TW201941746A - Ablation device - Google Patents

Abstract

Provided is an ablation device which can improve convenience. An ablation device 1 comprises: an electrode needle 11 which percutaneously punctures an affected part 90 inside a body, and which is supplied with electric power Pout; an insulating tube 12 which exposes an electrode area (exposed area Ae) while covering the periphery of the electrode needle 11 along the axial direction (Z-axis direction) of the electrode needle 11; a flow path 110 which is formed inside the electrode needle 11 and through which a liquid L for cooling flows; and a handle 13 fitted to the base end side of the electrode needle 11. The handle 13 includes: a handle body 130; an operation part 131; a liquid storage section 133 which is disposed inside the handle body 130 and temporarily stores the liquid L for cooling; and a slide mechanism 132 which is disposed inside the handle body 130 in parallel to the liquid storage section 133 and which performs a slide operation along the axial direction in conjunction with a prescribed operation of the operation part 131, thereby causing a slide operation of the insulating tube 12 along the axial direction.

Description

Ablation device

The present invention relates to an ablation device including an electrode needle for percutaneously puncturing an affected part of a body.

As one type of medical device for treating an affected part in a patient (for example, an affected part having a tumor such as a cancer), an ablation system for ablating (causing) such an affected part is proposed (for example, refer to Patent Document 1). This ablation system includes an ablation device having an electrode needle for percutaneously puncturing an affected part in the body, and a power supply device for supplying electric power for ablating the affected part.
[Prior technical literature]
[Patent Literature]

Patent Document 1: Japanese Patent Publication No. 2006-513830

However, in general, the above-mentioned ablation devices are required to improve convenience in use, for example. Therefore, it is desirable to provide an ablation device that can improve convenience.

An ablation device according to an embodiment of the present invention includes an electrode needle that percutaneously punctures an affected part in the body and is supplied with electric power for ablation; an insulating tube that exposes an electrode region located on the front end side of the electrode needle, and The axial direction of the electrode needle covers the periphery of the electrode needle; a flow path is formed inside the electrode needle, and a cooling liquid flows; and a handle is installed on the base end side of the electrode needle. The handle includes a handle main body as an exterior, an operation portion that performs a predetermined operation for sliding the insulating tube in the axial direction, a liquid storage portion disposed in the handle main body to temporarily store cooling liquid, and a sliding mechanism, The handle body is arranged side by side with the liquid containing portion, and in conjunction with a predetermined operation performed on the operation portion, it slides in the axial direction, thereby sliding the insulating tube in the axial direction.

In an ablation device according to an embodiment of the present invention, a liquid storage portion and a sliding mechanism are arranged in parallel to each other in the handle body, the liquid storage portion temporarily stores a cooling liquid, and the sliding mechanism is configured to make the insulating tube along the axis Slide to the established operation. This makes it possible to reduce the size of the entire handle, and to prevent a decrease in the adjustable range of the electrode region (exposed region exposed from the insulating tube) at the tip of the electrode needle. That is, it is possible to achieve both the miniaturization of the entire handle and the expansion of the adjustable range of the electrode area.

The length of the handle in the axial direction is preferably, for example, 86 mm or less. Therefore, if the length of the handle along the axial direction is greater than 86 mm, for example, when the patient enters the inside of a circular CT (Computed Tomography) scanning device and performs an operation, the handle and the CT scan are performed. The device may come into contact.

Further, the sliding mechanism includes a slider portion whose base end side is connected to the operation portion, and interlocks with the predetermined operation performed on the operation portion, and slides in the handle body along the axial direction relative to the handle body. And a joint portion that joins the front end side of the slider portion and the vicinity of the base end of the insulating tube. When the slide bar portion is located on the base end side of the handle body, the slide portion extends between the operation portion and the joint portion so as to bypass the liquid storage portion. In this case, when the predetermined operation is performed on the operation portion, it is possible to prevent interference between the slider portion and the liquid storage portion, and it is easy to reduce the size of the entire handle.

In an ablation device according to an embodiment of the present invention, if the flow path includes: a first flow path, the flow path when the cooling liquid flows from the proximal end side to the distal end side of the electrode needle; and the second flow path, The flow path when the cooling liquid flows from the front end side to the base end side of the electrode needle may be as described below. That is, the cooling liquid that can flow from the liquid supply pipe into the handle main body is not temporarily stored in the liquid storage portion, but is directly supplied into the first flow path; and the liquid supplied from the second flow path is also supplied. The cooling liquid is temporarily stored in the liquid container, and then flows out of the handle body into the drain pipe. In this case, the liquid (the liquid on the discharge side supplied from the second flow path) that is heated and temporarily contained in the liquid container during the ablation, and the liquid supply side that is supplied to the first flow path The liquid is not mixed in the handle body. Therefore, it is possible to suppress a decrease in the cooling effect of the cooling liquid caused by the liquid on the liquid-feeding side being heated. As a result, the convenience when using an ablation device can be further improved.

