阅读说明：本技术 消融器件 (Ablation device ) 是由 森谦二 儿玉祐贵 于 2018-09-28 设计创作，主要内容包括：本发明提供一种可以提高便利性的消融器件。消融器件(1)具备：电极针(11),对体内患部(90)经皮穿刺,并且被供给用于进行消融的电力(Pout)；流路(110),形成在电极针(11)的内部,有冷却用的液体(L)流动；第一温度测量元件(温度测量元件115a),配置在流路(110)内；第二温度测量元件(温度测量元件115b),在电极针(11)的内部,并且配置在电极针(11)的前端附近；以及手柄(13),安装在电极针(11)的基端侧。(An ablation device (1) is provided with an electrode needle (11) which percutaneously punctures an affected part (90) in a body and to which power (Pout) for ablation is supplied, a flow path (110) which is formed inside the electrode needle (11) and through which a cooling liquid (L) flows, a first temperature measurement element (temperature measurement element 115a) which is disposed inside the flow path (110), a second temperature measurement element (temperature measurement element 115b) which is disposed inside the electrode needle (11) and in the vicinity of the tip of the electrode needle (11), and a handle (13) which is attached to the proximal end side of the electrode needle (11).)

1. An ablation device, comprising:

an electrode needle which percutaneously punctures an affected part in a body and to which power for ablation is supplied;

a flow path formed inside the electrode needle and through which a cooling liquid flows;

a first temperature measuring element disposed in the flow path;

a second temperature measuring element disposed inside the electrode needle and in the vicinity of the tip of the electrode needle; and

and a handle mounted on a proximal end side of the electrode needle.

2. The ablation device of claim 1,

the second temperature measuring element is disposed in a region formed in the vicinity of the tip inside the electrode needle,

in the region, at least in the vicinity of the region where the second temperature measurement element is disposed, a heat conductive material is buried and sealed, and

the vicinity of the front end inside the electrode needle is joined to the arrangement region of the second temperature measurement element via the heat conductive material.

Technical Field

The present invention relates to an ablation device provided with an electrode needle for percutaneous puncture of an affected part in a body.

Background

As one of medical devices for treating an affected part in a patient's body (e.g., an affected part having a tumor such as cancer), an ablation system for ablating (cauterizing) such an affected part has been proposed (see, for example, patent document 1). The ablation system is provided with: an ablation device having an electrode needle for percutaneous puncture of an affected part in a body, and a power supply device for supplying electric power for ablation of the affected part.

Disclosure of Invention

However, the ablation device described above is generally required to improve convenience in use, for example. Accordingly, 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 which percutaneously punctures an affected part in a body and to which power for ablation is supplied; a flow path formed inside the electrode needle and through which a cooling liquid flows; a first temperature measuring element disposed in the flow path; a second temperature measuring element inside the electrode needle and disposed near a tip end of the electrode needle; and a handle attached to the proximal end side of the electrode needle.

In the ablation device according to the one embodiment of the present invention, the first temperature measurement element disposed in the flow path through which the cooling liquid flows and the second temperature measurement element disposed in the vicinity of the distal end of the electrode needle are provided inside the electrode needle. Thus, when the ablation is performed with the electrode percutaneously inserted into the affected part, the temperature of the cooling liquid is measured by the first temperature measuring element, and the temperature of the affected part is measured by the second temperature measuring element. That is, at the time of ablation, both the temperature of the cooling liquid and the temperature of the affected part can be measured at the same time (concurrently).

In the ablation device according to the one embodiment of the present invention, a seal member may be further provided inside the electrode needle to separate the flow path from the region where the second temperature measurement element is disposed. In this case, since the cooling liquid can be prevented from flowing into the vicinity of the region where the second temperature measurement element is disposed, the accuracy of measuring the temperature of the affected part of the second temperature measurement element can be improved. The result is: the convenience in using the ablation device can be further improved.

