JP5682654B2 - Fluid ejecting apparatus and surgical instrument - Google Patents

Description

  The present invention relates to a fluid ejecting apparatus that ejects fluid at a high speed, and more particularly, to a fluid ejecting apparatus and a fluid ejecting apparatus that are suitable for controlling a fluid ejecting operation according to a contact state between an ejection target and an ejection tip. The present invention relates to a driving method and a surgical instrument.

Conventionally, as a fluid ejecting apparatus for incising or excising a living tissue, there is a fluid ejecting apparatus by the present inventors (see Patent Document 1).
The fluid ejecting apparatus includes a pulsation including a fluid chamber whose volume can be changed, an inlet channel and an outlet channel communicating with the fluid chamber, and a volume changing unit that changes the volume of the fluid chamber in response to supply of a drive signal. A connecting channel having a fluid ejection opening (nozzle) having one end communicating with the generating unit and the outlet channel and the other end being smaller than the diameter of the outlet channel; Is provided with a rigid connection channel pipe capable of transmitting the pulsation of the fluid flowing from the fluid chamber to the fluid ejection opening, and a pressure generator for supplying the fluid to the inlet channel. A fluid is supplied to the inlet channel at a constant pressure, and the volume changing unit changes the volume of the fluid chamber to generate pulsation and perform a fluid discharging operation.
When the volume of the fluid chamber of the fluid ejecting apparatus is not changed, the fluid flows in a state where the supply pressure from the pressure generating unit and the flow path resistance are balanced. In this state, the discharge of fluid from the nozzle is continuous, and since the speed is low, there is almost no ability to cut tissue.

On the other hand, when the fluid chamber is rapidly reduced, the pressure in the fluid chamber increases. At that time, since the increase amount of the fluid discharged from the outlet channel is larger than the decrease amount of the flow rate of the fluid flowing from the inlet channel into the fluid chamber, a pulsating flow is generated in the connection channel. The pressure fluctuation at the time of discharge propagates through the connection flow channel pipe, and the fluid is ejected at high speed from the fluid ejection opening of the nozzle at the tip.
By repeating this operation, fluid can be discharged by a high-speed pulse jet. By performing the expansion / contraction operation of the fluid chamber with a piezoelectric element, it is possible to start and stop within a few [msec] or less.
The same applies to the fluid ejecting apparatus according to another invention (see Patent Document 2) in which the pressure generating unit by the applicants is unnecessary.

JP 2008-82202 A JP 2005-152127 A

However, when the above-described conventional fluid ejecting apparatus is applied to an operation as, for example, a water knife, the operation is performed with the nozzle almost in close contact with the affected area. For this reason, when the nozzle moves away from the affected area while ejecting the fluid at high pressure, the droplets may be scattered by the fluid ejection, and the excised tissue pieces such as cancer cells may be scattered around.
Therefore, the present invention has been made paying attention to such an unsolved problem of the prior art, and controls the fluid ejection operation according to the contact state between the ejection object and the ejection tip. It is an object of the present invention to provide a fluid ejecting apparatus, a driving method for the fluid ejecting apparatus, and a surgical instrument suitable for the above.

[Form 1]
To achieve the above object, a fluid ejecting apparatus according to aspect 1 includes a fluid chamber whose volume can be changed,
An inlet channel and an outlet channel communicating with the fluid chamber;
Volume changing means for changing the volume of the fluid chamber;
Fluid supply means for supplying fluid to the inlet channel;
A fluid ejection opening provided at an end of the outlet channel opposite to the end communicating with the fluid chamber;
A first electrode having a predetermined polarity having a conductive first contact portion serving as a power supply portion provided in the fluid ejection opening or a member in the vicinity thereof;
A second electrode having a polarity different from the predetermined polarity to be paired with the first electrode, the second electrode having a conductive second contact part serving as a power supply unit;
Energization determining means for determining whether or not the first electrode and the second electrode are energized;
Operation control means for controlling the operation of the volume changing means based on the determination result of the energization determining means.

  With such a configuration, for example, the fluid ejection opening or a member in the vicinity thereof is ejected in the same manner in a state in which the second contact portion is brought into contact with a fluid ejection target capable of flowing a current such as a human body. When contact is made with an object that can be connected to the injection target, such as the target or liquid in the vicinity thereof, the first contact portion provided in the fluid injection opening or a member in the vicinity thereof can be connected to the injection target or this. Touching an object. As a result, the first electrode and the second electrode are energized through the injection object or the injection object and the object that can be conducted therewith, and the energization determining unit determines that the current is energized.

On the other hand, when at least one of the first contact portion or the second contact portion is separated from the injection target object or the object that can be conducted therewith, the first electrode and the second electrode are not energized. It is determined that the power is not supplied.
That is, when the second contact portion is in contact with the injection target and the fluid injection opening or a member in the vicinity thereof is in contact with the injection target or an object that can be conducted therewith, the first The first electrode and the second electrode are not energized when the electrode and the second electrode are energized and are not in contact with the object to be ejected or the object that can be conducted therewith.
When it is determined that the energization determining unit is energized, the operation control unit can control the operation based on the determination result so that, for example, the volume changing unit can change the volume.

Further, when the operation control unit determines that the energization determining unit is not energized, based on the determination result, for example, the operation control unit controls the operation so that the volume changing unit cannot perform the volume changing operation, It is possible to control the operation so as to weaken the injection force.
Therefore, when the first electrode and the second electrode are not energized, the ejection operation can be prevented or the ejection force can be weakened, so that the fluid ejection opening or a member in the vicinity thereof can be used. When an operator (for example, a practitioner) moves away from an object to be ejected or an object that can communicate with the object, the fluid is ejected in an unexpected direction or the excised material is scattered. Can be prevented.

[Form 2]
Further, the fluid ejecting apparatus according to aspect 2 is the attachment means capable of attaching the second electrode so that the second contact portion contacts the fluid ejection object in the fluid ejecting apparatus according to aspect 1. Is provided.
If it is such a structure, a 2nd electrode can be attached by an attachment means, for example so that a 2nd contact part may contact the injection target object through which electric currents, such as a human body, flow. Then, with the second electrode attached, the fluid ejection opening or a member in the vicinity thereof is brought into contact with the ejection object or a conductive object in the vicinity thereof, so that the injection target (and the conductive object) The first electrode and the second electrode can be energized via the first electrode, and the first electrode and the second electrode can be separated by separating (not contacting) the first electrode from the object to be ejected or an object that can conduct with the first electrode. It is possible not to energize the two electrodes.

[Form 3]
Furthermore, the fluid ejecting apparatus according to aspect 3 is the fluid ejecting apparatus according to aspect 1 or 2, wherein the fluid ejecting opening or a member in the vicinity thereof is formed of a conductive member, and the fluid ejecting opening or the member in the vicinity thereof. Was used as the first contact portion to constitute the first electrode.
With such a configuration, the first contact portion can be configured by the original parts constituting the apparatus, and therefore the first electrode can be formed at a relatively low cost without newly providing the first contact portion. Can be configured.

[Form 4]
Furthermore, the fluid ejecting apparatus according to aspect 4 is the fluid ejecting apparatus according to aspect 1, wherein one of the first electrode and the second electrode is provided in the fluid ejecting opening, and the other is provided in the adjacent member.
With such a configuration, the fluid ejection opening and its neighboring members are brought into contact with, for example, an ejection target through which a current such as a human body flows, so that the first electrode and the second electrode are interposed via the human body. The first electrode and the second electrode can be prevented from being energized by separating the fluid ejection opening and the member in the vicinity thereof from the human body.
Thereby, the trouble of attaching a 2nd electrode to an injection target object before use can be saved, and usability can be improved.

[Form 5]
Furthermore, the fluid ejecting apparatus according to aspect 5 is the fluid ejecting apparatus according to aspect 4, wherein the fluid ejecting opening and its neighboring members are formed of a conductive member, and one of the fluid ejecting opening and its neighboring members. The first electrode is configured as the first contact portion, and the second electrode is configured as the second contact portion.
With such a configuration, the first contact portion and the second contact portion can be configured by the original components that constitute the apparatus, so that the first contact portion and the second contact portion are newly provided. Therefore, the first electrode and the second electrode can be formed at a relatively low cost.

[Form 6]
Furthermore, the fluid ejecting apparatus according to aspect 6 is the fluid ejecting apparatus according to aspect 1, wherein the first contact portion and the second contact portion are provided in the adjacent members.
With such a configuration, the first electrode and the second electrode are brought into contact with each other through the human body by bringing a member in the vicinity of the fluid ejection opening, for example, into contact with an ejection target such as a human body. The first electrode and the second electrode can be prevented from being energized by separating the member near the fluid ejection opening from the human body.
Thereby, since troubles, such as attaching a 2nd electrode to an injection target object before use, can be saved, usability can be improved.
Furthermore, since the first contact portion and the second contact portion are provided only in the neighboring member, the first electrode and the second electrode can be manufactured at a lower cost than in the case where both the fluid ejection opening and the neighboring member are provided. Two electrodes can be constructed.

[Form 7]
Furthermore, the fluid ejecting apparatus according to aspect 7 is the fluid ejecting apparatus according to aspect 6, wherein the neighboring member is formed of a conductive member, and the first contact portion and the second contact portion are defined as the first contact portion. When the contact portion and the second contact portion are not in contact with the injection target, the first electrode and the second electrode are arranged on the adjacent member via an insulator so that the first electrode and the second electrode are not energized. did.
If it is such a structure, the 1st contact part and the 2nd contact part can be constituted by giving insulation processing to the original parts which constitute the member near the fluid ejection opening.
Thereby, since troubles, such as attaching a 2nd electrode to an injection target object before use, can be saved, usability can be improved.

