TWI693920B - Ablation device - Google Patents

Abstract

The invention provides an ablation device which can improve convenience. The ablation device (1) includes: an electrode needle (11), which punctures the affected part (90) in the body percutaneously and is supplied with electric power (Pout); an insulating tube (12) exposes the electrode area (exposed area Ae), and Cover the periphery of the electrode needle (11) along the axial direction (Z-axis direction) of the electrode needle (11); a flow path (110) is formed inside the electrode needle (11), and a cooling liquid (L) flows; And the handle (13) is installed on the base end side of the electrode needle (11). The handle (13) includes: a handle body (130); an operation portion (131); a liquid containing portion (133), which is arranged in the handle body (130) and temporarily contains a cooling liquid (L); and a sliding mechanism (132) , Arranged in parallel with the liquid storage part (133) in the handle body (130), and slides along the axial direction by interlocking with the predetermined operation on the operation part (131), so that the insulating tube (12) is along Slide axially.

Description

Ablation device

The present invention relates to an ablation device provided with an electrode needle for percutaneously puncturing an affected part in the body.

As one of medical devices for treating an affected part in a patient (for example, an affected part having a tumor such as cancer), an ablation system for ablating (burning) such an affected part has been proposed (for example, refer to Patent Document 1). The 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 Special Publication No. 2006-513830

However, in general, the ablation device described above is required to improve, for example, convenience in use. 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 punctures an affected part of the body percutaneously and is supplied with power for ablation; and an insulating tube that exposes the electrode area on the tip side of the electrode needle and extends along 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 has: a handle body as an exterior; an operation portion to perform a predetermined operation for sliding the insulating tube in the axial direction; a liquid storage portion, which is arranged in the handle body and temporarily accommodates cooling liquid; and a sliding mechanism, It is arranged in parallel with the liquid storage portion in the handle body, and slides along the axial direction in conjunction with a predetermined operation performed on the operating portion, thereby sliding the insulating tube along 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 with each other in the handle body, the liquid storage portion temporarily stores cooling liquid, and the sliding mechanism performs Swipe to the established operation. With this, it is possible to reduce the size of the handle as a whole, and to avoid a reduction in the adjustable range of the electrode area (exposed area exposed from the insulating tube) at the tip of the electrode needle. That is, it is possible to simultaneously achieve miniaturization of the handle as a whole, and to expand the adjustable range of the electrode area.

In addition, the length of the handle along the axial direction is preferably, for example, 86 mm or less. For this reason, if the length of the handle along the axial direction is greater than 86 mm, for example, when the patient enters a circular CT (Computed Tomography) scan device, the handle and the CT scan The device may come into contact.

In addition, the sliding mechanism includes a sliding rod portion whose base end side is connected to the operation portion and slides relative to the handle body in the handle body along the axial direction in conjunction with the predetermined operation performed on the operation portion ; And a joint portion that joins the front end side of the slide bar 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, it extends between the operation portion and the joint portion so as to bypass the liquid storage portion. In such a case, when the predetermined operation is performed on the operation portion, interference between the slider portion and the liquid storage portion can be prevented, and the overall handle can be easily miniaturized.

In an ablation device according to an embodiment of the present invention, if the flow path includes: a first flow path, a flow path when the cooling liquid flows from the base end side to the front end side of the electrode needle; and a 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 above. That is, the cooling liquid that can flow into the handle body from the liquid supply tube is not temporarily contained in the liquid storage portion, but is directly supplied into the first flow path; and the liquid supplied from the second flow path After the cooling liquid is temporarily contained in the liquid storage portion, it flows out of the handle body into the drain tube. 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 storage portion during the ablation, and the liquid supply side 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 due to the heating of the liquid on the liquid sending side. As a result, the convenience when using the ablation device can be further improved.

In this case, an inner tube may be further provided, the inner tube penetrating the liquid accommodating portion in the handle body, and disposed inside the electrode needle along the axial direction and constituting the first flow path, the cooling liquid The liquid is directly supplied into the inner tube from the liquid supply tube. In such a case, by the inner tube constituting the first flow path penetrating the liquid accommodating portion in the handle body, the handle as a whole can be made more compact while suppressing the liquid (heated liquid) on the discharge side ) The adverse effect on the liquid on the liquid feed side (reduction of cooling effect) is minimized. As a result, the convenience when using the ablation device can be further improved.