In the ablation device according to the one embodiment of the present invention, the second temperature measuring element may be disposed in a region formed in the vicinity of the distal end inside the electrode needle; a region in which a heat conductive material is embedded and sealed at least in the vicinity of the region in which the second temperature measurement element is disposed; and the vicinity of the tip inside the electrode needle and the arrangement region of the second temperature measurement element are joined to each other through the heat conductive material. In doing so, since the temperature difference between the vicinity of the affected part and the second temperature measurement element can be reduced, the temperature measurement accuracy of the affected part of the second temperature measurement element can be improved. The result is: the convenience in using the ablation device can be further improved.

In this case, the region may communicate with the outside of the electrode needle. In this case, since air can be prevented from accumulating in the region, the temperature measurement accuracy of the affected part of the second temperature measurement element can be further improved. The result is: the convenience in using the ablation device can be further improved.

According to the ablation device of one embodiment of the present invention, since the first temperature measuring element and the second temperature measuring element are provided inside the electrode needle, both the temperature of the cooling liquid and the temperature of the affected part can be measured at the same time during the ablation. Therefore, convenience in using the ablation device can be improved.

Drawings

Fig. 1 is a schematic block diagram of an example of the overall structure of an ablation system provided with an ablation device of an embodiment of the present invention.

Fig. 2 is a schematic side view of a detailed structural example of the ablation device shown in fig. 1.

Fig. 3 is a schematic cross-sectional view of an example of the internal structure of the tip side of the electrode needle shown in fig. 2.

Fig. 4 is a schematic view showing an example of a cauterization state formed at a diseased part by ablation.

Fig. 5 is a schematic side view of one example of a sliding action of the ablation device shown in fig. 2.

Fig. 6 is a schematic cross-sectional view of an example of the internal structure of the tip side of the electrode needle of the ablation device of the modification.

Detailed Description

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. The following description is made in the order described below.

1. Embodiment (example of the case where the region near the tip inside the electrode needle communicates with the outside)

2. Modification (example in which the region near the tip inside the electrode needle does not communicate with the outside)

3. Other modifications

<1 > embodiment >

[ Overall Structure of ablation System 5 ]

Fig. 1 is a schematic block diagram of an example of the overall structure of an ablation system 5 provided with an ablation device (ablation device 1) of an embodiment of the present invention. As shown in fig. 1, the ablation system 5 is a system used for treating an affected part 90 in a patient 9, and performs predetermined ablation (cauterization) on such an affected part 90.

The affected part 90 may be 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 apparatus 2, and a power supply apparatus 3. In addition, the counter electrode plate 4 shown in fig. 1 can be suitably used for ablation using the ablation system 5.

(ablation device 1)

The ablation device 1 is used for the ablation, 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 for percutaneous puncture of an affected area 90 in the body of the patient 9 as indicated by an arrow P1 in fig. 1, and a liquid L supplied from a liquid supply device 2 (described later) circulates inside the electrode needle 11 (see fig. 1).

The insulating tube 12 exposes an electrode region (exposure region Ae described later) located on the distal 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 the ablation device 1 will be described later (see fig. 2 and 3).

(liquid supply apparatus 2)

The liquid supply device 2 is a device for supplying the liquid L for cooling to the ablation device 1 (inside the electrode needle 11), and has, for example, a liquid supply unit 21 as shown in fig. 1, and examples of the liquid L for cooling include, for example, sterile water, sterile physiological saline, and the like.

The liquid supply unit 21 supplies the liquid L to the ablation device 1 as needed under control based on a control signal CT L2 described later, specifically, for example, as shown in fig. 1, the liquid supply unit 21 performs a liquid L supplying operation so 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), and the liquid supply unit 21 performs or stops such a liquid L supplying operation under control based on the control signal CT L2, and the liquid supply unit 21 is configured to include, for example, a liquid pump.

