JP2014195671A - Drive control part for fluid squirting device and surgical instrument - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a fluid squirting device which can squirt by switching a resection fluid and a contrast medium.SOLUTION: A fluid squirting device 1 includes: a fluid squirting part 40 which squirts either a resection fluid or a contrast medium; a pump 20 as fluid feeding means for feeding the resection fluid or the contrast medium to the fluid squirting part 40; a catheter 6 for connecting the fluid squirting part 40 and the pump 20; and valves 31, 32 as switching means for switching the fluid to be squirted to either the resection fluid or the contrast medium. In performing a resection on an object to be resected within a capillary tissue confirmed by imaging, the fluid to be fed is switched from the contrast medium to the resection fluid for performing the resection. In confirming the state of the capillary tissue after the resection, the fluid to be fed can be switched from the resection fluid to the contrast medium. Consequently, the insertion and removal of the catheter 6 is not required for each imaging and resection, and burdens on both a patient and an operator are significantly reduced.

Description

The present invention relates to a fluid ejecting apparatus that switches ablation fluid or contrast medium and ejects it from one fluid ejecting unit.

Conventionally, in order to enable the imaging of the circulatory system, a contrast catheter that is inserted into a blood vessel of a living body and ejects a contrast agent has been used (for example, see Patent Document 1).

On the other hand, there has been proposed a fluid ejecting apparatus that is inserted into a thin tube tissue such as a blood vessel of a living body and is arranged at the distal end of a catheter and ejects a resection fluid in a pulsed manner as being suitable for excision of an obstruction in the blood vessel (
For example, see Patent Document 2).

JP 2000-84087 A Japanese Patent No. 4311483

Patent Document 1 and Patent Document 2 described above are fluid ejecting apparatuses suitable for imaging in a living tubule tissue and excision of an obstruction in the tubule tissue. Here, when excising the object to be excised in the tubule tissue confirmed by contrast imaging, the ablation catheter must be taken out and the excision catheter having the excision fluid ejecting apparatus must be inserted into the tubule tissue again. Alternatively, the contrast catheter must be reinserted when confirming the state of the tubule tissue after resection.

As described above, alternately inserting the contrast catheter and the excision catheter into the tubule tissue has a problem that a burden is great for both the patient and the practitioner.

SUMMARY An advantage of some aspects of the invention is to solve at least a part of the problems described above, and the invention can be implemented as the following forms or application examples.

Application Example 1 A fluid ejecting apparatus according to this application example includes one fluid ejecting unit that ejects either a resection solution or a contrast agent, and a fluid that supplies the ablation solution or the contrast agent to the fluid ejecting unit. A supply means, a fluid supply tube connecting the fluid ejecting section and the fluid supply means,
Switching means for switching the fluid to be ejected to either the excision fluid or the contrast agent;
Is provided.

According to this application example, the fluid supplied to the fluid ejecting unit is switched to either the excision fluid or the contrast agent by the switching unit, the excision fluid is ejected from one fluid ejecting apparatus, the tissue is excised, and the contrast agent is ejected. Thus, it is possible to perform tissue imaging. Therefore, when excising the target to be excised in the tubule tissue confirmed by the contrast medium, the fluid to be supplied is switched from the contrast medium to the excision liquid, and excision is performed. When the state of the tubule tissue after excision is confirmed, the excision liquid To a contrast medium.

Therefore, it is not necessary to insert and withdraw the catheter for every contrast and excision, and the burden can be remarkably reduced for both the patient and the practitioner.

Application Example 2 In the fluid ejecting apparatus according to the application example, the fluid ejecting unit includes a fluid chamber and a volume changing unit that modifies the volume of the fluid chamber. It is preferable that switching is possible.

The fluid ejecting apparatus having such a configuration converts the fluid into a pulsating flow by driving the volume changing unit and ejects the pulsed flow. Further, when the volume changing means is not driven (when the volume of the fluid chamber is kept constant), continuous flow injection can be performed. That is, pulse flow injection or continuous flow injection can be selected, and it is possible to use in an appropriate injection state suitable for the application of the fluid injection device.