According to the ablation device of one embodiment of the present invention, since the liquid storage portion and the sliding mechanism are arranged in parallel with each other in the handle body, it is possible to simultaneously achieve the miniaturization of the handle as a whole and the expansion of the adjustable range of the electrode area . Therefore, the convenience when using the ablation device can be improved.

Hereinafter, an embodiment of the present invention will be described in detail with reference to the drawings. In addition, the description will be made in the following order. 1. Embodiment (an example in which a liquid storage portion and a sliding mechanism are arranged in parallel in the handle body) 2. Modification

<1. Embodiment> [Overall Configuration of Ablation System 5] FIG. 1 is a schematic block diagram of an example of the overall configuration of an ablation system 5 provided with 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, examples of the affected part 90 include an affected part having tumors 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 addition, when ablation using the ablation system 5 is performed, the counter plate 4 shown in FIG. 1 can also be suitably used.

(Ablation device 1) The ablation device 1 is a device used during the ablation described above, and mainly includes an electrode needle 11 and an insulating tube 12, which will be described in detail later.

The electrode needle 11 is a needle percutaneously puncturing the affected part 90 in the patient 9 as indicated by an arrow P1 in FIG. 1. In addition, inside the electrode needle 11, the liquid L supplied from the liquid supply device 2 described later circulates (see FIG. 1 ).

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

In addition, 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 that supplies the cooling liquid L to the ablation device 1 (inside the electrode needle 11 ), and as shown in FIG. 1, has a liquid supply portion 21. In addition, examples of the liquid L for cooling include sterile water and sterile physiological saline.

The liquid supply unit 21 supplies the above-mentioned 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 such that the liquid L circulates between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (in a predetermined flow path 110 described later). Supply action. In addition, in accordance with the control based on the control signal CTL2, the supply operation of the liquid L is executed or stopped. In addition, the liquid supply unit 21 is configured to include, for example, a liquid pump or the like.

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

The input unit 31 inputs various setting values and an instruction signal (operation signal Sm) for instructing a predetermined action described later. Such an operation signal Sm is input from the input unit 31 according to the operation of the operator (for example, technician) of the power supply device 3. However, these setting values may not be input in response to the operation of the operator, and may be set in the power supply device 3 in advance, for example, when the product is shipped. In addition, the set value input by the input unit 31 is supplied to the control unit 33 described later. In addition, such an input unit 31 is configured using, for example, a predetermined dial pad, buttons, touch panel, or 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. Such a power supply unit 32 is configured using a predetermined power supply circuit (for example, a switching regulator, etc.). In addition, 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, performs predetermined calculation processing, and is configured using, for example, a microcomputer. Specifically, the control unit 33 first has a function of using the control signal CTL1 to control the supply operation of the power Pout of the power supply unit 32 (power supply control function). In addition, 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 (liquid supply unit 21) using the control signal CTL2.

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

The display unit 34 is a part (monitor) that displays various information and outputs it to the outside. Examples of the information to be displayed include the aforementioned various setting 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 as the display object is not limited to these information, and other information can be displayed as a substitute, or other information can be added for display. The display unit 34 is configured using various types of displays (for example, a liquid crystal display, a CRT (Cathode Ray Tube) display, an organic EL (Electro Luminescence) display, etc.).

(Opposite plate 4) As shown in FIG. 1, the counter electrode plate 4 is used in a state of being attached to the body surface of the patient 9 during ablation. During 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. Also, 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 supply unit 32 to the control in the power supply device 3 The unit 33 will be described in detail later.

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

(Electrode needle 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 an exposed area Ae (electrode area that functions as an electrode during ablation) on the tip side not covered by the insulating tube 12 along the axial direction (Z-axis direction), and is covered by the insulating tube 12 Area (covered area on the base end side). Between the exposed area Ae of the electrode needle 11 and the counter electrode plate 4, as described above, electric power Pout for ablation is supplied. In addition, the electrode needle 11 is made of metal materials such as stainless steel, nickel-titanium alloy, titanium alloy, and platinum.