[Form 8]
Furthermore, the fluid ejecting apparatus according to aspect 8 is the fluid ejecting apparatus according to aspect 1 or 2, wherein the high-frequency current applying means applies a high-frequency current between the first electrode and the second electrode.
Switching means for electrically disconnecting the first electrode and the second electrode from the energization determining means and electrically connecting to the high frequency current applying means when a high frequency current is applied by the high frequency current applying means. And comprising.
With such a configuration, since the high frequency current can be applied between the first electrode and the second electrode by the high frequency current applying means, in addition to the function as a water knife by fluid ejection, The function can be demonstrated.
Thereby, for example, when unexpected bleeding occurs during the operation, it is possible to take measures such as coagulating blood with an electric knife to stop the bleeding.

[Form 9]
Furthermore, the fluid ejecting apparatus according to the ninth aspect is the fluid ejecting apparatus according to any one of the first to eighth aspects, wherein the suction opening serving as the adjacent member provided to be positioned in the vicinity of the fluid ejecting opening. And a suction tube having a passage for the sucked object;
Suction force applying means for applying a suction force for sucking an object in the vicinity of the opening of the suction tube.
With such a configuration, when a suction force is applied by the suction force applying means, the fluid ejected from the fluid ejection opening and an object (for example, a tissue piece) excised or removed by the fluid ejection are suctioned. can do.
Thus, for example, when the fluid ejection device of this embodiment is used as a water knife for surgery, a resected living tissue piece or discharged fluid can be aspirated, so that surgery is performed while securing a good visual field. Can do.
Further, the suction pipe is made of a conductive member, and the first electrode is provided with the opening of the suction pipe as the first contact portion, so that the current flowing through the passage portion of the suction pipe is near the fluid chamber. Therefore, the wiring necessary for configuring the first electrode can be simplified.

[Form 10]
Furthermore, the fluid ejecting apparatus according to the tenth aspect is the fluid ejecting apparatus according to any one of the first to ninth aspects, wherein one end of the fluid ejecting apparatus communicates with the outlet flow path, and the fluid ejecting opening is provided at the other end. In addition, a connection flow channel pipe is provided for transmitting the pulsation of the fluid flowing from the fluid chamber to the other end.
With such a configuration, since the distance from the fluid chamber to the fluid ejection opening can be increased, for example, when the fluid ejection device of this embodiment is used as a water knife for surgery, surgery such as brain surgery is performed. It can be applied in various operations in the place where the part is deep.

[Form 11]
Furthermore, in the fluid ejecting apparatus according to the eleventh aspect, in the fluid ejecting apparatus according to the ninth aspect, the connection channel pipe is formed of a conductive member.
With such a configuration, when the first electrode is provided so as to have the first contact portion in the fluid ejection opening, the current flowing through the first contact portion is passed through the connection flow channel tube. Since it can send to the fluid chamber vicinity, the wiring required in order to comprise a 1st electrode can be simplified.

[Form 12]
Furthermore, the fluid ejecting apparatus according to the twelfth aspect is the fluid ejecting apparatus according to any one of the first to twelfth aspects, wherein the fluid supply unit includes a pressure generating unit that generates a pressure for supplying the fluid to the fluid chamber.
With such a configuration, the fluid can be supplied to the inlet flow path at a constant pressure by the pressure generating unit, so that the fluid is supplied to the inlet flow path and the fluid chamber even in a state where the drive of the volume changing unit is stopped. be able to.
Thus, the initial operation can be started without requiring the priming operation.
Here, as the pressure generator, for example, a pump that discharges fluid at a constant pressure can be employed.

[Form 13]
Furthermore, the fluid ejecting apparatus according to the thirteenth aspect is the fluid ejecting apparatus according to any one of the first to twelfth aspects, wherein the operation control means is determined to be energized by the energization determining means. Control is performed so that the operation of the volume changing means is prohibited when it is determined that the energization determining means is not energized.
With such a configuration, the fluid can be ejected when the first electrode and the second electrode are energized, and the first electrode and the second electrode are energized. It is possible to prevent the injection operation from occurring when there is not.
Therefore, when the fluid ejection opening or a member in the vicinity thereof is separated from the ejection target or an object that can communicate with the ejection target, the high pressure fluid is ejected in an unexpected direction, and the material removed or removed thereby. Can be prevented from occurring.

[Form 14]
On the other hand, in order to achieve the above object, a driving method of the fluid ejecting apparatus according to the fourteenth aspect includes a fluid chamber whose volume can be changed, an inlet channel and an outlet channel communicating with the fluid chamber, and a volume of the fluid chamber. Volume changing means for changing the fluid, fluid supply means for supplying fluid to the inlet flow path, and fluid ejection provided at the end of the outlet flow path opposite to the end communicating with the fluid chamber An opening, a first electrode provided so as to have a conductive first contact portion in contact with a fluid ejection target in the fluid ejection opening or a member in the vicinity thereof, and the fluid ejection target The fluid ejecting apparatus includes a second electrode having a polarity different from that of the first electrode having a conductive second contact portion in contact with the first electrode, an energization determining unit, and an operation control unit. And
An energization determining step for causing the energization determining means to determine whether or not the first electrode and the second electrode are energized;
An operation control step of causing the operation control means to control the operation of the volume changing means based on the determination result of the energization determining step.
Thereby, an effect | action and effect equivalent to the fluid injection apparatus of the said form 1 are acquired.

[Form 15]
In order to achieve the above object, the surgical instrument of form 15 is a surgical instrument that supports a therapeutic treatment of an affected area by jetting fluid,
The fluid ejecting apparatus according to any one of Form 1 to Form 13 is provided.
With such a configuration, it is possible to support a curative measure such as excision of an affected part such as a tumor by ejecting the fluid by the fluid ejecting apparatus according to any one of the first to thirteenth aspects.

It is explanatory drawing which shows schematic structure of the fluid injection apparatus 1 which concerns on this invention. It is sectional drawing which shows the structure of the pulsation generation | occurrence | production part 100 which concerns on this invention. 2 is an exploded view of a fluid ejecting portion of the fluid ejecting apparatus 1. FIG. It is a top view which shows the form of the inlet channel 503. FIG. 4 is a block diagram showing a detailed configuration of a drive unit 30. FIG. FIG. 6 is an explanatory diagram illustrating a configuration of a first electrode 50. FIG. 3 is a diagram illustrating a wiring configuration of an electrode line of a first electrode 50 and a supply line of a drive signal. It is a flowchart in the state in which the connection switch of the 1st electrode 50 and the 2nd electrode 51 is the electricity supply determination part 30b in the drive switch of an electric knife. It is a flowchart which shows the drive signal supply process in the drive signal supply part 30f. It is explanatory drawing which shows schematic structure of the fluid injection apparatus 3 which concerns on 2nd Embodiment. (A) is explanatory drawing explaining the structure of the 1st electrode 50 and the 2nd electrode 52, (b) is B-B 'sectional drawing in (a). (A) is sectional drawing for demonstrating the 1st structure of a 1st electrode and a 2nd electrode, (b) demonstrates the 2nd structure of a 1st electrode and a 2nd electrode. It is sectional drawing for doing. (A) is sectional drawing for demonstrating the 3rd structure of a 1st electrode and a 2nd electrode, (b) is (a) of the nozzle 211, the connection flow-path pipe | tube 200, and the suction pipe 700. It is sectional drawing of CC 'direction shown in FIG.

[First Embodiment]
Hereinafter, a first embodiment of the present invention will be described with reference to the drawings. 1 to 9 are views showing a fluid ejection device, a driving method of the fluid ejection device, and a surgical instrument according to the first embodiment of the present invention.
The fluid ejecting apparatus according to the present invention can be used in various ways such as drawing with ink, washing fine objects and structures, cutting and excision of objects, scalpels for operation, etc. In the embodiment, a fluid ejecting apparatus suitable for incising or excising living tissue will be described as an example. Therefore, the fluid used in the embodiment is water, physiological saline, chemical solution, or the like.

First, the configuration of the fluid ejection device according to the present invention will be described with reference to FIG. FIG. 1 is an explanatory diagram showing a schematic configuration of a fluid ejecting apparatus 1 according to the present invention.
As shown in FIG. 1, the fluid ejecting apparatus 1 includes, as a basic configuration, a fluid container 10 that contains a fluid, a pump 20 that serves as a pressure generating unit, and a pulsation generating unit 100 that pulsates and flows fluid supplied from the pump 20. And a driving unit 30 that drives the pulsation generating unit 100, a first electrode 50, and a second electrode 51.
Further, the pulsation generating unit 100 is connected with a thin pipe-shaped connection flow channel pipe 200, and a nozzle 211 having a diameter smaller than the flow channel diameter of the connection flow channel pipe 200 is attached to the tip of the connection flow channel pipe 200. Has been.

The connection channel pipe 200 is made of a conductive member, and the outer periphery is coated with an insulator.
The nozzle 211 is made of a conductive member and serves as a first contact portion of the first electrode 50 serving as a positive electrode. Further, the nozzle 211 is electrically connected to the connection flow channel pipe 200 via the insertion portion. The detailed configuration of the first electrode 50 will be described later.
From the pulsation generating unit 100, the first electrode 50, the nozzle 211 serving as the first contact unit, the electrode wire that is conducted through the connection flow channel pipe 200, and the volume changing unit 405 (see FIG. 2). A cable 45 that is a group of supply lines that supply drive signals extends, and each line of the cable 45 is electrically connected to a corresponding component of the drive unit 30.

The 2nd electrode 51 used as a negative electrode is comprised including the 2nd contact part 51a and the cable 51b.
The 2nd contact part 51a has an adhesive sticking part which can be stuck so that the electroconductive part electrically connected with the cable 51b may contact the injection target of fluid, such as a human body.
One end of the cable 51 b is electrically connected to the second contact portion 51 a and the conductive portion, and the other end is electrically connected to the drive portion 30.

