other hand, this metal thin film resistor 32, which also serves as a γ measurement resistor, has two SINs 3, '
J is connected to the temperature detection section 62 through the cow, and is connected to the galvanometer G1 through the differential amplifier A. : Guided.

Note that RT is the resistance of the metal thin film resistor 32.

Further, in FIG. 9(b), by setting the resistances of the three conductive wires drawn out from the metal thin film resistor 32 to equal values R, it is possible to offset the misconnection caused by these temperature changes. Note that 0 is a reference voltage, and Rv is a balancing adjustment resistor.

On the other hand, when performing treatment in combination with an endoscope with a narrow channel, a two-conductor type with fewer conductors is better. This 2
The conductor type will be explained with reference to FIG. 10.

As shown in FIG. 10(a), a current I is applied to the metal thin film resistor 32 by a known constant current source 61.

In actual treatment equipment, the conductor resistance R depends on the length of the probe.
L exists, the heat actually generated by the resistance Rv of the metal thin film resistor 32 decreases, and the temperature detectability of the metal thin film resistor 32 decreases. Therefore, it is desirable to use a +u/pt clad wire with low resistance as the conductor of the coaxial cable 31.

Since the conductor resistance RL can be almost ignored by using the Nl/Pt clad wire, the basic circuit of FIG. 10(a) can be considered to be the same as that of FIG. 10(b).

Then, the mino j consumed at the tip is as follows: P=I RT (W) If this flow is continued for 1 second, the heat becomes J = P -1 (Joule). Further, the humidity increase Δt is as follows: Δt=r'/S (S is self-heating m). When platinum is used as the metal 7RfJ resistor 32, the
The resistance value at t is Rt = R(1+3.90802・io't0.5&
0195・1O−6t2). Here, R is the rated resistance value. At this time, resistance R
Since the voltage V and current I (V) - Rt across t can be measured, the temperature t at the tip of the probe can be determined.

The temperature can be controlled up and down by increasing or decreasing the electric power P, that is, by increasing or decreasing the current I.In order to improve the initial heating (improve the temperature rise), a large current may be passed at the beginning of heating as shown in Figure 11. can.

Incidentally, the main body 57 is provided with heat dissipation grooves 63 for cooling.

According to this first embodiment, since the heat generating element is composed of the metal 7i9 film resistor 32, there is no large variation in the resistance value (measurable), unlike when using a semiconductor element. This can be seen from the fact that it is used as a temperature resistor.

), it is possible to realize a heating element having a constant resistance value with extremely little variation.

Moreover, it is easy to form it into a desired shape.

Further, since the metal thin film resistor 32 is also used as a temperature sensor as a temperature measuring resistor, it can be made smaller than when a temperature sensor is provided separately.

In addition, the temperature coefficient in this case is extremely stable and has sufficient resistance to high temperatures, making it possible to perform highly accurate temperature detection. Temperature control can be performed. Furthermore, it is possible to realize a highly reliable cautery hemostasis device that is less susceptible to deterioration over long-term use.

FIG. 12 shows the main parts of a second embodiment of the present invention.

In the first embodiment, one side of the metal thin film resistor 32 (the surface on the ground side) is thermally and electrically connected to the cap 53 via the solder 54, but in the second embodiment, Ki1 through the power transmission coil 71? The knob 53 and the metal thin film resistor 32 are electrically connected. The other surface of this metal thin film resistor 32 is connected to the power transmitting coil 5 as in the first embodiment.
2 is electrically connected.

Further, the area around the metal thin film resistor 32 is filled with a heat compound 72 (in this case, the key 53).
The metal thin film resistor 32
The fever is immediately conveyed to Cap 53. In this figure, the entire periphery of the metal thin film resistor 32 may be covered with the heat compound 72 without providing the insulating tube 57.

The rest of the structure is the same as that of the first embodiment, and has almost the same effects.

FIG. 13 shows the main parts of a third embodiment of the present invention.