In this case, an inner tube may be further provided. The inner tube penetrates the liquid containing portion in the handle body, and is arranged along the axial direction inside the electrode needle to form the first flow path and the cooling liquid. It is supplied directly from the inside of the liquid supply pipe to the inside of the inner pipe. In this case, since the inner tube constituting the first flow path penetrates the liquid containing portion in the handle body, the size of the entire handle can be reduced, and the liquid on the discharge side (heated liquid) can be suppressed. ) The adverse effect (reduction of cooling effect) on the liquid on the liquid supply side is minimized. As a result, the convenience when using an ablation device can be further improved.

According to the ablation device according to an embodiment of the present invention, since the liquid storage portion and the sliding mechanism are arranged side by side in the handle body, it is possible to simultaneously achieve miniaturization of the entire handle and expansion of an adjustable range of the electrode region. . Therefore, convenience in using the ablation device can be improved.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. The description will be performed in the following order.
1. Embodiment (an example in which a liquid container and a sliding mechanism are arranged side by side in a handle body)
2. Modification

<1. Embodiment>
[Overall composition of the ablation system 5]
FIG. 1 is a schematic block diagram of an overall configuration example of an ablation system 5 including an ablation device (ablation device 1) according to an embodiment of the present invention.

As shown in FIG. 1, this ablation system 5 is a system used when treating an affected part 90 in a patient 9, and performs predetermined ablation (cauterization) on such an affected part 90.

In addition, as the affected part 90, there may be mentioned an affected part having a tumor such as cancer (liver cancer, lung cancer, breast cancer, kidney cancer, thyroid cancer, etc.).

As shown in FIG. 1, the ablation system 5 includes an ablation device 1, a liquid supply device 2, and a power supply device 3. In the ablation using the ablation system 5, the counter electrode plate 4 shown in FIG. 1 may be suitably used.

(Ablative device 1)
The ablation device 1 is a device used at the time of the above-mentioned ablation, and mainly includes an electrode needle 11 and an insulating tube 12, which will be described in detail later.

As shown by arrow P1 in FIG. 1, the electrode needle 11 is a needle that percutaneously punctures the affected part 90 in the patient 9. In addition, the liquid L supplied from the liquid supply device 2 to be described later circulates inside the electrode needle 11 (see FIG. 1).

The insulating tube 12 exposes an electrode region (exposed region Ae described later) on the front end side of the electrode needle 11, and covers the periphery of the electrode needle 11 along the axial direction of the electrode needle 11.

A detailed configuration example of such an ablation device 1 will be described later (see FIGS. 2 and 3).

(Liquid supply device 2)
The liquid supply device 2 is a device for supplying the cooling liquid L to the ablation device 1 (inside the electrode needle 11), and as shown in FIG. 1, the liquid supply device 2 includes a liquid supply unit 21. Examples of the cooling liquid L include sterile water and sterile physiological saline.

The liquid supply unit 21 supplies the liquid L to the ablation device 1 at any time in accordance with control based on a control signal CTL2 described later. Specifically, as shown in FIG. 1, the liquid supply unit 21 performs the liquid L so as to circulate the liquid L between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (inside a predetermined flow path 110 described later). Supply action. In addition, according to the control based on the control signal CTL2, the supply operation of such a liquid L is executed or stopped. The liquid supply unit 21 is configured to include, for example, a liquid pump.

(Power supply unit 3)
The power supply device 3 supplies power Pout (for example, radio frequency (RF) power) for ablation between the electrode needle 11 and the counter electrode plate 4, and controls a supply operation of the liquid L of the liquid supply device 2. As shown in FIG. 1, this power supply device 3 includes an input section 31, a power supply section 32, a control section 33, and a display section 34.

The input unit 31 inputs various set values and instruction signals (operation signals Sm) for instructing a predetermined operation described later. The operation signal Sm is input from the input unit 31 in accordance with the operation of the operator (for example, a technician) of the power supply device 3. However, these set values may not be input in response to an operator's operation, and may be set in the power supply device 3 in advance, for example, when a product is shipped. The setting value input by the input unit 31 is supplied to a control unit 33 described later. The input unit 31 is configured using, for example, a predetermined dial, a button, a touch panel, and the like.