Next, based on FIG.1 and FIG.2, the flow of the fluid in the fluid injection apparatus 1 is demonstrated easily.
Here, FIG. 2 is a sectional view showing the structure of the pulsation generator 100 according to the present invention. In FIG. 2, the left-right direction corresponds to the up-down direction. FIG. 2 is a cross-sectional view taken along line AA ′ in FIG. 4 to be described later.
The fluid stored in the fluid container 10 is sucked by the pump 20 through the connection tube 15 and supplied to the pulsation generator 100 through the connection tube 25 at a constant pressure. The pulsation generating unit 100 includes a fluid chamber 501 and a volume changing unit 405 that changes the volume of the fluid chamber 501 in accordance with a drive signal from the driving unit 30. The volume changing unit 405 is driven to pulsate. And the fluid is ejected at high speed through the connection flow channel pipe 200 and the nozzle 211. Detailed description of the pulsation generator 100 will be described later.

The pressure generating unit is not limited to the pump 20, and the infusion bag may be held at a position higher than the pulsation generating unit 100 by a stand or the like. Therefore, the pump 20 is unnecessary, and the configuration can be simplified, and there are advantages that sterilization and the like are facilitated.
The discharge pressure of the pump 20 is generally set to 3 atm (0.3 MPa) or less. Moreover, when using an infusion bag, the altitude difference between the pulsation generator 100 and the top surface of the infusion bag is the pressure. When using an infusion bag, it is desirable to set the altitude difference so as to be about 0.1 to 0.15 atm (0.01 to 0.15 MPa).

In addition, when performing an operation using the fluid ejecting apparatus 1, the part grasped by the operator is the pulsation generator 100. Therefore, it is preferable that the connection tube 25 up to the pulsation generator 100 be as flexible as possible. For this purpose, it is preferable that the pressure is reduced within a range in which fluid can be sent to the pulsation generator 100 with a flexible and thin tube.
In particular, when there is a possibility that a malfunction of the device may cause a serious accident as in the case of brain surgery, it is necessary to avoid a high-pressure fluid from being ejected when the connection tube 25 is disconnected. Therefore, it is required to keep the pressure low.

Next, the structure of the pulsation generator 100 will be described with reference to FIGS.
Here, FIG. 3 is an exploded view of the fluid ejection portion of the fluid ejection device 1, and FIG. 4 is a plan view showing the form of the inlet channel 503, where the upper case 500 is joined to the lower case 301. The state visually recognized from is shown.
2 to 4, the pulsation generating unit 100 includes an upper case 500 having screw holes 500a at four corners and a lower case having screw holes 301a (not shown) at four corners. 301. Then, the upper case 500 and the lower case 301 are joined so that the screw holes 500a and 301a face each other on the surfaces where the upper case 500 and the lower case 301 face each other, and the four fixing screws 600 (partially omitted in the drawing) are screw holes 500a and 301a. The upper case 500 and the lower case 301 are screwed together.

The lower case 301 is a hollow cylindrical member having a flange, and one end is sealed with a bottom plate 311. A piezoelectric element 401, which is one of the members constituting the volume changing unit 405, is disposed in the internal space of the lower case 301.
The piezoelectric element 401 is a laminated piezoelectric element and constitutes an actuator. One end of the piezoelectric element 401 is fixed to the diaphragm 400 via the upper plate 411, and the other end is fixed to the upper surface 312 of the bottom plate 311.
Diaphragm 400 is formed of a disk-shaped thin metal plate, and a peripheral edge thereof is closely fixed to the bottom surface of recess 303 in an annular recess 303 formed on the upper surface side of lower case 301. On the upper surface of the diaphragm 400, a reinforcing plate 410 made of a disk-like thin metal plate having a circular opening at the center is laminated.

With this configuration, when the driving unit 30 inputs a driving signal (applying an operating voltage) to the piezoelectric element 401, the piezoelectric element 401 expands and contracts, and the upward force during the extension and the downward direction when contracted. This moves the upper plate 411 in the vertical direction. When the upper plate 411 moves, the diaphragm 400 is deformed, and the volume of the fluid chamber 501 is changed.
That is, the volume changing unit 405 is configured by the piezoelectric element 401, the upper plate 411, the diaphragm 400, and the reinforcing plate 410.
The upper case 500 is formed with a circular concave portion at the center of the surface facing the lower case 301. The upper case 500 is composed of the concave portion and the diaphragm 400, and the shape of the rotating body filled with fluid is the fluid chamber 501. Become. That is, the fluid chamber 501 is a space surrounded by the sealing surface 505 of the recess of the upper case 500, the inner peripheral side wall 501 a, and the diaphragm 400. An outlet channel 511 is formed in a substantially central portion of the fluid chamber 501.

The outlet channel 511 is penetrated from the fluid chamber 501 to the end of the outlet channel pipe 510 projecting from one end face of the upper case 500. A connection portion between the outlet channel 511 and the sealing surface 505 of the fluid chamber 501 is smoothly rounded to reduce fluid resistance.
In addition, although the shape of the fluid chamber 501 described above is a substantially cylindrical shape with both ends sealed in the present embodiment, it may be conical, trapezoidal, hemispherical, or the like when viewed from the side. For example, if the connecting portion between the outlet channel 511 and the sealing surface 505 is shaped like a funnel, bubbles in the fluid chamber 501 described later can be easily discharged.
A connection channel pipe 200 is connected to the outlet channel pipe 510. A connection channel 201 is perforated in the connection channel pipe 200, and the diameter of the connection channel 201 is larger than the diameter of the outlet channel 511. Further, the thickness of the pipe portion of the connection flow path pipe 200 is formed in a range having rigidity that does not absorb the pressure pulsation of the fluid.

A nozzle 211 is inserted into the distal end portion of the connection flow channel pipe 200. The nozzle 211 is formed with a fluid ejection opening 212. The diameter of the fluid ejection opening 212 is smaller than the diameter of the connection channel 201.
On the side surface of the upper case 500, an inlet channel tube 502 for inserting the connection tube 25 for supplying fluid from the pump 20 is projected, and the inlet channel tube 502 is provided with a connection channel 504 on the inlet channel side. I'm leaning. The connection flow path 504 communicates with the inlet flow path 503. The inlet channel 503 is formed in a groove shape on the peripheral edge of the sealing surface 505 of the fluid chamber 501 and communicates with the fluid chamber 501.

A packing box 304 is formed on the lower case 301 side, and a packing box 506 is formed on the upper case 500 side at positions separated from each other in the outer peripheral direction of the diaphragm 400 on the joint surface between the upper case 500 and the lower case 301. A ring-shaped packing 450 is mounted in a space formed by 304 and 506.
Here, when the upper case 500 and the lower case 301 are assembled, the peripheral portion of the diaphragm 400 and the peripheral portion of the reinforcing plate 410 are the peripheral portion of the sealing surface 505 of the upper case 500 and the concave portion 303 of the lower case 301. It is closely attached by the bottom. At this time, the packing 450 is pressed by the upper case 500 and the lower case 301 to prevent fluid leakage from the fluid chamber 501.
The fluid chamber 501 is in a high pressure state of, for example, 30 atm (3 MPa) or more when fluid is discharged, and the fluid may slightly leak at the joints of the diaphragm 400, the reinforcing plate 410, the upper case 500, and the lower case 301. Though possible, leakage is prevented by the packing 450.

When the packing 450 is disposed as shown in FIG. 2, the packing 450 is compressed by the pressure of the fluid leaking from the fluid chamber 501 at a high pressure, and is further strongly pressed against the walls in the packing boxes 304 and 506. Can be more reliably prevented. From this, a high pressure rise in the fluid chamber 501 can be maintained during driving.
Next, the inlet channel 503 formed in the upper case 500 will be described in more detail.
As shown in FIG. 4, the inlet channel 503 is formed by a groove formed at the peripheral edge of the sealing surface 505 of the upper case 500 and a reinforcing plate 410 that is pressed and fixed to the sealing surface 505.
The inlet channel 503 has one end communicating with the fluid chamber 501 and the other end communicating with the connection channel 504. A fluid reservoir 507 is formed at a connection portion between the inlet channel 503 and the connection channel 504. The connection between the fluid reservoir 507 and the inlet channel 503 is smoothly rounded to reduce the fluid resistance.

In addition, the inlet channel 503 communicates with the inner peripheral side wall 501a of the fluid chamber 501 in a substantially tangential direction. The fluid supplied from the pump 20 at a constant pressure flows along the inner peripheral wall 501a (in the direction indicated by the arrow in the figure) to generate a swirling flow in the fluid chamber 501. Due to the centrifugal force of the swirling flow, the low-density bubbles contained in the fluid chamber 501 concentrate at the center of the swirling flow.
Then, the bubbles collected at the center are excluded from the outlet channel 511. For this reason, it is more preferable that the outlet channel 511 is provided in the vicinity of the center of the swirling flow, that is, in the axial center portion of the rotating body. In the example of FIG. 4, the planar shape of the inlet channel 503 is curved in a spiral shape. The inlet channel 503 may be communicated with the fluid chamber 501 in a straight line, but is curved from the need to increase the channel length of the inlet channel 503 in order to obtain a desired inertance in a narrow space. .

  In addition, as shown in FIG. 2, the reinforcement board 410 is arrange | positioned between the diaphragm 400 and the peripheral part of the sealing surface 505 in which the inlet flow path 503 is formed. The meaning of providing the reinforcing plate 410 is to improve the durability of the diaphragm 400. Since the notch-like connection opening 509 is formed in the connection portion of the inlet channel 503 with the fluid chamber 501, stress concentration occurs in the vicinity of the connection opening 509 when the diaphragm 400 is driven at a high frequency. May cause fatigue failure. Therefore, by providing the reinforcing plate 410 having a continuous opening without a notch, stress concentration does not occur in the diaphragm 400.

  In the fluid ejecting apparatus 1 described above, four screw holes 500a are formed at the outer peripheral corner of the upper case 500, and the upper case 500 and the lower case 301 are screwed together at the screw hole positions. Although it joined, it is not restricted to this structure. For example, although illustration is omitted, the reinforcing plate 410 and the diaphragm 400 can be joined and laminated and fixed together. As an adhering means, solid layer diffusion bonding, welding, or the like can be adopted even when sticking using an adhesive, but the reinforcing plate 410 and the diaphragm 400 are more closely attached to each other at the joining surface. preferable.

