WO2010061680A1 - Catheter - Google Patents

Catheter Download PDF

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Publication number
WO2010061680A1
WO2010061680A1 PCT/JP2009/065749 JP2009065749W WO2010061680A1 WO 2010061680 A1 WO2010061680 A1 WO 2010061680A1 JP 2009065749 W JP2009065749 W JP 2009065749W WO 2010061680 A1 WO2010061680 A1 WO 2010061680A1
Authority
WO
WIPO (PCT)
Prior art keywords
catheter according
medicine
supporter
catheter
flow
Prior art date
Application number
PCT/JP2009/065749
Other languages
French (fr)
Japanese (ja)
Inventor
香由 木村
正伸 清原
Original Assignee
オリンパス株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from JP2008305499A external-priority patent/JP2010125226A/en
Priority claimed from JP2008305501A external-priority patent/JP2010125228A/en
Priority claimed from JP2008305500A external-priority patent/JP2010125227A/en
Application filed by オリンパス株式会社 filed Critical オリンパス株式会社
Publication of WO2010061680A1 publication Critical patent/WO2010061680A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0067—Catheters; Hollow probes characterised by the distal end, e.g. tips
    • A61M25/0068—Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
    • A61M25/0069—Tip not integral with tube
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/02—Holding devices, e.g. on the body
    • A61M25/04—Holding devices, e.g. on the body in the body, e.g. expansible
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters

Definitions

  • the present invention relates to a catheter attached to a body organ of a mammal including human beings, and more particularly to a catheter for administering a drug from the surface of the body organ to the body organ.
  • Patent Document 1 a catheter that administers a drug by inserting a puncture needle into a body organ of a mammal including a human is known (see Patent Document 1).
  • the conventional catheter basically administers the drug only to one point inside the internal organ, even if it is desired to administer the drug to the affected area having a certain volume, the part of the affected part separated from the administration position I wasn't able to spread the drug very much.
  • the depth of the puncture needle may be insufficient and the puncture needle may come off. In such a case, sufficient drug administration is performed. I could't.
  • the drug is administered by sticking a sheet or gel soaked with the drug on the surface of the internal organ (see Patent Document 2).
  • the present invention has been made in view of the above, and an object of the present invention is to provide a catheter capable of easily and reliably administering a drug to a predetermined region near the surface of a body organ.
  • a catheter according to the present invention is a catheter attached to a body organ of a mammal including a human, and a conduit for guiding a drug from a drug supply source into the body;
  • the total area of the one or more openings is wider than the cross-sectional area of the internal passage.
  • the pad is a flexible sheet portion, and the one or more openings are provided on the back surface of the pad.
  • the back surface of the sheet portion is formed with a close contact area that is in close contact with the surface of the internal organ and a non-adhesion area that is not in close contact with the surface of the internal organ.
  • the plurality of openings are provided in the non-contact region.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the surface of the close contact area is formed smoothly, and the surface of the non-contact area is formed rougher than the close contact area.
  • the catheter according to the present invention is the above-described invention, wherein the one or more openings are not positioned separately from the non-contact area where the one or more openings are positioned on the back surface of the sheet portion.
  • a flow path connecting the region is formed.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a groove formed on a back surface of the sheet portion.
  • the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the sheet portion. It is characterized by that.
  • the catheter according to the present invention is characterized in that, in the above-described invention, the flow path is a lumen formed in the seat portion.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a lumen formed inside the seat portion, and the inside of the lumen is porous.
  • the catheter according to the present invention further includes a spacer disposed between the back surface of the sheet portion and the surface of the internal organ, and the spacer is formed on the side wall and the sheet portion side.
  • An upper opening and a lower opening formed on the internal organ side, and at least a surface of the internal organ covered by the lower opening serves as the non-contact region.
  • the catheter according to the present invention includes a connection member that connects the conduit and the seat portion, and the conduit and the seat portion are detachably coupled by the connection member. It is characterized by that.
  • the catheter according to the present invention is characterized in that, in the above invention, the back surface of the sheet portion is in close contact with the surface of the internal organ by intermolecular force.
  • the seat portion is connected to the conduit on the conduit side, and has a cross-sectional area wider than the cross-sectional area of the internal passage of the conduit, It has the connection part which forms the empty room which contact
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the seat portion is provided with an air vent valve.
  • the catheter according to the present invention is characterized in that, in the above invention, the sheet portion is formed of a member having air permeability.
  • the pad is a flexible supporter part that winds around the internal organs and has a supporter function, and the one or more openings are on the back surface of the pad. It is provided in.
  • the supporter portion has a plurality of connection bands, and the position is fixed with respect to the internal organ surface by surrounding the internal organs with the connection bands. It is characterized by.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, a hook is provided at a distal end portion of the connection band.
  • a cord is provided at a distal end portion of the connection band, and adjustment of tightening of the cord to adjust fixation of the supporter portion to the internal organ. It is characterized by.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the supporter part includes an adjustment part for adjusting the adhesion strength to the internal organ.