The power supply unit 32 supplies the electric power Pout between the electrode needle 11 and the counter electrode plate 4 in accordance with a control signal CTL1 described later. The power supply unit 32 is configured using a predetermined power supply circuit (for example, a switching regulator). When the power Pout is composed of high-frequency power, the frequency is, for example, about 450 kHz to 550 kHz (for example, 500 kHz).

The control unit 33 controls the entire power supply device 3 and performs predetermined arithmetic processing, and is configured using, for example, a microcomputer. Specifically, the control unit 33 first has a function (power supply control function) for controlling a supply operation of the power Pout of the power supply unit 32 using the control signal CTL1. The control unit 33 has a function (liquid supply control function) for controlling the supply operation of the liquid L of the liquid supply device 2 (the liquid supply unit 21) using the control signal CTL2.

Further, as shown in FIG. 1, such a control unit 33 supplies temperature information It measured in the ablation device 1 (temperature sensor such as a thermocouple disposed inside the electrode needle 11) at any time. As shown in FIG. 1, the measurement value of the impedance value Zm is supplied to the control unit 33 from the power supply unit 32 at any time.

The display section 34 is a section (monitor) that displays various information and outputs it to the outside. Examples of the information to be displayed include the aforementioned various set values input from the input unit 31, various parameters supplied from the control unit 33, and temperature information It supplied from the ablation device 1. However, the information to be displayed is not limited to these information, and other information may be displayed instead, or other information may be added for display. The display unit 34 is configured by using various types of displays (for example, a liquid crystal display, a CRT (Cathode Ray Tube) display, and an organic EL (Electro Luminescence) display).

(Opposite plate 4)
As shown in FIG. 1, the counter electrode plate 4 is used in a state of being mounted on the body surface of the patient 9 during ablation. At the time of ablation, high-frequency energization (power supply Pout) is performed between the electrode needle 11 (the aforementioned electrode region) of the ablation device 1 and the pair of electrode plates 4, which will be described in detail later. During such ablation, as shown in FIG. 1, the impedance value Zm between the electrode needle 11 and the counter electrode plate 4 is measured at any time, and the measured impedance value Zm is supplied from the power source unit 32 to the control in the power source device 3. The unit 33 will be described in detail later.

[Detailed configuration of the ablation device 1]
Next, a detailed configuration example of the ablation device 1 will be described with reference to FIG. 2. FIG. 2 is a schematic side view (YZ side view) of a detailed configuration example of the ablation device 1 shown in FIG. 1. In addition, in FIG. 2, as shown by an arrow, an enlarged view of a portion indicated by a symbol P2 (a partial area of the electrode needle 11 and the insulating tube 12) is shown below in FIG. 2.

(Electrode pin 11)
As shown in FIG. 2, the electrode needle 11 is provided along the Z-axis direction, and the length (axial length) along the Z-axis direction is, for example, about 30 mm to 350 mm. In addition, the electrode needle 11 has, along the axial direction (Z-axis direction), an exposed area Ae on the front end side that is not covered by the insulating tube 12 (an electrode region that functions as an electrode during ablation) and is covered by the insulating tube 12. Area (covered area on the base end side). As described above, between the exposed area Ae of the electrode needle 11 and the counter electrode plate 4, power Pout for ablation is supplied. The electrode needle 11 is made of a metal material such as stainless steel, nickel-titanium alloy, titanium alloy, or platinum.

(Insulated tube 12)
As described above, the insulating tube 12 partially exposes the front end side (exposed area Ae) of the electrode needle 11 and covers the periphery of the electrode needle 11 along the Z-axis direction. In addition, the insulating tube 12 is configured to correspond to a predetermined operation of a handle 13 to be described later, and as shown by an arrow d2 in FIG. 2, it can slide along the axial direction (Z-axis direction) relative to the electrode needle 11. Thereby, the length (axial length) of the exposed area Ae of the electrode needle 11 along the Z-axis direction can be adjusted.

The length (axial length) of the exposed area Ae of the electrode needle 11 that can be adjusted by the insulating tube 12 in the Z-axis direction is, for example, about 3 mm to 50 mm. The insulating tube 12 is made of, for example, synthetic resins such as PEEK (polyetheretherketone), PI (polyimide), fluorine-based resins, and polyetherblocked amines.

(Handle 13)
The handle 13 is a portion that is grasped (held) by an operator (doctor) when using the ablation device 1. As shown in FIG. 2, the handle 13 mainly includes a handle main body 130 attached to the base end side of the electrode needle 11, and an operation portion (sliding handle portion) 131.

The handle main body 130 corresponds to a portion (handle portion) actually held by the operator, and also functions as an external decoration of the handle 13. The handle body 130 is made of a synthetic resin such as polycarbonate, acrylonitrile-butadiene-styrene copolymer (ABS), acrylic, polyolefin, and polyoxymethylene.