Further, in the fluid ejecting apparatus 1 described above, the outlet flow channel 511 and the nozzle 211 are configured to be connected via the connection flow channel pipe 200. However, the configuration is not limited to this, and the connection flow channel tube 200 is not used. In addition, it is possible to insert the nozzle 211 at the end of the outlet channel pipe 510 opposite to the fluid chamber 501. In this case, a simpler configuration is possible.
Further, when used for surgery, it is preferable to use the connection channel tube 200 so that the distance between the handpiece and the fluid ejection opening 212 is appropriately long.

Next, the principle of fluid discharge of the pulsation generator 100 of this embodiment will be described.
The fluid discharge of the pulsation generating unit 100 of the present embodiment is due to the difference between the inertance L1 on the inlet flow path side (sometimes referred to as synthetic inertance L1) and the inertance L2 on the outlet flow path side (sometimes referred to as synthetic inertance L2). Done.
First, inertance will be described.
The inertance L is expressed by L = ρ × h / S, where ρ is the density of the fluid, S is the cross-sectional area of the flow path, and h is the length of the flow path. When the pressure difference in the flow path is ΔP and the flow rate of the fluid flowing through the flow path is Q, the relationship of ΔP = L × dQ / dt is derived by modifying the equation of motion in the flow path using the inertance L. It is.

That is, the inertance L indicates the degree of influence on the time change of the flow rate. The larger the inertance L, the less the time change of the flow rate, and the smaller the inertance L, the greater the time change of the flow rate.
In addition, the combined inertance related to the parallel connection of a plurality of flow paths and the series connection of a plurality of flow paths having different shapes is obtained by combining the inertance of individual flow paths in the same way as the parallel connection or series connection of inductances in an electric circuit. Can be calculated.
Note that the inertance L1 on the inlet flow path side is set so that the diameter of the connection flow path 504 is sufficiently large with respect to the inlet flow path 503, and therefore, the inertance L1 may be calculated only for the inertance of the inlet flow path 503. Further, since the connection tube connecting the pump 20 and the inlet channel has flexibility, it is excluded from the calculation of the inertance L1.

Further, the inertance L2 on the outlet flow path side has an influence on the inertance L2 when the diameter of the connection flow path 201 is much larger than that of the outlet flow path and the pipe portion (tube wall) of the connection flow path pipe 200 is thin. Minor. Therefore, the inertance L2 on the outlet channel side may be replaced with the inertance of the outlet channel 511.
When the thickness of the pipe wall of the connection flow path pipe 200 is thick, the inertance L2 is a combined inertance of the outlet flow path 511, the connection flow path 201, and the nozzle 211.
In this embodiment, the flow path length and cross-sectional area of the inlet flow path 503 and the flow path length and cross-sectional area of the outlet flow path 511 are such that the inertance L1 on the inlet flow path side is larger than the inertance L2 on the outlet flow path side. Is set.

Next, based on FIG. 5, the detailed structure of the drive part 30 is demonstrated.
Here, FIG. 5 is a block diagram illustrating a detailed configuration of the drive unit 30.
As shown in FIG. 5, the drive unit 30 includes an operation control unit 30a, an energization determination unit 30b, a high-frequency current application unit 30c, a connection switching unit 30d, a data storage unit 30e, a drive signal supply unit 30f, And a synchronization signal generator 30g.
The operation control unit 30a plays a role of giving an operation command to each component unit in response to an operation input from an input device (not shown) of the fluid ejecting apparatus 1, and the current application process and connection of the high-frequency current application unit 30c. It has a function of controlling various operation processes such as a switching process of the switching unit 30d and a drive signal supply process of the drive signal supply unit 30f.

Specifically, the operation control unit 30a stops supplying the drive signal to the drive signal supply unit 30f when the drive switch (not shown) of the water pulse knife changes from the on state to the off state. A stop command is output to As a result, the supply of the drive signal by the drive signal supply unit 30f is stopped.
When the drive switch (not shown) of the electric knife is turned on when the drive switch of the water pulse knife is turned off, the first electrode 50 and the second electrode are connected to the connection switching unit 30d. A control signal is output so that the connection destination of 51 is switched from the energization determination unit 30b to the high-frequency current application unit 30c. Note that this operation is omitted when the connection destination of the first electrode 50 and the second electrode 51 is the high-frequency current application unit 30c from the beginning.

Furthermore, when the connection destination is switched to the high frequency current application unit 30c, a high frequency current application command is output to the high frequency current application unit 30c. Thereby, a high frequency current is applied between the first electrode 50 and the second electrode 51 from the high frequency current application unit 30 c. That is, by bringing the nozzle 211 close to the human body, an arc is generated from the tip of the nozzle 211 and functions as an electric knife.
Further, when the drive switch of the electric knife changes from the on state to the off state, a stop command is output to the high frequency current application unit 30c. As a result, the application of the high-frequency current from the high-frequency current application unit 30 c to the area between the first electrode 50 and the second electrode 51 is stopped.

When the drive switch for the water pulse knife (not shown) is turned on while the drive switch for the electric knife is turned off, the first electrode 50 and the second electrode are connected to the connection switching unit 30d. A control signal is output so that the connection destination of 51 is switched from the high-frequency current application unit 30c to the energization determination unit 30b. In addition, when the connection destination of the 1st electrode 50 and the 2nd electrode 51 is the electricity supply determination part 30b from the beginning, this operation | movement is abbreviate | omitted.
Further, when the connection destination is switched to the energization determination unit 30b, a drive signal supply command or a stop command is output to the drive signal supply unit 30f based on the determination result of the energization determination unit 30b. As a result, a command signal based on the determination result of the energization determination unit 30b is output to the drive signal supply unit 30f.

The energization determining unit 30b includes a power source that outputs a weak applied voltage and applied current and a load for detecting energization, and the high potential side terminal of the power source and the first electrode 50 are electrically connected via the connection switching unit 30d. The low potential side terminal of the power source and the second electrode 50 are electrically connected. Note that the power source may be either a DC power source or an AC power source.
Further, the energization determining unit 30b detects the energization state between the first electrode and the second electrode by detecting the current flowing through the load for detecting energization or the voltage applied to the load, and from this detection result, It is determined whether or not the first electrode 50 and the second electrode 50 are energized. When it is determined that power is supplied, a signal indicating that power is supplied (for example, a high level signal) is output to the operation control unit 30a. When it is determined that power is not supplied, power is not supplied. Is output to the operation control unit 30a.

The high-frequency current application unit 30c applies a high-frequency current between the first electrode 50 and the second electrode 51 via the connection switching unit 30d in response to an operation command from the operation control unit 30a. Thus, the first electrode 50 becomes an active electrode, the second electrode 51 becomes a return electrode, an arc is generated from the nozzle 211 constituting the first electrode 50, and the function as an electric knife is exhibited.
The connection switching unit 30d is configured to electrically connect the first electrode 50 and the second electrode 51 and the energization determining unit 30b, and the first electrode 50 and the second electrode based on a control signal from the operation control unit 30a. The electrical connection between the electrode 51 and the high-frequency current application unit 30c is switched.

For switching the connection, a mechanical switch may be used, or a switching element such as a power transistor may be used.
The data storage unit 30e includes a storage medium that stores waveform information of a plurality of types of signal waveforms with different periods and amplitudes corresponding to the set injection strength, and other data used for processing of each component. In addition, it has a function of reading data stored in the storage medium in response to a read request from each component and writing data in the storage medium in response to a write request from each component.

The drive signal supply unit 30f functions to supply the drive signal to the piezoelectric element 401 of the volume changing unit 405 in synchronization with the synchronization signal from the synchronization signal generating unit 30g in response to a drive signal supply command from the operation control unit 30a. have.
Specifically, based on the waveform designation information included in the supply command, the corresponding waveform information (digital waveform data) is read from the data storage unit 30e, and the read waveform information is DA-converted to generate an analog drive signal. The generated drive signal is supplied to the piezoelectric element 401 in synchronization with the synchronization signal. The waveform designation information is identification information attached to the signal waveform corresponding to the injection strength.

Furthermore, it has a function of stopping the supply of the drive signal in response to a drive signal stop command from the operation control unit 30a. In the present embodiment, when a stop command is input from the operation control unit 30a during the supply of the drive signal, the supply of the drive signal is stopped after supplying the waveform of one cycle during the supply to the piezoelectric element 401 to the end. It is supposed to be.
The synchronization signal generator 30g includes an oscillator such as a ceramic resonator or a crystal resonator, a counter (or a PLL circuit), and the like, and generates a synchronization signal from the clk using a signal output from the oscillator as a reference clock signal clk. It has a function to do. Then, the reference clock signal and the synchronization signal are supplied to the drive signal supply unit 30f.

  The drive unit 30 includes a computer system for realizing the functions of the respective components using software and executing software for controlling hardware necessary for realizing the functions. Although not shown, the hardware configuration of this computer system includes a processor (Processor), a RAM (Random Access Memory), and a ROM (Read Only Memory), which are connected by various internal and external buses. It has become.

In addition, a display device such as a CRT or LCD monitor, an input device such as an operation panel, a mouse, and a keyboard is connected to the bus via an input / output interface (I / F) such as IEEE1394, USB, and parallel port. ing.
When the power is turned on, the system program stored in the ROM or the like loads various dedicated computer programs for realizing the functions of the above-described units stored in the ROM in the RAM, and the programs loaded in the RAM are loaded into the RAM. Each function as described above is realized by a processor performing predetermined control and arithmetic processing by making full use of various resources in accordance with written instructions.