  • the catheter according to the present invention is characterized in that, in the above invention, the adjusting section is a plurality of balloons arranged in a distributed manner.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the adjustment portion is a plurality of openings formed in a dispersed manner.
  • the back surface of the supporter portion is formed with a close contact area that is in close contact with the surface of the internal organ and a non-adhesion area that is not in close contact with the surface of the internal organ.
  • the plurality of openings are provided in the non-contact region.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the surface of the close contact area is formed smoothly, and the surface of the non-contact area is formed rougher than the close contact area.
  • the catheter according to the present invention is the above-described invention, wherein the one or more openings are not located on the back surface of the supporter part, apart from the non-contact area where the one or more openings are located.
  • a flow path connecting the region is formed.
  • the catheter according to the present invention is characterized in that, in the above invention, the flow path is a groove formed on a back surface of the supporter portion.
  • the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the supporter portion. It is characterized by that.
  • the catheter according to the present invention is characterized in that, in the above invention, the flow path is a lumen formed inside the supporter portion.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a lumen formed inside the supporter portion, and the inside of the lumen has a porous shape.
  • the catheter according to the present invention further includes a spacer disposed between the back surface of the supporter portion and the surface of the internal organ, and the spacer is formed on the side wall and the supporter side.
  • An upper opening and a lower opening formed on the internal organ side, and at least a surface of the internal organ covered by the lower opening serves as the non-contact region.
  • the catheter according to the present invention includes a connection member that connects the conduit and the supporter portion, and the conduit and the supporter portion are detachably coupled by the connection member. It is characterized by that.
  • the catheter according to the present invention is characterized in that, in the above invention, the back surface of the supporter is in close contact with the surface of the internal organ by intermolecular force.
  • the catheter according to the present invention is the catheter according to the above invention, wherein the supporter portion is connected to the duct on the duct side and has a cross-sectional area wider than the cross-sectional area of the internal passage of the duct, It has the connection part which forms the empty room which contact
  • the catheter according to the present invention is characterized in that, in the above invention, the supporter part is provided with an air vent valve.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the supporter part is formed of a member having air permeability.
  • the pad is prohibited or permitted from one state in which the pad receives energy transmitted from the outside of the pad and permits or prohibits the flow of the drug in the pad. And a gate mechanism for transitioning to the other state.
  • the energy is energy that propagates into the catheter via the catheter surface.
  • the state transition of the gate mechanism is caused by the energy that has entered from the catheter surface around the gate mechanism.
  • Such energy is, for example, wave energy irradiated from the outside.
  • wave energy is energy that travels in the form of waves, including but not limited to sound waves, ultrasonic waves, electromagnetic waves (including radio waves, infrared rays, visible light, ultraviolet rays), shock waves, and mechanical vibrations. Pulses are also included in the wave. Application of such energy causes destruction, deformation (melting, expansion, etc.) of the members of the gate mechanism, and as a result, a transition state of the gate mechanism occurs.
  • the gate mechanism has a member to be destroyed that is destroyed by the irradiation of the wave energy, and the state is changed by the destruction of the member to be destroyed. It is characterized by.
  • the member to be destroyed is a member that prohibits the flow of the medicine
  • the gate mechanism receives the irradiation of the wave energy and destroys the member to be destroyed.
  • the medicine flow is changed from a state in which the medicine flow is prohibited to a state in which the medicine is allowed to flow.
  • the member to be destroyed is a member that allows the flow of the medicine, and is biased in a direction to move to a position that prohibits the flow of the medicine
  • the gate mechanism has an urging member that is prevented from moving by a breaking member, and the gate mechanism inhibits the urging member from flowing the drug by receiving the wave energy and destroying the member to be broken. It is moved to a position to make a transition from a state in which the medicine flow is allowed to a state in which it is prohibited.
  • the catheter according to the present invention is characterized in that, in the above invention, the member to be destroyed is ceramic.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the gate mechanism has a deformable member that is deformed by receiving the energy, and the state is changed by deformation of the deformable member.
  • the gate mechanism makes a transition from a state in which the flow of the medicine is prohibited to a state in which the flow of the medicine is permitted by receiving the energy and deforming the deformable member.
  • the deformation member is a member that allows the flow of the medicine, and is biased in a direction to move to a position that prohibits the flow of the medicine, and the deformation member And the gate mechanism moves the urging member to a position where the flow of the medicine is prohibited by the deformation of the deforming member upon receiving the energy. It is characterized by making a transition from a state in which the flow is allowed to a state in which it is prohibited.
  • the deformable member is a thermoplastic plastic.
  • the wave energy is a combination of one or more of an electromagnetic wave including a sound wave, an ultrasonic wave, an infrared ray and visible light, including a high frequency, a shock wave, and a mechanical vibration. It is characterized by energy.