In this third embodiment, a water supply channel 82 is provided on the central axis of the ablation probe device 81, and the ablation probe 83 on the 9iI side is provided.
The water is emitted to the target area through a water nozzle 84 that communicates with the water supply channel 82, thereby ensuring reliable cleaning.

In this case, the coaxial cable 31 in the first embodiment is a hollow coaxial cable, and the metal thin film resistor 3
2 also has a hollow part. (Note that the metal thin film resistor 32 can have various shapes).

According to this embodiment, since water is fed coaxially, the target area can be reliably washed.

FIG. 14 shows the main parts of a fourth embodiment of the present invention.

In this embodiment, the metal thin film resistor 32 is connected to the DC power supply section 91.
It is also connected to a high frequency power supply section 92.

Therefore, the high frequency (for example, 40
High frequency heating is performed by supplying a current of about 0 to 450 KHz. On the other hand, the thirst level is measured by flowing a minute current from the DC power supply section 91.

This embodiment allows for an inherently safe ablation because the current loop is created only within the probe.

Also, because the tip is coated, it eliminates the sticking problem that occurs with bipolar systems.

By the way, the metal thin film resistor 3 used in each example of the present invention
2 can be made into various shapes, so it is not limited to the one used for the probe as described above, but can also be used for the treatment instrument 9 as shown in FIG.
It is also possible to supply power via a coaxial cable 98 that is attached to, for example, the cup 96, 96 on the distal end side of the device 5 and wound around the outer circumference of the opening/closing wire 97.

FIG. 16 shows the structure of the distal end side of the ablation probe according to the sixth embodiment of the present invention.

In this embodiment, instead of using the metal thin film resistor 32, a ceramic platinum resistor element (or a ceramic platinum element) 10 is used.
2 is used.

The front end of the sheath 104 through which the coaxial cable 103 is inserted is fixed to the tip body 105.
The proximal end side of the substantially cylindrical ceramic platinum element 102 is inserted into the diameter-enlarged recess at the front end and fixed by adhesive or the like.

The side outer circumferential surface of the ceramic platinum element 102 and the hemispherical top (tip) side outer circumference are coated with a non-mucosal coating member 1065 such as fluororesin.

The ceramic platinum element 102 has two holes in the axial direction of a cylindrical ceramic member 107 (J, for example, a platinum resistance element wire 108 formed into a coil shape is inserted through the holes, and both ends of the platinum resistance element wire 108 are inserted. are electrodes 109a, 10
9b is installation.

The one electrode 109a is, for example, a ceramic member 10
7, and is electrically connected to the core wire 111a of the coaxial cable 103 by brazing or the like. The outer periphery of the electrode 109a and the core wire 111a is covered with an insulating tube 112 such as a glass tube to prevent the outer periphery from short-circuiting with the metal member constituting the tip body 105.

The other electrode 109b protrudes toward the side near i3E, is housed in a notch or hole in the tip body 105, and is electrically connected to the tip body 105 by soldering or the like. The shield wire (external conductor >111t) of the coaxial cable 103 is inserted into a hole or notch in the tip body 105 and electrically connected to the tip body 105 by brazing or the like. In other words, one electrode 109a of the platinum resistance element wire 108 is electrically connected to the core wire 111a of the coaxial cable 103, and the other electrode 109b is electrically connected to the external conducting wire 111b via the metal tip body 105.

Incidentally, each hole of the ceramic member 107 into which the platinum resistance element wire 108 is inserted and the front 3211 portion of the ceramic member 107 are filled with a powder 113.

This embodiment uses an ablation probe 10 that is used at the 6IS position where water supply is not required, such as for hemostasis or ablation in the lungs.
1, and there is no water supply nozzle etc. Therefore, the rear end of this probe 101 does not have a water supply connector, but only an electrical connector (not shown).

The rest of the structure is the same as that of the first embodiment, and its effects are also substantially the same. Furthermore, in this embodiment, the first
Embodiment J: The structure on the tip side of the limb can be simplified and realized at low cost.

FIG. 17 shows the configuration of the distal end side of an ablation probe 121 according to a seventh embodiment of the present invention.