(Power supply device 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 the supply operation of the liquid L by the liquid supply device 2, and 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 operation described later. Such an operation signal Sm is input from the input unit 31 in response to an operation by an operator (e.g., an engineer) of the power supply apparatus 3. However, these setting values may be set in the power supply device 3 in advance, for example, at the time of shipment of a product, without being input according to an operation by an operator. The set value input through 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 is configured by using a predetermined power supply circuit (e.g., a switching regulator) such that the power supply unit 32 supplies the electric power Pout between the electrode needle 11 and the counter electrode 4 in accordance with a control signal CT L1 described later, and when the electric power Pout is configured by high-frequency electric power, the frequency is, for example, about 450kHz to 550kHz (e.g., 500 kHz).

Specifically, the control unit 33 first has a function (electric power supply control function) of controlling the supply operation of the electric power Pout of the power supply unit 32 using the control signal CT L1, and the control unit 33 has a function (liquid supply control function) of controlling the supply operation of the liquid L of the liquid supply device 2 (liquid supply unit 21) using the control signal CT L2.

As shown in fig. 1, for example, temperature information It1 and It2 measured in the ablation device 1 (temperature measurement elements 115a and 115b described later) are supplied to the control unit 33 as needed. As shown in fig. 1, the measured value of the impedance value Zm is supplied from the power supply unit 32 to the control unit 33 as needed.

The display unit 34 is a part (monitor) for displaying various information and outputting the information to the outside, and examples of the information to be displayed include the various setting values input from the input unit 31, various parameters supplied from the control unit 33, and temperature information It1, It2 supplied from the ablation device 1, but the information to be displayed is not limited to these information, and other information may be displayed instead of or in addition to the information to be displayed, and such a display unit 34 is configured using various types of displays (for example, a liquid crystal display, a crt (cathode Ray tube) display, an organic E L (Electro L) display, and the like).

(opposite pole plate 4)

The counter electrode plate 4 is used in a state of being attached to the body surface of the patient 9 at the time of ablation, for example, as shown in fig. 1. During ablation, high-frequency energization (supply power Pout) is performed between the electrode needle 11 (the electrode region) of the ablation device 1 and the pair of electrode plates 4, which will be described in detail later. In 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 unit 33 in the power supply device 3, which 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 and 3. Fig. 2 is a schematic side view (Y-Z side view) of a detailed structural example of the ablation device 1 shown in fig. 1. Fig. 3 is a schematic cross-sectional view (Y-Z cross-sectional view) of an example of the internal structure of the distal end side of the electrode needle 11 shown in fig. 2. In fig. 2, as indicated by arrows, an enlarged view of a portion indicated by a reference character P2 (a partial region of the electrode pin 11 and the insulating tube 12) is shown below in fig. 2.

(electrode needle 11)

As shown in fig. 2 and 3, 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 30mm to 350 mm. The electrode needle 11 includes, in the axial direction (Z-axis direction): an exposed region Ae on the distal end side (an electrode region functioning as an electrode at the time of ablation) not covered with the insulating tube 12, and a region covered with the insulating tube 12 (a covered region on the proximal end side). As described above, the electric power Pout for ablation is supplied between the exposed region Ae of the electrode needle 11 and the counter electrode plate 4. The electrode needle 11 is made of a metal material such as stainless steel, nickel-titanium alloy, or platinum.

Here, for example, as shown in fig. 3, the internal structure of the tip end side of the electrode needle 11 is as follows. That is, inside the electrode needle 11, a flow path 110, an inner tube 111, regions (holes) 112a,112b, a heat conductive material 113, a sealing member 114, and temperature measurement elements 115a,115b are provided.

Specifically, as shown by a broken line arrow in fig. 3, the cooling liquid L circulates inside the electrode needle 11 in the flow path 110, and in other words, the flow path 110 is provided with a flow path that is an outward flow path of the cooling liquid L (a flow path when the cooling liquid flows from the base end side to the distal end side of the electrode needle 11), and a flow path that is a return flow path of the cooling liquid L (a flow path when the cooling liquid flows from the distal end side to the base end side of the electrode needle 11).