  • the catheter according to the present invention is characterized in that, in the above invention, the wave energy is energy output from a laser device.
  • the wave energy is energy output from an ultrasonic transducer.
  • the wave energy is energy output from a shock wave generator.
  • the catheter according to the present invention is the above-described invention, wherein the pad has a drug discharge unit for discharging the drug in the pad, the drug discharge unit and the gate mechanism are plural, and at least one drug
  • the ejection unit is characterized in that the gate mechanism makes a transition between an active state in which the medicine is ejected and an inactive state in which the medicine is not ejected.
  • the gate mechanism is provided inside the sheet-like pad.
  • the catheter according to the present invention is characterized in that, in the above invention, the pad has an osmotic membrane, and the drug is discharged into the body through the osmotic membrane.
  • the catheter according to the present invention is characterized in that, in the above-mentioned invention, the pad has an opening, and the drug is discharged into the body through the opening.
  • a puncture needle is provided at a distal end of the conduit, and the drug is discharged into the body through the puncture needle, and the gate mechanism is connected to the conduit. It is provided in the middle.
  • the conduit has a branch portion that branches from one passage on the drug supply side to a plurality of passages, and the gate mechanism is connected to the branch portion.
  • a plurality of at least one passage branched from the branching portion performs a state transition between an active state in which a drug is caused to flow through the passage and an inactive state in which the agent is not caused to flow through the passage by the gate mechanism.
  • the catheter according to the present invention is characterized in that, in the above invention, the branch portion is a mesh-like passage.
  • the pad forms one or more openings that communicate with the internal passage of the duct, and the total area of the one or more openings is Since it is made wider than the cross-sectional area of the internal passage, it is possible to easily and reliably administer the drug to a predetermined region near the surface of the internal organ.
  • FIG. 1 is a schematic diagram showing a state where the catheter according to the first embodiment of the present invention is applied to a human body.
  • FIG. 2 is a schematic view showing an installation state of the catheter shown in FIG. 1 in the vicinity of the internal organ.
  • FIG. 3 is a plan view showing an installed state of the catheter shown in FIG. 1 in the vicinity of the internal organ.
  • FIG. 4 is a cross-sectional view showing a configuration of a modified example of the catheter shown in FIG.
  • FIG. 5 is a plan view showing a modification of the sheet portion of the catheter shown in FIG.
  • FIG. 1 is a schematic diagram showing a state where the catheter according to the first embodiment of the present invention is applied to a human body.
  • FIG. 2 is a schematic view showing an installation state of the catheter shown in FIG. 1 in the vicinity
  • FIG. 8 is a cross-sectional view showing a configuration of a modified example of the flow path of the catheter shown in FIG.
  • FIG. 9 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG.
  • FIG. 10 is a cross-sectional view illustrating a configuration of a modified example of the flow path of the catheter illustrated in FIG. 6.
  • FIG. 11 is a schematic diagram showing an installation mode of the catheter according to the second embodiment of the present invention.
  • FIG. 12 is a schematic diagram showing a configuration of a modified example of the spacer of the catheter according to the second embodiment of the present invention.
  • FIG. 13 is a schematic diagram showing a configuration of a modification of the catheter spacer according to the second embodiment of the present invention.
  • FIG. 14 is a schematic diagram showing a state in which the catheter according to the third embodiment of the present invention is applied to a human body.
  • FIG. 15 is a schematic diagram showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ.
  • FIG. 16 is a plan view showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ.
  • FIG. 17 is a cross-sectional view showing a configuration of a modified example of the catheter shown in FIG.
  • FIG. 18 is a perspective view showing a modification of the supporter unit shown in FIG.
  • FIG. 19 is a perspective view showing a modification of the supporter unit shown in FIG.
  • FIG. 20 is a perspective view showing a modification in which a plurality of balloons are provided on the supporter unit shown in FIG.
  • FIG. 21 is a cross-sectional view showing a deformed state of the balloon shown in FIG.
  • FIG. 22 is a perspective view showing a modified example in which a plurality of openings are formed in the supporter part shown in FIG.
  • FIG. 23 is a plan view showing a modification of the supporter portion of the catheter shown in FIG.
  • FIG. 26 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG.
  • FIG. 27 is a cross-sectional view showing a configuration of a modified example of the flow path of the catheter shown in FIG. FIG.
  • FIG. 28 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG.
  • FIG. 29 is a schematic diagram showing an installation mode of the catheter according to the fourth embodiment of the present invention.
  • FIG. 30 is a schematic diagram showing a configuration of a modified example of the spacer of the catheter according to the fourth embodiment of the present invention.
  • FIG. 31 is a schematic diagram showing a configuration of a modification of the catheter spacer according to the fourth embodiment of the present invention.
  • FIG. 32 is a schematic diagram illustrating a state in which the catheter according to the fifth embodiment of the present invention is applied to a human body.
  • FIG. 33 is a view of the drug discharge portion of the catheter shown in FIG. 32 as seen from the back side.