Next, based on FIGS. 6-7, the detailed structure of the 1st electrode 50 is demonstrated.
Here, FIG. 6 is an explanatory diagram illustrating the configuration of the first electrode 50, and FIG. 7 is a diagram illustrating the wiring configuration of the electrode lines of the first electrode 50 and the drive signal supply lines.
As shown in FIGS. 6 and 7, the first electrode 50 includes a nozzle 211 that becomes the first contact portion 50 a, a connection flow channel pipe 200 that becomes a conductive path 50 b to the pulsation generation portion 100, and a pulsation generation portion. 100 and electrode line 50c wired inside.
The electrode wire 50c is covered with an insulating film having heat resistance, one end is electrically connected to the conductive path 50b, and the other end is electrically connected to the switch of the connection switching unit 30d.

As shown in FIG. 7, the electrode wire 50 c is wired through a passage formed inside the pulsation generator 100. Similarly, the supply line PZT (+) connected to the high potential side of the piezoelectric element 401 and the supply line PZT (−) connected to the low potential side of the piezoelectric element 401 are covered with a heat-resistant insulating film. And are wired through a passage formed inside the pulsation generator 100.
The wiring paths of the electrode line 50c and the supply lines PZT (+) and PZT (-) are merged near the outlet, and the electrode line 50c, the supply lines PZT (+) and PZT (-) are grouped as a cable 45. Is done.
As described above, since the nozzle 211 is formed of a conductive member and the connection flow channel pipe 200 is also formed of a conductive member, the first contact portion 50a, the conductive path 50b, and the electrode line 50c are electrically connected. .

Therefore, in a state where the second contact portion 51a of the second electrode 51 is in contact with the human body, the nozzle 211 (first contact portion 50a) is used as an ejection target portion in the human body or a conductor (liquid or the like) in contact therewith. When brought into contact, the first electrode 50 and the second electrode 51 are energized.
On the other hand, as described above, since the outer periphery of the connection flow channel pipe 200 is insulatively coated, even if the outer periphery of the connection flow path tube 200 comes into contact with the injection target portion in the human body or a conductor in contact therewith, the first The electrode and the second electrode are not energized.

Next, the flow of the operation control process of the drive signal supply unit 30f in the operation control unit 30a will be described with reference to FIG.
Here, FIG. 8 is a flowchart showing an operation control process of the drive signal supply unit 30f in the operation control unit 30a. However, FIG. 8 is a flowchart in a state where the drive switch of the electric knife is in the OFF state and the connection destination of the first electrode 50 and the second electrode 51 is the energization determination unit 30b.
When a dedicated program is executed by the processor and the operation control process of the drive signal supply unit 30f is started, first, the process proceeds to step S100 as shown in FIG.

In step S100, the operation control unit 30a determines whether or not the drive switch for the water pulse knife (hereinafter referred to as WPS) is turned on. If it is determined that the drive switch is turned on (Yes), step S102 is performed. If not (No), the determination process is repeated until it is turned on.
When the process proceeds to step S102, the operation control unit 30a determines whether or not the first electrode 50 and the second electrode 51 are in the energized state based on the determination signal from the energization determining unit 30b. If it is (the determination signal is at a high level) (Yes), the process proceeds to step S104. If not (No), the process proceeds to step S110.

That is, when the first electrode 50 and the second electrode 51 are not energized, the drive signal supply command is not output to the drive signal supply unit 30f even when the drive switch is turned on.
When the process proceeds to step S104, the operation control unit 30a outputs a drive signal supply command to the drive signal supply unit 30f, and the process proceeds to step S106.
In step S106, the operation control unit 30a determines whether or not the drive switch has been turned off. If it is determined that the drive switch has been turned off (Yes), the process proceeds to step S108; The process proceeds to S102.

When the process proceeds to step S108, the operation control unit 30a outputs a drive signal supply stop command to the drive signal supply unit 30f, and the process proceeds to step S100.
On the other hand, in step S102, when the process shifts to step S110 instead of the energized state, the operation control unit 30a outputs a supply stop command for stopping the supply of the drive signal to the drive signal supply unit 30f, and the process proceeds to step S100. To do. If it is determined that the drive state is not energized and the drive signal is not supplied, the process may be shifted to step S100 without outputting the supply stop command.

Next, the flow of drive signal supply processing in the drive signal supply unit 30f will be described with reference to FIG.
Here, FIG. 9 is a flowchart showing a drive signal supply process in the drive signal supply unit 30f.
When the dedicated program is executed by the processor and the drive signal supply process is started, the process proceeds to step S200 as shown in FIG.
In step S200, the drive signal supply unit 30f determines whether or not a drive command from the operation control unit 30a has been input. If it is determined that the drive command has been input (Yes), the process proceeds to step S202; No) repeats the determination process until input.

When the process proceeds to step S202, the drive signal supply unit 30f reads the waveform data of the waveform type used for driving the piezoelectric element 401 from the data storage unit 30e based on the identification information of the designated waveform included in the drive command, The process proceeds to S204.
In step S204, the drive signal supply unit 30f converts the digital waveform signal of the waveform data read out in step S202 into an analog waveform signal, and proceeds to step S206.
In step S206, the drive signal supply unit 30f outputs, to the piezoelectric element 401, a drive signal having an analog signal waveform obtained by DA conversion in step S204, in synchronization with the synchronization signal from the synchronization signal generation unit 30g. Then, the process proceeds to step S208.

In step S208, the drive signal supply unit 30f determines whether or not a stop command is input from the operation control unit 30a. If it is determined that the stop command has been input (Yes), the process proceeds to step S210; ) Continues the output processing of the drive signal in step S204.
When the process proceeds to step S210, the drive signal supply unit 30f outputs all signals for one cycle, stops the supply of the drive signal, and then proceeds to step S200.

Next, a specific operation of the fluid ejecting apparatus 1 of the present embodiment will be described.
First, before the fluid ejecting apparatus 1 is driven, the second electrode 51 is attached to a human arm or the like. Thereafter, when the power of the fluid ejecting apparatus 1 is turned on, an initialization operation is performed. At this time, if at least one of the WPS drive switch and the electric knife drive switch is turned on, the fluid ejecting apparatus 1 sounds a warning sound from a speaker (not shown) or displays a warning message on the display device. The user is prompted to turn off the switch by turning on a lamp (not shown).

On the other hand, when the WPS drive switch and the electrosurgical knife drive switch are off, the system shifts to the drive standby state after initialization. Note that the first electrode 50 and the second electrode 51 are connected to the energization determination unit 30b.
In this state, when the WPS drive switch is turned on (“Yes” branch of step S100), the operation control unit 30a is connected to the first electrode 50 and the second electrode based on the determination signal from the energization determination unit 30b. It is determined whether or not the electrode 51 is energized (step S102).
At this time, when the nozzle 211 is not in contact with the affected part or the like, it is not energized ("No" branch in step S102), so the determination process is repeated.

On the other hand, when the nozzle 211 comes into contact with the second electrode 51 such as liquid in the affected area and its surroundings by the practitioner's hand, the first electrode 50 and the second electrode 51 through the affected area. Is energized, and the energization determining unit 30b outputs a determination signal (high level) indicating that energization is performed to the operation control unit 30a. As a result, the operation control unit 30a determines that the first electrode 50 and the second electrode 51 are energized (“Yes” in step S102), and supplies the drive signal to the drive signal supply unit 30f. A command is output (step S104).
On the other hand, when the drive signal supply unit 30f receives the drive signal supply command (“Yes” in step S200), the drive signal supply unit 30f stores the corresponding waveform information in the data storage unit 30e based on the identification information of the waveform information included in the supply command. To a work memory such as a RAM (step S202).
Next, the waveform data read to the work memory is D / A converted to generate an analog drive signal (step S204).

Next, the generated analog drive signal is output to the piezoelectric element 401 in synchronization with the synchronization signal from the synchronization signal generator 30g (step S206).
Here, before the drive signal is supplied, the fluid is always supplied to the inlet channel 503 by the pump 20 at a constant hydraulic pressure. As a result, when the piezoelectric element 401 does not operate, the fluid flows into the fluid chamber 501 due to the discharge force of the pump 20 and the difference between the fluid resistance values of the entire inlet channel side.
Here, if a drive signal is input to the piezoelectric element 401 and the piezoelectric element 401 suddenly expands, the pressure in the fluid chamber 501 is sufficiently large in the inertances L1 and L2 on the inlet channel side and the outlet channel side. If it has, it will rise rapidly and reach several tens of atmospheres.

Since this pressure is much larger than the pressure by the pump 20 applied to the inlet channel 503, the inflow of fluid from the inlet channel side into the fluid chamber 501 is reduced by the pressure, and the outflow from the outlet channel 511. Will increase.
However, since the inertance L1 of the inlet channel 503 is larger than the inertance L2 of the outlet channel 511, the inertance L1 is discharged from the outlet channel more than the reduction amount of the flow rate of fluid flowing from the inlet channel 503 into the fluid chamber 501. Since the increase amount of the fluid is larger, a pulsed fluid discharge, that is, a pulsating flow is generated in the connection channel 201. The pressure fluctuation at the time of discharge propagates through the connection flow channel pipe 200, and the fluid is ejected from the fluid ejection opening 212 of the nozzle 211 at the tip.

Here, since the diameter of the fluid ejection opening 212 of the nozzle 211 is smaller than the diameter of the outlet channel 511, the fluid is ejected as high-speed pulsed droplets.
On the other hand, the inside of the fluid chamber 501 is in a vacuum state immediately after the pressure rises due to the interaction between the decrease in the fluid inflow amount from the inlet channel 503 and the increase in the fluid outflow from the outlet channel 511.
The piezoelectric element 401 in the expanded state contracts at a speed corresponding to the falling waveform shape of the drive waveform, and finally the fluid flow returns to the steady state before the drive signal is supplied.
In addition, since the fluid chamber 501 has a substantially rotating body shape and is provided with the inlet channel 503 and the outlet channel 511 is provided in the vicinity of the rotating shaft having a substantially rotating body shape, the fluid chamber 501 is provided. A swirling flow is generated inside, and bubbles (vacuum bubbles and gas bubbles) contained in the fluid are quickly discharged from the outlet channel 511 to the outside.