(Insulation tube 12) As described above, the insulating tube 12 partially exposes the distal end side (exposed region 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 be able to slide relative to the electrode needle 11 along the axial direction (Z-axis direction) as shown by an arrow d2 in FIG. 2 in accordance with a predetermined operation of the handle 13 described later. Thereby, the length (axial length) of the exposed area Ae of the electrode needle 11 along the Z-axis direction can be adjusted.

In addition, the length (axial length) of the exposed area Ae of the electrode needle 11 that can be adjusted by such an insulating tube 12 along the Z-axis direction is, for example, about 3 mm to 50 mm. The insulating tube 12 is made of synthetic resin such as PEEK (polyether ether ketone), PI (polyimide), fluorine-based resin, and polyether block amide.

(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 body 130 attached to the proximal end of the electrode needle 11, and an operation portion (sliding handle portion) 131.

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

The operation portion 131 performs a predetermined operation (slide operation) for sliding the insulating tube 12 relative to the electrode needle 11 along its axial direction (Z-axis direction), and protrudes to the outside of the handle body 130 (Y-axis direction). The operation portion 131 is made of, for example, the same material (synthetic resin or the like) as the aforementioned handle body 130. 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 against the electrode needle 11 in the Z-axis direction (for example, refer to arrow d2 in FIG. 2 ). This will be described in detail later. With this, 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 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 (Y-Z exploded side view) of a configuration example of main parts inside the handle 13 shown in FIG. 2. In addition, FIG. 4 is a schematic perspective view of a configuration example of the main part inside such a handle 13. FIG. 5(A) is a schematic cross-sectional view (Z-X cross-sectional view) of an example of the internal configuration in the vicinity of the liquid storage portion (liquid storage portion 133 described later) shown in FIGS. 3 and 4. 5(B) is a schematic cross-sectional view (Z-X cross-sectional view) of an example of the internal configuration of the tip side of the electrode needle 11 shown in FIG. 2.

In addition, in FIGS. 3 and 4, for convenience of explanation, the state in which one side portion of the handle body 130 along the X-axis direction is detached 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 appropriately omitted from illustration.

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

(Sliding mechanism 132) The sliding mechanism 132 slides along the Z-axis direction in conjunction with the above-mentioned sliding operation on the operation portion 131 to thereby slide the insulating tube 12 relative to the electrode needle 11 along the Z-axis direction, which will be described in detail later. As shown in FIG. 3, such a sliding mechanism 132 has a sliding bar portion (parallel bar portion) 132a and an engaging portion 132b.

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

As shown in FIG. 3, the slide bar portion 132a is mainly arranged in parallel along the Z-axis direction between the aforementioned operation portion 131 and other internal members such as the liquid storage portion 133. In addition, the proximal end side of the slide bar portion 132a is connected to the operation portion 131, and the distal end side thereof is connected (joined) to the joint portion 132b. In this way, the slide bar portion 132 a is slid relative to the handle body 130 in the Z-axis direction in the handle body 130 in conjunction 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 slide bar portion 132a is located on the front end side compared to the front end of other internal members such as the liquid storage portion 133. In other words, when the slider portion 132a is located on the base end side of the handle body 130, it extends between the operation portion 131 and the engagement portion 132b so as to bypass other internal members such as the liquid storage portion 133. This makes it possible to prevent interference of the slide bar portion 132a with other internal members such as the liquid storage portion 133 when the sliding operation is performed on the operation portion 131, and it is easy to miniaturize the entire handle 13.

In addition, the slide bar portion 132a and the engaging portion 132b are integrally formed with the aforementioned operation portion 131, for example. However, each of the slide bar portion 132a, the engaging portion 132b, and the operation portion 131 may be separately formed.

In this way, as shown in FIGS. 3 and 4, the sliding 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 sliding mechanism 132 (sliding bar portion 132a) and the liquid storage portion 133 are arranged in parallel (in this example, they are arranged in parallel along the Y-axis direction).

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

(Stream 110) Here, the configuration of the flow channel 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), inside the electrode needle 11, the flow path 110 is formed 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 indicated by the dotted 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 a path to the cooling liquid L Flow path when the proximal end side flows toward the distal end side), and a flow path 110b that is the return path of the cooling liquid L (flow path when flowing from the distal end side of the electrode needle 11 to the proximal end side).