  • FIG. 33 is a view of the drug discharge portion of the catheter shown in FIG. 32 as seen from the back side.
  • FIG. 34 is an exploded perspective view showing the configuration of the medicine discharge section of the catheter shown in FIG.
  • FIG. 35 is a perspective view showing the configuration of the second gate mechanism.
  • FIG. 36 is a perspective view showing the configuration of the first gate mechanism.
  • FIG. 37 is a schematic diagram showing the operation of the first gate mechanism.
  • FIG. 38 is a schematic diagram showing an example of a mechanism for supplying energy to the gate mechanism from the outside via the surface of the catheter.
  • FIG. 39 is a schematic diagram showing an example of a mechanism for supplying energy to the gate mechanism from the outside via the surface of the catheter.
  • FIG. 40 is a schematic view of Modification 1 of the medicine ejection unit viewed from the back side.
  • FIG. 41 is a schematic diagram of Modification 2 of the medicine ejection unit viewed from the back side.
  • FIG. 42 is a perspective view showing a configuration of Modification Example 3 of the catheter.
  • FIG. 43 is an exploded perspective view showing the configuration of the gate mechanism of Modification 4 of Embodiment 5 of the present invention.
  • FIG. 44 is a diagram illustrating the operation of the gate mechanism shown in FIG.
  • FIG. 1 is a schematic diagram showing a state where the catheter according to the first embodiment of the present invention is applied to a human body.
  • FIG. 2 is a schematic diagram showing an installed state of the catheter shown in FIG. 1 in the vicinity of the internal organ.
  • FIG. 3 is a plan view showing an installation state of the catheter shown in FIG. FIG. 1 shows a case where, for example, about several tens ml of anticancer drug or the like is continuously and intensively discharged over a long period of about one week on the surface of a body organ 4 such as the liver for planned administration.
  • medical agent here contains a liquid and a gel-form chemical
  • the catheter 10 has a tube (pipe) 2 and a sheet portion 1.
  • the tube 2 is connected to a drug injection device 3 attached to the body surface 6, and the sheet portion 1 corresponding to the pad of the present invention is in close contact with the surface of the internal organ 4 supported by the organ supporting tissue 5 in the body. It is fixed to the internal organ 4.
  • the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week.
  • the medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10.
  • the medicine feeding device 3 into the body through the tube 2, and the medicine diffuses from the opening 12 provided on the back surface of the sheet portion 1 to a predetermined range on the back surface side of the sheet portion 1. And absorbed by the internal organ 4 from its surface.
  • medical agent injection apparatus 3 does not need to be attached to the body surface 6,
  • positioned apart from the body are possible.
  • the sheet portion 1 is a sheet-like material made of a flexible biocompatible material, such as a PVDC (polyvinylidene chloride) film, a polyethylene film, or silicon rubber.
  • the tube 2 extends from the surface of the sheet portion 1 and is formed of a flexible biocompatible material such as polyethylene.
  • an opening 12 communicating with the internal passage of the tube 2 is formed on the back surface of the sheet portion 1.
  • a connecting portion 11 is provided on the sheet portion 1 side of the tube 2, and an empty chamber 23 surrounded by the connecting portion 11 and the organ surface 8 of the internal organ 4 is formed.
  • the opening 12 below the vacant chamber 23 is in contact with the region E2 of the organ surface 8 that is the surface of the internal organ 4 in an area wider than the cross-sectional area of the internal passage of the tube 2.
  • the back surface of the peripheral portion excluding the connecting portion 11 of the sheet portion 1 is formed smoothly, forms a close contact region 21, and is in close contact with the region E 1 of the body organ 4.
  • the mucous membrane 9 on the surface of the internal organ 4 promotes close contact with the close contact region 21.
  • the back surface of the connection part 11 is made into the rough surface, for example, it is preferable that it is a porous material, for example, and it becomes easy to form the empty room 23 by this.
  • the upper part of the opening 12 becomes a non-contact region 22 that does not adhere to the organ surface 8, and a vacancy 23 is formed, and the periphery of the vacancy 23 adheres closely to the organ surface 8. It becomes area 21.
  • the medicine 7 introduced from the medicine feeding device 3 through the tube 2 flows into the vacant chamber 23 formed inside the connecting portion 11.
  • the drug 7 that has flowed into the vacant chamber 23 penetrates and fills the vacant chamber 23 and is absorbed into the internal organ 4 from the region E2 (opening 12) in contact with the organ surface 8.
  • the medicine 7 is administered from the region E2 (opening 12) of the organ surface 8 having an area larger than the cross section of the internal passage of the tube 2, and the catheter 10 is closely fixed to the body organ 4, the comparison is made. Stable drug administration can be easily performed over a long period of time.
  • the adhesion region 21 is, for example, a polymer composition in which 10 to 100 parts by weight of a hydrogenated diene block copolymer is blended with 100 parts by weight of an epoxidized diene block copolymer. You may make it use a thing.