The operation portion 131 performs a predetermined operation (sliding operation) for sliding the insulating tube 12 along the axial direction (Z-axis direction) relative to the electrode needle 11 and protrudes to the outside (Y-axis direction) of the handle body 130. The operation portion 131 is made of, for example, the same material (synthetic resin or the like) as the handle body 130 described above. The operation portion 131 is configured to be slidable relative to the handle body 130 along the axial direction (Z-axis direction) of the handle 13.

By performing such a sliding operation on the operation portion 131 (for example, refer to arrow d1 in FIG. 2), the insulating tube 12 is slid along the Z-axis direction relative to the electrode needle 11 (for example, refer to arrow d2 in FIG. 2). This will be described in detail later. Thereby, the length (axial length) of the exposed area Ae of the electrode needle 11 along the Z-axis direction can be adjusted.

[Detailed structure of the handle 13]
Next, a detailed configuration example of the handle 13 will be described with reference to FIGS. 3 to 5. FIG. 3 is a schematic side view (YZ exploded side view) of a main part configuration example of the inside of the handle 13 shown in FIG. 2. FIG. 4 is a schematic perspective view of a configuration example of a main part inside the handle 13 as described above. FIG. 5 (A) is a schematic cross-sectional view (ZX cross-sectional view) of an internal configuration example in the vicinity of the liquid storage portion (the liquid storage portion 133 described later) shown in FIGS. 3 and 4. 5 (B) is a schematic cross-sectional view (ZX cross-sectional view) of an internal configuration example of the distal end side of the electrode needle 11 shown in FIG. 2.

In addition, in FIG. 3 and FIG. 4, for convenience of explanation, a state in which one side portion of the handle body 130 along the X-axis direction is removed is illustrated. In addition, in these FIGS. 3 and 4, for convenience of explanation, the configuration other than the main part inside the handle 13 is omitted as appropriate.

As shown in FIGS. 3, 4, and 5 (A), a slide mechanism 132 and a liquid storage portion 133 are provided inside the handle 13 (inside the handle main body 130).

(Sliding mechanism 132)
The sliding mechanism 132 slides along the Z-axis direction in cooperation with the aforementioned sliding operation performed on the operation portion 131, so that the insulating tube 12 slides along the Z-axis direction with respect to the electrode needle 11, which will be described in detail later. As shown in FIG. 3, the slide mechanism 132 includes a slide bar portion (parallel bar portion) 132a and an engaging portion 132b.

As shown in FIG. 3, the joint portion 132 b joins a portion near a front end side of a slide bar portion 132 a described later and a base end of the insulating tube 12.

As shown in FIG. 3, the slide bar portion 132 a is mainly arranged in parallel along the Z-axis direction between the aforementioned operation portion 131 and other internal components such as the liquid storage portion 133. The base end side of the slider part 132 a is connected to the operation part 131, and the front end side thereof is connected (joined) to the joint part 132 b. In this way, the slide bar portion 132 a is slid relative to the handle body 130 along the Z-axis direction within the handle body 130 in cooperation with the sliding operation performed on the operation portion 131.

As shown in FIG. 3, when the operation portion 131 is located on the base end side of the handle body 130, the front end of the slider portion 132 a is located on the front end side compared to the front end of other internal components such as the liquid storage portion 133. In other words, when the slider portion 132 a is located on the base end side of the handle body 130, it extends between the operation portion 131 and the joint portion 132 b to bypass other internal components such as the liquid storage portion 133. Thereby, when sliding operation is performed on the operation portion 131, it is possible to prevent interference between the slide bar portion 132a and other internal components such as the liquid storage portion 133, and it is easy to downsize the entire handle 13.

The slider portion 132 a and the joint portion 132 b are integrally formed with the aforementioned operation portion 131, for example. However, these slider parts 132a, the joint part 132b, and the operation part 131 may each be shape | molded individually.

In this way, as shown in FIG. 3 and FIG. 4, the slide mechanism 132 is arranged in parallel with the liquid storage portion 133 in the handle body 130. That is, in the handle body 130, the slide mechanism 132 (slider part 132a) and the liquid storage part 133 are arrange | positioned side by side (in this example, they are arrange | positioned side by side along the Y-axis direction).