The inner tube 111 is provided along the axial direction (Z-axis direction) of the electrode needle in the flow path 110, and the inner tube 111 is configured as a flow path of the aforementioned outward path of the cooling liquid L, for example, as shown in fig. 3.

The regions 112a,112b are formed in the vicinity of the front end inside the electrode needle 11, respectively, and extend in the axial direction (Z-axis direction) of the electrode needle. As shown in fig. 3, the region 112b is formed in the vicinity of the foremost end inside the electrode needle 11, and communicates with the outside of the front end side of the electrode needle 11 and the region 112a, respectively. The region 112a is formed on the proximal end side of the electrode needle 11 with respect to the region 112b, and communicates with the region 112b as described above.

The heat conductive material 113 is filled at least in the vicinity of the arrangement region of the temperature measuring element 115b described later in the regions 112a and 112 b. Specifically, in this example, as shown in fig. 3, the heat conductive material 113 is embedded in a region 112b (the vicinity of the distal end inside the electrode needle 11) of these regions 112a and 112 b. Thereby, the region 112b is sealed (the portion corresponding to the hole of the region 112b is blocked), and the vicinity of the tip inside the electrode needle 11 and the arrangement region of the temperature measurement element 115b described later are joined by the heat conductive material 113. However, in some cases, the heat conductive material 113 may be embedded in both the regions 112a and 112 b. The heat conductive material 113 is made of a material having high heat conductivity, such as solder (solder) or a brazing material.

As shown in fig. 3, the sealing member 114 separates an arrangement region (region on the side of the regions 112a and 112b in this example) of the temperature measuring element 115b described later from the flow path 110, in other words, the sealing member 114 prevents (seals) the cooling liquid L flowing through the flow path 110 from flowing into the regions 112a and 112b, and such a sealing member 114 is arranged in the vicinity of the tip of the flow path 110 and is made of a thermosetting resin such as an epoxy resin, a urethane resin, a silicone resin, or a phenol resin, or a metal material such as solder or a brazing material.

Specifically, in this example, the temperature measuring element 115a is disposed in the inner tube 111, and the inner tube 111 constitutes the aforementioned forward flow path, and the temperature measuring element 115a measures the temperature of the cooling liquid L flowing through the flow path 110, and in this example, measures the temperature of the cooling liquid L flowing from the proximal end side to the distal end side in the electrode needle 11.

As shown in fig. 3, the temperature measuring element 115b is disposed inside the electrode needle 11 and near the tip of the electrode needle 11. Specifically, in this example, the temperature measuring element 115b is disposed in the region 112b (the vicinity of the distal end inside the electrode needle 11). The temperature measuring element 115b measures the temperature (tissue temperature) of the affected part 90 at the time of ablation.

Here, for example, if the distance from the flow path 110 to the temperature measuring element 115b (the Z-axis length of the region 112a) is too short, the temperature measuring element 115b is cooled by the cooling liquid L, and the temperature measuring accuracy of the affected part 90 of the temperature measuring element 115b may be degraded, whereas, if the distance from the flow path 110 to the temperature measuring element 115b (the Z-axis length of the region 112a) is too long, the cooling effect of the liquid L may be insufficient at the time of ablation, and as a result, the affected part 90 is rapidly carbonized, and the ablation range may become small, and as is clear from the above, the distance from the flow path 110 to the temperature measuring element 115b (the Z-axis length of the region 112a) is, for example, preferably about 0mm to 10mm, and more preferably about 0.2mm to 1.0 mm.

The temperature measuring elements 115a and 115b are each configured using, for example, a thermocouple, and the temperature information It1 (information indicating the temperature of the cooling liquid L) is output from the temperature measuring element 115a, and the temperature information It2 (information indicating the temperature of the affected part 90) is output from the temperature measuring element 115 b.