In addition, such a flow path 110 corresponds to a specific example of the "flow path" of the present invention. In addition, the flow path 110a corresponds to a specific example of the "first flow path" of the present invention, and the flow path 110b corresponds to a specific example of the "second flow path" of 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 in the Z-axis direction (see FIG. 5(A)). In the symbol P3), the flow path 110a (forward path) is formed inside the electrode needle 11. As shown in FIGS. 5(A) and 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 (flow path 110), and the liquid delivery tube 81. Axis direction) configuration. Then, as shown in FIG. 5(A), the cooling liquid L is directly supplied into the inner tube 111 from the liquid supply tube 81.

With such a structure, the cooling liquid L flowing into the handle body 130 from the liquid supply tube 81 is not temporarily accommodated in the liquid storage portion 133, but directly (through the inner tube 111) flows toward the flow path Supply within 110a (refer to FIG. 5(A)). In addition, the cooling liquid L supplied from the flow path 110b serving as the return path is temporarily stored in the liquid storage portion 133, and then flows out of the handle body 130 into the drain pipe 82 (see FIG. 5(A)). With such a configuration, it is possible to provide a liquid supply pipe 81 and a liquid discharge pipe 82 branched from each other for flowing the cooling liquid L into the handle body 130, and the liquid discharge pipe 82 for cooling The liquid L is discharged from the handle body 130.

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

Moreover, 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), from the liquid supply device 2 (liquid supply Part 21) The liquid L is supplied to the electrode needle 11 (refer FIG. 1). Thereby, during the ablation, the electrode needle 11 is cooled, and as a result, an excessive increase in the temperature (tissue temperature) of the affected part 90 can be suppressed, and the abrupt rise in the aforementioned impedance value Zm due to tissue carbonization can be prevented .

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

In addition, as shown in FIGS. 2, 7 (A), and 7 (B), in such ablation, in the handle 13 of the ablation device 1, the operation portion 131 is previously subjected to the aforementioned sliding operation. Specifically, if the operation portion 131 is slid along the Z-axis direction (for example, refer to the arrow d1 in FIGS. 2 and 7(B)); in conjunction with the sliding operation of the operation portion 131, the The sliding mechanism 132 performs a sliding operation along the Z-axis direction (refer to arrow d0 in FIG. 7(B)). Then, in conjunction with the sliding action of the sliding mechanism 132, the insulating tube 12 also performs a sliding action along the Z-axis direction (for example, refer to arrow d2 in FIGS. 2 and 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 during ablation can also be arbitrarily adjusted. Range (corresponding to the range of 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 part 90 for ablation, whereby only the affected part 90 can be selectively Burning. That is, the part other than the affected part 90 is not burned, and the original function can be maintained. On the other hand, for example, when a large tumor is formed, by setting a large exposed area Ae (ablation range), the large tumor can be cauterized together (together).

In addition, the sliding operation of the operation unit 131 and the sliding operation of the sliding mechanism 132 and the insulating tube 12 linked to the sliding operation in this way 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 at the time of sliding can also be lightly fixed at a predetermined distance along the Z-axis direction.

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

That is, first, for example, in the radiology department, when performing ablation treatment on liver cancer, generally, an ablation device is used under CT scanning. In short, the ablation device is used when 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 the general handle of the ablation device in which the sliding mechanism 132 and the liquid storage portion 133 are connected in series in the handle body, if the size of the handle is so reduced (in the ablation device of the above-mentioned comparative example), it is as follows. That is, in the ablation device of this comparative example, although the overall size of the handle can be reduced, the electrode area (the exposed area Ae exposed from the insulating tube 12) at the tip of the electrode needle 11 can be along the axial direction (Z (Axis direction) The adjustment range is reduced. As described above, the electrode area (exposed area Ae) is equivalent to the ablation range when performing ablation with the electrode needle 11 (see FIGS. 7(A) and 7(B)); therefore, if the adjustment range of the ablation range is reduced , The convenience when using the ablation device may be impaired.

(C. This embodiment) In contrast, in the ablation device 1 of the present embodiment, as shown in FIG. 3, it is different from the ablation device of the above-mentioned comparative example and has the following structure. That is, the liquid accommodating portion 133 and the sliding mechanism 132 are arranged in parallel with each other in the handle body 130, the liquid accommodating portion 133 temporarily accommodates the cooling liquid L, and the sliding mechanism 132 is used to slide the insulating tube 12 in the Z-axis direction The established operation.