By continuously supplying the drive signal to the piezoelectric element 401, the pulsating flow from the nozzle 211 can be continuously ejected.
Thus, when the practitioner moves the pulsation generating unit 100 while the drive signal is continuously supplied and the pulsating flow is continuously ejected, the energization is performed when the nozzle 211 is separated from the affected part or the surrounding liquid. A determination signal (low level) indicating that no power is supplied is output from the determination unit 30b to the operation control unit 30a.
Thereby, the operation control unit 30a determines that the first electrode 50 and the second electrode 51 are not energized ("No" branch in step S102), and supplies a drive stop command to the drive signal supply unit 30f. Is output (step S110).

When the supply stop command is input from the operation control unit 30a ("Yes" branch in step S208), the drive signal supply unit 30f supplies the drive signal currently being supplied for one cycle, and then the drive signal Is stopped (step S210).
When the WPS drive switch is turned on and the nozzle 211 comes into contact with the affected area and the surrounding liquid again, the first electrode 50 and the second electrode 51 are energized (“Yes” in step S102). ), A drive signal supply command is output to the drive signal supply unit 30f. As a result, a drive signal is supplied to the piezoelectric element 401 and pulsating flow injection is resumed.
In this state, when the WPS drive switch is turned off by the practitioner, the operation control unit 30a determines that the drive switch is turned off ("Yes" branch of step S106), and the drive signal supply unit 30f A supply stop command is output to (step S108).

As a result, the drive signal supply unit 30f stops supplying the drive signal after supplying the currently supplied drive signal for one period (step S210). When the supply of the drive signal is stopped, the pulsating flow injection is also stopped.
On the other hand, when the electrosurgical knife drive switch is turned on while the WPS drive switch is in the off state, the operation control unit 30a causes the connection switching unit 30d to connect the first electrode 50 and the second electrode 51 to each other. A control signal for switching the connection destination from the energization determining unit 30b to the high-frequency current applying unit 30c is output.
As a result, the connection destination of the first electrode 50 and the second electrode 51 is switched to the high-frequency current application unit 30c.

When the connection destination is switched to the high frequency current application unit 30c, the operation control unit 30a outputs a high frequency current application command to the high frequency current application unit 30c. Thereby, a high frequency current is applied between the first electrode 50 and the second electrode 51 from the high frequency current application unit 30 c.
As a result, the nozzle 211 is brought close to the affected part of the human body to which the second electrode is attached, whereby an arc is generated from the tip of the nozzle 211, the fluid ejecting apparatus 1 functions as an electric knife, and the affected part is excised. Measures such as coagulation of tissue and hemostasis are possible.
As described above, the fluid ejecting apparatus 1 of the present embodiment performs the fluid ejecting operation when the WPS drive switch is turned on while the first electrode 50 and the second electrode 51 are energized. The operations of the drive signal supply unit 30f and the volume changing unit 405 are controlled. On the other hand, when the first electrode 50 and the second electrode 51 are not energized, the drive signal supply unit 30f and the volume change so that the fluid ejection operation is not performed even when the WPS drive switch is turned on. The operation of the unit 405 is controlled.

Furthermore, when the first electrode 50 and the second electrode 51 are not energized during the fluid ejection operation, the drive signal supply unit 30f and the volume changing unit 405 are configured to stop the fluid ejection operation. Control the behavior.
As a result, when the first electrode 50 and the second electrode 51 are not energized, it is possible to prevent the ejection operation from being performed. Therefore, when the nozzle 211 moves away from the affected area or the liquid around it, Injection of high-pressure pulsating flow in the direction of the patient (for example, toward a person in the operating room or a region that is not desired to be removed), or scattering of the excised tissue fragment due to injection from an unexpected direction or position It can be prevented from occurring.

Furthermore, in the fluid ejecting apparatus 3 according to the present embodiment, the nozzle 211 and the connection flow channel pipe 200 are formed from conductive members, and the first electrode 50 is configured from the nozzle 211, the connection flow channel pipe 200, and the electrode wire 50c. Therefore, since the original member which comprises the fluid ejecting apparatus 1 is utilized, the 1st electrode 50 can be comprised at low cost compared with the structure provided separately.
Furthermore, in the fluid ejection device 1 of the present embodiment, a high frequency current is applied between the first electrode 50 and the second electrode 51 by the high frequency current application unit 30c to generate an arc at the tip of the nozzle 211. The injection device 1 can function as an electric knife.

  In the first embodiment, the nozzle 211 and the fluid ejection opening 212 correspond to the fluid ejection opening described in any one of Embodiments 1, 3, 10 and 14, and the volume changing unit 405 and the drive signal supply The part 30f corresponds to the volume changing means according to any one of the forms 1, 13, and 14, and the fluid container 10 and the pump 20 correspond to the fluid supply means according to any one of the forms 1, 12, and 14. The operation control unit 30a corresponds to the operation control means described in any one of the forms 1, 13, and 14, and the energization determining unit 30b is the energization described in any one of the forms 1, 8, 13, and 14. Corresponding to the determination unit, the high-frequency current application unit 30c corresponds to the high-frequency current application unit described in the eighth mode, and the connection switching unit 30d corresponds to the switching unit described in the eighth mode.

[Second Embodiment]
Hereinafter, a second embodiment of the present invention will be described with reference to the drawings. 10 to 11 are diagrams showing a fluid ejection device, a method for driving the fluid ejection device, and a surgical instrument according to a second embodiment of the present invention.
The present embodiment includes a suction pipe and a pump for sucking an object near the nozzle 211 provided so as to cover the connection flow path pipe 200 as compared with the first embodiment. The difference is that the second contact portion constituting the second electrode is provided at the opening of the suction tube. Accordingly, the other components are the same as those in the first embodiment, so that different parts will be described in detail below, and overlapping parts will not be described as appropriate.

First, the configuration of the fluid ejecting apparatus according to the present embodiment will be described with reference to FIG. FIG. 10 is an explanatory diagram showing a schematic configuration of the fluid ejecting apparatus 3 according to the present embodiment.
As shown in FIG. 10, the fluid ejecting apparatus 3 includes, as a basic configuration, a fluid container 10 that stores fluid, a pump 20 that serves as a pressure generation unit, a suction container 70 that stores a suction object, and suction force applying means. A suction pump 60, a pulsation generator 100 that pulsates the fluid supplied from the pump 20, a drive unit 30 that drives the pulsation generator 100, a first electrode 50, and a second electrode 52. It consists of
The pulsation generating unit 100 is connected to a thin pipe-shaped connection flow channel pipe 200, and a nozzle 211 having a diameter smaller than the flow channel diameter of the connection flow channel pipe 200 is attached to the tip of the connection flow channel pipe 200. Yes.

Further, a pipe-shaped suction pipe 700 having a diameter larger than the diameter of the connection flow path pipe 200 that includes the connection flow path pipe 200 is connected to the pulsation generating unit 100.
Between the inner peripheral surface of the suction tube 700 and the outer peripheral surface of the connection flow channel tube 200, a passage for aspirated material such as a discharged liquid or a tissue piece is formed due to a difference in diameter between the two.
On the pulsation generating unit 100 side of the suction pipe 700, an outlet channel pipe 702 for feeding the suctioned substance to the suction container 70 is projected, and the suctioned substance is connected to the outlet channel pipe 702. The air is sucked by the suction pump 60 through 65 and discharged to the suction container 70 through the connection tube 75.
The connection flow channel pipe 200 and the suction pipe 700 are made of a conductive member, and the suction pipe 700 is coated with an insulator on the outer periphery except for the tip (an arbitrary range including the open end face).

The nozzle 211 is made of a conductive member and serves as a first contact portion of the first electrode 50 serving as a positive electrode. Further, the nozzle 211 is electrically connected to the connection flow channel pipe 200 via the insertion portion.
The tip of the suction tube 700 (the portion not covered with the insulating coating) serves as a second contact portion of the second electrode 52 serving as a negative electrode. The detailed configuration of the second electrode 52 will be described later.
From the pulsation generating unit 100, the first electrode 50, the nozzle 211 serving as the first contact unit, the electrode wire 50c conducting through the connection channel tube 200, and the second electrode are configured. The cable 47 is formed by bringing together an electrode wire 52b that is electrically connected to the suction tube 700 having a contact portion of 2 at the tip, and supply lines PZT (+) and PZT (−) that supply a drive signal to the volume changing portion 405. Each line of the cable 47 is electrically connected to a corresponding component of the drive unit 30.

Next, based on FIG. 11, the detailed structure of the 1st electrode 50 and the 2nd electrode 52 is demonstrated.
Here, FIG. 11A is an explanatory diagram illustrating the configuration of the first electrode 50 and the second electrode 52, and FIG. 11B is a cross-sectional view taken along the line BB ′ in FIG.
As shown in FIGS. 11A and 11B, the first electrode 50 includes a nozzle 211 that becomes the first contact portion 50 a and a connection flow channel tube 200 that becomes the conductive path 50 b to the pulsation generating portion 100. And the electrode wire 50c wired inside the pulsation generator 100.
The second electrode 52 has a tip portion serving as a second contact portion 52a, a main body portion serving as a conductive path to the pulsation generation unit 100, and an electrode wire 52b wired inside the pulsation generation unit 100. It is comprised including.
The electrode wire 50c is covered with an insulating film having heat resistance, one end is electrically connected to the conductive path 50b, and the other end is electrically connected to the switch of the connection switching unit 30d.

The electrode wire 52b is covered with an insulating film having heat resistance, and one end is electrically connected to the suction tube 700 and the other end is electrically connected to a switch of the connection switching unit 30d.
The electrode wires 50c and 52b are wired through a passage (not shown) formed inside the pulsation generator 100. Similarly, the supply line PZT (+) connected to the high potential side of the piezoelectric element 401 and the supply line PZT (−) connected to the low potential side of the piezoelectric element 401 are covered with a heat-resistant insulating film. And is routed through a passage (not shown) formed inside the pulsation generator 100.
The wiring paths of the electrode line 50c, the electrode line 52b, the supply line PZT (+) and PZT (−) merge near the outlet, and the electrode line 50c, the electrode line 52b, the supply line PZT (+) and PZT (−) ) Are grouped together as a cable 47.