Here, the pulsating flow means a fluid flow in which the fluid flow direction is constant and the fluid flow rate or flow velocity is accompanied by periodic or irregular fluctuations. The pulsating flow includes an intermittent flow in which the flow and stop of the fluid are repeated. However, since the flow rate or flow velocity of the fluid only needs to fluctuate periodically or irregularly, the pulsating flow is not necessarily an intermittent flow. Similarly, ejecting fluid in pulses means ejecting fluid in which the flow rate or movement speed of the fluid to be ejected varies periodically or irregularly. An example of pulse flow injection is intermittent injection in which fluid injection and non-injection are repeated. However, the flow rate or movement speed of the fluid to be injected only needs to fluctuate periodically or irregularly. There is no need.

Application Example 3 In the fluid ejection device according to the application example described above, it is preferable that the contrast medium ejection pressure by the fluid ejection unit is controlled to a level that does not have an ablation force.

In this way, safety can be ensured without damaging a living tissue at the time of contrast medium injection. Further, if the injection pressure is lowered, the contrast agent may be injected by pulse flow injection.

BRIEF DESCRIPTION OF THE DRAWINGS FIG. FIG. 3 is a cross-sectional view illustrating the fluid ejecting unit according to the first embodiment. FIG. 6 is an explanatory diagram illustrating a part of a fluid ejection device according to a first modification of the first embodiment. FIG. 5 is a configuration explanatory view showing a part of a fluid ejection device according to a second modification of the first embodiment. FIG. 4 is a configuration explanatory view showing a fluid ejection device according to a second embodiment. FIG. 9 is a configuration explanatory view showing a fluid ejection device according to a modification of the second embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the drawings. 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, surgical scalpels, etc., but incising or excising living tissue by ejecting excision fluid. A fluid ejecting apparatus capable of ejecting a contrast agent and injecting it into a capillary tissue will be described as an example. Therefore, the excision fluid used in the embodiment is water or physiological saline.
Note that the drawings referred to in the following description are schematic views in which the vertical and horizontal scales of members or portions are different from actual ones for convenience of illustration.
(Embodiment 1)

FIG. 1 is a configuration explanatory diagram illustrating a fluid ejection device according to the first embodiment. In FIG. 1, the fluid ejecting apparatus 1 includes an excision fluid container 2, a contrast medium container 3, a switching unit 30, a drive control unit 10 including a pump 20 as a fluid supply unit, and a fluid ejecting unit 40. Has been.

The switching means 30 includes a valve 31 and a valve 32, and is controlled to be opened and closed by a valve control circuit (not shown). The excision fluid container 2 and the pump 20 are connected by a fluid supply pipe 4 via a valve 32, and the excision fluid is fed. Further, the contrast agent container 3 and the pump 20 are connected by a fluid supply pipe 5 via a valve 31, and the contrast agent is fed.

The valves 31 and 32 are check valves because the liquid flow from the excision fluid container 2 and the contrast medium container 3 to the pump 20 is enabled and the flow in the reverse direction is impossible, and the switching means in the present embodiment. 30 is a three-way valve structure which has two inflow side flow paths and one outflow side flow path.

The drive control unit 10 includes a pump drive circuit that controls the drive of the pump 20, a valve control circuit that controls the opening and closing of the valves 31 and 32 of the switching unit 30, and a piezoelectric element drive circuit that controls the drive of the fluid ejecting unit 40 ( Both are omitted), and a start switch 11 of the fluid ejection device 1,
And a changeover switch 12 for switching the supply of ablation fluid or contrast medium.

The fluid ejecting unit 40 and the pump 20 are connected by a fluid supply tube 6. The fluid supply tube 6 has flexibility because it is inserted following a thin tube tissue such as a blood vessel, and corresponds to a catheter in this embodiment. Therefore, the fluid supply tube 6 is hereinafter referred to as a catheter 6.