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

That is, first, the overall size of the 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, for example, 86 mm or less (Lz≦86 mm). In this regard, for example, if the overall size (axial length Lz) of the handle 13 is greater than 86 mm; as described above, the handle 13 and the CT scanning device may be operated when the patient enters the state of the circular CT scanning device contact. In addition, in consideration of securing the exposed area Ae (ablation range), the lower limit of the size (axial length Lz) of the entire handle 13 may be, for example, 30 mm. That is, in this case, 30mm≤Lz≤86mm is satisfied. In addition, in this ablation device 1, it is possible to avoid a reduction in the adjustable range of the electrode region (the exposed region Ae exposed from the insulating tube 12) located at the tip of the electrode needle 11 (see FIGS. 7(A) and 7(B)) . In short, in this ablation device 1, unlike the ablation device of the comparative example described above, it is possible to simultaneously achieve the miniaturization of the handle 13 as a whole and the expansion of the adjustable range of the electrode area (the ablation range described above).

As described above, in the ablation device 1 of the present embodiment, since the liquid accommodating portion 133 and the sliding mechanism 132 are arranged side by side in the handle body 130, it is possible to simultaneously achieve the miniaturization of the handle 13 as a whole and the adjustable ablation range The expansion of scope. Therefore, in this ablation device 1, compared with, for example, the ablation device of the comparative example described above, effective ablation can be performed, and as a result, convenience during use can be improved.

In addition, in the ablation device 1 of the present embodiment, the cooling liquid L flowing into the handle body 130 from the liquid delivery tube 81 is not temporarily stored in the liquid storage portion 133, but directly goes to the flow path 110a that becomes the forward path. (Inner tube 111) Internal supply (refer to FIG. 5(A)). In addition, the cooling liquid L supplied from the flow path 110b serving as the return path is temporarily stored in the liquid storage portion 133, and then flows out of the handle body 130 into the drain pipe 82 (see FIG. 5(A)). Thereby, as shown in FIG. 5(A), the liquid L (liquid L on the discharge side supplied from the flow path 110b) that is heated and temporarily contained in the liquid storage portion 133 during ablation, and the flow path 110a The supplied liquid L on the liquid-feeding 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 liquid L on the liquid sending side being heated. As a result, in this embodiment, the convenience when using the ablation device 1 can be further improved.

Furthermore, in the present 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 storage portion 133 and forms a flow path inside the electrode needle 11 110a (to the road). Then, the cooling liquid L is directly supplied into the inner tube 111 from the liquid supply tube 81 (see FIG. 5(A) ). Thereby, by the inner tube 111 constituting the flow path 110a penetrating the liquid accommodating portion 133 in the handle body 130, the handle 13 as a whole can be made more compact, and the liquid L (heated liquid L) on the discharge side can be suppressed The adverse effect (reduction of cooling effect) on the liquid L on the liquid sending side is minimized. As a result, in this embodiment, the convenience when using the ablation device 1 can be further improved.

<2. Modifications> Although the embodiments have been described above to describe the present invention, the present invention is not limited to the embodiments, and various changes can be made.

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

In addition, in the above-mentioned embodiment, although the configuration of the electrode needle, the insulating tube, the handle, and the like of the ablation device is specifically described, the configuration of these members is not limited to the contents described in the above-mentioned embodiment, and other configurations may be adopted. Specifically, for example, in some cases, the electrode needle is not a monopolar type described in the above embodiment, but may be a bipolar type. In addition, for example, on the liquid feed side described above, the cooling liquid may be temporarily stored in the liquid storage portion and then supplied into the flow path (first flow path). In addition, for example, in some cases, the aforementioned inner tube (forming the first flow path) may also be configured not to penetrate the liquid storage portion (a structure that bypasses the liquid storage portion into the flow path).

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

In addition, in the above-mentioned embodiment, although the ablation device that performs high-frequency energization 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, microwaves, and the like.

In addition, in the above-described embodiment, the control operation (ablation technique) of the control unit 33 including the power supply control function and the liquid supply control function has been specifically described. However, the control methods (ablation method) of the power supply control function, the liquid supply control function, etc. are not limited to the methods listed in the above embodiments.

