JP2010063587A - Fluid injection device and surgical instrument - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a fluid injection device having outer members for sealing a pulsation generation section and being detachably attached to the pulsation generation section. <P>SOLUTION: The fluid injection apparatus 10 includes: a pulsation generation section 30 having a fluid chamber 120 and a diaphragm 70 for changing the volume of the fluid chamber 120, and pulsatingly discharging the fluid; a connecting duct tube 90 having a connecting duct 92 communicated with the fluid chamber 120 and a fluid injection opening 97, transmitting the pulsation of the fluid passed from the pulsation generation section 30 to the fluid injection opening 97 and detachably mounted to the pulsation generation section 30; a fluid feed tube 25 being press-fitted in a part of the pulsation generation section 30 and feeding the fluid to the fluid chamber 120; a drive signal cable for inputting drive signals to the pulsation generation section 30; a first protection tube 27 press-fitted in a part of the pulsation generation section 30 and where the drive signal cable is inserted; and an upper case 35 and a lower case 36, as outer members, for sealing the circumference of the pulsation generation section 30 and being detachably attached to the pulsation generation section 30. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a fluid ejection device including a pulsation generator that pulsates and discharges a fluid, a connection flow channel pipe that is inserted into the pulsation generator, an outer member that seals the pulsation generator, and a surgical instrument including the fluid ejection device About.

  In the operation using the ejected fluid, the organ parenchyma can be incised while preserving the vasculature such as blood vessels. Furthermore, since incidental damage to living tissue other than the incision is slight, the burden on the patient is small. In addition, since there is little bleeding, the bleeding does not interfere with the field of view of the operative field, so that a rapid operation is possible.

  As a fluid ejection device for incising or excising a living tissue, a pulsation generating unit that performs a fluid discharge operation by reducing the volume of a fluid chamber, a connection channel tube connected to an outlet channel of the pulsation generating unit, and pulsation generation A fluid ejecting apparatus having a cover that seals a part is known (for example, see Patent Document 1).

JP 2005-152127 A

  When incising or excising a living tissue using such a fluid ejecting apparatus, fluid supply including a cover as well as a connecting flow channel tube that is considered to come into contact with the living tissue except for a pulsation generating portion sealed by the cover is provided. Blood or body fluid may adhere to the tube or drive signal cable.

  In such a case, it is desirable that the cover, the connection channel tube, the fluid supply tube, and the drive signal cable be disposable for each operation.

  However, in Patent Document 1 described above, since the connection channel tube and the drive signal cable are not easily detachable from the pulsation generating portion, the fluid ejecting apparatus in a state in which these are mounted must be disposable. , Leading to higher running costs.

  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 a fluid chamber, a diaphragm that changes the volume of the fluid chamber, a pulsation generator that pulsates and discharges fluid, and a connection that communicates with the fluid chamber. A connecting flow path pipe having a flow path and a fluid ejection opening, which transmits a pulsation of a fluid flowing from the pulsation generation section to the fluid ejection opening, and is detachably attached to the pulsation generation section A fluid supply tube that is press-fitted into the pulsation generator and supplies fluid to the fluid chamber, a drive signal cable that inputs a drive signal to the pulsation generator, and a drive signal cable that is press-fitted into the pulsation generator A first protection tube to be inserted and an outer shell member that seals the pulsation generation unit and is detachable from the pulsation generation unit are provided.

  According to this application example, since the pulsation generating unit is sealed by the outer member, the pulsation generating unit does not come into contact with blood, body fluid, or the like, and can be used repeatedly by removing the outer member.

  In addition, it is possible to prevent the drive characteristics of the pulsation generation unit from being affected by moisture entering the pulsation generation unit.

  In addition, since the connecting flow channel tube is detachable from the pulsation generating portion, it can be easily replaced with one that has been cleaned and disinfected after the treatment. Furthermore, there is an effect that a plurality of types of connection channel pipes are prepared and a shape suitable for the treatment site can be selected and used.

  In addition, the fluid supply tube is press-fitted into the pulsation generator, but if a flexible material is used, the user can easily attach the fluid supply tube that has been pulled out, cleaned and sterilized after the operation to the pulsation generator. Become.

  The drive signal cable is electrically connected to the pulsation generator. Therefore, it is difficult for the user to exchange. Therefore, by providing a first protective tube through which the drive signal cable is inserted and replacing the first protective tube, the drive signal cable that does not come into contact with blood, body fluid, or the like can be repeatedly used in a state where it is connected to the pulsation generator. .

  For this reason, the connecting flow channel tube, the fluid supply tube and the first protective tube that come into contact with blood, body fluid, etc. are used disposable, and the pulsation generating portion (with drive signal cable) that does not contact blood, body fluid, etc. is used repeatedly. It is possible to improve safety and reduce running costs by repeatedly using a high-cost pulsation generator.

  Furthermore, the connecting flow channel tube, the fluid supply tube, and the first protective tube that come into contact with blood, body fluid, and the like can be easily separated from the pulsation generating portion and can be separated as medical waste.

  Application Example 2 The fluid ejection device according to the application example described above includes a case member in which the outer member is divided, and a seal member is provided between the mutually facing surfaces of the divided case member. preferable.

  According to such a configuration, by providing the seal member between the mutually facing surfaces of the divided case member, the sealing performance is improved as compared with the structure in which the case member is directly pressed as in the above-described prior art document. be able to.

  Application Example 3 In the fluid ejecting apparatus according to the application example, the drive signal cable extends through the outer member to the outside, and the first protection tube through which the drive signal cable is inserted includes the outer shell. It is preferable to be detachable from the member.

  According to such a structure, it can replace | exchange in the state mounted | worn with the removable outer shell member and the 1st protection tube, and it enables it to perform replacement | exchange work easily. Further, the outer shell member and the first protective tube can be separated.

  Application Example 4 In the fluid ejection device according to the application example described above, it is preferable that the second protective tube through which the fluid supply tube is inserted is detachably attached to the outer member.

  According to such a configuration, since the fluid supply tube is inserted through the second protective tube, the fluid supply tube does not contact blood, body fluid, or the like. Therefore, the second protective tube can be used disposable, and the pulsation generator can be used repeatedly with the drive signal cable and the fluid supply tube attached. Further, the outer shell member and the second protective tube can be separated.

  Application Example 5 In the fluid ejection device according to the application example described above, it is preferable that a resin is filled in a space between the pulsation generation unit and the outer member.

  According to such a structure, the sealing property of a pulsation generation | occurrence | production part can be improved by filling resin in the space between a pulsation generation | occurrence | production part and an outline member. In addition, when the outer member is removed, the pulsation generating part is covered with resin, so that the pulsation generating part is scratched and dust and moisture are prevented from entering inside, and it is easy to handle. .

  Moreover, since the press-fitting portion between the fluid supply tube and the pulsation generating portion is also covered with resin, the press-fitting strength is reinforced, and the fluid supply tube can be prevented from coming off during use.

Application Example 6 In the fluid ejection device according to the application example, it is preferable that a release layer is provided on the inner surface of the outer member.
Here, as the release layer, for example, a fluorine-based release agent can be employed.

  Thus, by providing the release layer at the interface between the outer member and the filled resin, the outer member and the filled resin can be easily separated.

  The release layer can be easily formed by applying or immersing a release agent on the inner surface of the outer member.

  Application Example 7 The fluid ejecting apparatus according to the application example includes a resin layer formed so as to seal the periphery of the pulsation generating unit, and the outer member sealing the outer peripheral space of the resin layer. It is desirable that

  Even with such a configuration, the pulsation generating portion can be sealed by the resin layer, the fluid supply tube press-fitting strength can be reinforced, and the fluid supply tube can be prevented from coming off during use.

  Further, by providing a space between the outer member and the sealing layer, the dimensional variation of the outer member can be absorbed in this space. In such a configuration, it is not necessary to provide a release layer as described above.

  Application Example 8 In the fluid ejecting apparatus according to the application example described above, the fluid supply tube and the drive signal cable extend in the same direction from the pulsation generation unit, and the fluid supply tube and the drive signal cable are connected to each other. It is desirable that the third protective tube to be inserted is detachably attached to the outer member.

  According to such a configuration, since the fluid supply tube and the drive signal cable are inserted into one third protective tube, the structure of the connection portion with the pulsation generating portion is more than the configuration in which these are dispersedly arranged. Since it can be simplified and the number of protective tubes can be reduced to one, the attaching / detaching operation can be easily performed. In addition, there is an effect that handling in a treatment or the like becomes easy.

  Application Example 9 A surgical instrument according to this application example includes the fluid ejection device according to any one of the application examples described above.

  According to this application example, since the pulsation generating part of the fluid ejection device is sealed by the outer member, the pulsation generating part does not come into contact with blood, body fluid, etc., and the outer member can be removed and used repeatedly. It is. Therefore, the connection flow channel tube, the fluid supply tube, and the first protection tube that are highly safe and come into contact with blood, body fluid, and the like can be easily separated from the pulsation generating portion, and can be separated as medical waste.

  In addition, since the connection channel tube is detachable, there are effects that a plurality of types of connection channel tubes are prepared and a shape suitable for the treatment site can be selected and used.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
1 to 5 show the fluid ejecting apparatus of the first embodiment, FIG. 6 shows the second embodiment, FIG. 7 shows the third embodiment, FIG. 8 shows the fourth embodiment, and FIG.
The embodiment shown in the following description is an example of the present invention, and the drawings to be referred to are schematic diagrams in which the vertical and horizontal scales of members or portions are different from actual ones for convenience of illustration.

The fluid ejecting system and fluid ejecting apparatus according to the present invention can be used in various ways such as drawing using ink, cleaning fine objects and structures, cooling devices for electronic devices, surgical scalpels, etc. In the embodiment to be described, a fluid ejecting apparatus suitable for incising or excising a living tissue will be described as an example. Therefore, the fluid used in the embodiment is a liquid such as water or physiological saline, and the fluid may be expressed as a liquid.
(Fluid injection system)

  FIG. 1 is an explanatory diagram showing a schematic configuration of a fluid ejection system. In FIG. 1, a fluid ejection system 1 is supplied from a pump and a control device 20 including a liquid container that stores liquid as a basic configuration, a pump (not shown) as a pressure generation unit, and a drive control circuit unit. A fluid ejecting apparatus 10 that pulsates and ejects the liquid to be pulsated, and a fluid supply tube 25 that communicates the fluid ejecting apparatus 10 and the pump (hereinafter simply referred to as a tube 25).

  Furthermore, a drive signal cable 15 for inputting a drive signal from the control device 20 (drive control circuit) to the pulsation generator 30 is provided.

  The fluid ejecting apparatus 10 includes a pulsation generator 30 that pulsates and discharges the supplied liquid at a high pressure and a high frequency, and a connection flow channel pipe 90 connected to the pulsation generation unit 30. A nozzle 95 having a fluid ejection opening 97 with a reduced cross-sectional area of the flow path is inserted into the part.

  Next, the flow of liquid in the fluid ejection system 1 will be described. The liquid stored in the liquid container provided in the control device 20 is supplied to the pulsation generator 30 through the tube 25 at a constant pressure by a pump.

  The pulsation generating unit 30 includes a fluid chamber 120 (see FIG. 2) and a volume changing unit for the fluid chamber 120. The volume changing unit is driven to generate pulsation, and liquid is supplied from the fluid ejection opening 97. Is jetted at high speed. Detailed description of the pulsation generator 30 will be described later with reference to FIGS.

  The pressure generating unit is not limited to the pump, and an infusion bag as a liquid container may be held at a position higher than the pulsation generating unit 30 by a stand or the like. Accordingly, there is an advantage that a pump is not required, the configuration can be simplified, and the liquid channel can be easily sterilized.

  The discharge pressure of the pump is generally set to 3 atm (0.3 MPa) or less. Moreover, when using an infusion bag, the altitude difference between the pulsation generating unit 30 and the upper surface of the infusion bag is a pressure, which is about 0.1 to 0.15 atm (0.01 to 0.015 MPa). It is desirable to set the altitude difference.

  When performing an operation using the fluid ejection system 1, the main part that the operator holds is the pulsation generator 30. Therefore, it is preferable that the tube 25 connected to the pulsation generator 30 is as flexible as possible. For this purpose, it is preferable to use a flexible and thin tube and to reduce the pressure within a range in which the liquid can be fed to the pulsation generator 30.

In particular, when there is a possibility that a failure of the fluid ejection system 1 may cause a serious accident as in the case of brain surgery, it is necessary to avoid high-pressure fluid from being ejected when the tube 25 is cut. Not only that, it is required to keep the pressure low.
(Embodiment 1)

Next, the structure of the fluid ejection device 10 according to the first embodiment will be described.
2 is a cross-sectional view showing the main configuration of the pulsation generator according to the first embodiment along the liquid flow direction, FIG. 3 is a side view shown from the left side of FIG. 2, and FIG. 4 is shown from the right side. It is a side view.

  First, a schematic configuration of the fluid ejecting apparatus 10 will be described with reference to FIGS. The fluid ejecting apparatus 10 includes a pulsation generator 30 and a connection flow channel tube 90 having a connection flow channel 92 and a nozzle 95 for discharging liquid.

  The pulsation generating unit 30 tightly clamps the periphery of a diaphragm 70 as a volume changing means composed of a ring-shaped spacer 60 and a disk-shaped thin metal plate on the surfaces where the first machine frame 80 and the second machine frame 50 face each other. In addition, the fluid chamber 120 is configured to be surrounded by the wall surface 82 of the first machine casing 80, the diaphragm 70, and the inner peripheral wall surface of the spacer 60.

  A tube connecting pipe portion 81 is projected from the outer side surface of the first machine casing 80, and an inflow connecting flow path 84 is opened in the tube connecting pipe portion 81. A connection channel 85 that communicates with the fluid chamber 120 is connected to the inflow connection channel 84 and communicates with an inlet channel 83 that is formed in the wall surface 82. The inlet channel 83 communicates with the fluid chamber 120.

  A tube 25 having flexibility is press-fitted into the tube connection pipe portion 81. The tube 25 is connected to a pump provided inside the control device 20 (see FIG. 1), and is configured so that liquid is supplied into the fluid chamber 120 via the inlet channel 83.

  The first machine frame 80 includes an outlet channel 88 at a substantially center of the wall surface 82 and substantially perpendicular to the diaphragm 70 (that is, the wall surface 82), an outlet connection channel 89 communicating with the outlet channel 88, Has been established.

  The first machine casing 80 is provided with a connection channel pipe insertion portion 80a in a direction opposite to the fluid chamber 120, and an outlet channel 88 and an outlet connection channel 89 communicating with the fluid chamber 120 are opened. ing. Further, a female screw is formed in a range from the distal end portion of the connection flow channel insertion portion 80a to the outlet connection flow channel 89.

  The connection channel pipe 90 is detachably attached to the connection channel pipe insertion portion 80a of the first machine casing 80. Specifically, a male screw 90a is formed on the outer periphery of the end portion of the connection channel tube 90 on the first machine casing 80 side. By screwing these screw portions, the connecting flow channel tube 90 is fixed to the first machine casing 80 (that is, the pulsation generating portion 30). Therefore, the connection flow channel tube 90 is detachable from the pulsation generator 30.

  On the outer peripheral portion in the longitudinal direction of the connection flow channel tube 90, flat cut portions 90b facing each other are formed. The cut portion 90b can be grasped and rotated by a jig or the like, and the connecting flow channel tube 90 can be attached to and detached from the pulsation generating portion 30.

  A connection flow channel 92 communicating with the outlet connection flow channel 89 is opened in the connection flow channel tube 90, and a nozzle 95 is press-fitted at a tip portion opposite to the outlet flow channel 88.

  The nozzle 95 has a nozzle channel 96 communicating with the connection channel 92 and a fluid ejection opening 97.

  Here, the outlet connection channel 89, the connection channel 92, and the nozzle channel 96 have the same cross-sectional area, and this cross-sectional area is larger than the cross-sectional area of the outlet channel 88. The cross-sectional area of the fluid ejection opening 97 is smaller than the cross-sectional area of the connection channel 92.

  In addition, the said cross-sectional area represents the cross-sectional area of a flow path when cut | disconnecting perpendicularly | vertically with respect to the flow direction of a liquid.

  On the other hand, the second machine casing 50 is a cylindrical member having an outer flange part 56 and a cylinder part 51, and a cylindrical hole 51 a penetrating the second machine casing 50 is opened.

  One of the openings of the hole 51a is sealed with the lower plate 100. A piezoelectric element 40 as a drive source is disposed inside the hole 51a. The piezoelectric element 40 is a stacked piezoelectric element and constitutes a columnar actuator.

  One end of the piezoelectric element 40 is fixed to the diaphragm 70 via the upper plate 110, and the other end is fixed to the inner surface of the lower plate 100.

  Driving electrodes (not shown) are respectively provided on the opposing side surfaces of the piezoelectric element 40, and a driving signal cable 15 including connection leads 151 and 152 with insulation coating is connected to these driving electrodes. The drive signal cable 15 is drawn to the outside through a lead insertion hole 54a provided in the first protective tube connecting pipe portion 54 that protrudes from the outer side surface of the cylinder portion 51 of the second machine casing 50, and is supplied to the control device 20. It is connected to a drive control circuit section (not shown) of (see FIG. 1).

  The first machine frame 80 and the second machine frame 50 are screwed and fixed at the four corners with the fixing screws 161 in a state where the peripheral edge of the diaphragm 70 and the spacer 60 are sandwiched, and are brought into close contact with each other.

  On the other hand, after adjusting the dimensions of the second machine casing 50 and the lower plate 100 so that the piezoelectric element 40 does not deform the diaphragm 70, the four corners are screwed and fixed by the fixing screws 160.

  A tube 25 is press-fitted into a tube connecting pipe portion 81 projecting from the pulsation generating portion 30. The first protective tube 27 is press-fitted into the first protective tube connecting pipe portion 54.

  The drive signal cable 15 is connected to the control device 20 (see FIG. 1) through the lead insertion hole 54a and the first protective tube 27. Therefore, it is preferable that the first protective tube 27 has a length from the pulsation generating unit 30 to the control device 20. However, when performing the operation, the first protective tube 27 may have a length up to a range where blood, body fluid, or ejected liquid does not adhere. That's fine.

  Further, the first protective tube 27 is preferably flexible and needs only be strong enough to protect the drive signal cable 15, so that it is easy to handle by making it as thin as possible.

  The pulsation generating unit 30 is covered with an outer member that seals the periphery and is detachable from the pulsation generating unit 30. In the present embodiment, the outer member is composed of an upper case 35 and a lower case 36 as case members.

  The upper case 35 and the lower case 36 hold the pulsation generating part 30 so as to sandwich the connecting flow channel pipe insertion part 80a of the first machine casing 80 and the cylinder part 51 of the second machine casing 50. The upper case 35 and the lower case 36 are screwed and fixed by a fixing screw 162 in the vicinity of the connection flow path tube insertion portion 80a and by a fixing screw 163 in the cylinder portion 51. Therefore, the upper case 35 and the lower case 36 have a structure that can be attached to and detached from the pulsation generator 30.

  Further, a packing 130 as a seal member is provided between the end surfaces of the upper case 35 and the lower case 36 facing each other. The shape of the packing 130 will be described with reference to FIG.

  FIG. 5 is a perspective view showing the shape of the packing. The packing 130 is composed of a plate-like outer peripheral portion 132 having a shape along end surfaces facing each other of the upper case 35 and the lower case 36, and a cylindrical portion 131 projecting from the outer peripheral portion 132.

  A through-hole 131a is formed in the cylindrical portion 131, and the base portion 90c of the connection flow channel tube 90 is inserted into the through-hole 131a (see FIG. 2).

  As shown in FIG. 2, the packing 130 is provided with an outer peripheral portion 132 between end faces of the upper case 35 and the lower case 36 that face each other, and the base portion 90 c of the connection flow channel tube 90 is connected to the through hole 131 a of the cylindrical portion 131. It is assembled by inserting into.

  Then, the upper case 35 and the lower case 36 are screwed and fixed by the fixing screws 162 and 163, and the packing 130 is pressed.

  A cylindrical packing 135, a first protective tube 27, and a lower case 36 through which the first protective tube communicates are provided between the tube 25 and the lower case 36 through which the tube 25 is inserted. A cylindrical packing 136 is attached.

  In the present embodiment, the packings 135 and 136 have a cylindrical shape with a hook that is easy to handle, but may be a simple cylindrical shape or an O-ring.

  In this way, the upper case 35 and the lower case 36 are sealed around the pulsation generating unit 30 by the packings 130, 135, and 136.

  The separation of the fluid ejecting apparatus 10 configured as shown in FIGS. 2 to 4 is performed by first removing the connection flow path tube 90 from the pulsation generating unit 30, and subsequently pulling out the tube 25 and the first protective tube 27. The upper case 35 and the lower case 36 are separated by loosening the fixing screws 162 and 163. By doing so, the pulsation generating unit 30 can be separated without coming into contact with blood or body fluid.

  The diameter of the base portion 90c of the connection flow channel tube 90 is set larger than the outer diameter of the male screw 90a. This is because when the connecting flow channel tube 90 is removed from the pulsation generator 30, consideration is given to avoiding damage to the packing 130 by the male screw 90a.

Next, the operation of the pulsation generator 30 will be described.
The liquid is always supplied to the inlet channel 83 by a pump at a constant hydraulic pressure. As a result, when the piezoelectric element 40 does not operate, the liquid flows into the fluid chamber 120 due to the difference between the discharge pressure of the pump and the fluid resistance value of the entire inlet channel.

  Here, if a drive signal is input to the piezoelectric element 40 and the piezoelectric element 40 expands suddenly, the pressure in the fluid chamber 120 is such that the combined inertances L1 and L2 on the inlet channel side and the outlet channel side are sufficiently large. 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 applied to the inlet channel 83, the inflow of liquid from the inlet channel 83 into the fluid chamber 120 is reduced by the pressure, and the outflow from the outlet channel 88. Will increase.

  However, since the synthetic inertance L1 on the inlet flow path side is larger than the synthetic inertance L2 on the outlet flow path side, the liquid is discharged from the outlet flow path 88 more than the decrease in the flow rate of the liquid flowing into the fluid chamber 120 from the inlet flow path 83. The increased amount of liquid is larger. As a result, a pulsed fluid discharge, that is, a pulsating flow is generated in the outlet channel 88.

  The pressure fluctuation at the time of discharge propagates in the connection flow path 92 of the connection flow path pipe 90, and the liquid is ejected in a pulse form from the fluid ejection opening 97 (both see FIG. 2) of the nozzle 95 at the tip. The Since the diameter of the fluid ejection opening 97 is reduced more than the diameter of the outlet channel 88, the liquid is ejected as a high-pressure, high-speed pulsed droplet.

  On the other hand, the inside of the fluid chamber 120 is in a vacuum state immediately after the pressure rises due to the interaction between the decrease in the amount of liquid inflow from the inlet channel 83 and the increase in the outflow of liquid from the outlet channel 88. As a result, the flow of the liquid in the inlet channel 83 returns to the fluid chamber 120 at a speed similar to that before the operation of the piezoelectric element 40 after a predetermined time has elapsed due to both the pressure of the pump and the vacuum state in the fluid chamber 120. To do. If the piezoelectric element 40 is expanded after the flow of the liquid in the inlet channel 83 is restored, the liquid can be continuously ejected from the nozzle 95 in a pulse shape.

  Therefore, according to this embodiment, since the pulsation generating unit 30 is sealed by the upper case 35 and the lower case 36 as outer members, the upper case 35 and the lower case do not come into contact with blood or body fluids. 36 can be removed and the pulsation generator 30 can be used repeatedly.

  Further, it is possible to prevent a short circuit between the drive electrodes of the piezoelectric element 40 and deterioration of the piezoelectric characteristics due to moisture entering the inside of the pulsation generating unit 30.

  Moreover, since the connection flow path tube 90 is configured to be detachable from the pulsation generating section 30, it can be replaced with one that has been easily cleaned and disinfected after the treatment. Furthermore, there is an effect that a plurality of types of the shape of the connection flow channel tube 90 are prepared, and a shape suitable for the treatment site can be selected and used.

  Further, since the tube 25 has a structure that is press-fitted into the pulsation generating unit 30 and has flexibility, the tube 25 that has been easily pulled out, cleaned, and disinfected after the operation by the user is easily attached to the pulsation generating unit 30. It becomes possible.

  The drive signal cable 15 (consisting of connection leads 151 and 152) is electrically connected to the pulsation generator 30 by solder or the like. Therefore, it is difficult for the user to exchange. Therefore, the drive signal cable 15 that is not in contact with blood, body fluid, or the like is connected to the pulsation generator 30 by replacing the first protection tube 27 by adopting a configuration in which the drive signal cable 15 is inserted into the first protection tube 27. Can be used repeatedly.

  For this reason, the connection flow channel tube 90, the tube 25, the first protective tube 27, the upper case 35, and the lower case 36 that come into contact with blood, body fluid, etc. are disposable, and the pulsation generator 30 (not in contact with blood, body fluid, etc.) The drive signal cable 15) can be used repeatedly, and safety can be increased and running cost can be reduced.

  Furthermore, the connection flow channel tube, the fluid supply tube, the first protective tube, the upper case 35, and the lower case 36 that come into contact with blood, body fluid, and the like can be easily separated from the pulsation generating unit 30, and can be separated as medical waste.

  The outer member includes an upper case 35 and a lower case 36, and a packing 130 is provided between end faces of the upper case 35 and the lower case 36 that face each other. Further, since the packing 135 is provided at the insertion portion of the tube 25 to the lower case 36 and the packing 136 is provided at the insertion portion of the first protective tube 27 to the lower case 36, the sealing performance of the pulsation generating portion 30 can be further improved. it can.

  In the present embodiment, the first protective tube 27 is press-fitted into the first protective tube connecting pipe portion 54 protruding from the lower case 36, but the first protective tube 27 is first protected in the lower case 36. It is good also as a structure which provides a tube connection pipe part and press-fits there.

  Although not shown, the description will be given with reference to FIG. Such a structure can be implemented by forming, in the lower case 36, a first protective tube connecting pipe portion having the same shape as the first protective tube connecting pipe portion 54 provided in the second machine casing 50.

  The drive signal cable 15 is inserted into the through hole provided in the second machine casing 50, the first protective tube connecting pipe portion provided in the lower case 36, and the first protective tube 27, and the control device 20 (see FIG. 1). Connected to.

  If it does in this way, it can replace | exchange in the state with which the lower case 36 and the 1st protection tube 27 were mounted | worn, and it enables it to perform replacement | exchange work easily.

  Further, if the first protective tube 27 is formed of a flexible material, it can be attached to and detached from the lower case 36. The lower case 36 and the first protective tube 27 are separated and collected separately. can do.

In addition, since the upper case 35 and the lower case 36 are gripping portions that are gripped by the practitioner, the upper case 35 and the lower case 36 may be formed in a shape that is easy to grip and have rigidity enough to prevent deformation by gripping.
(Embodiment 2)

  Next, Embodiment 2 will be described with reference to the drawings. The second embodiment is characterized in that a second protective tube that is inserted through the tube is provided. Therefore, the description will focus on the differences from the first embodiment.

  FIG. 6 is a partial cross-sectional view illustrating a part of the fluid ejection device according to the second embodiment. In FIG. 6, the tube 25 is press-fitted into a tube connecting pipe portion 81 projecting from the pulsation generating portion 30 (specifically, the first machine casing 80), is inserted through the lower case 36, and is extended to the outside. ing.

  The lower case 36 is provided with a second protective tube connecting pipe portion 36d protruding outward, and the second protective tube 26 is press-fitted into the second protective tube connecting pipe portion 36d.

  The second protective tube 26 has the flexibility that can be press-fitted or pulled out from the second protective tube connecting pipe portion 36d in the same manner as the first protective tube 27 described above.

The second protective tube 26 is preferably provided from the connecting portion with the lower case 36 to the pump of the control device 20 (see FIG. 1). However, the length of the second protective tube 26 is within a range where blood or body fluid does not adhere in the treatment. Also good.
In the configuration of the present embodiment, the packing 135 provided in the first embodiment is not necessary.

  According to such a configuration, since the tube 25 is inserted into the second protective tube 26, the tube 25 does not come into contact with blood, body fluid, or ejected liquid. Therefore, the second protective tube 26 can be used disposable, and the pulsation generator 30 can be used repeatedly with the drive signal cable 15 and the tube 25 attached.

  Further, the lower case 36 and the second protective tube 26 can be separated from the pulsation generating unit 30 in a connected state, and the lower case 36 and the second protective tube 26 can be separated and collected separately. .

  The fluid flows through the tube 25 at a constant pressure. Therefore, the tube 25 is required to have rigidity and fixing force enough to withstand this pressure. However, the second protective tube 26 may be a thin tube regardless of the fluid pressure.

Furthermore, in the unlikely event that the tube 25 is damaged during the treatment, the second protective tube 26 can prevent the liquid from splashing and improve safety.
(Embodiment 3)

  Next, Embodiment 3 will be described with reference to the drawings. The third embodiment is characterized in that a resin is filled in a space between the pulsation generating part and the upper case 35 and the lower case 36. Therefore, the description will focus on the differences from the first embodiment.

  FIG. 7 is a partial cross-sectional view illustrating a part of the fluid ejection device according to the third embodiment. In FIG. 7, the lower case 36 is provided with a second protective tube connecting pipe part 36d and a first protective tube connecting pipe part 36e.

  A second protective tube 26 is press-fitted into the second protective tube connecting pipe part 36d, and a first protective tube 27 is press-fitted into the first protective tube connecting pipe part 36e.

  The drive signal cable 15 is inserted into the through hole 51 b provided in the second machine casing 50 and further inserted into the first protective tube 27. The tube 25 is inserted through the second protective tube 26. Therefore, the drive signal cable 15 and the tube 25 are protected so that blood, body fluid, and jetted liquid are not attached.

  In the present embodiment, as shown in FIG. 7, the space formed between the upper case 35 and the lower case 36 and the pulsation generator 30 is filled with the resin 140. As the resin 140, it is more preferable to use a material having low water absorption.

  The resin 140 is injected and filled from through holes 35b and 35c opened in the upper case 35. If the through hole 35b is an injection hole and the through hole 35c is an air vent hole, resin injection can be performed satisfactorily.

  The resin 140 may enter the inside from the through hole 51b of the second machine casing 50 or may enter the opening of the first protective tube connecting pipe portion 36e of the lower case 36.

  In this way, the resin 140 covers the pulsation generating unit 30 with the resin 140, and further covers the pulsation generating unit 30, the connection channel tube 90, the press-fitting portion of the tube 25, and the drawing portion of the drive signal cable 15.

  In such a structure, it is more preferable that a release layer (not shown) is provided on the inner surfaces of the upper case 35 and the lower case 36. As the release layer, a fluorine-based release agent or the like can be adopted, and it can be formed as a thin film on the inner surfaces of the upper case 35 and the lower case 36 by a method such as spray coating or immersion.

  Thus, by providing the release layer at the interface between the inner surfaces of the upper case 35 and the lower case 36 and the filled resin 140, the upper case 35 and the lower case 36 can be easily separated.

  Therefore, according to the configuration of the present embodiment, the pulsation generating portion 30 sealed with the resin 140 can be repeatedly used without blood or body fluid adhering thereto.

  Further, by filling the space between the pulsation generating unit 30 and the upper case 35 and the lower case 36 with the resin 140, the hermeticity of the pulsation generating unit 30 can be improved. Further, when the upper case 35 and the lower case 36 are removed, the pulsation generating part 30 is covered with the resin 140, so that the pulsation generating part 30 is damaged or moisture or dust or the like enters inside. It has the effect of preventing and handling.

  In addition, since the portion where the tube 25 is press-fitted into the pulsation generating portion 30 is also covered with the resin, the press-fitting strength can be reinforced and the tube 25 can be prevented from coming off during use.

  Furthermore, the lead-out portion of the drive signal cable 15 from the pulsation generating portion 30 can also be reinforced by the resin 140.

  Note that the upper case 35, the lower case 36, the first protective tube 27, the second protective tube 26, the connection flow channel tube 90, and the pulsation generating unit 30 can be separated from each other and separated and collected. Can be easily performed.

  The resin 140 can be regarded as being molded by molding using the upper case 35 and the lower case 36 as molding dies. Therefore, it can be molded with high precision and can be used repeatedly for the unused upper case 35 and lower case 36 to be replaced.

In the configuration of the present embodiment, the packings 135 and 136 provided in the first embodiment can be omitted.
(Embodiment 4)

  Subsequently, Embodiment 4 will be described with reference to the drawings. The basic structure of the fourth embodiment is the same as that of the third embodiment described above (see FIG. 7), but the resin layer formed so as to seal the periphery of the pulsation generating portion and the outer peripheral space of this resin layer are sealed. It is characterized by comprising an upper case and a lower case. Therefore, the description will focus on the differences from the third embodiment.

  FIG. 8 is a partial cross-sectional view illustrating a part of the fluid ejection device according to the fourth embodiment. In FIG. 8, a resin layer 141 is formed on the surface of the pulsation generator 30. The resin layer 141 is formed to include the entire surface of the pulsation generator 30, the connection portion between the base 90 c of the connection flow channel tube and the pulsation generator 30, the press-fitting portion of the tube 25, and the lead portions of the connection leads 151 and 152. The

  The resin layer 141 is formed by applying, dipping, or molding a resin in a state where the connection flow path tube 90 and the tube 25 are attached to the pulsation generating unit 30 and in a state where the connection leads 151 and 152 are connected. Is possible. A space is formed between the resin layer 141, the upper case 35, and the lower case 36.

  The structures of the upper case 35 and the lower case 36 and the joining structure of the first protective tube 27 and the pulsation generating portion 30 of the second protective tube 26 are the same as those in the third embodiment (see FIG. 7), and the description thereof is omitted. To do. However, the upper case 35 does not have the through holes 35b and 35c provided in the third embodiment.

  Even with such a configuration, the pulsation generator 30 can be sealed by the upper case 35 and the lower case 36. Further, the pulsation generating unit 30 itself can be sealed by the resin layer 141, and the press-fitting strength of the tube 25 can be reinforced, so that the tube 25 can be prevented from coming off during use.

  Further, the lead-out portion from the pulsation generating portion 30 of the drive signal cable 15 can be reinforced.

Further, by providing a space between the upper case 35, the lower case 36, and the resin layer 141, the dimensional variation of the upper case 35 and the lower case 36 can be absorbed in this space. In such a configuration, it is not necessary to provide a release layer as described above.
(Embodiment 5)

  Next, Embodiment 5 will be described with reference to the drawings. The fifth embodiment is characterized in that the tube 25 and the drive signal cable 15 are inserted into one protective tube with respect to the first to fourth embodiments described above. The pulsation generating unit 30 and the connection flow channel pipe 90 will be described by exemplifying the configuration of the first embodiment.

  FIG. 9 is a partial cross-sectional view illustrating a part of the fluid ejection device according to the fifth embodiment. In FIG. 9, the tube connecting pipe portion 81 and the through hole 51b through which the drive signal cable 15 is inserted are provided close to each other in the same direction.

  The lower case 36 is provided with a third protective tube connecting pipe portion 36f protruding therefrom, and the third protective tube 28 is press-fitted into the third protective tube connecting pipe portion 36f. The third protective tube connecting pipe portion 36f has a size that allows the tube 25 and the drive signal cable 15 to be inserted therethrough. Accordingly, the tube 25 and the drive signal cable 15 are inserted and extended into the third protective tube 28.

  The third protective tube 28 has flexibility, and can be easily operated by making it as thin as possible if it has a press-fit strength that does not come off the lower case 36 during use.

  With such a configuration, since the tube 25 and the drive signal cable 15 (connection leads 151 and 152) are inserted into the single third protective tube 28, pulsation is generated as compared with a configuration in which they are dispersedly arranged. The structure of the connection part with the part 30 can be simplified. Further, since the number of protective tubes can be reduced to one, separation work is facilitated. In addition, there is an effect that handling in a treatment or the like becomes easy.

  The configuration of the present embodiment can also be applied to a structure in which the resin 140 is filled as in the third embodiment described above, and a structure in which the resin layer 141 is formed on the peripheral surface of the pulsation generating unit 30 as in the fourth embodiment. .

  Further, a heat-shrinkable tube can be used as the first protective tube 27, the second protective tube 26, and the third protective tube 28. In such a case, it is possible to heat the heat-shrinkable tube and attach it closely to the lower case 36. When separating, it is possible to cut it with a cutter or the like.

  Further, the periphery of the resin layer 141 can be molded to replace the upper case 35 and the lower case 36. In such a configuration, a thin portion can be provided in the outer peripheral molding part, and the thin portion can be cut and separated. In this case, if the above-described release layer is formed on the surface of the resin layer 141, the mold part and the resin layer 141 can be easily separated.

  Therefore, if the fluid ejecting apparatus 10 described above is used as a surgical instrument for incising or excising a living tissue, it is possible to incise an organ substance while preserving a vascular structure such as a blood vessel.

  Further, since the pulsation generating unit 30 is sealed by the outer members (upper case 35 and lower case 36), the pulsation generating unit 30 does not come into contact with blood, body fluids, etc., and the outer member is removed and used repeatedly. Is possible.

  In addition, it is possible to prevent the drive characteristics of the pulsation generating unit 30 from being affected by moisture entering the pulsation generating unit 30, thereby improving reliability.

  Further, since the connection flow channel tube 90 is detachable, there are effects that a plurality of types of the connection flow channel tube 90 are prepared and a shape suitable for the treatment site can be selected and used.

  In addition, the connection flow channel tube 90, the fluid supply tube 25, and the first protective tube 27 that come into contact with blood, body fluid, and the like are disposable, and the pulsation generator 30 (with the drive signal cable 15) that does not come into contact with blood, body fluid, etc. is repeatedly used. In addition to improving safety, the running cost can be reduced by repeatedly using the high-cost pulsation generator 30.

  Furthermore, there is an effect that the connection flow path tube 90, the fluid supply tube 25 and the first protection tube 27 can be easily separated from the pulsation generating unit 30 and easily separated as medical waste.

Explanatory drawing which shows schematic structure of a fluid injection system. FIG. 3 is a cross-sectional view illustrating the main configuration of a pulsation generating unit according to Embodiment 1 cut along a liquid flow path direction. The side view illustrated from the left side of FIG. The side view illustrated from the right side of FIG. The perspective view which shows the shape of packing. FIG. 9 is a partial cross-sectional view illustrating a part of a fluid ejection device according to a second embodiment. FIG. 9 is a partial cross-sectional view illustrating a part of a fluid ejection device according to a third embodiment. FIG. 9 is a partial cross-sectional view illustrating a part of a fluid ejection device according to a fourth embodiment. FIG. 9 is a partial cross-sectional view illustrating a part of a fluid ejection device according to a fifth embodiment.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 10 ... Fluid injection apparatus, 15 ... Drive signal cable, 25 ... Fluid supply tube, 27 ... 1st protection tube, 30 ... Pulsation generation | occurrence | production part, 35 ... Upper case, 36 ... Lower case, 40 ... Piezoelectric element, 70 ... Diaphragm, 90 ... Connection channel tube, 92 ... Connection channel, 97 ... Fluid ejection opening, 120 ... Fluid chamber.

Claims (9)

A pulsation generator that pulsates and discharges fluid, and a fluid chamber; and a diaphragm that changes the volume of the fluid chamber;
A connecting flow path that communicates with the fluid chamber; and a fluid ejection opening. The pulsation of the fluid flowing from the pulsation generation unit is transmitted to the fluid ejection opening and is detachable from the pulsation generation unit. A connecting flow channel pipe to be mounted;
A fluid supply tube that is press-fitted into the pulsation generator and supplies fluid to the fluid chamber;
A drive signal cable for inputting a drive signal to the pulsation generator,
A first protective tube that is press-fitted into the pulsation generator and through which the drive signal cable is inserted;
An outer member that seals the pulsation generator and is detachable from the pulsation generator;
Is provided. The fluid ejection device according to claim 1,
The outer member comprises a divided case member,
The fluid ejecting apparatus according to claim 1, further comprising: a sealing member provided between the opposing surfaces of the divided case member. The fluid ejection device according to claim 1 or 2,
The drive signal cable extends outside through the outer member;
A fluid ejecting apparatus, wherein a first protective tube through which the drive signal cable is inserted is detachably attached to the outer member. In the fluid ejection device according to any one of claims 1 to 3,
A fluid ejecting apparatus, wherein a second protective tube through which the fluid supply tube is inserted is detachably attached to the outer member. The fluid ejection device according to any one of claims 1 to 4,
A fluid ejecting apparatus, wherein a resin is filled in a space between the pulsation generating unit and the outer member. The fluid ejection device according to claim 5, wherein
A fluid ejecting apparatus, wherein a release layer is provided on an inner surface of the outer member. The fluid ejection device according to claim 1 or 2,
A fluid ejecting apparatus comprising: a resin layer formed so as to seal the periphery of the pulsation generating unit; and the outer member sealing an outer peripheral space of the resin layer. The fluid ejection device according to claim 1 or 2,
The fluid supply tube and the drive signal cable extend in the same direction from the pulsation generating unit,
A fluid ejecting apparatus, wherein a third protective tube into which the fluid supply tube and the drive signal cable are inserted is detachably attached to the outer member.   A surgical instrument comprising the fluid ejection device according to any one of claims 1 to 8.

Images