  • the close contact between the sheet portion 1 and the internal organ 4 is not limited to intermolecular force, and may be realized by applying gel at the close contact portion, adhering with sutures, fibrin glue or the like.
  • the tube 2 and the seat portion 1 can be detachably attached by connecting portions 30a and 30b (30) realized by a fluid socket or a fluid outlet provided at each end portion. It may be.
  • an air vent valve 31 for venting the air in the empty chamber 23 may be provided in the connecting portion 11.
  • the air vent valve 31 is provided with a filter through which air can pass to the outside but no medicine or the like can pass.
  • the air remaining in the vacant chamber 23 is pressed by the inflow of the drug 7, but the internal air is released to the outside by the air vent valve 31, so that the drug can be reliably administered. it can.
  • the material of the seat part 1 or the connecting part 11 may be formed of a breathable material through which only air can pass.
  • the non-contact region 22 is a closed region surrounded by the contact region 21, but not limited thereto, as shown in FIG.
  • An opening region 22 a that communicates with the outside may be provided in a part of the region 22.
  • the medicine 7 that has flowed into the vacant room 23a corresponding to the vacant room 23 is not in a pressurized state in the vacant room 23a, and the medicine 7 can be smoothly introduced through the tube 2 by releasing the pressure. .
  • the amount of the drug 7 to be introduced is very small, and by adjusting the dose corresponding to the absorption of the drug into the body organ 4, it is possible to prevent the drug from being greatly administered beyond the non-contact region 22. .
  • the medicine 7 may spread beyond the non-contact region 22.
  • the non-contact regions 22b and 22c may be formed in different regions in the sheet portion 1 to provide the vacancies 23b and 23c.
  • the opening 12 on the tube 2 side is disposed in one non-contact area 22b, and a flow path 32 communicating with each other is provided between the non-contact areas 22b and 22c.
  • the flow path 32 is realized, for example, by setting a flow path forming region 33 on the back surface of the sheet portion 1 as a material having a rough surface, as shown in FIG.
  • This flow path forming region 33 is in a state of floating from the organ surface 8, and the flow path 32 is formed.
  • bubbles 35 are formed inside the sheet portion 1 in the flow path forming region, and at least the back side of the sheet portion 1 is a convex portion, and the sheet portion 1 on the side surface of the convex portion is separated from the organ surface 8.
  • the space between the sheet portion 1 and the organ surface 8 may be separated and used as the flow path 32.
  • the formation of the bubbles 35 can be realized by making a cut corresponding to the flow path forming region inside the sheet portion 1 and injecting air into the cut. This break can be realized by forming a laminate.
  • a foaming agent that reacts with light or heat is injected into the flow path forming region inside the sheet portion 1 and is expanded by irradiating the foaming agent with light or heat to form bubbles. It may be.
  • a lumen that is a communication hole 36 may be formed in the flow path forming region in the sheet portion 1 to form the flow path 32.
  • the flow path 32 may be formed by filling the lumen with a porous material 37.
  • the porous material 37 is realized by, for example, a bundle of hollow fibers (hollow fibers) having an inner diameter of about 100 ⁇ m used for artificial kidneys and the like. This hollow fiber is realized by regenerated cellulose (such as cuprophan or acetyl cellulose), polymethyl methacrylate, polyvinyl alcohol ethylene copolymer, polysulfone, or the like.
  • the sheet portion 1 having a material such as vinyl chloride in part may be focused on ultraviolet rays along the target lumen shape to destroy the crosslinked structure of vinyl chloride, thereby forming a porous structure.
  • a spacer is further provided between the seat portion 1 and the internal organ 4 so that an empty chamber corresponding to the empty chamber 23 can be reliably formed.
  • FIG. 11 is a schematic diagram showing an installation mode of the catheter according to the second embodiment of the present invention.
  • a spacer 40 covered with the sheet part 1 is provided between the sheet part 1 and the internal organ 4.
  • This spacer 40 is for reliably forming the empty chamber 23 shown in FIG. 3, and includes a side wall 42 and a flange 41 formed on the side of the body organ 4 at the periphery of the side wall 42.
  • the side wall 42 is formed so as to surround the empty room 45 corresponding to the empty room 23.
  • the cylinder formed by the side wall 42 is formed with an upper opening 43 on the seat portion 1 side and a lower opening 44 on the body organ 4 side.
  • the upper opening 43 covers the sheet portion 1.
  • the opening on the tube 2 side of the sheet portion 1 to which the tube 2 is coupled is covered with the upper opening 43.
  • the back surface of the flange 41 has a smooth surface like the contact area 21, and is in close contact with the organ surface 8 of the internal organ 4 to fix the spacer 40.
  • the spacer 40 secures the vacant chamber 45 having a predetermined volume, and the vacant chamber 45 as a closed space is further ensured by the contact region 21 at the periphery of the seat portion 1.