In addition, the series of processing described in the above embodiment may be performed by hardware (circuit) or software (program). In the case of software, the software is composed of a group of programs for executing 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 and a recording medium.

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

1‧‧‧ablation device 11‧‧‧electrode needle 110, 110a, 110b 111‧‧‧Inner tube 12‧‧‧Insulation tube 13‧‧‧handle 130‧‧‧Handle body 131‧‧‧Operation part (sliding handle part) 132‧‧‧sliding mechanism 132a‧‧‧slider part (parallel part) 132b‧‧‧Joint 133‧‧‧Liquid container 2‧‧‧Liquid supply device 21‧‧‧Liquid Supply Department 3‧‧‧Power supply device 31‧‧‧Input 32‧‧‧Power Department 33‧‧‧Control Department 34‧‧‧Display 4‧‧‧Pole plate 5‧‧‧ablation system 81‧‧‧Liquid delivery tube 82‧‧‧Drainage tube 9‧‧‧Patient 90‧‧‧Affected Department L‧‧‧Liquid CTL1, CTL2‧‧‧Control signal Sm‧‧‧Operation signal Pout‧‧‧Electricity It‧‧‧Temperature Information Zm‧‧‧impedance Ae‧‧‧ exposed area (electrode area) Ah1, Ah2‧‧‧‧ thermal solidification area Lz‧‧‧Axial length

1 is a schematic block diagram of an example of the overall configuration of an ablation system provided with an ablation device according to an embodiment of the present invention. 2 is a schematic side view of a detailed configuration example of the ablation device shown in FIG. 1. 3 is a schematic side view of a configuration example of main parts inside the handle shown in FIG. 2. 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 of an internal configuration example of the vicinity of the liquid container shown in FIGS. 3 and 4 and the tip side of the electrode needle shown in FIG. 2. FIG. 6 is a schematic diagram of an example of a cauterized state formed on an affected part by ablation. 7 is a schematic side view of an example of sliding of the ablation device shown in FIG. 2.

1‧‧‧ablation device

12‧‧‧Insulation tube

13‧‧‧handle

130‧‧‧Handle body

131‧‧‧Operation part (sliding handle part)

132‧‧‧sliding mechanism

132a‧‧‧slider part (parallel part)

132b‧‧‧Joint

133‧‧‧Liquid container

Lz‧‧‧Axial length

Claims (4)

An ablation device includes: an electrode needle that punctures an affected part of the body percutaneously and is supplied with electric power for ablation; an insulating tube that exposes an electrode region on the tip side of the electrode needle and along the axis of the electrode needle Covering the periphery of the electrode needle; a flow path formed inside the electrode needle to allow cooling liquid to flow; and a handle installed on the base end side of the electrode needle, the handle having a handle body as an exterior; An operation portion performs a predetermined operation for sliding the insulating tube along the axial direction; a liquid storage portion is disposed in the handle body to temporarily accommodate the cooling liquid; and a sliding mechanism is provided in the handle body The liquid storage portion is arranged in parallel, and slides along the axial direction in conjunction with the predetermined operation performed on the operating portion, thereby sliding the insulating tube along the axial direction; the sliding mechanism includes: a sliding rod portion , The base end side of which is connected to the operation portion, and interlocks with the predetermined operation performed on the operation portion, slides in the handle body along the axial direction relative to the handle body; and an engaging portion engages the slide bar portion The distal end side of and the proximal end of the insulating tube, when the slide bar portion is located at the proximal end side of the handle body, 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 along the axial direction is 86 mm or less. The ablation device according to claim 1 or 2, wherein the flow path includes: The first flow path is a flow path when the cooling liquid flows from the base end side to the front end side of the electrode needle; and the second flow path is the cooling liquid from the front end side to the base end side of the electrode needle The flow path during the flow, the cooling liquid flowing into the handle body from the liquid supply tube is not temporarily stored in the liquid storage portion, but is directly supplied into the first flow path and from the second flow path After the cooling liquid supplied inside is temporarily contained in the liquid storage portion, it flows out of the handle body into the drain tube. The ablation device according to claim 3, further comprising an inner tube that penetrates the liquid storage portion in the handle body, is disposed along the axial direction inside the electrode needle, and constitutes the first flow path, The cooling liquid is directly supplied into the inner tube from the liquid feed tube.

Images