The fluid ejecting unit 40 supplies the excision fluid or contrast agent supplied from the pump 20 to the fluid ejecting opening 8.
3 is a configuration capable of pulse flow injection or continuous flow injection, and the configuration will be described below with reference to the drawings.

FIG. 2 is a cross-sectional view illustrating the fluid ejecting unit according to the present embodiment. The fluid ejecting unit 40 is configured in a cylindrical shape having a substantially circular cross section in a state where the opposing surfaces of the upper case 61 and the lower case 62 are joined to each other. A concave portion is formed in a surface facing the upper case 61 of the lower case 62, and a space formed by the concave portion and the diaphragm 51 that is closely fixed between the opposed surfaces of the upper case 61 and the lower case 62 is formed. This is the fluid chamber 70.

In the lower case 62, an inlet channel 81 and an outlet channel 82 communicating with the fluid chamber 70 are formed,
A piezoelectric element 52 as volume changing means is fixed to the surface of the diaphragm 51 opposite to the fluid chamber 70. The tip of the outlet channel 82 is a fluid ejection opening 83.

As is clear from FIG. 2, the fluid ejection section 40 according to the present embodiment has an inlet channel 81, a fluid chamber 70, and an outlet channel 82 formed in a straight line. By adopting such a configuration, it is possible to reduce the number of wall portions with which the fluid collides, and thus it is possible to reduce the bubbles remaining in the wall portion with which the fluid collides. As a result, the fluid chamber 70 is influenced by the retained bubbles.
Can be prevented from decreasing.
The inlet channel 81, the fluid chamber 70, and the outlet channel 82 are not necessarily formed on a straight line.

In FIG. 2, the diaphragm 51 is disposed in parallel with the bottom surface of the fluid chamber 70 (the surface formed by the lower case 62). In other words, it can be said that the diaphragm 51 is arranged in parallel to the direction in which the fluid flows. With this configuration,
The outer diameter of the fluid ejecting section 40 can be made substantially the same as the outer diameter of the catheter 6, and the fluid ejecting section 40 can be inserted into a thin tube tissue such as a blood vessel as will be described later.

In addition, by arranging the diaphragm 51 in parallel with the bottom surface of the fluid chamber 70, the area in which the diaphragm 51 forms the fluid chamber 70 can be increased. As a result, the amount by which the volume of the fluid chamber 70 is reduced by the deformation of the diaphragm 51 (= fluid exclusion volume in the fluid chamber) can be increased. For example, when the diaphragm 51 is disposed perpendicular to the bottom surface of the fluid chamber 70, the area where the diaphragm 51 forms the fluid chamber 70 is limited to the outer diameter of the fluid ejecting unit 40.
Due to the deformation of the diaphragm 51, the fluid exclusion volume of the fluid chamber 70 cannot be increased.

Next, the fluid ejection operation of the fluid ejection unit in the present embodiment will be described with reference to FIGS. 1 and 2. First, the case of pulse flow injection will be described. The fluid ejection of the fluid ejecting unit 40 of the present embodiment is performed by the difference between the synthetic inertance L1 on the inlet flow path 81 side and the synthetic inertance L2 on the outlet flow path 82 side.

First, inertance will be described.
The inertance L is ρ when the fluid density is ρ, the cross-sectional area of the flow path is S, and the length of the flow path is h.
L = ρ × h / S. When the pressure difference in the flow path is ΔP and the flow rate of the fluid flowing in the flow path is Q, the equation of motion in the flow path is transformed using the inertance L so that ΔP = L × dQ /
The relationship dt is derived.

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.

The combined inertance L1 on the inlet channel 81 side is calculated in the range of the inlet channel 81.
The synthetic inertance L2 on the outlet channel 82 side is calculated in the range of the outlet channel 82.

In this embodiment, the flow path length and cross-sectional area of the inlet flow path 81 and the outlet flow path 82 are set so that the synthetic inertance L1 on the inlet flow path 81 side is larger than the synthetic inertance L2 on the outlet flow path 82 side. Set the channel length and cross-sectional area.