This probe 121 has a structure in which a water supply nozzle 122 is provided in the sixth embodiment.

Ceramic member 107 and tip main body 1 in FIG.
A part of the outer periphery of the nozzle 122 is notched in a tapered shape, and several nozzles 122 are provided (for example, at three locations as shown in FIG. 4) through which the discharged water can be projected in a nearly forward direction.

Each nozzle 122 communicates with a water supply channel 123 outside the coaxial cable 103.

An insulating seal member 124 is provided on the outer periphery of the front end portion of the coaxial cable 103 and the inner periphery of the tip body 105 on the outer periphery.
is filled to prevent the water supply liquid from entering the electrode 109a side.

In this embodiment, a water supply connector (not shown) is provided at the rear of the probe 121 Q7j as well as an electrical connector as shown in FIG.

The rest of the structure is the same as that of the sixth embodiment.

Further, the effects of this embodiment are almost the same as those of the first embodiment. Moreover, it also has the same effects as the sixth embodiment.

FIG. 18 shows a 4'4 structure on the distal end side of an ablation probe 131 according to an eighth embodiment of the present invention.

In this embodiment, a hollow portion 133 for water supply is provided in the ceramic platinum element 132 as shown in FIGS. 18 and 19.
133 is provided in the structure.

Note that FIG. 18 shows a cross section taken along the line CC in FIG. 19. .

The front end of the sheath 135 through which the two-core cable 134 is inserted is
It is fixed to the outer periphery of the rear end of the tip body 136.

The tip main body 136 is made of a non-conductive ceramic member or the like.

The base side of a ceramic platinum cord 132 whose outer surface is coated with a non-adhesive coating member 137 is fitted into the front end of the tip main body 136 and fixed with an adhesive or the like.

The ceramic platinum cord 132 has a cylindrical ceramic member 138 provided with a hollow portion 133° 133 for water supply and a hollow portion 140, 140 through which the platinum resistance element wire 139 is passed, and is folded back at the tip side. Platinum resistance element wire 1
39 is passed through the platinum resistance element F! Attached to both ends of 139 [Platinum electrode 1/11a and 141b are 2-core cape]'
v 134 (7) The ends of the core wires 142a and 142b are electrically connected to each other by pressure bonding, conductive adhesive, or the like.

Each hollow part 133 for water supply has a tip main body 136
The water supply channel 1 inside the sheath 135 passes through the hollow part 143 provided in the
44, and the liquid supplied from the proximal side is communicated with each hollow part 1.
It is designed to be able to eject forward through 33.133.

Note that the hollow part 140.1 through which the platinum resistance element wire 139 is passed
The inside of the ceramic member 138 is filled with a powder 145, and the tip of the ceramic member 138 is also provided with a powder 145 in a hemispherical shape.

The effects of this embodiment are almost the same as those of the seventh embodiment.

FIG. 20 shows the structure of the distal end side of an ablation probe 151 according to a ninth embodiment of the present invention.

This probe 151 has a structure that does not have a water supply function in the eighth embodiment shown in FIG. 18.

In other words, the ceramic member 138 has a hollow portion 133.13.
3 is not provided, and the tip body 136 also has a hollow portion 14.
3 is not provided.

The rest of the structure is the same as that shown in FIG. 18, and the functions and effects other than the water supply function are also the same.

FIG. 22 shows the distal end side of an ablation probe 161 according to a ninth embodiment of the present invention.

In this embodiment, for example, in the embodiment shown in FIG.
Ceramic platinum resistance element 16 is constructed by using straight platinum resistance element wire 162 instead of coiled platinum resistance element wire 108.
3.

Further, the nozzle 164 has a structure that extends linearly to the tip side. Further, the coating member 106 is connected to the nozzle 164.
It is also formed on the bottom and sides.

The rest of the structure is similar to that shown in FIG. 17.

The operation and effects of this embodiment are similar to those shown in FIG. 17. In addition, there is a possibility of increasing adaptability such as reducing inductance.

FIG. 22 shows a treatment instrument 171 according to a tenth embodiment of the present invention.