As described above, since the nozzle 211 is formed of a conductive member and the connection flow channel pipe 200 is also formed of a conductive member, the first contact portion 50a, the conductive path 50b, and the electrode line 50c are electrically connected. .
Furthermore, since the suction tube 700 is formed of a conductive member, the second contact portion 52a and the electrode wire 52b are electrically connected.
With the above-described configuration, both the nozzle 211 (first contact portion 50a) and the tip end portion (second contact portion 52a) of the suction pipe 700 are made to eject target portions (affected portions) in the human body or a conductor (liquid or the like) in contact therewith. ), The first electrode 50 and the second electrode 51 are energized.

When the first electrode 50 and the second electrode 51 are in an energized state, the determination signal of the energization determining unit 30b is at a high level, and the operation control unit 30a is in this state when the WPS drive switch is turned on. A drive signal supply command is output to the drive signal supply unit 30f.
As a result, the piezoelectric element 401 of the volume changing unit 405 is driven to inject a high-pressure fluid (pulsating flow).
On the other hand, with the above configuration, the nozzle 211 (first contact portion 50a) and the tip portion (second contact portion 52a) of the suction tube 700 are the injection target portion (affected portion) in the human body or a conductor (liquid or the like) in contact therewith. 1), the first electrode 50 and the second electrode 51 are not energized.

When the first electrode 50 and the second electrode 51 are not in the energized state, the determination signal of the energization determining unit 30b is at a low level, and in this state, the operation control unit 30a turns on the WPS drive switch. However, the drive signal supply command is not output to the drive signal supply unit 30f. If the drive switch is on, a drive signal supply stop command is output to the drive signal supply unit 30f.
As described above, the fluid ejecting apparatus 3 of the present embodiment performs the fluid ejecting operation when the WPS drive switch is turned on while the first electrode 50 and the second electrode 52 are energized. The operations of the drive signal supply unit 30f and the volume changing unit 405 are controlled. On the other hand, when the first electrode 50 and the second electrode 52 are not energized, the drive signal supply unit 30f and the volume change so that the fluid ejection operation is not performed even when the WPS drive switch is turned on. The operation of the unit 405 is controlled.

Furthermore, when the first electrode 50 and the second electrode 51 are not energized during the fluid ejection operation, the drive signal supply unit 30f and the volume changing unit 405 are configured to stop the fluid ejection operation. Control the behavior.
As a result, when the first electrode 50 and the second electrode 51 are not energized, it is possible to prevent the ejection operation from being performed. Therefore, when the nozzle 211 moves away from the affected area or the liquid around it, Of high-pressure pulsatile flow in the direction of the patient (for example, to a person in the operating room or a region that is not desired to be removed) or the excision of a tissue piece removed by high-pressure injection from an unexpected direction or position It is possible to prevent scattering and the like from occurring.

  Further, in the fluid ejecting apparatus 3 according to the present embodiment, the nozzle 211, the connection channel pipe 200, and the suction pipe 700 are formed from conductive members, and the first electrode 50 is the nozzle 211, the connection channel pipe 200, and the electrode. Since the second electrode 52 is composed of the suction pipe 700 and the electrode line 52b, the original member constituting the fluid ejecting apparatus 3 is used, so that the second electrode 52 is lower than the separately provided configuration. The first electrode 50 and the second electrode 52 can be formed at a low cost.

  In the second embodiment, the nozzle 211 and the fluid ejection opening 212 correspond to the fluid ejection opening according to any one of modes 1, 3, 4, 5, 9, 10, and 14, and the volume is changed. The unit 405 and the drive signal supply unit 30f correspond to the volume changing means described in any one of the first, thirteen, and fourteenth aspects, and the fluid container 10 and the pump 20 are described in any one of the first, twelve, and fourteenth forms. The suction container 70 and the pump 60 correspond to the suction force applying means according to the ninth embodiment, and the operation control unit 30a is the operation control according to any one of the first, thirteen and fourteenth embodiments. Corresponding to the means, the energization determining unit 30b corresponds to the energization determining means described in any one of the first, eighth, thirteenth and fourteenth aspects, and the high frequency current applying unit 30c corresponds to the high frequency current applying means described in the eighth aspect. Correspondingly, the connection switching unit 30 Corresponds to the switching means according to the eighth.

[Modification of Second Embodiment]
A modification of the second embodiment of the present invention will be described below with reference to the drawings. FIGS. 12 to 13 are views showing a modification of the fluid ejection device, the driving method of the fluid ejection device, and the surgical instrument according to the second embodiment of the present invention.
This embodiment is different from the second embodiment in that the suction tube 700 is provided with the first contact portion of the first electrode and the second contact portion of the second electrode portion. . Accordingly, the other components are the same as those in the second embodiment, so that different parts will be described in detail below, and overlapping parts will not be described as appropriate.

First, the first and second configurations of the first electrode and the second electrode of the present modification will be described with reference to FIG. FIG. 12A is a cross-sectional view of the nozzle 211, the connection flow channel pipe 200, and the suction pipe 700 for explaining the first configuration of the first electrode and the second electrode in the present modification. ) Is a cross-sectional view of the nozzle 211, the connection channel pipe 200, and the suction pipe 700 for explaining the second configuration of the first electrode and the second electrode.
First, based on FIG. 12A, the first configuration of the first electrode and the second electrode in the present modification will be described.
As shown in FIG. 12A, the first electrode 53 serving as a positive electrode includes a first contact portion 53a formed at the distal end portion of the suction tube 700 formed of a conductive member, and a pulsation generating portion 100. And an electrode wire 53b that is electrically connected to the rear end of the suction tube 700.

The second electrode 54 serving as the negative electrode is wired inside the first contact portion 54a formed at the distal end portion of the suction tube 700 and the pulsation generating portion 100, and is electrically connected to the rear end portion of the suction tube 700. And an electrode line 54b.
The suction tube 700 includes a first tube wall portion 700 a that becomes a conductive path of the first electrode 53, a second tube wall portion 700 b that becomes a conductive path of the second electrode 54, and a cylindrical insulator 55. The first tube wall portion 700a and the second tube wall portion 700b are insulated by the insulator 55.
The electrode wire 53b is covered with a heat-resistant insulating coating, and one end is electrically connected to the first tube wall portion 700a and the other end is electrically connected to the switch of the connection switching portion 30d. Accordingly, the first contact portion 53a and the electrode line 53b are conducted.

The electrode wire 54b is covered with a heat-resistant insulating coating, one end is electrically connected to the second tube wall 700b, and the other end is electrically connected to the switch of the connection switching unit 30d. Therefore, the second contact portion 54a and the electrode line 54b are conducted.
The electrode wires 53b and 54b are wired through a passage (not shown) formed inside the pulsation generator 100. Similarly, the supply line PZT (+) connected to the high potential side of the piezoelectric element 401 and the supply line PZT (−) connected to the low potential side of the piezoelectric element 401 are covered with a heat-resistant insulating film. And is routed through a passage (not shown) formed inside the pulsation generator 100.
From the pulsation generating unit 100, a cable 47 in which the electrode wire 53b, the electrode wire 54b, the supply line PZT (+) and the supply line PZT (−) are gathered extends. Are electrically connected to corresponding components of the drive unit 30.

Next, a second configuration of the first electrode and the second electrode in this modification will be described with reference to FIG.
As shown in FIG. 12B, the first electrode 53 serving as the positive electrode is connected to the first contact portion 53a formed at the distal end portion of the suction tube 700 formed of a conductive member, and the first contact. And an electrode wire 53b electrically connected to the portion 53a.
The second electrode 54 serving as the negative electrode is wired inside the first contact portion 54a formed at the distal end portion of the suction tube 700 and the pulsation generating portion 100, and is electrically connected to the rear end portion of the suction tube 700. And an electrode line 54b.

The suction tube 700 includes a first tube wall portion 700a that becomes the first contact portion 53a of the first electrode 53, a second tube wall portion 700b that becomes a conductive path of the second electrode 54, and a cylindrical insulator. 55, and the first tube wall portion 700a and the second tube wall portion 700b are insulated by the insulator 55.
The electrode wire 53b is covered with an insulating film having heat resistance, one end is electrically connected to the first contact portion 53a, and the other end is electrically connected to the switch of the connection switching portion 30d. Accordingly, the first contact portion 53a and the electrode line 53b are conducted.

The electrode wire 54b is covered with a heat-resistant insulating coating, one end is electrically connected to the second tube wall 700b, and the other end is electrically connected to the switch of the connection switching unit 30d. Therefore, the second contact portion 54a and the electrode line 54b are conducted.
The electrode line 54b is routed through a passage (not shown) formed inside the pulsation generator 100. From the pulsation generator 100, the electrode line 54b, the supply line PZT (+), and the supply line A cable 47 in which PZT (−) is bundled extends, and each line of the cable 47 is electrically connected to a corresponding component of the drive unit 30.
The electrode wire 53b is arranged so as not to get in the way during the operation, such as being fixed over the outer peripheral surface of the suction tube 700.

With the first and second configurations described above, both the first contact portion 53a and the second contact portion 54a formed at the distal end portion of the suction tube 700 can be electrically contacted with the injection target portion (affected portion) or the human body. When brought into contact with a body (such as a liquid), the first electrode 53 and the second electrode 54 are energized.
When the first electrode 53 and the second electrode 54 are in an energized state, the determination signal of the energization determining unit 30b is at a high level, and the operation control unit 30a is in this state when the WPS drive switch is turned on. A drive signal supply command is output to the drive signal supply unit 30f.
As a result, the piezoelectric element 401 of the volume changing unit 405 is driven to inject a high-pressure fluid (pulsating flow).