Next, the fluid ejection operation will be described.
Fluid is always supplied to the inlet channel 81 at a constant pressure (steady flow rate) by the pump 20. As a result, when the piezoelectric element 52 does not operate, the discharge force of the pump 20 and the inlet channel 8
The fluid flows into the fluid chamber 70 due to the difference in the channel resistance of the entire side.

Here, if a drive signal is input and the piezoelectric element 52 is suddenly displaced in a convex shape toward the fluid chamber 70 in the normal direction of the surface of the diaphragm 51 on the fluid chamber 70 side, the diaphragm 51 is similarly moved by the piezoelectric element 52. The diaphragm 51 is pressed in a convex shape toward the fluid chamber 70, and the diaphragm 51 is deformed in a direction to reduce the volume of the fluid chamber 70. If the combined inertances L1 and L2 on the inlet channel 81 side and the outlet channel 82 side have a sufficient size, the pressure in the fluid chamber 70 rises rapidly and reaches several tens of atmospheres.

Since this pressure is much larger than the pressure by the pump 20 applied to the inlet channel 81, the inflow of the fluid from the inlet channel 81 into the fluid chamber 70 is reduced by the pressure, and from the outlet channel 82. Outflow increases.

However, the combined inertance L1 on the inlet flow path 81 side is larger than the synthetic inertance L2 on the outlet flow path 82 side, and is discharged from the outlet flow path 82 more than the reduction amount of the flow rate flowing into the fluid chamber 70 from the inlet flow path 81. Since the increased amount of fluid to be applied is larger, pulsed fluid discharge, that is, pulsating flow is generated in the outlet channel 82. The fluid is ejected from the fluid ejection opening 83 due to the pressure fluctuation during the ejection.

On the other hand, the inside of the fluid chamber 70 is in a low pressure state close to a vacuum immediately after the pressure increase due to the interaction between the decrease in the fluid inflow amount from the inlet channel 81 and the increase in the fluid outflow from the outlet channel 82. When the piezoelectric element 52 is restored to its original shape, the fluid in the inlet flow path 81 flows before the operation of the piezoelectric element 52 (before displacement) after a predetermined time has elapsed due to both the pressure of the pump 20 and the low pressure state in the fluid chamber 70. ) Returns to the fluid chamber 70 at the same speed.

If the piezoelectric element 52 is displaced after the fluid flow in the inlet channel 81 is restored, pulsed droplets are continuously ejected from the fluid ejection opening 83.

The above-described fluid ejecting unit 40 exemplifies a configuration in which fluid is ejected in a pulsed manner by the inertance effect. However, a check valve is provided in the inlet channel 81 and the check valve is opened when the fluid flows into the fluid chamber 70. The check valve may be closed when the volume of the fluid chamber 70 is reduced.

When the piezoelectric element 52 is not driven, that is, when the volume of the fluid chamber 70 is kept constant, no pulsating flow is generated, and the fluid is ejected by continuous flow ejection.

Accordingly, the fluid ejection from the fluid ejection opening 83 is a pulse flow ejection when the fluid ejection section 40 is driven and a pulse flow ejection, and a continuous flow ejection when the fluid ejection section 40 is not driven. Thus, it is possible to switch between pulse flow injection and continuous flow injection.

Subsequently, a driving method of the fluid ejecting apparatus 1 according to the present embodiment will be described with reference to FIGS. 1 and 2. First, it is determined by operating the changeover switch 12 whether to eject the excision fluid or the contrast agent. Here, a case where a contrast agent is selected will be described. When a contrast agent is selected, the valve control circuit closes the valve 32 and opens the valve 31. Therefore, the excision fluid does not flow.

Next, when the start switch 11 is turned on, the pump 20 is started by the pump drive circuit. When it is determined in advance that the contrast medium is ejected continuously, the piezoelectric element 52 is not driven. Further, in the case of pulse flow injection, as the start switch 11 is turned on, the piezoelectric element 52 is driven by the piezoelectric element drive circuit to generate a pulsating flow and pulse flow injection is performed.
At this time, in the case of injecting the contrast agent, the injection pressure is set to a level that does not damage the living tissue, whether continuous flow injection or pulse flow injection.