  • the opening 12 of the sheet portion 1 is substantially the opening 12 a below the spacer 40.
  • the spacer 50 which can form the non-contact
  • the sheet portion 1 is covered so that the opening on the tube 2 side is located in the upper opening 53.
  • seat part 1 does not cover the side surface opening 55, you may cover it.
  • the spacer 50 forms an empty space by the upper surface on the sheet portion 1 side having the upper opening 53, the lower opening 54 formed on the body organ 4 side, the side wall 52, and the side surface opening 55.
  • a spacer 60 capable of forming the non-contact region 22 and the vacant spaces 23b and 23c corresponding to FIG. 6 may be used.
  • the sheet portion 1 is covered so that the opening on the tube 2 side is located in the upper opening 64.
  • the side walls 62 and 63 and the flange 61 are provided, and further the lower openings 65 and 67 are formed, and the space between the empty chambers 69b and 69c is formed.
  • a bridge portion 68 for connection is provided.
  • the bridge portion 68 may or may not be formed with a flow path that communicates between the vacancies 69b and 69c. Further, when the flow path is provided, the upper opening 66 may be blocked.
  • the spacers 40, 50, 60 are closely fixed to the internal organ 4 by the back surfaces of the flanges 41, 51, 61.
  • the present invention is not limited to this, and stitching, adhesion, etc.
  • the spacers 40, 50, 60 may be fixed to the internal organ 4.
  • Embodiments 1 and 2 since a sheet-like sheet portion is used as a pad, a drug can be administered over a wide range on the organ surface with a simple configuration.
  • FIG. 14 is a schematic diagram showing a state in which the catheter according to the third embodiment of the present invention is applied to a human body.
  • FIG. 15 is a schematic diagram showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ.
  • FIG. 16 is a plan view showing an installed state of the catheter shown in FIG. 14 in the vicinity of the internal organ.
  • FIG. 14 shows, for example, a case where a drug such as an anticancer drug of about several tens ml is continuously and intensively discharged over a long period of about one week on the surface of a body organ 4 such as the liver for planned administration.
  • medical agent here contains a liquid and a gel-form chemical
  • the catheter 10 has a tube 2 and a supporter 101.
  • the tube 2 is connected to the drug injection device 3 attached to the body surface 6, and the supporter unit 101 corresponding to the pad of the present invention surrounds the surface of the internal organ 4 supported in the body by the organ supporting tissue 5, The position is fixed with respect to the organ 4 surface.
  • the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week.
  • the medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10.
  • a prescribed amount of medicine is introduced from the medicine injection device 3 into the body through the tube 2, and the medicine diffuses from the opening 12 provided on the back surface of the supporter unit 101 to a predetermined range on the backside of the supporter unit 101. And absorbed by the internal organ 4 from its surface.
  • medical agent injection apparatus 3 does not need to be attached to the body surface 6,
  • positioned apart from the body are possible.
  • the supporter unit 101 is formed of a sheet-like, flexible biocompatible material, such as a PVDC (polyvinylidene chloride) film, a polyethylene film, or silicon rubber.
  • the tube 2 extends from the surface of the supporter 101 and is formed of a flexible biocompatible material such as polyethylene.
  • an opening 12 communicating with the internal passage of the tube 2 is formed on the back surface of the supporter 101.
  • a connecting part 11 is provided on the supporter 101 side of the tube 2, and an empty chamber 23 surrounded by the connecting part 11 and the organ surface 8 of the internal organ 4 is formed.
  • the opening 12 below the vacant chamber 23 is in contact with the region E2 of the organ surface 8 that is the surface of the internal organ 4 in an area wider than the cross-sectional area of the internal passage of the tube 2.
  • the supporter part 101 has at least a part of the surface in contact with the body organ 4 on the back surface formed in a smooth manner, and is in close contact with the body organ 4 by intermolecular force.
  • the back surface of the peripheral portion excluding the connecting portion 11 of the supporter portion 101 is formed smoothly, forms a close contact region 21, and is in close contact with the region E 1 of the internal organ 4.
  • the mucous membrane 9 on the surface of the internal organ 4 promotes close contact with the close contact region 21.
  • the back surface of the connection part 11 is made into the rough surface, for example, it is preferable that it is a porous material, for example, and it becomes easy to form the empty room 23 by this.
  • the upper portion of the opening 12 becomes a non-contact area 22 that does not adhere to the organ surface 8, and a vacancy 23 is formed, and the periphery of the vacancy 23 adheres closely to the organ surface 8. It becomes area 21.
  • the medicine 7 introduced from the medicine feeding device 3 through the tube 2 flows into the vacant chamber 23 formed inside the connecting portion 11.
  • the drug 7 that has flowed into the vacant chamber 23 penetrates and fills the vacant chamber 23 and is absorbed into the internal organ 4 from the region E2 (opening 12) in contact with the organ surface 8.