Here, the temperature measuring element 115a corresponds to a specific example of the "first temperature measuring element" of the present invention. In addition, the temperature measuring element 115b corresponds to a specific example of the "second temperature measuring element" of the present invention.

(insulating 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. Further, the insulating tube 12 is configured to: as shown by an arrow d2 in fig. 2, the electrode needle 11 is slidable in the axial direction (Z-axis direction) in response to a predetermined operation of a handle 13 described later. This makes it possible to adjust the length (axial length) of the exposed region Ae of the electrode needle 11 along the Z-axis direction.

The length (axial length) of the exposed region Ae of the electrode needle 11 along the Z-axis direction, which can be adjusted by the insulating tube 12, is, for example, about 3mm to 50 mm. The insulating tube 12 is made of synthetic resin such as PEEK (polyether ether ketone), PI (polyimide), fluorine resin, or 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 (handle member) 130 attached to the proximal end side of the electrode needle 11, and an operation portion 131.

The handle body 130 also functions as an outer decoration of the handle 13, corresponding to a portion (grip portion) actually gripped by the operator. The handle body 130 is made of a synthetic resin such as polycarbonate, acrylonitrile-butadiene-styrene (ABS), acrylic, polyolefin, or polyoxymethylene.

The operation portion 131 is a portion used at the time of a predetermined operation (sliding operation) for sliding the insulating tube 12 along the axial direction (Z-axis direction) thereof with respect to the electrode needle 11, and protrudes outward (Y-axis direction) of the handle main body 130. The operation portion 131 is made of the same material (synthetic resin or the like) as the handle body 130 described above, for example. 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 of the operation unit 131 (see, for example, arrow d1 in fig. 2), the insulating tube 12 is slid in the Z-axis direction with respect to the electrode needle 11 (see, for example, arrow d2 in fig. 2), which will be described in detail later. This makes it possible to adjust the length (axial length) of the exposed region Ae of the electrode needle 11 along the Z-axis direction.

[ actions and actions/effects ]

(A, basic action)

In the ablation system 5, when an affected part 90 having a tumor such as cancer is to be treated, the affected part 90 is ablated as specified (see fig. 1). In such ablation, first, as indicated by an arrow P1 in fig. 1, the electrode needle 11 of the ablation device 1 is percutaneously punctured from the distal end side (exposed region Ae side) of the affected part 90 in the body of the patient 9. Then, electric power Pout (for example, high-frequency electric power) is supplied from the power supply device 3 (power supply unit 32) between the electrode needle 11 and the counter electrode plate 4, whereby the affected part 90 is ablated by joule heating.

In addition, at the time of such ablation, the liquid L (see fig. 1) is supplied from the liquid supply device 2 (liquid supply unit 21) to the electrode needle 11 so that the liquid L for cooling circulates between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (inside the aforementioned flow path 110), whereby the electrode needle 11 is cooled (cooling) at the time of ablation, and as a result, an excessive increase in the temperature of the affected area 90 (tissue temperature) can be suppressed, and a rapid increase in the aforementioned impedance value Zm due to charring of the tissue can be prevented.

The temperature (cauterization temperature) of the affected part 90 during such ablation is usually 40 to 100 ℃, preferably 50 to 80 ℃. Here, if the cauterization temperature is too low, the affected part 90 cannot be reliably heat-coagulated. On the other hand, if the cauterization temperature is too high, charring of the tissue of the affected part 90 occurs, and the impedance value Zm rapidly rises, so that the current is not easily flowed, and as a result, the ablation range may become small.

Fig. 4 is a schematic view showing an example of a cauterization state formed at the affected part 90 by such ablation. As shown in fig. 4, if the ablation is performed using the electrode needle 11 inserted into the affected part 90; a substantially spherical thermal solidification region Ah2 (see the dotted arrow in fig. 3) can be obtained by, for example, gradually diffusing the initially football-shaped (elliptical sphere-shaped) thermal solidification region Ah 1. Accordingly, the affected part 90 can be effectively treated by performing isotropic ablation on the entire affected part 90.