On the other hand, when at least one of the first contact portion 53a and the second contact portion 54a is separated from the injection target portion (affected portion) in the human body or a conductor (liquid or the like) in contact therewith, the first electrode 53 and the second electrode The electrode 54 is not energized.
When the first electrode 53 and the second electrode 54 are not in the energized state, the determination signal of the energization determining unit 30b becomes a low level, and the operation control unit 30a turns on the WPS drive switch in this state. However, the drive signal supply command is not output to the drive signal supply unit 30f. If the drive switch is on, a drive signal supply stop command is output to the drive signal supply unit 30f.

Next, based on FIG. 13, the 3rd structure of the 1st electrode of this modification and a 2nd electrode is demonstrated. FIG. 13A is a cross-sectional view for explaining a third configuration of the first electrode and the second electrode in the present modification, and FIG. 13B is a diagram illustrating the nozzle 211 and connection in the fluid ejecting apparatus 3. It is sectional drawing of CC 'direction shown to (a) of the flow-path pipe | tube 200 and the suction pipe 700. FIG.
As shown in FIGS. 13 (a) and 13 (b), the suction tube 700 is made of an insulator and has cylindrical first, second and third insulating tube wall portions 55a, 55b having different diameters. 55c and a cylindrical first conductive tube wall portion 700c formed concentrically by a conductor between the first and second insulating tube wall portions 55a and 55b (diameter of 55a> diameter of 700c> diameter of 55b) ) And the second and third insulating tube wall portions 55b and 55c, a cylindrical second conductive tube wall portion 700d formed concentrically by a conductor (diameter of 55b> diameter of 700d> 55c Diameter).

That is, the diameter R1 of the first insulating tube wall 55a, the diameter R2 of the second insulating tube wall 55b, the diameter R3 of the third insulating tube wall 55c, and the first conductive tube wall 700c The diameter R4 and the diameter R5 of the second conductive tube wall 700d have a relationship of “R1>R4>R2>R5A> R3”.
The first electrode 56 serving as the positive electrode includes a first contact portion 56a formed at a tip portion of the first conductive tube wall portion 700c constituting the suction tube 700, and a main body portion of the first conductive tube wall portion 700c. And a conductive path 56b configured from the above, and an electrode line 56c that is wired inside the pulsation generating unit 100 and is electrically connected to the rear end of the first conductive tube wall 700c.
The second electrode 54 serving as the negative electrode includes a second contact portion 57a formed at the tip of the second conductive tube wall portion 700d constituting the suction tube 700, and a main body portion of the second conductive tube wall portion 700d. And an electrode wire 57c that is wired inside the pulsation generating portion 100 and electrically connected to the rear end portion of the second conductive tube wall portion 700d.

The electrode wire 56c is covered with a heat-resistant insulating coating, one end is electrically connected to the first conductive tube wall 700c, and the other end is electrically connected to the switch of the connection switching unit 30d. Yes. Accordingly, the first contact portion 56a and the electrode line 56c are conducted through the conductive path 56b.
The electrode wire 57c is covered with a heat-resistant insulating coating, and one end is electrically connected to the second conductive tube wall portion 700d and the other end is electrically connected to the switch of the connection switching portion 30d. Yes. Accordingly, the second contact portion 57a and the electrode line 57c are conducted through the conductive path 57b.
The electrode wires 56c and 57c are wired through a passage (not shown) formed inside the pulsation generator 100. From the pulsation generator 100, the electrode wire 56c, the electrode wire 57c, and the supply line PZT A cable 47 in which (+) and the supply line PZT (−) are collectively extended, and each line of the cable 47 is electrically connected to a corresponding component of the drive unit 30.

With the third configuration, the first contact portion 56a formed at the distal end portion of the first conductive tube wall portion 700c and the second contact portion formed at the distal end portion of the second conductive tube wall portion 700d. When both 57a are brought into contact with an injection target part (affected part) in a human body or a conductor (liquid or the like) in contact therewith, the first electrode 56 and the second electrode 57 are energized.
When the first electrode 56 and the second electrode 57 are in an energized state, the determination signal of the energization determining unit 30b is at a high level, and the operation control unit 30a is in this state when the WPS drive switch is turned on. A drive signal supply command is output to the drive signal supply unit 30f.
As a result, the piezoelectric element 401 of the volume changing unit 405 is driven to inject a high-pressure fluid (pulsating flow).

On the other hand, when at least one of the first contact portion 56a and the second contact portion 57a is separated from the injection target portion (affected portion) in the human body or a conductor (liquid or the like) in contact therewith, the first electrode 56 and the second electrode The electrode 57 is not energized.
When the first electrode 56 and the second electrode 57 are not in the energized state, the determination signal of the energization determining unit 30b is at a low level, and the operation control unit 30a turns on the WPS drive switch in this state. However, the drive signal supply command is not output to the drive signal supply unit 30f. If the drive switch is on, a drive signal supply stop command is output to the drive signal supply unit 30f.

  As described above, the fluid ejection device 3 to which the first to third configuration examples of the present modification are applied has the first electrode 53 and the second electrode 54 (or the first electrode 56 and the second electrode 57). When the WPS drive switch is turned on in the energized state, the operation of the drive signal supply unit 30f and the volume changing unit 405 is controlled so as to perform the fluid ejection operation. On the other hand, when the first electrode 53 and the second electrode 54 (or the first electrode 56 and the second electrode 57) are not energized, the fluid ejection operation is performed even if the WPS drive switch is turned on. The operations of the drive signal supply unit 30f and the volume changing unit 405 are controlled so as not to be performed.

Further, when the first electrode 53 and the second electrode 54 (or the first electrode 56 and the second electrode 57) are not energized during the fluid ejection operation, the fluid ejection operation is stopped. In this manner, the operations of the drive signal supply unit 30f and the volume changing unit 405 are controlled.
As a result, when the first electrode 53 and the second electrode 54 (or the first electrode 56 and the second electrode 57) are not energized, it is possible to prevent the ejection operation from being performed. Pulsating flow of high pressure in an unexpected direction (for example, toward a person in the operating room or a portion not desired to be removed) when the part (and the nozzle 211) is away from the affected part or the surrounding liquid It is possible to prevent the excision of the excised tissue pieces due to the injection of the high pressure from the unexpected direction or position.

Further, the first to third configurations of the present modification are configured such that the first contact portion 53a (or 56a) of the first electrode 53 (or 56) and the second electrode 54 (or 57) and the second electrode Since both the contact portions 53a (or 57a) are provided in the suction pipe 700, conventional nozzles 211 and connection flow path pipes 200 can be used as they are.
In addition, in the said 1st-2nd embodiment and the said modification, although it was set as the structure which functions as the electric knife with the fluid injection apparatus 1 or 3 by the high frequency current application part 30c and the connection switching part 30d, this structure It is good also as a structure which has not only the function as a water pulse knife but not only. In that case, the high-frequency current application unit 30c and the connection switching unit 30d are not necessary.

Moreover, in the said 1st-2nd embodiment and the said modification, although the 1st electrode was made into the positive electrode and the 2nd electrode was made into the negative electrode, it is good also as a reverse polarity.
In the first embodiment, the first electrode 50 is configured such that the nozzle 211 serves as the first contact portion 50a, and the second contact portion 51a of the second electrode 51 is replaced with a human body or the like. Although it was set as the structure affixed on an injection target object, it is not restricted to this structure, In the structure like the modification of the said 2nd Embodiment, it is a 1st contact part with respect to the nozzle 211 and the connection flow path pipe 200. It is good also as a structure which forms both 50a and the 2nd contact part 51a.

In addition, the first to second embodiments and the modification examples described above are preferable specific examples of the present invention, and various technically preferable limitations are given. However, the scope of the present invention is not limited to the above. Unless otherwise specified in the description, the present invention is not limited to these forms. In the drawings used in the above description, for convenience of illustration, the vertical and horizontal scales of members or parts are schematic views different from actual ones.
Further, the present invention is not limited to the first to second embodiments and the modifications described above, but includes modifications and improvements as long as the object of the present invention can be achieved. .

  DESCRIPTION OF SYMBOLS 1 ... Fluid injection apparatus, 2 ... Fluid injection part, 20 ... Pump as a pressure generation part, 30 ... Drive part, 50, 53, 56 ... 1st electrode, 50a, 53a, 56a ... 1st contact part, 51 , 52, 54, 57 ... second electrode, 51a, 52a, 54a, 57a ... second contact part, 60 ... suction pump, 30a ... operation control part, 30b ... energization determination part, 30c ... high frequency current application part, 30d ... Connection switching unit, 30e ... Data storage unit, 30f ... Drive signal supply unit, 100 ... Pulsation generating unit, 200 ... Connection channel tube, 201 ... Connection channel, 400 ... Diaphragm, 401 ... Piezoelectric element, 501 ... Fluid Chamber 211, Nozzle 212, Fluid ejection opening, 503, Inlet channel, 511, Outlet channel.

Claims (4)

A fluid chamber for pressurizing the fluid;
An outlet channel communicating with the fluid chamber;
A connecting pipe that communicates with the outlet channel and has an outer peripheral surface of a first diameter , including a fluid ejection opening for ejecting fluid;
A suction pipe having an inner peripheral surface with a second diameter larger than the first diameter, having a tip including a suction opening , and forming a suction path between the outer peripheral surface and the inner peripheral surface A suction tube,
Suction force applying means for applying a suction force to the suction tube;
A first electrode having a first contact portion provided at the tip of the suction tube ;
A second electrode having a second contact portion provided at a position having an insulator between the first contact portion and the tip of the suction tube;
High-frequency current applying means for applying a high- frequency current between the first electrode and the second electrode ;
A fluid ejecting apparatus comprising: The fluid ejection device according to claim 1,
I) The fluid ejecting apparatus, wherein the fluid ejecting opening protrudes from the suction opening. The fluid ejecting apparatus according to claim 1 or 2,
The fluid ejecting apparatus according to claim 1, wherein an outer periphery of the suction tube excluding the second electrode is covered with an insulator.   A surgical instrument using the fluid ejection device according to any one of claims 1 to 3.

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