In addition, as a contrast agent, when inject | pouring into tubule tissue, such as a blood vessel, the iodine contrast agent etc. which are a radiopaque substance are used, for example, and X-ray contrast is performed as needed.

When the affected part to be excised is specified by the contrast agent, the activation switch 11 is turned off to temporarily stop driving the pump 20. When the pulse flow injection is being performed, the driving of the piezoelectric element 52 is stopped, and then the driving of the pump 20 is stopped. Then, the changeover switch 12 is operated to switch from contrast medium discharge to excision liquid discharge. Along with this operation, the valve control circuit controls the valve 3
2 is opened and the valve 31 is closed. Therefore, the contrast agent does not flow.

Next, when the start switch 11 is turned on, the pump 20 is started by the pump drive circuit. When the excision fluid discharge is a pulse flow injection, the start switch 11 is turned on.
The piezoelectric element 52 is driven by the piezoelectric element driving circuit, and a pulsating flow is generated, resulting in pulse flow ejection. In addition, when it is determined in advance that the continuous flow injection is performed, the piezoelectric element 52 is not driven.
When the excision fluid is discharged, the injection pressure necessary for excision or incision is controlled in order to excise or incise the living tissue. Next, the ablation force in the case of pulse flow injection and continuous flow injection will be described.

In the case of pulse flow injection, the body tissue is excised so as to be scraped off mainly by the leading wave of the pulsed fluid or the impact pressure of the fluid particles. At this time, the factors that determine the excision force due to the impact pressure of one pulse are the volume change amount (fluid exclusion volume) of the fluid chamber 70 that determines the size of the fluid particle of the pulse flow,
This is the speed at which the volume of the fluid chamber 70 that determines the speed of the fluid particles in the pulse flow is reduced (corresponding to the driving time of the piezoelectric element 52 when the volume of the fluid chamber 70 is reduced). Good. Moreover, it has the characteristic that the injection flow rate may be small.

In the case of continuous flow injection, excision or incision is performed while the living tissue is expanded by the fluid pressure of the continuously injected fluid. Therefore, the excision force due to the fluid pressure is affected by the fluid supply pressure by the pump 20. Therefore, in the case of continuous flow injection, the injection flow rate is likely to increase as compared with pulse flow injection.

In consideration of the characteristics of these continuous flow injection and pulse flow injection, it is more preferable to use continuous flow injection when injecting a contrast medium into a tubule tissue, and to use pulse flow injection for excision of living tissue,
In the case of a contrast medium, the fluid supply pressure of the pump 20 is controlled within a range where there is no excision force.

As described above, when the fluid to be supplied to the fluid ejecting unit 40 is switched to either the excision liquid or the contrast agent by the switching unit 30, the supply is performed when the excision target in the tubule tissue confirmed by the contrast is excised. When the excision fluid is switched from the contrast medium to the excision solution and the state of the tubule tissue after the excision is confirmed, the excision fluid can be switched to the contrast medium.

Therefore, it is not necessary to insert and withdraw the catheter 6 for every contrast and excision, and the burden on both the patient and the practitioner can be significantly reduced.

The fluid ejecting section 40 includes a fluid chamber 70 and a piezoelectric element 52 and a diaphragm 51 as volume changing means for changing the volume of the fluid chamber 70, and the fluid is converted into a pulsating flow by driving the piezoelectric element 52. When the piezoelectric element 52 is not driven and the piezoelectric element 52 is not driven (when the volume of the fluid chamber 70 is maintained constant), the fluid injection can be switched such that the continuous flow injection is performed.

In the case of pulse flow injection, the body fluid is cut off by mainly using the leading wave of the pulsed fluid or the impact pressure of the fluid particles, so that the fluid supply pressure to be supplied may be low and the supply flow rate can be extremely reduced. It is suitable for excision of living tissue.

In addition, in the case of continuous flow injection, it is considered that it is suitable for exfoliation and excision of obstructions in a thin tube tissue because it is excised while expanding the living tissue with the fluid pressure of the fluid. If it switches, it can respond to various operations. At this time, if an injection flow changeover switch is provided, the changeover can be easily performed.

Further, in the case of continuous flow injection, since the injection flow rate is easily increased as compared with pulse flow injection even when the fluid supply pressure is lowered, it is more suitable for contrast medium injection.
(Modification 1)

Subsequently, a modification of the above-described first embodiment will be described. The first modification is characterized in that a dedicated pump is provided for supplying the contrast medium and the excision fluid. The description will focus on the differences from the first embodiment. In addition, the same code | symbol is attached | subjected and demonstrated to a common element with Embodiment 1. FIG.
FIG. 3 is an explanatory diagram illustrating a part of the fluid ejection device according to the first modification. In FIG.
A pump 21 is connected to the fluid supply pipe 4 that supplies the excision fluid, and a pump 20 is connected to the fluid supply pipe 5 that supplies the contrast medium.

A switching means 30 is disposed between the catheter 6 and the pump 20 and the pump 21. The switching means 30 includes a valve 31 and a valve 32, and is controlled to be opened and closed by a valve control circuit (not shown). The pump 21 and the catheter 6 are connected via a valve 32, and excision fluid is sent. Further, the pump 20 and the catheter 6 are connected via a valve 31, and a contrast medium is fed. The switching means 30 in the modified example 1 has a three-way valve structure having two inflow side channels and one outflow side channel.

Subsequently, a driving method of the fluid ejecting apparatus 1 according to Modification 1 will be described with reference to FIGS. 1 and 3. First, it is determined whether to operate the changeover switch 12 to eject the excision fluid or the contrast agent. Here, a case where a contrast agent is selected will be described. When a contrast agent is selected, the valve control circuit closes the valve 32 and opens the valve 31. Therefore, the excision fluid does not flow.

Next, when the start switch 11 is turned on, the pump 20 is started by the pump drive circuit. When it is determined in advance that the contrast medium is ejected continuously, the piezoelectric element 52 is not driven. Further, in the case of pulse flow injection, as the start switch 11 is turned on, the piezoelectric element 52 is driven by the piezoelectric element drive circuit to generate a pulsating flow and pulse flow injection is performed.
At this time, in the case of injecting the contrast agent, the injection pressure is set to a level that does not damage the living tissue, whether continuous flow injection or pulse flow injection.

When the affected part to be excised is specified by the contrast agent, the activation switch 11 is turned off to temporarily stop driving the pump 20. When the pulse flow injection is being performed, the driving of the piezoelectric element 52 is stopped, and then the driving of the pump 20 is stopped. Then, the changeover switch 12 is operated to switch from contrast medium discharge to excision liquid discharge. Along with this operation, the valve control circuit controls the valve 3
2 is opened and the valve 31 is closed. Therefore, the contrast agent does not flow.

Next, when the start switch 11 is turned ON, the pump 21 is started by the pump drive circuit. When the excision fluid discharge is a pulse flow injection, the start switch 11 is turned on.
The piezoelectric element 52 is driven by the piezoelectric element driving circuit, and a pulsating flow is generated, resulting in pulse flow ejection. In addition, when it is determined in advance that the continuous flow injection is performed, the piezoelectric element 52 is not driven.
When the excision fluid is discharged, the injection pressure necessary for excision is controlled in order to excise or incise the living tissue.

Even with the configuration of the first modification, the same effects as those of the first embodiment described above can be obtained. Further, since the dedicated pump 20 and the pump 21 are respectively provided for the supply of the contrast medium and the ablation liquid, the fluid can be supplied at a fluid supply pressure suitable for the supply of the contrast medium or the ablation liquid. There is an advantage.
(Modification 2)

Subsequently, a fluid ejecting apparatus according to Modification 2 will be described. Modification 2 is characterized in that a dedicated pump and a valve are provided for supplying the contrast medium and the excision solution, respectively. The description will focus on the differences from the first embodiment and the first modification. In addition, the same code | symbol is attached | subjected and demonstrated to a common element with Embodiment 1. FIG.