For example, as shown in fig. 2, 5(a), and 5(B), in such ablation, the above-described sliding operation of the operation portion 131 is performed in advance in the handle 13 of the ablation device 1. Specifically, if the operation unit 131 is slid in the Z-axis direction (see, for example, arrow d1 in fig. 2 and 5B); then, in conjunction with the sliding operation of the operation unit 131, the sliding mechanism 132 in the handle body 130 slides in the Z-axis direction (see fig. 5a and 5B). Then, in conjunction with the sliding operation of the sliding mechanism 132, the insulating tube 12 also slides in the Z-axis direction (see, for example, arrow d2 in fig. 2 and 5B). Thus, for example, as shown in fig. 5a and 5B, the size (length along the Z-axis direction) of the exposed region Ae on the distal end side of the electrode needle 11 can be arbitrarily adjusted, and the ablation range (range corresponding to the exposed region Ae) at the time of ablation can be arbitrarily adjusted.

Thus, for example, when a small tumor is formed in a deep region of the liver, the exposed region Ae (ablation range) is set to be small, and the distal end of the electrode needle 11 is inserted into the affected part 90 to be ablated, whereby only the affected part 90 can be selectively cauterized. That is, the portion other than the affected part 90 is not cauterized, and the original function can be maintained. On the other hand, for example, when a large tumor is formed, by setting a large exposure area Ae (ablation range), the large tumor can be cauterized together (at once).

The sliding operation of the operation unit 131 and the sliding operation of the sliding mechanism 132 and the insulating tube 12 in conjunction with the sliding operation may be adjusted stepwise (intermittently) in the axial direction (Z-axis direction) of the electrode needle 11. In other words, the positions of the operation portion 131, the sliding mechanism 132, and the insulating tube 12 during sliding may be slightly fixed at predetermined distances along the Z-axis direction.

(B. comparative example)

In the ablation device 1 of the present embodiment shown in fig. 2 and 3, only 1 (1) temperature measurement element (element for measuring the temperature of the cooling liquid L) is provided inside the electrode needle 11.

However, when the ablation device of the comparative example is used, the following problems may occur when ablation is performed in a state where the electrode needle 11 has punctured the affected part 90 percutaneously.

That is, the ablation device of this comparative example measures only the temperature of the cooling liquid L, and does not measure the temperature of the affected part 90 (tissue temperature) at the time of ablation as described above, in other words, cannot measure both the temperature of the cooling liquid L and the temperature of the affected part 90 at the same time (concurrently) at the time of ablation of this comparative example.

As such, in the case of using the ablation device of the comparative example, it is not easy to perform effective ablation, with the result that: the convenience of using the ablation device may be compromised.

(C. this embodiment mode)

In contrast, in the ablation device 1 of the present embodiment, as shown in fig. 3, unlike the ablation device of the comparative example described above, the following 2 types of temperature measuring elements 115a and 115b are provided inside the electrode needle 11, that is, the temperature measuring element 115a disposed in the flow path 110 through which the cooling liquid L flows and the temperature measuring element 115b disposed in the vicinity of the tip of the electrode needle 11 are provided inside the electrode needle 11 of the ablation device 1.

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 follows.

That is, when ablation is performed in a state where the electrode needle 11 has punctured the affected part 90 percutaneously, the temperature of the cooling liquid L is measured by the temperature measuring device 115a, and the temperature of the affected part 90 (tissue temperature) is measured by the temperature measuring device 115 b.