  • the medicine 7 is administered from the region E2 (opening 12) of the organ surface 8 having an area larger than the cross section of the internal passage of the tube 2, and the catheter 10 is closely fixed to the body organ 4, the comparison is made. Stable drug administration can be easily performed over a long period of time.
  • the adhesion region 21 is, for example, a polymer composition in which 10 to 100 parts by weight of a hydrogenated diene block copolymer is blended with 100 parts by weight of an epoxidized diene block copolymer. You may make it use a thing.
  • the close contact between the supporter 101 and the internal organ 4 is not limited to the intermolecular force, and may be realized by applying gel at the close contact portion, adhering by suturing, fibrin glue or the like.
  • connection between the tube 2 and the supporter 101 is made detachable by connecting portions 30a and 30b (30) realized by a fluid socket or a fluid outlet provided at each end. It may be.
  • an air vent valve 31 for venting the air in the empty chamber 23 may be provided in the connecting portion 11.
  • the air vent valve 31 is provided with a filter through which air can pass to the outside but no medicine or the like can pass.
  • the air remaining in the vacant chamber 23 is pressed by the inflow of the drug 7, but the internal air is released to the outside by the air vent valve 31, so that the drug can be reliably administered. it can.
  • the supporter 101 or the connecting part 11 may be made of a breathable material through which only air can pass.
  • the supporter unit 101 shown in FIG. 14 surrounds the surface of the internal organ 4 by fitting the internal organ 4 into the internal organ 4 from one end of the internal organ 4, but as shown in FIG. It is preferable to provide the connecting bands 101a to 101e.
  • a male and female hook 111 is provided at the corresponding distal end of each of the connecting bands 101a to 101e, and the position of the internal organ 4 is fixed by the hook 111 after the surface of the internal organ 4 is covered. In this case, even if the organ supporting tissue 5 is present, the position of the supporter 101 can be easily fixed with respect to the internal organ 4.
  • the position of the supporter 101 may be fixed with respect to the internal organ 4 by connecting the distal ends of the connecting bands 101a to 101e to each other using the cord 112.
  • the cord 112 includes a string, a thread, a wire, and the like.
  • the balloons 103 distributed in the supporter unit 101 may be formed.
  • the balloon 103 is filled with a fluid 104 such as air or physiological saline, and the presence of the balloon 103 can increase the fixing strength of the supporter 101 to the internal organ 4. it can.
  • the fixation strength is adjusted by puncturing the desired balloon 103 with a puncture needle 105 or the like to break the balloon 103 and causing the fluid 104 in the balloon 103 to flow out.
  • the fixing strength can be reduced.
  • the balloon 103 may be newly formed by blowing fluid with the puncture needle 105 or the like and closing the puncture portion.
  • the fixing strength is adjusted by providing openings 106 dispersedly arranged in the supporter part 101 and forming a cut part 107 by making a cut between the adjacent openings 106. It may be.
  • the non-contact region 22 is a closed region surrounded by the contact region 21, but not limited to this, as shown in FIG.
  • An opening region 22 a that communicates with the outside may be provided in a part of the region 22.
  • the medicine 7 that has flowed into the vacant room 23a corresponding to the vacant room 23 is not in a pressurized state in the vacant room 23a, and the medicine 7 can be smoothly introduced through the tube 2 by releasing the pressure. .
  • the amount of the drug 7 to be introduced is very small, and by adjusting the dose corresponding to the absorption of the drug into the body organ 4, it is possible to prevent the drug from being greatly administered beyond the non-contact region 22. .
  • the medicine 7 may spread beyond the non-contact region 22.
  • the non-contact regions 22b and 22c may be formed in different regions in the supporter 101 to provide the vacancies 23b and 23c.
  • the opening 12 on the tube 2 side is disposed in one non-contact area 22b, and a flow path 32 communicating with each other is provided between the non-contact areas 22b and 22c.
  • the flow path 32 is realized by setting a flow path forming region 33 on the back surface of the supporter 101 as a material having a rough surface. This flow path forming region 33 is in a state of floating from the organ surface 8, and the flow path 32 is formed.
  • bubbles 35 are formed inside the supporter part 101 in the flow path forming region, and at least the back side of the supporter part 101 is a convex part, and the supporter part 101 on the side surface of the convex part is separated from the organ surface 8.
  • the space between the supporter 101 and the organ surface 8 may be separated and used as the flow path 32.
  • the formation of the bubbles 35 can be realized by making a cut corresponding to the flow path forming region inside the supporter 101 and injecting air into the cut. This break can be realized by forming a laminate.
  • a foaming agent that foams in response to light or heat is injected into the flow path forming region inside the supporter 101, and the foaming agent is expanded by irradiating light or heat to form bubbles. It may be.
  • a lumen that is a communication hole 36 may be formed in the flow path forming region in the supporter 101 to form the flow path 32.
  • the lumen 32 may be filled with a porous material 37 to form the flow path 32.