FIG. 4 is a configuration explanatory view showing a part of the fluid ejection device according to the second modification. In FIG.
A pump 21 is connected to the fluid supply pipe 4 that supplies the excision fluid, and a valve 34 is disposed upstream of the pump 21. A pump 20 is connected to the fluid supply pipe 5 that supplies the contrast agent, and a valve 33 is disposed on the upstream side of the pump 20. The valves 33 and 34 are controlled to open and close by a valve control circuit (not shown). The fluid supply pipe 5 and the fluid supply pipe 4 are connected to the catheter 6 by a pipe joint 35.

The driving method of Modification 2 is the same as that of Modification 1 described above, but when supplying a contrast agent,
The valve 33 is opened and the pump 20 is started. At this time, the valve 34 is closed. In the case of excision fluid, the valve 34 is opened and the pump 21 is started. At this time, the valve 33 is closed.

Even with the configuration of the second modification, the same effects as those of the first embodiment and the first modification described above can be obtained.

The valve 33 may be disposed between the pump 20 and the pipe joint 35, and the valve 34 may be disposed between the pump 21 and the pipe joint 35.
(Embodiment 2)

Next, the fluid ejecting apparatus according to the second embodiment will be described with reference to the drawings. Embodiment 2
In contrast to the configuration in which the first embodiment described above sends the ablation solution or contrast medium to the fluid ejecting section using a single catheter 6, the ablation solution and the contrast agent are each fed by a dedicated fluid supply tube. It is characterized by The parts common to the first embodiment are denoted by the same reference numerals, and different points will be mainly described.

FIG. 5 is an explanatory diagram illustrating a configuration of the fluid ejecting apparatus according to the second embodiment. In FIG. 5, the fluid ejection device 1 includes a fluid supply pipe 5 connected to the contrast agent container 3, a valve 33, a pump 20,
The tube 9, the fluid supply pipe 4 connected to the excision fluid container 2, the valve 34, the pump 21, the tube 8, and the fluid ejecting unit 40 communicating with the tubes 8 and 9 are configured. Therefore,
The excision solution is sent to the tube 8 and the contrast medium is sent to the tube 9. Pumps 20 and 21
Since the configuration on the upstream side is the same as that of Modification 2 described above, the description thereof is omitted.

The basic configuration of the fluid ejecting unit 40 is the same as that of the first embodiment (see FIG. 2), and the introduction tube 7 is connected to the end of the inlet channel 81 side. The introduction tube 7 is flexible, and the tube 8,
9 is inserted. Plug members 90 and 91 are provided at both ends of the introduction tube 7. The plug member 90 and the plug member 91 are hermetically sealed while securing the flow paths of the tubes 8 and 9.

A space 93 surrounded by the fluid ejecting unit 40, the plug member 90, and the introduction tube 7 is a liquid reservoir, and since the tubes 8 and 9 cannot be directly connected to the inlet flow path 81, they are provided as buffers.

The driving method of the present embodiment is the same as that of the second modification described above, except that the contrast agent is fed through the dedicated tube 9 and the excision solution is fed through the dedicated tube 8. Therefore, it has the same effect as the first embodiment described above.

In addition, the contrast medium is fed from the contrast medium container 3 to the tube 9 through a dedicated flow path, and the excision liquid is fed from the excision liquid container 2 to the tube 8 through a dedicated flow path. It is possible to fix the fluid supply pressure to an appropriate value, and there is an effect that control becomes easy.
Furthermore, the thin tubes 8 and 9 can be protected by providing the introduction tube 7.

In this embodiment, the introduction tube 7 is configured to cover most of the tubes 8 and 9 in the length direction, but may be provided only in the range of the plug member 90 on the fluid ejecting unit 40 side. Good.
(Modification of Embodiment 2)

Subsequently, a modification of the second embodiment will be described with reference to the drawings. This modification is characterized in that the introduction tube 7 and the tubes 8 and 9 of Embodiment 2 described above are integrated. Therefore, it demonstrates centering on a different location from Embodiment 2. FIG. In addition, the same code | symbol is attached | subjected and demonstrated to a common part.

FIG. 6 is a configuration explanatory view showing a fluid ejecting apparatus according to a modification of the second embodiment. In FIG. 6, a fluid supply tube 101 having flexibility is connected to the fluid ejecting unit 40, and an end opposite to the fluid ejecting unit 40 is connected to the branch joint 110.

The fluid supply tube 101 is opened with a first flow path 102 for feeding a contrast medium and a second flow path 103 for feeding a cutting fluid. And the 1st flow path 102 and the 2nd flow path 10
3 and an inlet channel 81 is provided with a space 93 as a liquid reservoir. Therefore, it can be said that the fluid supply tube 101 is a catheter having the first flow path 102 and the second flow path 103.

The branch joint 110 includes a connection channel 111 that communicates with the first channel 102, and a connection channel 111.
The connection flow path 112 communicates with the connection pipe 116, and the connection pipe 116 is connected to the pump 20. Further, the branch joint 110 includes the second flow path 10.
3 and a connection flow path 114 communicating with the connection flow path 113 are formed. The connection flow path 114 communicates with the connection pipe 115, and the connection pipe 115 is connected to the pump 21. The configuration upstream from the pumps 20 and 21 is the same as that of the second modification described above, and a description thereof will be omitted.

The driving method of this modification is the same as that of the second embodiment described above except that the contrast medium is sent through the first flow path 102 and the excision liquid is sent through the second flow path 103. Therefore,
This has the same effect as the second embodiment described above.

Further, since the first flow path 102 and the second flow path 103 are formed in the fluid supply tube 101, the flow path diameter is larger than that of the second embodiment (see FIG. 5) having the tubes 8 and 9 and the introduction tube 7. Can be increased, and the flow path resistance can be reduced.
1 fluid supply pressure can be reduced.

In the first and second embodiments described above, the fluid ejecting unit 40 is configured to generate the pulsating flow by pressing the diaphragm 51 with the piezoelectric element 52. However, the configuration is not limited to this, and the configuration generating the pulsating flow. Any other form may be used. For example, the volume of the fluid chamber may be changed by driving a piston (plunger) using a piezoelectric element to generate a pulsating flow. Alternatively, the liquid in the fluid chamber may be formed into a bubble (bubble) by laser induction, and a pulsating flow may be generated by ejecting the bubble. Even in these configurations, it is possible to switch to the continuous flow injection if the driving of the fluid injection unit is stopped.

Moreover, in Embodiment 1 and Embodiment 2 described above, two types of fluids to be ejected, the excision fluid and the contrast agent, are exemplified, but the number of fluids is not limited to two and can be increased. For example, in addition to the excision fluid and the contrast agent, a medical solution for treatment can be used, and it is also possible to appropriately combine these plural types of liquids and to switch and eject them according to the application.

DESCRIPTION OF SYMBOLS 1 ... Fluid ejection apparatus, 2 ... Ablation fluid container, 3 ... Contrast medium container, 6 ... Catheter (fluid supply tube), 20 ... Pump as fluid supply means, 30 ... Switching means, 31, 32 ... Valve,
40: Fluid ejecting section.

Claims (3)

One fluid ejecting section that ejects either the excision fluid or the contrast medium;
Fluid supply means for supplying the excision fluid or the contrast agent to the fluid ejection unit;
A fluid supply tube connecting the fluid ejecting section and the fluid supply means;
Switching means for switching the fluid to be ejected to either the excision fluid or the contrast agent;
A fluid ejecting apparatus comprising: The fluid ejection device according to claim 1,
The fluid ejecting apparatus according to claim 1, wherein the fluid ejecting unit includes a fluid chamber and a volume changing unit configured to change a volume of the fluid chamber, and is switchable between pulse flow ejection and continuous flow ejection. The fluid ejection device according to claim 1 or 2,
The fluid ejecting apparatus, wherein the contrast medium ejecting pressure by the fluid ejecting unit is controlled to have no ablation force.

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