(Liquid container 133)
In the handle body 130, the liquid storage portion 133 temporarily stores the cooling liquid L in the liquid storage portion 133. As shown in FIG. 4 and FIG. 5 (A), the liquid storage portion 133 is connected to a liquid supply pipe 81 for flowing cooling liquid L (from the liquid supply portion 21 described above) into the handle body 130, and A drain pipe 82 that discharges the cooling liquid L from the inside of the handle body 130 (to the liquid supply unit 21). In addition, through the liquid feed pipe 81, the liquid storage portion 133, and the liquid discharge pipe 82, a flow path for the liquid L for cooling to and from (circulate) is formed inside the handle body 130 and the electrode needle 11.

(Flow Path 110)
Here, the configuration of the flow path 110 formed inside the electrode needle 11 will be described in detail with reference to FIGS. 5 (A) and 5 (B).

First, as shown in FIG. 5 (B), a flow path 110 is formed in the electrode needle 11 along the axial direction (Z-axis direction) of the electrode needle 11 and is a flow path through which the cooling liquid L flows. Specifically, as shown by the dashed arrows in FIGS. 5 (A) and 5 (B), the flow path 110 is provided with a flow path 110a (from the electrode needle 11) which is an outward path of the cooling liquid L. The flow path when the base end side flows toward the front end side) and the flow path 110b (the flow path when the liquid flows from the front end side to the base end side) of the cooling liquid L is a return path.

In addition, such a flow path 110 corresponds to a specific example of the “flow path” of the present invention. The flow path 110 a corresponds to a specific example of the “first flow path” in the present invention, and the flow path 110 b corresponds to a specific example of the “second flow path” in the present invention.

As shown in FIGS. 5 (A) and 5 (B), an inner tube 111 is provided in the handle body 130, and the inner tube 111 penetrates the liquid storage portion 133 along the Z-axis direction (see FIG. 5 (A)). The middle symbol is P3), and the above-mentioned flow path 110 a (forward path) is formed inside the electrode needle 11. As shown in FIG. 5 (A) and FIG. 5 (B), the inner tube 111 is located along the axial direction (Z of the electrode needle 11) inside the handle body 130, the electrode needle 11 (the flow path 110), and the liquid feeding tube 81. Axis direction). Then, as shown in FIG. 5 (A), the cooling liquid L is directly supplied from the liquid supply pipe 81 into the inner pipe 111.

With such a structure, the cooling liquid L flowing into the handle main body 130 from the liquid supply pipe 81 is not temporarily stored in the liquid storage portion 133, but flows directly through the inner tube 111 to the flow path that becomes the return path. Supply within 110a (see FIG. 5 (A)). The cooling liquid L supplied from the return path 110b is temporarily stored in the liquid storage portion 133, and then flows out of the handle main body 130 into the drain pipe 82 (see FIG. 5 (A)). With this configuration, a branching liquid feeding pipe 81 and a draining pipe 82 can be provided. The liquid feeding pipe 81 is used to flow the cooling liquid L into the handle body 130, and the liquid draining pipe 82 is used to cool the liquid. The liquid L is discharged from the inside of the handle body 130.

[Actions and effects / effects]
(A. Basic actions)
In this ablation system 5, when treating an affected part 90 having a tumor such as a cancer, a predetermined ablation is performed on such an affected part 90 (see FIG. 1). In such an ablation, first, as shown by an arrow P1 in FIG. 1, the electrode needle 11 of the ablation device 1 is percutaneously punctured from the front end side (the exposed area Ae side) of the affected part 90 in the patient 9. Then, power Pout (for example, high-frequency power) is supplied between the electrode needle 11 and the counter electrode plate 4 from the power source device 3 (power source unit 32), so that the Joule fever of the affected part 90 is ablated.

During such ablation, the liquid L for cooling is circulated between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (in the aforementioned flow path 110), and the liquid is supplied from the liquid supply device 2 (liquid supply Section 21) supplies the liquid L to the electrode needle 11 (see FIG. 1). Thereby, during the ablation, the electrode needle 11 is cooled. As a result, an excessive increase in the temperature (tissue temperature) of the affected part 90 can be suppressed, and the aforementioned sharp increase in the impedance value Zm due to carbonization of the tissue can be prevented. .

FIG. 6 is a schematic diagram of an example of a cauterized state formed in the affected part 90 by such ablation. As shown in FIG. 6, if the above-mentioned ablation is performed by using the electrode needle 11 penetrating into the affected part 90, for example, the rugby-shaped (ellipsoidal) thermal coagulation region Ah1 gradually diffuses, and a substantially spherical thermal coagulation can be obtained. Area Ah2 (refer to the dotted arrow in FIG. 6). Thereby, by performing isotropic ablation on the entire affected part 90, the affected part 90 can be effectively treated.