In this embodiment, a ceramic platinum element 172 is attached to the cup 96.96 in place of the metal thin film resistor 32 in the treatment instrument 95 shown in FIG.

Note that other embodiments can be constructed by combining the embodiments described above.

[Effects of the Invention] As described above, according to the present invention, since the heating element is constructed using a thin metal film, it is possible to form a heating element that is small and has little variation, and can be used for a long period of time. There is little deterioration even with respect to the temperature, and highly accurate temperature control is possible.

[Brief explanation of the drawing]

FIG. 1 is a conceptual diagram showing the conceptual structure of the present invention, FIGS. 2 to 11 relate to the first embodiment of the present invention, and FIG.
A perspective view of the embodiment, FIG. 3 shows the tip 9i of the ablation probe device:
4 is a sectional view taken along line A-A in FIG. 3, and FIG. 5 is a metal thin film resistor, with (a) being a plan view and (b) being a front view. , Figure (C) is a side view, Figures 6 and 7 show the pump, Figure (b) is a side view, Figure (C) is
is a bottom view, FIG. 8 is an explanatory diagram showing different embodiments of the shape of the tip side of the piston, FIG. 9 is a principle diagram of 4-wire and 3-wire temperature measurement, and FIG. 10 is a 2-wire J ( Fig. 11 is a diagram showing the heating current, Fig. 12 is a sectional view of the main part of the second embodiment of the present invention, and Fig. 13 is a cross-sectional view of the main part of the second embodiment of the present invention. FIG. 14 is a principle explanatory diagram of the fourth embodiment of the present invention; FIG. 15 is a perspective view showing two main parts of the fifth embodiment of the present invention; FIG. 16 is a sectional view showing the structure on the tip side of the sixth embodiment of the present invention, FIG. 17 is a sectional view showing the structure on the tip side of the seventh embodiment of the present invention, and FIG. The tip side structure of the eighth embodiment of the invention is shown in a small size [17i side view, FIG. 19 is a sectional view taken along the line 13-B in FIG. 18, and FIG. 21 is a 1J sectional view showing the structure on the tip side of the 10th practical example of the present invention, and FIG. 22 is a perspective view showing the structure on the tip side of the 11th embodiment of the present invention. 1... Platinum resistance element 2... Power supply part 3... Thirst detection part 4... 1-control part 11... Cauterization and hemostasis 13... Main body part 16... Cauterization Probe device 21...sheath 22...cautery bulb [-1-
32...Metal thin film resistor Figure 1 Figure 6 Figure 8 (a) Busy〕 (d) (f) Figure 12 Figure 14 Figure 15 Procedure 13 Official document (self-prompted) Specification In the 8th line of page 2 of Middle Box 1, it says [...Can be done early on June 15, 1989...]. Initial period...” Shimazu corrected. 1. Indication of the case Special revised application No. 62902 of 1999 2. Name of the invention Cautery hemostasis device 3. Person making the amendment Relationship with the case Special r1 Representative Toshibe Shimoyama 6. Specification subject to amendment m. Column Special ♂ 1 "Detailed Description of the Invention" Written by Chien Shiguchi, Director-General of the Agency (Method) ) is a bottom view" should be corrected to read "Figure 6 is a side view and Figure 7 is a bottom view.'' 2. Name of the invention 3. Person making the amendment Address related to the case Name 4. Agent address Cautery hemostatic device special crystal 1 Applicant Olympus Optical Industry, 2-43-2 Hatagaya, Shibuya-ku, Tokyo (037) Representative of Co., Ltd.
Toshibe Yama, 7-4-4-6 Nishi-Shinjuku, Shinjuku-ku, Tokyo, "Brief explanation of one drawing of the specification subject to amendment" column

Claims (1)

[Scope of Claims] A cautery hemostasis device in which a cautery probe is provided at the tip of an elongated sheath that can be inserted into a treatment instrument channel of an endoscope, wherein a heating element in the ablation probe is constructed of a platinum resistance element. A cautery hemostasis device characterized by: