JP5603559B2 - Chemical spray device - Google Patents

Description

  TECHNICAL FIELD The present invention relates to a chemical liquid spray administration device for spraying a chemical liquid to an affected part of a living body (human or animal).

In recent years, for example, in order to weaken the onset of side effects or prevent a decrease in medicinal effect, the necessary minimum chemical solution is limited to the affected area by discharging the drug solution as close to the affected area as possible. There is a need to administer.
Therefore, conventionally, as shown in Patent Document 1 below, for example, a nozzle is provided at the distal end portion (one end portion) of the catheter, and a pressurizing chamber is formed on the proximal end side (the other end side) of the nozzle. There is provided a drug solution administration device having a configuration in which a reservoir is formed on the base end side (the other end side) of the pressure chamber. In this chemical solution administration device, an injection valve that communicates and shuts off the nozzle and the pressurizing chamber, and a loading valve that communicates and shuts off the pressurizing chamber and the reservoir are provided inside the catheter. Further, a pressurized gas conduit communicating with a pressurized gas source is connected to the pressurizing chamber.

  In the above configuration, the chemical solution in the reservoir is introduced into the pressurizing chamber by loading the drug in the reservoir and inserting the catheter into the body and opening the loading valve with the nozzle close to the affected area. Thereafter, a pressurized gas is introduced from the pressurized gas conduit into the pressurized chamber with the loading valve closed, and when the pressure in the pressurized chamber is sufficiently increased, the injection valve is opened, The liquid medicine is discharged from the discharge hole toward the affected area.

JP-T-2006-527023

  However, in the above-described conventional chemical spray administration apparatus, since the chemical liquid aerosolized in the catheter adheres to the inner surface of the catheter, the discharge amount of the chemical liquid from the discharge hole is smaller than the filling amount of the chemical liquid in the catheter. . Therefore, there is a problem that the amount of the chemical solution administered to the affected area becomes unstable and it is difficult to administer an accurate amount of the chemical solution. If the amount of the drug solution administered to the affected area is small, the desired drug effect may not be obtained.

  In consideration of the burden on the patient, there is a desire to complete the administration time in as short a time as possible, but the above-described conventional chemical spray administration device has low drug solution administration efficiency. Here, it is conceivable to increase the number of discharge holes in order to increase the administration efficiency of the drug solution.However, if the distance between the discharge holes is short, the drug solutions discharged from the plurality of discharge holes come into contact with each other immediately after the discharge, and the affected area There exists a problem that the quantity of the chemical | medical solution administered tends to become non-uniform | heterogenous. In addition, when the distance between the discharge holes is short, the chemical liquid tends to accumulate on the nozzle tip surface where the discharge holes are formed. As a result, the discharge holes are clogged, or the chemical liquid drips as droplets and the affected part There is a problem that more than necessary chemicals are administered in the vicinity.

  The present invention has been made in consideration of the above-described conventional problems, and an object of the present invention is to provide a chemical spray administration device capable of administering an appropriate amount of a chemical solution to an affected part of a living body in a short time.

The medicinal solution spray administration device according to the present invention comprises a medicinal solution filling part filled with a medicinal solution inside, a catheter having a proximal end connected to the medicinal solution filling part and a discharge hole for discharging the medicinal solution at the distal end, A discharge mechanism that discharges the chemical liquid in the chemical liquid filling portion from the discharge hole through the catheter, and a voltage is applied to the chemical liquid that is sent to the discharge hole by the discharge mechanism, so that the chemical liquid is supplied to the discharge hole. A voltage application section that is atomized and at least part of which is provided in the internal space of the catheter , and a plurality of the discharge holes are formed at the distal end of the catheter, and the plurality of the discharge holes are 20 μm or more. It is characterized by being arranged with an interval of.

  With such a feature, after the catheter is inserted into the patient's body from the distal end, the chemical solution in the chemical solution filling section is fed from the proximal end of the catheter toward the distal end side by the discharge mechanism, whereby the chemical solution is discharged from the discharge hole. Further, by applying a voltage to the drug solution flowing through the catheter by the voltage application unit, the drug solution to which the voltage is applied is split into a mist when exposed to the outside air, and the drug solution in the catheter and the affected part of the living body A potential difference is generated between the two and the chemical fine particles reach the affected part along the electric lines of force from the discharge hole toward the affected part. At this time, since the chemical liquid fine particles that have reached the affected area are charged, they are reliably attached to a living body (affected area) having a potential of 0V. In addition, since a plurality of discharge holes are formed, the amount of the chemical liquid sprayed at a time increases compared to the case where there is one discharge hole, and the chemical liquid is efficiently administered to the affected area. Further, since the plurality of discharge holes are arranged with an interval of 20 μm or more, the chemicals (liquid yarns) sprayed from the discharge holes are separated without contacting each other. Thereby, the chemical liquid fine particles having a stable particle diameter are sprayed, and the chemical liquid is prevented from dripping as droplets.

  In the medicinal-solution spray administration apparatus according to the present invention, it is preferable that the catheter has one internal space communicating with the medicinal-solution filling portion, and each discharge hole communicates with the internal space.

  Thereby, since the chemical solution sent out from the inside of the chemical solution filling portion circulates in one internal space of the catheter and reaches each of the plurality of discharge holes, the flow path for each discharge hole is formed in the catheter. In comparison, the chemical liquid circulation is facilitated, and the chemical liquid in the chemical liquid filling portion is delivered to each discharge hole in a short time. Further, by delivering the chemical liquid to each discharge hole through one internal space, liquid pressure loss when the chemical liquid is delivered from the chemical liquid filling portion to the discharge hole is suppressed.

  In the medicinal-spray administration device according to the present invention, it is preferable that the plurality of discharge holes are disposed at positions that are substantially rotationally symmetric with respect to the central axis of the internal space of the catheter.

  Thereby, the chemical solution discharge speed from each discharge hole is made uniform, and the atomization position of the chemical solution in each discharge hole is made uniform.

  In the medicinal-solution spray administration device according to the present invention, it is preferable that the distal end surface of the catheter in which the plurality of discharge holes are formed is formed in a rotational curved surface centered on the central axis of the catheter.

As a result, the opening end face (end side) of each discharge hole is inclined with respect to the central axis of the catheter, and the chemicals sprayed from each discharge hole are more reliably separated from each other. Thereby, the chemical liquid fine particles having a more stable particle diameter are sprayed, and the chemical liquid is reliably prevented from dripping as droplets.
In addition, since the chemical liquid (a plurality of liquid yarns) discharged from each discharge hole spreads and is released outward in the radial direction of the catheter, the chemical liquid is sprayed over a wide range.
Furthermore, since the distal end of the catheter has a shape without an acute ridge line (corner), the influence on the living body when the distal end of the catheter comes into contact with the lumen surface of the living body is reduced.

  Moreover, it is preferable that the chemical | medical solution spray administration apparatus which concerns on this invention is gradually diameter-reduced as the said discharge hole goes to the catheter outer side from the catheter inner side.

  As a result, when the chemical solution passes through the discharge hole, it is rectified so that the diameter thereof is gradually reduced from the opening end on the inlet side (starting end side) to the opening end on the outlet side (terminal end side). Further, the angle formed by the inner peripheral surface of the terminal end portion of the discharge hole and the distal end surface of the catheter becomes an acute angle. As a result, the chemical liquid (liquid yarn) discharged from the discharge holes is less likely to spread in a conical shape, and is easily discharged only in the discharge direction (direction perpendicular to the opening end face on the outlet side), and is discharged from each discharge hole. It becomes difficult for chemicals (liquid yarn) to come into contact with each other. Thereby, the chemical liquid fine particles having a more stable particle diameter are sprayed, and the chemical liquid is reliably prevented from dripping as droplets.

  In the medicinal-spray administration device according to the present invention, the catheter is provided with a gas flow passage through which the pumped gas flows, and the distal end of the gas flow passage is formed at the distal end surface of the catheter. Preferably, the plurality of discharge holes are disposed around the tip opening end.

  Thereby, the chemicals (liquid yarns) discharged from the discharge holes are separated from each other by the gas released from the opening end of the gas flow passage. Moreover, the in-vivo mucus adhering to the catheter front end surface is blown off by the gas released from the end opening end of the gas flow passage. Further, the chemical liquid (chemical liquid fine particles) sprayed from the discharge hole is delivered further on the flow of the gas discharged from the end opening end of the gas flow passage.

  In the medicinal-solution spray administration device according to the present invention, it is preferable that each medicinal solution ejected from the plurality of ejection holes is charged to the same polarity by the voltage application unit.

  As a result, the chemical liquids (liquid yarns) discharged from the discharge holes repel each other and are unlikely to contact each other.

  According to the medicinal-solution spray administration device according to the present invention, the amount of medicinal solution sprayed at a time increases and the medicinal solution is efficiently administered to the affected area, so that the medicinal solution can be administered in a short time. In addition, since fine chemical liquid particles having a stable particle diameter are sprayed and the chemical liquid is prevented from dripping and dropping, an appropriate amount of the chemical liquid can be administered to the affected area.

BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a schematic diagram of a drug solution spray administration device for explaining a first embodiment of the present invention. FIG. 2 is a cross-sectional view of a drug solution filling unit and a catheter for explaining the first embodiment of the present invention. 1 is a cross-sectional view of a distal end portion of a catheter for explaining a first embodiment of the present invention. FIG. 3 is an end view of the distal end side of the catheter for explaining the first embodiment of the present invention. FIG. 3 is a schematic diagram showing a state of spraying a chemical solution for explaining the first embodiment of the present invention. It is sectional drawing of the front-end | tip part of the catheter for demonstrating the 2nd Embodiment of this invention. It is the schematic diagram showing the spray condition of the chemical | medical solution for demonstrating the 2nd Embodiment of this invention. It is sectional drawing of the front-end | tip part of the catheter for demonstrating the 3rd Embodiment of this invention. It is an end elevation of the distal end side of a catheter for explaining a third embodiment of the present invention. It is sectional drawing between ZZ shown in FIG. It is sectional drawing of the front-end | tip part of the catheter for demonstrating the 4th Embodiment of this invention. It is an end elevation of the distal end side of a catheter for explaining a fourth embodiment of the present invention. It is an end elevation of the distal end side of a catheter for explaining another embodiment of the present invention. It is an end elevation of the distal end side of a catheter for explaining another embodiment of the present invention. It is the schematic diagram showing the spraying condition of the chemical | medical solution for demonstrating other embodiment of this invention.

  Hereinafter, first to fourth embodiments of a medicinal-solution spray administration device according to the present invention will be described with reference to the drawings.

[First Embodiment]
First, a first embodiment will be described with reference to FIGS.
FIG. 1 is a diagram schematically illustrating a schematic configuration of a drug spray administration apparatus 1 according to the present embodiment, and FIG. 2 schematically illustrates a drug solution filling unit 2 and a catheter 3 provided in the drug spray administration apparatus 1. FIG. 3 is a cross-sectional view of the distal end portion of the catheter 3 cut in the axial direction, FIG. 4 is an end view showing the distal end surface of the catheter 3, and FIG. FIG.
2 indicates the central axis of the catheter 3 and is simply referred to as “axis O” hereinafter. In the present embodiment, the length direction of the axis O is referred to as “axial direction”, and the direction perpendicular to the axis O is referred to as “radial direction”.

As shown in FIG. 1, the chemical solution spraying dispensing device 1 is a device for administering to the affected area Y ₁ a chemical X in the lumen Y of a living body, a liquid chemical X as the chemical particles X ₁ mist a device for spraying the affected area Y _1. The schematic configuration of the chemical spray administration apparatus 1 includes a chemical solution filling unit 2 in which the chemical solution X is filled, and a discharge hole 30 that has a proximal end connected to the chemical solution filling unit 2 and discharges the chemical solution X at the tip. The catheter 3, the discharge mechanism 4 that discharges the drug solution X in the drug solution filling unit 2 from the discharge hole 30 through the catheter 3, and the voltage application unit that applies a voltage to the drug solution X sent to the discharge hole 30 by the discharge mechanism 4 5 is provided.

  As shown in FIGS. 1 and 2, the chemical solution filling unit 2 includes a disposable syringe 20 that is a chemical solution tank that stores the chemical solution X, and a piston 21 that pumps the chemical solution X in the disposable syringe 20 to the catheter 3. It has been. The medicinal solution filling unit 2 is configured to send the medicinal solution X in the disposable syringe 20 from the tip into the catheter 3 by moving the above-described piston 21 toward the catheter 3 along the longitudinal axis direction of the disposable syringe 20. It is.

  The catheter 3 is a tube that is inserted into the lumen Y of the living body, and has a flexibility that is flexible enough to be inserted into the non-linear lumen Y. Inside the catheter 3, one internal space 31 extending in the axial direction is formed over substantially the entire length. As the catheter 3, for example, a non-conductive material made of tetrafluoroethylene resin is used, and a thin tube having an outer diameter of about 1.6 mm, an inner diameter of about 0.9 mm, and a length of about 2000 mm is used.

  One end (base end) of the catheter 3 is connected to the distal end of the disposable syringe 20 via a voltage applying electrode 52 described later, and the internal space 31 of the catheter 3 and the internal space 22 of the disposable syringe 20 are communicated with each other. . The disposable syringe 20 is disposed outside the living body, and the proximal end of the catheter 3 is disposed outside the body.

  As shown in FIGS. 3 and 4, the other end (tip) of the catheter 3 is provided with a tip wall 32 that closes the internal space 31 of the catheter 3. The tip wall 32 is a wall portion provided perpendicular to the axis O, and has a thickness T of, for example, about 0.1 to 5.0 mm. A plurality of discharge holes 30 are formed in the tip wall 32. The discharge hole 30 is a fine through-hole for discharging the chemical liquid X, and for example, a round hole having a diameter of about 0.075 mm is formed. The plurality of discharge holes 30 are disposed at positions that are substantially rotationally symmetric with respect to the central axis (axis O) of the internal space 31. More specifically, three discharge holes 30 are evenly arranged around the axis O in the tip wall 32. The interval L between the plurality of ejection holes 30 is set to 20 μm or more.

Also, the catheter 3 is inserted into the endoscope in the forceps channel 60 of the mirror 6 as shown in FIG. 1, the distal end surface of the catheter 3 (discharge hole 30) is opposed to the affected area Y _1. At this time, the discharge hole 30, by the catheter 3 is moved forward and backward along the axial direction, close to the affected area Y _1, or is spaced.

  The catheter 3 having the above-described configuration is obtained by cutting a multi-lumen pipe having a plurality of through-holes extending in the axial direction into a thin plate by precision extrusion molding, and then replacing the thin plate piece with one through-hole extending in the axial direction. It can be manufactured by melt bonding or bonding with an end face of a pipe made of ethylene tetrafluoride resin. The catheter 3 is preferably formed of a material having water repellency such as, for example, ethylene tetrafluoride resin. Further, as shown in FIG. 3, a water repellent film 33 for improving the water repellency is formed on the catheter 3. It is desirable to coat the outer surface.

  As shown in FIG. 1, the discharge mechanism 4 is a mechanism for reciprocating the piston 21 along the inner peripheral surface of the disposable syringe 20. As a schematic configuration thereof, a motor 40, a control circuit 41, a ball screw 42 and a movable part 43.

  The motor 40 is a drive unit that is rotationally driven based on a signal from the control circuit 41, and is connected to the power supply unit 7. The ball screw 42 is for transmitting the rotational motion of the motor 40, and rotates axially in conjunction with the rotational drive of the motor 40. The movable portion 43 is a member screwed to the ball screw 42 and moves along the longitudinal axis direction of the disposable syringe 20 as the ball screw 42 rotates. The movable portion 43 is detachably attached to the piston 21, and the piston 21 moves along the longitudinal axis direction of the disposable syringe 20 as the movable portion 43 moves. The control circuit 41 controls the number and speed of the liquid medicine X delivered from the disposable syringe 20 to the catheter 3 by controlling the rotation speed of the motor 40, and discharges the liquid medicine X discharged from the discharge hole 30. The amount and the discharge speed are controlled. An operation start switch (not shown) or the like is connected to the control circuit 41. When the operation start switch or the like is operated, a signal is transmitted from the control circuit 41 to the motor 40, and a signal is transmitted to the voltage generation circuit 50 described later. Send.

In addition, the control circuit 41 is a combination data of a preset amount of the liquid medicine X (the number of rotations of the motor 40) and a liquid supply speed of the liquid medicine X (the rotation speed of the motor 40) from the disposable syringe 20 to the discharge hole 30. You may have the memory | storage part which does not show in figure which memorize | stores the table which stores. Further, in that case, when the chemical circuit X is fed, the control circuit 41 calls a table according to the usage of the chemical liquid X, and defines at least one of a liquid feeding amount and a liquid feeding speed corresponding to the usage. May be.
Further, the control circuit 41 may incorporate a control terminal (not shown) connected to an external switch (not shown). For example, when the user operates an external switch, which is a dial, the control circuit 41 causes at least one of, for example, a liquid feed amount (the rotational speed of the motor 40) of the chemical solution X and a liquid feed speed (the rotational speed of the motor 40). It may be set and controlled while adjusting.
Incidentally, changing the feed rate of the chemical X by the control circuit 41, the diameter of the chemical particles X ₁ is changed.

  The voltage application unit 5 is means for applying a voltage to the drug solution X sent from the drug solution filling unit 2 to the catheter 3. As a general configuration, the voltage application unit 5 includes a voltage generation circuit 50, an electrode contact member 51, and a voltage application electrode 52. And a ground band 53. The voltage applying unit 5 generates a high voltage, which is an applied voltage of, for example, 4 kV or more in the voltage generating circuit 50 by the power supplied from the power supply unit 7, and the high voltage is applied to the voltage applying electrode 52 via the electrode contact member 51. It is configured to supply to.

  The voltage generation circuit 50 is electrically connected to the power supply unit 7 and is supplied with power from the power supply unit 7. The voltage generation circuit 50 is electrically connected to the control circuit 41 and generates a voltage according to a signal transmitted from the control circuit 41. More specifically, a signal is transmitted from the control circuit 41 to the voltage generation circuit 50 by operating an operation start switch (not shown) and the like, and the operation of the voltage generation circuit 50 is controlled based on the signal. Generation is controlled. In addition, the voltage generation circuit 50 alternatively selects the polarity of the high voltage as either the positive side polarity or the negative side polarity.

In addition, the voltage generation circuit 50 may be provided with a storage unit (not shown) that stores a table storing combination data of preset polarity of the applied voltage, magnitude of the applied voltage, application duration, and the like. . The application duration is, for example, an application time for supplying a high voltage to the chemical solution X by supplying a high voltage to the voltage application electrode 52. When the high voltage is supplied to the voltage application electrode 52, the voltage generation circuit 50 calls a table according to the use application of the chemical solution X, and at least the polarity of the application voltage, the magnitude of the application voltage, and the application duration corresponding to the use application. One may be defined.
The voltage generation circuit 50 may include a control terminal (not shown) connected to an external switch (not shown). For example, when the user operates an external switch that is a dial, the voltage generation circuit 50 adjusts at least one of, for example, the polarity of the applied voltage, the magnitude of the applied voltage, and the application duration of the applied voltage. It may be set and controlled.
Note that changing the magnitude of the applied voltage by the voltage generating circuit 50, the diameter of the chemical particles X ₁ is changed.

  The electrode contact member 51 has a tapered needle shape in the application direction in order to concentrate application of a high voltage in the voltage application electrode 52, and for example, a stainless steel electrode is preferable. The electrode contact member 51 may be a general electric contactor gold-plated contact probe. The tip of the electrode contact member 51 is detachably contacted with an outer peripheral surface of a cylindrical electrode portion 54 described later.

The ground band 53 comes into contact with a part of the living body and becomes a 0 V potential, and is connected to the voltage generation circuit 50. The ground band 53 is attached to a finger or the like, for example. Accordingly, the affected part Y ₁ in the living body becomes electrical ground. That affected area Y ₁ is a different site of potential chemical liquid X in the discharge hole 30 is a site where high voltage is applied.

  The voltage application electrode 52 is made of a conductive metal, a conductive resin, or a cylindrical tube portion 54 made of a resin formed with a conductive film, and an inner peripheral surface of the cylindrical electrode portion 54. A linear electrode portion 55 connected thereto.

  The cylindrical electrode portion 54 is interposed between the distal end portion of the drug solution filling portion 2 and the proximal end portion of the catheter 3. One end of the cylindrical electrode portion 54 is detachably fastened to the distal end portion of the disposable syringe 20 by screwing. On the other hand, the other end of the cylindrical electrode portion 54 is firmly joined to the proximal end portion of the catheter 3 with, for example, an adhesive (not shown). Further, the inner diameter of the cylindrical electrode portion 54 is substantially the same as the inner diameter of the distal end portion of the drug solution filling portion 2 and the inner diameter of the catheter 3, and the inner side of the cylindrical electrode portion 54 is the internal space 22 of the drug solution filling portion 2 and the catheter. The three internal spaces 31 communicate with each other.

  The linear electrode portion 55 is inserted into the catheter 3 and extends on the axis O, and extends to the distal end portion of the catheter 3 (near the discharge hole 30). The material of the linear electrode portion 55 is preferably low in electrical resistance and stable in characteristics with respect to the chemical solution X. For example, platinum, gold, silver, or stainless steel is more preferable. Further, the diameter of the linear electrode portion 55 is smaller than the inner diameter of the internal space 31 of the catheter 3. Further, the length of the linear electrode portion 55 is shorter than the entire length of the catheter 3 and has a length that does not protrude from the discharge hole 30 and extends to the vicinity of the discharge hole 30. For example, when the catheter 31 has an outer diameter of approximately 1.6 mm, an inner diameter of approximately 0.9 mm, and a length of approximately 2000 mm, the linear electrode portion 55 having a diameter of approximately 0.3 mm and a length of approximately 1980 mm can be used.

  Further, the voltage application unit 5 incorporates a high resistance circuit, an overcurrent detection circuit, or the like (not shown) as a high voltage safety measure. As the high resistance circuit, a protective high resistance for preventing sparks and electric shock to the living body is arranged in series with the electrode contact member 51. The overcurrent detection circuit detects a current that flows when a high voltage is supplied from the voltage generation circuit 50 to the voltage application electrode 52, and when the current value exceeds a preset value, the voltage generation circuit 50 is stopped, and the generation of the high voltage is stopped. In consideration of safety to the living body, the set value in the overcurrent detection circuit is preferably set to about 100 μA or less, or preferably about 10 μA or less.

The high voltage safety measures need not be limited to the above. For example, the voltage generation circuit 50 cooperates with the discharge mechanism 4 and when the chemical solution X in the disposable syringe 20 is exhausted (for example, the piston 21 is placed on the catheter 3 side). And the generation of the high voltage may be stopped. In other words, the voltage generation circuit 50 is configured to generate a high voltage and supply the high voltage only during the feeding of the chemical solution X by the discharge mechanism 4.
Further, the voltage generation circuit 50 includes a transformer (not shown) that boosts (generates) the power supply unit 7 to a high voltage.

  The discharge mechanism 4, the voltage generation circuit 50, the electrode contact member 51, and the power supply unit 7 are built in the housing 8, and the tip of the electrode contact member 51 protrudes from the housing 8. Further, the distal end portion of the above-described disposable syringe 20, the voltage applying electrode 52 (cylindrical electrode portion 54), and the proximal end portion of the catheter 3 are inserted into the disposable syringe fixing frame 9 which is an electrically insulating portion such as rubber. ing. The disposable syringe fixing frame 9 is fixed to the housing 8. The voltage application electrode 52 and the electrode contact member 51 are prevented from contacting the outside by the disposable syringe fixing frame 9 and the housing 8.

In addition, an opening / closing transparent resin cover 10 that prevents a finger or the like from being caught is provided at a portion where the piston 21 moves.
The disposable syringe 20, the piston 21, the catheter 3, and the voltage application electrode 52 are detachable from the movable portion 43 and the electrode contact member 51. That is, the disposable syringe 20, the piston 21, the catheter 3, and the voltage application electrode 52 can be detached from the movable portion 43 and the electrode contact member 51, and are discarded after use as a disposable part depending on the case. The voltage generation circuit 50, the electrode contact member 51, the chemical solution feeding mechanism 6, the power supply unit 7, the housing 8, the disposable syringe fixing frame 9, and the cover 10 are, for example, an unused disposable syringe 20, piston 21, catheter 3. Further, it can be connected to the voltage application electrode 52 and reused as a reuse part.

The material used for the catheter 3 is not particularly limited, and an optimum material can be selected from general polymer materials according to the purpose. Further, the material is not limited to a single material, and a material obtained by combining a plurality of polymer materials, a material obtained by adding an inorganic material to a polymer material, or the like can be used. In the present embodiment, for example, tetrafluoroethylene resin is used as an example, but other fluororesins may be used, and the present invention is not limited to fluororesins, and is not limited to the fluororesins, but within a range where no problems occur due to mechanical characteristics. Polymer materials may be used.
Here, by using a material having a melting point lower than the autoclave sterilization treatment temperature for at least a part of the catheter 3, it is destroyed by the sterilization treatment and cannot be reused, thereby preventing infection due to reuse. be able to. For example, for autoclave sterilization at 135 ° C., linear low density polyethylene (LLDPE) having a melting point of 135 ° C. or less is used, and it is destroyed by sterilization and cannot be reused.

  Next, the operation of the chemical spray administration apparatus 1 having the above configuration will be described.

First, the disposable syringe 20 is screwed and connected to the cylindrical electrode portion 54 of the voltage application electrode 52 to which the catheter 3 is joined.
Next, after filling the disposable syringe 20 with a desired amount of the chemical solution X, the piston 21 is inserted into the disposable syringe 20. The above-mentioned “desired amount” is an appropriate amount for treating the affected area Y ₁ with the chemical solution X, and is an amount fed from the disposable syringe 20 to the discharge hole 30 by the discharge mechanism 4.

Next, the piston 21 is engaged with the movable portion 43 of the discharge mechanism 4, and the distal end portion of the catheter 3, the cylindrical electrode portion 54 and the disposable syringe 20 is inserted into the disposable syringe fixing frame 9, and the cylindrical electrode portion 54 is inserted. The tip of the electrode contact member 51 is brought into contact with the outer peripheral surface of the cover, and then the cover 10 is closed.
Thereby, the chemical | medical solution spray administration apparatus 1 is comprised, and the preparation of the chemical | medical solution spray administration apparatus 1 is completed.

Next, the catheter 3 is inserted into the lumen Y of the patient from the distal end. In detail, inserted into the forceps channel 60 of the endoscope 6 to the catheter 3, moving the catheter 3 while observing the affected area Y ₁ by the observation optical system (not shown) provided in the endoscope 6, the discharge to oppose the hole 30 in the affected area _{Y 1.}

  Next, when an operation start switch or the like (not shown) is operated to start operation, a drive start signal is transmitted from the control circuit 41 to the motor 40, and the motor 40 is rotationally driven. When the motor 40 is driven, the ball screw 42 is axially rotated, the axial rotation of the ball screw 42 moves the movable portion 43 along the longitudinal axis of the disposable syringe 20, and the piston 21 is along the longitudinal axis of the disposable syringe 20 on the catheter 3 side. It moves to (the tip side of the disposable syringe 20). Thereby, the chemical solution X in the disposable syringe 20 is pushed out from the tip of the disposable syringe 20 and is pumped into the catheter 3 through the cylindrical electrode portion 54. In the catheter 3, one internal space 31 is formed, and each discharge hole 30 is communicated with the internal space 31, so that the drug solution X fed into the catheter 3 passes through one internal space 31. It reaches each discharge hole 30 through.

  Further, when an operation start switch (not shown) or the like is operated to start operation, a drive start signal is transmitted from the control circuit 41 to the voltage generation circuit 50, and a high voltage is generated from the voltage generation circuit 50. This high voltage is supplied to the voltage application electrode 52 via the electrode contact member 51. Then, a high voltage is applied from the inner peripheral surface of the cylindrical electrode portion 54 to the chemical solution X flowing through the cylindrical electrode portion 54, and at the same time, a high voltage is applied from the linear electrode portion 55 to the chemical solution X flowing through the catheter 3. Is applied.

As described above, the drug solution X that is pumped by the discharge mechanism 4 and to which a voltage is applied by the voltage application unit 5 is sprayed as atomized charged drug solution fine particles X ₁ from the plurality of discharge holes 30 of the catheter 3.
If it demonstrates in detail, the chemical | medical solution X in the discharge hole 30 forms the gas-liquid interface between the gas outside the catheter 3. When a voltage is applied to this gas-liquid interface, the gas-liquid interface becomes electrohydrodynamically unstable due to the electrostatic force acting on the surface of the chemical liquid X, and an unstable point is generated. Chemical particles X ₁ of the charged atomized state from the point of instability is sprayed. When a high voltage acts on the gas-liquid interface and the electric field density at the gas-liquid interface in the discharge hole 30 reaches a critical value, a thin liquid thread (thread-like chemical liquid X) is drawn from the surface of the chemical liquid X, and the liquid thread Expands and contracts. In this case, the chemical liquid X from the tip of Ekiito is, as a number of chemical particles X _1, divide a thin liquid thread. Further, when the value of the high voltage is increased, the interface in the thin liquid yarn becomes more unstable, and a large number of unstable points are generated simultaneously. Chemical X from these unstable point, is a number sprayed from the discharge holes 30 as the chemical particles X ₁ of the charged complete atomization state.
Since the catheter 3 is made of a non-conductive material made of tetrafluoroethylene resin, the chemical solution X is sprayed without staying in the catheter 3.

When a high voltage as described above is applied to the drug solution X, a potential difference occurs between the chemical X and diseased Y ₁ in the discharge hole 30, toward the affected area Y ₁ from the discharge hole 30 as shown in FIG. 5 Electrical A force line E is formed. Chemical particles X ₁ which is sprayed from the discharge hole 30, because of the positively charged side polarity or negative polarity, as shown in FIG. 5, the affected area Y ₁ from the discharge hole 30 along the electric flux lines E as described above To reach. The charged liquid chemical particle X ₁ is reliably attached to the affected part Y ₁ having a potential of 0V. That is, when a high voltage is positive polarity, chemical particles X ₁ is positively charged side polarity, if a high voltage is negative polarity, chemical particles X ₁ is charged to the negative side polarity. In general, the living body is in the vicinity of 0V, and in the present embodiment, the living body is set to 0V by the ground band 53. Therefore, the drug solution X (charged drug solution fine particles X ₁ ) in the affected area Y ₁ and the discharge hole 30 of the living body. Have different potentials. Therefore, the medicinal solution fine particles X ₁ charged to the positive side polarity or the negative side polarity adhere to the affected part Y ₁ .

In addition, since a plurality of discharge holes 30 are formed at the distal end of the catheter 3 described above, a larger amount of the drug solution X is sprayed at a time than when there is only one discharge hole 30. Thus, the chemical liquid X is administered efficiently affected area Y _1.
Further, since the plurality of discharge holes 30 are disposed at positions that are substantially rotationally symmetric with respect to the axis O, the chemical solution discharge speed from each discharge hole 30 is made uniform, and each discharge from each discharge hole 30 is performed. The atomization position of the liquid yarn is made uniform.

By the way, when the interval L between the plurality of discharge holes 30 is close, the chemical liquids X discharged from the respective discharge holes 30 come into contact with each other, or the chemical liquid X adheres to the distal end surface of the catheter 3 to clog the discharge holes 30. As a result, the spraying of the chemical solution X stops or becomes unstable. Therefore, to the separated state each thin liquid thread discharged from the respective discharge holes 30 becomes important in order to form a fine chemical particles X _1. If the interval L between the plurality of discharge holes 30 is less than 20 μm, the chemicals X discharged from the discharge holes 30 may come into contact with each other. That is, if the interval L between the plurality of discharge holes 30 is made as large as possible, the spraying of the chemical solution X is less likely to stop or become unstable, and is desirably disposed near the outer edge of the distal end surface of the catheter 3. Is preferred. In the chemical spray administration apparatus 1 having the above-described configuration, since the plurality of discharge holes 30 are arranged at intervals of 20 μm or more, the chemical liquid X (liquid yarn) sprayed from each discharge hole 30 is in contact with each other. Separated without.

According to the chemical solution spraying injection device 1 having the above-mentioned structure, the discharge hole 30 is formed with a plurality, the amount of the chemical liquid X to be sprayed increases at a time, to efficiently affected area Y ₁ because chemical X is administered , it is possible to shorten the time of administration to the affected area Y ₁ chemical solution X. Thereby, a patient's burden can be reduced.
4 and 5, three discharge holes 30 are formed. Needless to say, a larger amount of the drug solution X can be administered in a short time by forming a larger number of discharge holes 30.

Further, in the above-described chemical spray administration apparatus 1, the plurality of discharge holes 30 are arranged with an interval of 20 μm or more, and the chemical liquid X (liquid yarn) sprayed from each discharge hole 30 does not contact each other. Since the chemical liquid fine particles X ₁ having a stable particle diameter are sprayed and the chemical liquid X is prevented from dripping as droplets, the surface of the lumen Y in the vicinity of the discharge hole 30 is more than necessary. chemicals X can be prevented from being administered, it can be administered a drug solution X proper amount to the affected area Y _1. Thereby, while being able to show the medicinal effect of the chemical | medical solution X reliably, the side effect of the chemical | medical solution X can be reduced.

Further, in the above-described chemical spray administration apparatus 1, the chemical liquid X delivered from the chemical liquid filling unit 2 circulates in one internal space 31 of the catheter 3 and reaches each of the plurality of discharge holes 30. Compared with the case where every 30 channels are formed in the catheter 3, the chemical liquid flow is facilitated, and the chemical liquid X in the chemical liquid filling unit 2 is delivered to each discharge hole 30 in a short time. This makes it possible to efficiently spray the chemical X, it is possible to shorten the time of administration to the affected area Y ₁ chemical solution X.
In addition, since the chemical liquid X flows through one internal space 31 and reaches each of the plurality of discharge holes 30, liquid pressure loss when the chemical liquid X is delivered to the discharge holes 30 is suppressed. Thereby, the discharge mechanism 4 with a small output (liquid feeding force) can be used.

  Further, in the above-described chemical spray administration apparatus 1, the plurality of discharge holes 30 are disposed at positions that are substantially rotationally symmetric with respect to the axis O, and the liquid discharge speed from each discharge hole 30 is made uniform, Since the atomization position of the liquid yarn discharged from the discharge hole 30 is made uniform, the spray amount and spray range can be made substantially uniform in all directions.

Further, in the above-described chemical spray administration apparatus 1, since each chemical liquid X (liquid yarn) discharged from each of the plurality of discharge holes 30 is charged with the same polarity, the chemical liquid X (discharged from each discharge hole 30) ( The liquid yarns repel each other and are difficult to contact. Thus, it is possible to spray the chemical particles X ₁ stable particle size, together with the chemical liquid X can be prevented from dripping it becomes droplets can be sprayed a chemical X more widespread. For example, when the leading end to the three discharge holes 30 of the catheter 3 is formed, as shown in FIG. 5, as an area where chemical liquid fine particles X ₁ is sprayed, almost three spray region A ₁ to A ₃ are formed The

Also, in liquid spray dispensing device 1 described above, atomized chemical liquid X in the discharge hole 30, it has been administered to the affected area Y ₁ along the electric force lines E, the chemical X to the disposable syringe 20 and the catheter 3 without atomization Te, also without air to the discharge holes 30 in a state where the atomized chemical liquid X, also not using a gas pressure for administration to affected area Y ₁ chemical solution X. Therefore, it is possible to prevent the drug solution X remains in the catheter 3, the amount of the chemical liquid X which is fed to the discharge port 30 from the disposal syringe 20 will amount substantially the same chemical X adhering to the affected area Y _1. In other words, the amount of drug solution X was initially charged in a disposable syringe 20, the dose into the affected Y ₁ is substantially the same. Therefore, it is possible to appropriately dose a drug solution X to the affected area Y ₁ in vivo.

Further, if the chemical liquid fine particles are not charged, a force for maintaining the spherical shape by the surface tension of the chemical liquid fine particles acts on the chemical liquid fine particles. This force is stronger as the diameter of the chemical fine particles is smaller. For this reason, the chemical liquid fine particles are unlikely to adhere to the surface of the lumen Y, and a dry fog phenomenon in which the chemical liquid fine particles rise easily occurs. In contrast, in liquid spray dispensing device 1 described above, since the charges the chemical particles X _1, can be positively attaching chemical particles X ₁ to the affected area Y _1, the affected area Y ₁ chemical particles X ₁ from Is prevented from flying up. Thus, the surface of the lumen Y other than the affected area Y ₁ chemical particles X ₁ is scattered can be prevented chemical X is administered, can be administered a drug solution X proper amount to the affected area Y _1, the affected area The dose of the drug solution X to Y ₁ can be accurately managed.

In particular, when the drug solution X is administered to the lungs or alveoli of the respiratory system, the uncharged drug solution particles are easily discharged from the mouth by breathing out. For this reason, nebulizers used in inhalation therapy and the like require a chemical solution spraying operation in conjunction with expiration, such as spraying the chemical solution X in accordance with the inhalation. On the other hand, in liquid spray dispensing device 1 described above, since the charges the chemical particles X _1, regardless of the discharging breathing, can be attached a chemical X to the affected area Y _1.

  Further, if a high voltage is applied to the drug solution X in the catheter 3 only at the inner diameter portion of the cylindrical electrode portion 54, the voltage decreases until the drug solution X reaches the discharge hole 30, and the discharge hole The voltage acting on the chemical solution X at 30 may be lower than the high voltage generated by the voltage generation circuit 50. For this reason, the voltage generation circuit 50 must generate a voltage with the voltage drop added. On the other hand, in the drug spray administration device 1 described above, the linear electrode portion 55 extends to the vicinity of the discharge hole 30 and the tip of the linear electrode portion 55 is close to the discharge hole 30. The high voltage generated from the voltage generation circuit 50 acts on the chemical solution X in the discharge hole 30 as it is through the linear electrode portion 55. As a result, it is not necessary to generate a voltage with an added voltage drop in the voltage generation circuit 50, and the voltage value generated by the voltage generation circuit 50 can be lowered.

  In addition, depending on the drug solution X, the gas dissolved in the drug solution X in the catheter 3 may expand or gather due to the outside air temperature to form a gas layer. If the linear electrode portion 55 is not disposed in the catheter 3, when gas expands or collects inside the catheter 3, no voltage is applied to the drug solution X in the discharge hole 30, and the drug solution X is May not be atomized. On the other hand, in the above-described medicinal solution spray administration device 1, the tip of the linear electrode portion 55 extends to the vicinity of the discharge hole 30, so that a voltage can be reliably applied to the medicinal solution X in the discharge hole 30, and the chemical solution X can be reliably atomized.

Further, in the above-described chemical spray administration apparatus 1, if the electrical conductivity of the chemical X is within the range of 1 × 10 ⁻¹⁰ (S / m) to 1 × 10 ⁻¹ (S / m), it is controlled by the discharge mechanism 4. feed rate of the chemical liquid X to be, and the magnitude of the applied voltage is controlled by the voltage generating circuit 50, by changing at least one of, it is possible to vary the size of the chemical particles X _1.
Further, the to increase the liquid feed rate discharge mechanism 4, by increasing the applied voltage by the voltage generating circuit 50, while maintaining the diameter of the chemical particles X _1, to increase the dose of the drug solution X per unit time Can do.

Also, in liquid spray dispensing device 1 described above, the forceps channel 60 of the endoscope 6 is then inserted through the catheter 3, the chemical X while observing the affected area Y ₁ by unillustrated observation optical system of the endoscope 6 it can be sprayed, certainly the affected area Y ₁ can be administered a drug solution X.

Further, in the above-described drug spray administration device 1, generation of a high voltage can be controlled by turning on and off the voltage generation circuit 50 by an operation start switch (not shown) or the like, and spraying is instantaneously performed depending on whether or not the high voltage is applied. Can be started and stopped. Thus the present embodiment, set any application duration by the voltage generating circuit 50, ON voltage generating circuit 50, by controlling the presence or absence of application by OFF, the proper amount by the time required for the affected area Y ₁ it can be administered in chemical particulates X _1. That is, according to the present embodiment, an accurate administration time, in other words, a dosage can be managed.

In the drug spray administration device 1 described above, the voltage generation circuit 50 is disposed outside the lumen Y, and the discharge hole 30 is disposed inside the lumen Y. Thereby, the voltage generation circuit 50 can be kept away from the living body, which is safer.
Moreover, in the above-described drug spray administration device 1, the catheter 3 is a non-conductive material. Thereby, since a voltage does not act on a living body, it is safe.

[Second Embodiment]
Next, a second embodiment will be described with reference to FIGS.
FIG. 6 is a cross-sectional view of the distal end portion of the catheter 3 cut in the axial direction, and FIG. 7 is a schematic view showing the sprayed state of the drug solution X.
In addition, about the structure similar to 1st Embodiment mentioned above, while attaching | subjecting the same code | symbol, the description is abbreviate | omitted.

As shown in FIG. 6, the distal end surface 3 a of the catheter 3 in which the plurality of discharge holes 30 are formed is formed in a rotating curved surface shape with the axis O as the center.
More specifically, the distal end surface of the catheter 3 has a substantially spheroid shape. Specifically, the distal end wall 132 that closes the internal space 31 of the catheter 3 is formed in a hemispherical cup shape that bulges toward the distal end side of the catheter 3, and the wall thickness of the distal end wall 132 is, for example, about 0.3 mm. Has been. A plurality of discharge holes 30 are formed in the tip wall 132 at positions that are substantially rotationally symmetric with respect to the axis O. Each of the plurality of ejection holes 30 extends obliquely with respect to the axis O.

The above-mentioned tip wall 132 is manufactured, for example, by machining a tetrafluoroethylene resin or the like. Tetrafluoroethylene resin has sufficient compressive strength and bending strength, and can maintain a spheroidal shape even when pressed against the surface of a living body.
The catheter 3 is processed into a hemispherical cup shape and has a cup part (tip wall 132) having a plurality of discharge holes 30 formed therein, and has one through hole (internal space 31) extending in the axial direction. It can be manufactured by melting or bonding to the end face of the resin pipe with an adhesive or the like.

According to the medicinal-solution spray administration device 1 including the catheter 3 described above, the opening end surface 30a on the outlet side (terminal side) of each discharge hole 30 is inclined with respect to the axis O, and sprayed from each discharge hole 30 respectively. since chemical X together can be more reliably separated, are more stable chemical particles X ₁ is spray particle size, that chemical X is dripping becomes droplets is reliably prevented. This allows the chemical solution X of the above required amount to the surface of the lumen Y discharge holes 30 near can be prevented from being administered, administered in a short time chemical X proper amount to the affected area Y ₁ .

Further, as shown in FIG. 7, since the chemical liquid X (a plurality of liquid yarns) discharged from each discharge hole 30 spreads outward in the radial direction, the chemical liquid X is sprayed in a wider range. That is, the spray regions B _{1 to} B _{3 of the} chemical liquid fine particles X ₁ sprayed from the respective discharge holes 30 are larger than the spray regions A _{1 to} A ₃ in the above-described first embodiment. Thus, it is possible to administer effectively the drug solution X a wide affected part Y _1.
Furthermore, since the distal end of the catheter 3 has a shape without an acute ridge (corner), the influence on the living body when the distal end of the catheter 3 contacts the surface of the lumen Y is reduced. In this way, the safety to the living body can be further improved.

[Third Embodiment]
Next, a third embodiment will be described with reference to FIGS.
8 is a cross-sectional view of the distal end portion of the catheter 3 cut in the axial direction, FIG. 9 is an end view showing the distal end surface of the catheter 3, and FIG. 10 is a cross-sectional view between ZZ shown in FIG. is there.
In addition, about the structure similar to 1st Embodiment mentioned above, while attaching | subjecting the same code | symbol, the description is abbreviate | omitted.

As shown in FIGS. 8 to 10, the plurality of discharge holes 130 have a shape that is gradually reduced in diameter from the inner side of the catheter 3 toward the outer side of the catheter 3.
More specifically, a plurality of cone-shaped discharge holes 130 are formed in the distal end wall 32 that closes the internal space 31 of the catheter 3. The discharge hole 130 has a tapered shape that is gradually reduced in diameter from the opening end surface 130a on the inlet side (start end side) toward the opening end surface 130b on the outlet side (termination side). That is, the opening area _{S 2} of the opening area _{S 1} and the terminal side of the open end 130b of the beginning side of the opening end face _130a, is established the relationship _[S 1> S _2]. More specifically, for example, the opening end surface 130a on the start end side is formed with an inner diameter of about 0.1 mm, and the opening end surface 130b on the end side is formed with an inner diameter of about 0.05 mm.

The cone-shaped discharge hole 130 described above can be easily formed, for example, by precision laser processing, and the taper angle can be freely set.
The discharge hole 130 does not have to have a tapered shape in which the inner peripheral surface 130c is linearly inclined. For example, the discharge hole 130 is a mortar-shaped discharge hole in which the inner peripheral surface of the discharge hole bulges radially inward. Alternatively, it may be a bowl-shaped discharge hole in which the inner peripheral surface of the discharge hole bulges radially outward.

According to the drug spray administration device 1 having the discharge hole 130 described above, when the drug solution X passes through the discharge hole 130, the diameter gradually decreases from the opening end 130a on the discharge port 130 toward the opening end 130b on the termination side. Is rectified. In addition, an angle θ formed by the inner peripheral surface 130c of the terminal portion of the discharge hole and the distal end surface 3a of the catheter 3 (the outer surface of the distal end wall 32) becomes an acute angle. As a result, the chemical liquid X (liquid yarn) discharged from the discharge holes 130 does not easily spread in a conical shape, and is easily discharged only in the discharge direction (direction perpendicular to the opening end surface 130b on the terminal end side). It becomes difficult for the discharged chemicals X (liquid yarns) to come into contact with each other. As a result, the chemical liquid fine particles X ₁ having a more stable particle diameter are sprayed, and the chemical liquid X is surely prevented from dripping and dropping, and more than a necessary amount of chemical liquid is applied to the surface of the lumen Y in the vicinity of the discharge hole 130. X can be prevented from being administered, the chemical X proper amount to the affected area Y ₁ can be administered in a short time.

[Fourth Embodiment]
Next, a fourth embodiment will be described with reference to FIGS.
FIG. 11 is a cross-sectional view of the distal end portion of the catheter 3 cut in the axial direction, and FIG. 12 is an end view showing the distal end surface of the catheter 3.
In addition, about the structure similar to 1st Embodiment mentioned above, while attaching | subjecting the same code | symbol, the description is abbreviate | omitted.

As shown in FIGS. 11 and 12, the catheter 3 is provided with a gas flow passage 134 through which the pumped gas flows, and the distal end 134 a of the gas flow passage 134 is formed on the distal end surface 3 a of the catheter 3. A plurality of discharge holes 30 are provided around the tip opening end 134a.
More specifically, an air pipe 135 that blows gas is disposed in the internal space 31 of the catheter 3. The inner peripheral hole of the air pipe 135 serves as the gas flow passage 134 described above. The air pipe 135 is arranged coaxially with the catheter 3 with the axis O as a common axis. One end (base end) of the air pipe 135 is connected to an air pump (not shown). On the other hand, the other end (tip) of the air pipe 135 is penetrated through the tip wall 32 of the catheter 3, and the tip surface of the air pipe 135 is connected to the tip surface 3 a of the catheter 3 (the outer surface of the tip wall 32). It is formed substantially flush. The plurality of discharge holes 30 are disposed on the radially outer side of the air pipe 135 so as to surround the front end portion of the air pipe 135, and extend in parallel with the front end portion of the air pipe 135.
More specifically, for example, an air pipe 135 having an outer diameter of about 1.0 mm is disposed at the center of the catheter 3 having an outer diameter of about 2.0 mm, and a discharge pipe having a diameter of about 0.075 mm is disposed so as to surround the air pipe 135. A plurality of holes 30 are provided. In addition, the space | interval L between the discharge holes 30 at this time is set to about 0.05 mm.
The linear electrode portion 155 of the voltage application electrode 52 is disposed on the radially outer side of the air pipe 135 and is disposed between the outer peripheral surface of the air pipe 135 and the inner peripheral surface of the catheter 3. Yes.

According to the chemical spray administration apparatus 1 having the gas flow path 134 described above, the chemical liquids X (liquid yarns) discharged from the discharge holes 30 by the gas discharged from the distal end opening end 134a of the gas flow path 134 are respectively discharged. It becomes difficult to contact and is separated. As a result, the chemical liquid fine particles X ₁ having a more stable particle diameter are sprayed, and the chemical liquid X is reliably prevented from dripping and dropping, and the amount of the chemical liquid more than the necessary amount is applied to the surface of the lumen Y in the vicinity of the discharge hole 30. X can be prevented from being administered, the chemical X proper amount to the affected area Y ₁ can be administered in a short time.

In addition, mucus in the body attached to the distal end surface 3a of the catheter 3 is blown off by the gas released from the distal end opening end 134a of the gas flow passage 134. Thereby, clogging of the discharge hole 30 due to mucus in the body can be prevented.
Further, the chemical liquid X (chemical liquid fine particle X ₁ ) sprayed from the discharge hole 30 is delivered further by riding on the flow of gas discharged from the distal end opening end 134 a of the gas flow passage 134. As a result, the drug solution X can be administered to the affected part Y ₁ where it is difficult to bring the tip of the catheter 3 closer, and the time required for the drug solution treatment can be shortened. For example, the medicinal solution X can be administered to the alveoli by spraying the medicinal solution X from the bronchi in front of the affected part Y ₁ such as the alveoli.

As mentioned above, although embodiment of the chemical | medical solution spray administration apparatus concerning this invention was described, this invention is not limited to above-described embodiment, In the range which does not deviate from the meaning, it can change suitably.
For example, in the above-described embodiment, the three discharge holes 30 are formed. However, in the present invention, it is only necessary to form a plurality of discharge holes 30, and the number of the discharge holes 30 can be changed as appropriate. For example, as shown in FIG. 13, five discharge holes 30 may be formed. Here, it is not necessary inside diameter D ₂ of the four discharge holes 30B positioned on the inner diameter D ₁ and surrounding discharge hole 30A in the center is that always match, depending on the flow rate of the chemical liquid X in the catheter 3 The optimum value can be taken.

Further, in the above-described embodiment, the discharge holes 30 and 130 having a circular shape in cross section are formed at the distal end of the catheter 3 having a circular shape in cross section. However, in the present invention, the catheter 3 and the discharge holes 30 and 130 are provided. The cross-sectional view shape can be changed as appropriate. For example, as shown in FIG. 14, a catheter 203 having a hexagonal cross section can be used, and a discharge hole 230 having a triangular shape in cross section can be formed. The catheter 203 and the discharge hole 230 having such a shape can be easily manufactured by extrusion molding, machining, or the like.
Thus, by making the shape of the catheter other than circular, the frictional resistance with the catheter in the endoscope tube can be reduced and the catheter can be easily inserted into the target site, and the treatment time can be shortened. Further, by forming the discharge hole 230 having a triangular cross-sectional view, as shown in FIG. 15, the spray areas C _{1 to} C ₃ in each discharge hole 230 are clearly divided, and the drug solution X is uniformly applied to the affected area Y ₁ . Can be administered.

  In the above-described embodiment, the plurality of discharge holes 30 and 130 are disposed at positions that are substantially rotationally symmetric with respect to the axis O. However, in the present invention, the plurality of discharge holes are arranged with respect to the axis O. It is also possible to adopt a configuration in which the nozzles are arranged at positions that are not rotationally symmetric. For example, the discharge holes may be arranged unevenly.

  In the above-described embodiment, the catheter 3 is formed with one internal space 31, and the discharge holes 30 and 130 are communicated with the internal space 31. It is also possible to adopt a configuration in which the internal space is formed. For example, an internal space may be formed for each discharge hole. That is, a plurality of internal spaces may be formed in the catheter 3 and one discharge hole may be connected to each of the internal spaces.

  In the above-described embodiment, each chemical solution X discharged from the plurality of discharge holes 30 and 130 is charged to the same polarity by the voltage application unit 5, but the present invention discharges from the plurality of discharge holes. It is also possible to adopt a configuration in which the obtained chemical solution is charged with a different polarity. For example, as described above, when the catheter has a plurality of internal spaces, a positive polarity voltage is applied to the chemical solution flowing through a part of the plurality of internal spaces by the voltage application unit, and the remaining A negative polarity voltage may be applied to the chemical solution flowing through the internal space by a voltage application unit.

  In addition, the constituent elements in the above-described embodiment can be appropriately replaced with known constituent elements without departing from the gist of the present invention, and the above-described first to fourth embodiments and modification examples are possible. May be combined as appropriate.

DESCRIPTION OF SYMBOLS 1 Chemical liquid spray administration apparatus 2 Chemical liquid filling part 3, 203 Catheter 30, 130, 230 Discharge hole 31 Internal space 4 Discharge mechanism 5 Voltage application part 134 Gas flow path 134a Tip opening end O Axis line (central axis line)
X chemical

Claims (7)

A chemical solution filling portion in which the chemical solution is filled,
A catheter in which a proximal end is connected to the drug solution filling portion and a discharge hole for discharging the drug solution is formed at the tip;
A discharge mechanism for discharging the drug solution in the drug solution filling portion from the discharge hole through the catheter;
Applying a voltage to the drug solution sent to the discharge hole by the discharge mechanism to atomize the drug solution in the discharge hole , at least a part of the voltage application unit provided in the internal space of the catheter ;
With
A plurality of the discharge holes are formed at the distal end of the catheter, and the plurality of discharge holes are arranged at intervals of 20 μm or more.   The medicinal-solution spray administration device according to claim 1, wherein the catheter is formed with one internal space communicating with the medicinal-solution filling portion, and each discharge hole communicates with the internal space. .   The drug spray administration device according to claim 1, wherein the plurality of discharge holes are disposed at positions that are substantially rotationally symmetric with respect to a central axis of the internal space of the catheter.   The medical solution according to any one of claims 1 to 3, wherein a distal end surface of the catheter in which the plurality of discharge holes are formed is formed into a rotating curved surface centering on a central axis of the catheter. Nebulizer device.   The medicinal-solution spray administration device according to any one of claims 1 to 4, wherein the discharge hole is gradually reduced in diameter from the inside of the catheter toward the outside of the catheter.   The catheter is provided with a gas flow passage through which the pumped gas flows, and a distal opening end of the gas flow passage is formed on a distal end surface of the catheter, and the plurality of discharges around the distal opening end. The medicinal-solution spray administration device according to any one of claims 1 to 5, wherein a hole is provided.   The medicinal-solution spray administration device according to any one of claims 1 to 6, wherein each medicinal solution ejected from each of the plurality of ejection holes is charged to the same polarity by the voltage application unit.

Images