As shown in FIGS. 2, 7 (A), and 7 (B), in such an ablation, the handle 13 of the ablation device 1 performs the aforementioned sliding operation on the operation portion 131 in advance. Specifically, if a sliding operation is performed on the operation portion 131 along the Z axis direction (for example, refer to arrow d1 in FIG. 2 and FIG. 7 (B)); in conjunction with the sliding operation of the operation portion 131, the The slide mechanism 132 slides along the Z-axis direction (see arrow d0 in FIG. 7 (B)). Then, in conjunction with the sliding operation of the sliding mechanism 132, the insulating tube 12 also performs a sliding operation along the Z-axis direction (for example, refer to arrow d2 in FIG. 2 and FIG. 7 (B)). Thereby, as shown in FIGS. 7 (A) and 7 (B), the size (length along the Z-axis direction) of the exposed area Ae on the tip side of the electrode needle 11 can be arbitrarily adjusted, and the ablation at the time of ablation can also be arbitrarily adjusted. Range (the range corresponding to the exposed area Ae).

With this, for example, when a small tumor is formed in a deep region of the liver, a small exposed area Ae (ablation range) is set, and the tip of the electrode needle 11 is inserted into the affected area 90 to perform ablation, thereby selectively selecting only the affected area 90. Burning. That is, portions other than the affected part 90 are not burned, and the original function can be maintained. On the other hand, when a large tumor is formed, for example, by setting a large exposed area Ae (ablation range), the large tumor can be cauterized together (together).

In addition, each of the sliding operation performed on the operation portion 131, the sliding mechanism 132 and the insulating tube 12 linked with the sliding operation can also be stepped along the axial direction (Z-axis direction) of the electrode needle 11. (Intermittent) adjustment. In other words, the positions of the operating portion 131, the sliding mechanism 132, and the insulating tube 12 during sliding can also be fixed slightly according to a predetermined distance along the Z-axis direction.

(B. Comparative example)
Here, as an ablation device of a comparative example, the following configuration is considered. That is, the ablation device of this comparative example is different from the ablation device 1 of the present embodiment shown in FIGS. 3 and 4. In the handle body, the slide mechanism 132 is connected in series with the liquid storage portion 133 (along the electrode needle 11 The Z-axis direction is arranged side by side). However, in such an ablation device of the comparative example, the following problems may occur.

That is, first, for example, when performing ablation treatment of liver cancer in a radiology department, generally, an ablation device is used under a CT scan. In short, the ablation device is used in a state where the patient enters the inside of the circular CT scanning device. Therefore, if the ablation device is large, it is not easy to use; therefore, in general, miniaturization of the handle of the ablation device is required.

Therefore, in a general handle of an ablation device in which the sliding mechanism 132 and the liquid container 133 are connected in series in the handle body, if the handle is miniaturized as described above (in the above-mentioned ablation device of the comparative example), it is as follows. That is, in the ablation device of this comparative example, although it is possible to reduce the size of the entire handle, the electrode region (the exposed region Ae exposed from the insulating tube 12) at the tip of the electrode needle 11 can be along the axial direction (Z (Axis direction) adjustment range is reduced. Because of this, the electrode area (exposed area Ae) is equivalent to the ablation range when the electrode needle 11 is used for ablation (see FIGS. 7 (A) and 7 (B)); therefore, if the adjustment range of the ablation range is reduced, , The convenience of using the ablation device may be impaired.

(C. This embodiment)
On the other hand, as shown in FIG. 3, the ablation device 1 of this embodiment is different from the ablation device of the comparative example described above, and has the following configuration. That is, the liquid containing portion 133 and the sliding mechanism 132 are arranged side by side in the handle body 130. The liquid containing portion 133 temporarily stores the cooling liquid L. The sliding mechanism 132 slides the insulating tube 12 along the Z-axis direction. The established operation.

With such a configuration, the ablation device 1 of this embodiment is different from the ablation device of the comparative example described above, as described below.

That is, first, the size of the entire handle 13 can be reduced. Specifically, the overall size of the handle 13 (the axial length Lz (length along the Z-axis direction) shown in FIG. 3) can be set to, for example, 86 mm or less (Lz ≦ 86 mm). In this regard, if the overall size (axial length Lz) of the handle 13 is larger than 86 mm, for example, as described above, the handle 13 and the CT scanning device may be operated when the patient enters the inside of the circular CT scanning device. contact. In addition, if it is considered to secure the exposed area Ae (ablation range), the lower limit value of the overall size (axial length Lz) of the handle 13 may be, for example, 30 mm. That is, in this case, 30 mm ≦ Lz ≦ 86 mm is satisfied. In addition, in this ablation device 1, it is possible to prevent a decrease in the adjustable range of the electrode region (the exposed region Ae exposed from the insulating tube 12) at the tip of the electrode needle 11 (see FIGS. 7 (A) and 7 (B)). . In short, this ablation device 1 is different from the ablation device of the comparative example described above in that it can simultaneously achieve miniaturization of the entire handle 13 and expansion of the adjustable range of the electrode region (the ablation range).

As described above, in the ablation device 1 according to this embodiment, since the liquid storage portion 133 and the sliding mechanism 132 are arranged side by side in the handle body 130, it is possible to simultaneously achieve miniaturization of the entire handle 13 and adjustment of the ablation range. Expansion of scope. Therefore, the ablation device 1 can perform effective ablation compared with, for example, the ablation device of the comparative example described above, and as a result, convenience in use can be improved.

Moreover, in the ablation device 1 of the present embodiment, the cooling liquid L flowing from the liquid feeding tube 81 into the handle main body 130 is not temporarily accommodated in the liquid containing portion 133, but directly flows toward the flow path 110a which is the forward path. (Inner tube 111) is supplied (see FIG. 5 (A)). The cooling liquid L supplied from the return path 110b is temporarily stored in the liquid storage portion 133, and then flows out of the handle main body 130 into the drain pipe 82 (see FIG. 5 (A)). As a result, as shown in FIG. 5 (A), the liquid L (liquid L on the discharge side supplied from the flow path 110b) which is heated and temporarily contained in the liquid storage portion 133 during the ablation, and the flow path 110a The liquid L on the liquid supply side is not mixed in the handle body 130. Therefore, it is possible to suppress a decrease in the cooling effect of the cooling liquid L caused by the heating of the liquid L on the liquid-feeding side. As a result, in this embodiment, the convenience when using the ablation device 1 can be further improved.

Further, in this embodiment, as shown in FIG. 5 (A), an inner tube 111 is provided in the handle body 130. The inner tube 111 penetrates the liquid containing portion 133 and forms a flow path inside the electrode needle 11. 110a (going on). Then, the cooling liquid L is directly supplied into the inner tube 111 from the liquid feed tube 81 (see FIG. 5 (A)). Thereby, the inner tube 111 constituting the flow path 110a penetrates the liquid containing portion 133 in the handle main body 130, so that the size of the entire handle 13 can be further reduced, and the liquid L (heated liquid L) on the discharge side can be suppressed. The adverse effect on the liquid L on the liquid-feeding side (reduction of cooling effect) is minimized. As a result, in this embodiment, the convenience when using the ablation device 1 can be further improved.

＜ 2. Modifications ＞
Although the present invention has been described by exemplifying the embodiment, the present invention is not limited to the embodiment, and various changes can be made.

For example, the material of each member described in the above embodiment is not limited, and other materials may be used. In addition, although the structure of the ablation device and the like has been specifically described in the above embodiment, it is not always necessary to include all the members, and other members may be further provided. In addition, the values, ranges, and magnitude relationships of various parameters described in the above embodiments are not limited to those described in the above embodiments, and may be other values, ranges, and magnitude relationships.

In the above-mentioned embodiment, although the configurations of the electrode needle, the insulating tube, and the handle of the ablation device are specifically described, the configurations of these members are not limited to those described in the above-mentioned embodiment, and other configurations may be adopted. Specifically, for example, in some cases, the electrode needle is not a unipolar type described in the above embodiment, but may be a bipolar type. In addition, for example, on the aforementioned liquid-feeding side, the cooling liquid may be temporarily stored in the liquid container, and then may be supplied into the flow path (first flow path). In addition, for example, in some cases, the aforementioned inner tube (constituting the first flow path) may adopt a configuration that does not penetrate the liquid container (a configuration that bypasses the liquid container to the inside of the channel).

Furthermore, although the module configuration of the liquid supply device 2 and the power supply device 3 has been specifically described in the above-mentioned embodiment, it is not always necessary to include each module described in the above-mentioned embodiment, and other modules may be further provided. . In addition, the entire ablation system 5 may include other devices in addition to the devices described in the above embodiments.

Moreover, in the above-mentioned embodiment, although the ablation device which performs high-frequency electric conduction between the electrode needle 11 and the counter electrode plate 4 during ablation is specifically described, it is not limited to the above-mentioned embodiment. Specifically, it may be an ablation device that performs ablation using other electromagnetic waves such as radio waves and microwaves.

In addition, in the embodiment described above, the control operation (the method of ablation) of the control unit 33 including the power supply control function and the liquid supply control function was specifically described. However, the control methods (ablation methods) of these power supply control functions, liquid supply control functions, and the like are not limited to the methods listed in the above embodiments.