In this way, in the present embodiment, since the temperature of the cooling liquid L and the temperature of the affected part 90 can be measured at the same time, effective ablation can be performed in such a manner that, for example, a temperature increase of the cooling liquid L can be noticed on the basis of the temperature information It1 measured by the temperature measuring element 115a, in this case, for example, an insufficient cooling operation (cooling) for the electrode needle 11 can be prevented by cooling the cooling liquid L, and at the same time, a cauterized state of the affected part 90 such as whether the temperature of the tissue of the affected part 90 has sufficiently increased or excessively increased can be confirmed on the basis of the temperature information It2 measured by the temperature measuring element 115b, and thus, ablation can be performed while maintaining an appropriate temperature by controlling the supply of the electric power Pout, for example, and as a result, a sharp increase in the impedance value Zm due to the affected part 90 can be prevented, and a sufficient ablation range for the affected part 90 can be secured.

As described above, in the ablation device 1 of the present embodiment, since the 2 temperature measurement elements 115a and 115b are provided inside the needle electrode 11, both the temperature of the cooling liquid L and the temperature of the affected part 90 can be measured at the same time during ablation using the needle electrode 11, and therefore, in the ablation device 1, effective ablation can be performed as compared with the ablation device of the comparative example described above, for example, and as a result, the convenience in use can be improved.

In the present embodiment, as shown in fig. 3, since the sealing member 114 for separating the region where the temperature measurement element 115b is disposed from the flow path 110 is provided inside the electrode needle 11, the cooling liquid L can be prevented from flowing into the vicinity of the region where the temperature measurement element 115b is disposed (the region on the side of the regions 112a and 112b), and therefore the accuracy of measuring the temperature of the affected part 90 of the temperature measurement element 115b can be improved, and as a result, the convenience in using the ablation device 1 can be further improved.

Further, in the present embodiment, as shown in fig. 3, the temperature measuring element 115b is disposed in the region 112b inside the electrode needle 11. In the region 112b, a heat conductive material 113 is embedded and sealed at least in the vicinity of the region where the temperature measuring element 115b is disposed (in the region 112b), and the vicinity of the tip inside the electrode needle 11 and the region where the temperature measuring element 115b is disposed are joined to each other via the heat conductive material 113. Thus, the temperature difference between the vicinity of the affected part 90 and the temperature measuring element 115b can be reduced, and therefore the accuracy of measuring the temperature of the affected part 90 by the temperature measuring element 115b can be improved. The result is: the convenience in using the ablation device 1 can be further improved.

In the present embodiment, as shown in fig. 3, the region 112b (the region where the temperature measuring element 115b is disposed) communicates with the outside of the electrode needle 11. This can prevent air or the like from accumulating in the region 112b (air accumulation), for example, and therefore can further improve the accuracy of temperature measurement of the affected part 90 of the temperature measuring device 115 b. The result is: the convenience in using the ablation device 1 can be further improved.

<2. modification >

Next, a modified example of the above embodiment will be described. The same components as those in the embodiment are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

Fig. 6 is a schematic cross-sectional view (Y-Z side view) of an example of the internal structure of the tip side of the electrode needle 11A of the ablation device (ablation device 1A) of the modification.

The ablation device 1A of the present modification corresponds to the ablation device 1 of the embodiment, in which the electrode needle 11A is provided instead of the electrode needle 11, and the other configurations are the same. In the electrode needle 11 (see fig. 3), a region (region 112b) where the temperature measuring element 115b is disposed communicates with the outside of the electrode needle 11. On the other hand, in the electrode needle 11A, as shown in fig. 6, the region (region 112a) where the temperature measuring element 115b is disposed does not communicate with the outside of the electrode needle 11A. In short, the region 112b communicating with the outside is not formed in the electrode needle 11A, and the temperature measuring element 115b is disposed in the region 112a as a closed cavity in the electrode needle 11A.

However, in the present modification, the temperature measuring element 115b is also disposed near the tip of the electrode needle 11A (in the example shown in fig. 6, near the foremost end in the region 112a) so as to be able to measure the temperature of the affected part 90 with high accuracy. In the present modification, the heat conductive material 113 is also embedded in the region 112a at least in the vicinity of the region where the temperature measurement element 115b is disposed (in the example shown in fig. 6, the entire region in the region 112 a). In the present modification, a sealing member 114 for separating the arrangement region of the temperature measuring element 115b (in the region 112a) from the flow channel 110 is also provided inside the electrode needle 11A.