The series of processes described in the above embodiments may be performed by hardware (circuit) or by software (program). When it is performed by software, the software is composed of a program group for performing various functions by a computer. Various programs can be created and used in the aforementioned computer in advance, for example, and can also be installed and used in the aforementioned computer through a computer network or a recording medium.

Furthermore, the various examples described above can be applied in any combination.

1‧‧‧ ablation device

11‧‧‧ electrode needle

110, 110a, 110b ‧‧‧ flow path

111‧‧‧Inner tube

12‧‧‧ insulated tube

13‧‧‧Handle

130‧‧‧handle body

131‧‧‧Operation part (sliding handle part)

132‧‧‧ sliding mechanism

132a‧‧‧Sliding rod section (parallel rod section)

132b‧‧‧Joint

133‧‧‧Liquid container

2‧‧‧ liquid supply device

21‧‧‧Liquid Supply Department

3‧‧‧ Power supply unit

31‧‧‧Input Department

32‧‧‧Power Supply Department

33‧‧‧Control Department

34‧‧‧Display

4‧‧‧ pair of plates

5‧‧‧ Ablation System

81‧‧‧ liquid delivery tube

82‧‧‧Drain tube

9‧‧‧patient

90‧‧‧ affected area

L‧‧‧Liquid

CTL1, CTL2‧‧‧Control signals

Sm‧‧‧ operation signal

Pout‧‧‧ Electricity

It‧‧‧ Temperature Information

Zm‧‧‧Impedance

Ae‧‧‧ exposed area (electrode area)

Ah1, Ah2 ‧‧‧ Thermal solidification area

Lz‧‧‧Axial length

FIG. 1 is a schematic block diagram of an overall configuration example of an ablation system including an ablation device according to an embodiment of the present invention.

FIG. 2 is a schematic side view of a detailed configuration example of the ablation device shown in FIG. 1.

FIG. 3 is a schematic side view of a configuration example of a main part inside the handle shown in FIG. 2.

FIG. 4 is a schematic perspective view of a configuration example of main parts inside the handle shown in FIG. 2.

5 is a schematic cross-sectional view showing an example of the internal configuration of the vicinity of the liquid container shown in FIGS. 3 and 4 and the front end side of the electrode needle shown in FIG. 2.

FIG. 6 is a schematic diagram of an example of a cauterized state formed in an affected part by ablation.

FIG. 7 is a schematic side view showing an example of sliding of the ablation device shown in FIG. 2.

Claims (6)

An ablation device comprising: An electrode needle that percutaneously punctures the affected part of the body and is supplied with electricity for ablation; An insulating tube that exposes an electrode region on a front end side of the electrode needle and covers the periphery of the electrode needle along an axial direction of the electrode needle; A flow path is formed inside the electrode needle, and a cooling liquid flows; and The handle is mounted on the base end side of the electrode needle, The above handles have: Handle body as exterior; The operation unit performs a predetermined operation for sliding the insulating tube along the axial direction; A liquid storage portion arranged in the handle main body to temporarily store the cooling liquid; and The sliding mechanism is arranged in parallel with the liquid storage portion in the handle body, and slides along the axial direction by interlocking with the predetermined operation performed on the operation portion, thereby sliding the insulating tube along the axial direction. . The ablation device according to claim 1, wherein: The sliding mechanism has: A slider portion whose base end side is connected to the operation portion, and is linked to the predetermined operation performed on the operation portion, and slides relative to the handle body along the axial direction within the handle body; and A joint portion that joins the front end side of the slider portion and the vicinity of the base end of the insulating tube, When the slide bar portion is located on the base end side of the handle body, the slide portion extends between the operation portion and the joint portion so as to bypass the liquid storage portion. The ablation device according to claim 1, wherein: The length of the handle in the axial direction is 86 mm or less. The ablation device according to claim 2, wherein: The length of the handle in the axial direction is 86 mm or less. The ablation device according to any one of claims 1 to 4, wherein: The aforementioned flow paths include: The first flow path is a flow path when the cooling liquid flows from the proximal end side to the distal end side of the electrode needle; and The second flow path is a flow path when the cooling liquid flows from the front end side to the base end side of the electrode needle, The cooling liquid flowing from the liquid supply pipe into the handle body is not temporarily stored in the liquid storage portion, but is directly supplied into the first flow path, and The cooling liquid supplied from the second flow path is temporarily stored in the liquid storage portion, and then flows out of the handle body into the drain pipe. The ablation device according to claim 5, further comprising an inner tube that penetrates the liquid containing portion in the handle body, and is arranged along the axial direction inside the electrode needle and constitutes the first flow path, The cooling liquid is directly supplied from the liquid supply pipe into the inner pipe.