In the ablation device 1A (electrode needle 11A) of the present modification, similarly to the ablation device 1 (electrode needle 11) of the embodiment, as described below, for example, if the distance from the flow path 110 to the temperature measurement element 115b (the Z-axis length of the region 112a) is too short, the temperature measurement element 115b is cooled by the cooling liquid L, and the accuracy of temperature measurement of the affected part 90 of the temperature measurement element 115b may be degraded, whereas if the distance from the flow path 110 to the temperature measurement element 115b (the Z-axis length of the region 112a) is too long, for example, the cooling effect of the liquid L may be insufficient during ablation, and as a result, the affected part 90 is rapidly carbonized, and the ablation range may be narrowed.

In the ablation device 1A of the present modification example having such a configuration, since the 2 temperature measurement elements 115a and 115b are also provided inside the electrode needle 11A, the same effects can be obtained by the operation basically similar to that of the embodiment. That is, in the ablation device 1A, as compared with the ablation device of the comparative example described above, for example, effective ablation can be performed, and as a result, the convenience in use can be improved.

<3 > other modifications

Although the present invention has been described above by way of examples of the embodiments and modifications, the present invention is not limited to these embodiments and the like, and various modifications are possible.

For example, the material of each member described in the above embodiments and the like is not limited, and other materials may be used. Specifically, for example, the heat conductive material may be composed of a thermosetting resin such as an epoxy resin, a urethane resin, a silicone resin, or a phenol resin in some cases. In the above-described embodiments and the like, the configuration of the ablation device and the like has been specifically described, but it is not always necessary to provide all the components, and other components may be further provided. The values, ranges, size relationships, and the like of the various parameters described in the above embodiments and the like are not limited to those described in the above embodiments and the like, and may be other values, ranges, size relationships, and the like.

In the above-described embodiments and the like, the configurations of the electrode needle, the insulating tube, the handle, and the like of the ablation device are specifically described, but the configurations of these components are not limited to those described in the above-described embodiments and the like, and other configurations may be adopted. Specifically, for example, in some cases, the electrode needle may be bipolar instead of the unipolar type described in the above embodiment and the like. In addition, the insulating tube may not be slidable in the axial direction of the electrode needle. The number, type, arrangement position, and the like of the temperature measuring elements are not limited to those described in the above embodiments, and other configurations may be adopted. In some cases, for example, a sealing member or a heat conductive material may not be provided.

Further, in the above-described embodiments and the like, the module configurations of the liquid supply apparatus 2 and the power supply apparatus 3 are specifically described, but the modules described in the above-described embodiments and the like are not necessarily required to be provided, and other modules may be further provided. In addition, the entire ablation system 5 may be provided with other devices in addition to the respective devices described in the above embodiments and the like.

In the above-described embodiments and the like, the ablation device in which high-frequency energization is performed between the electrode needle 11 and the counter electrode plate 4 at the time of ablation has been specifically described; however, the present invention is not limited to the above embodiments. Specifically, an ablation device that performs ablation using other electromagnetic waves such as radio waves and microwaves may be used.

In the above-described embodiments and the like, the control operation (ablation technique) of the control unit 33 including the power supply control function and the liquid supply control function is specifically described. However, the control methods (ablation methods) for the power supply control function, the liquid supply control function, and the like are not limited to those described in the above embodiments and the like.

Note that the series of processing described in the above embodiments and the like may be performed by hardware (a circuit) or may be performed by software (a program). In the case of software, the software is constituted by a group of programs for executing various functions by a computer. The various programs may be, for example, pre-installed in the computer and used, or may be installed in the computer through a computer network or a recording medium and used.

Further, the above examples can be applied in any combination.