  • the porous material 37 is realized by, for example, a bundle of hollow fibers (hollow fibers) having an inner diameter of about 100 ⁇ m used for artificial kidneys and the like. This hollow fiber is realized by regenerated cellulose (such as cuprophan or acetyl cellulose), polymethyl methacrylate, polyvinyl alcohol ethylene copolymer, polysulfone, or the like.
  • the supporter 101 having a part of a material such as vinyl chloride may focus on ultraviolet rays along a target lumen shape to destroy the crosslinked structure of vinyl chloride, thereby forming a porous structure.
  • a spacer is further provided between the supporter 101 and the internal organ 4 so that a vacancy corresponding to the vacancy 23 can be reliably formed.
  • FIG. 29 is a schematic diagram showing an installation mode of the catheter according to the fourth embodiment of the present invention.
  • a spacer 40 covered with the supporter unit 101 is provided between the supporter unit 101 and the internal organ 4.
  • This spacer 40 is for reliably forming the empty space 23 shown in FIG. 16, and has a side wall 42 and a flange 41 formed on the side of the body organ 4 at the periphery of the side wall 42.
  • the side wall 42 is formed so as to surround the empty room 45 corresponding to the empty room 23.
  • An upper opening 43 on the supporter 101 side and a lower opening 44 on the body organ 4 side are formed in the cylinder formed by the side wall 42.
  • the upper opening 43 covers the supporter part 101.
  • the opening on the tube 2 side of the supporter part 101 to which the tube 2 is coupled is covered with the upper opening 43.
  • the back surface of the flange 41 has a smooth surface like the contact area 21, and is in close contact with the organ surface 8 of the internal organ 4 to fix the spacer 40.
  • the spacer 40 ensures a vacant chamber 45 having a predetermined volume, and the vacant chamber 45 as a closed space is further ensured by the contact region 21 at the periphery of the supporter 101.
  • the opening 12 of the supporter portion 101 is substantially the opening 12 a below the spacer 40.
  • the vacant chamber 45 can be reliably ensured, and the medicine administration region can be reliably widened through the opening 12a.
  • the instability of the region boundary in which a part of the non-contact region 22 changes to the contact region 21 or a part of the contact region 21 changes to the non-contact region 22 with time is reduced, and stable.
  • the necessary non-contact area 22 can be secured.
  • the spacer 50 which can form the non-contact
  • the supporter 101 is covered so that the opening on the tube 2 side is located in the upper opening 53. Further, the supporter unit 101 preferably does not cover the side opening 55, but may cover it.
  • the spacer 50 forms an empty space by the upper surface on the supporter 101 side having the upper opening 53, the lower opening 54 formed on the body organ 4 side, the side wall 52, and the side surface opening 55.
  • the supporter unit 101 is covered such that the opening on the tube 2 side is located in the upper opening 64.
  • the side walls 62 and 63 and the flange 61 are provided, and further the lower openings 65 and 67 are formed, and the space between the empty chambers 69b and 69c is formed.
  • a bridge portion 68 for connection is provided.
  • the bridge portion 68 may or may not be formed with a flow path that communicates between the vacancies 69b and 69c. Further, when the flow path is provided, the upper opening 66 may be blocked.
  • the spacers 40, 50, 60 are tightly fixed to the internal organ 4 by the back surfaces of the flanges 41, 51, 61.
  • the present invention is not limited to this, and stitching, adhesion, etc.
  • the spacers 40, 50, 60 may be fixed to the internal organ 4.
  • the support portion functioning as a supporter for winding the body organ is used as the pad, it is possible to stably and reliably administer the drug to the organ surface.
  • FIG. 32 is a schematic diagram illustrating a state in which the catheter according to the fifth embodiment of the present invention is applied to a human body.
  • FIG. 33 is a view of the drug discharge portion of the catheter shown in FIG. 32 as viewed from the internal organ side.
  • FIG. 34 is an exploded perspective view of the medicine discharge section of the catheter shown in FIG. FIG. 32 shows a case where, for example, a planned dosing is performed by continuously and intensively discharging a drug such as an anticancer drug of about several tens of ml to the surface of a body organ 4 such as the liver over a long period of about one week.
  • medical agent here contains a liquid and a gel-form chemical
  • the catheter 10 includes a tube 2 that is a drug passage and a sheet-like drug discharge unit 201.
  • the tube 2 is connected to the medicine injection device 3 attached to the body surface 6 and is connected to the medicine ejection unit 201 via the connector 216a.
  • the drug discharge unit 201 corresponds to the pad of the present invention, is in close contact with the surface of the internal organ 4 supported in the body by the organ support tissue 5, and is fixed to the internal organ 4.
  • the drug to be supplied is penetrated into the body organ 4 surface.
  • the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week.
  • the medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10. That is, a prescribed amount of medicine is introduced from the medicine injection device 3 into the body through the tube 2, and the medicine diffuses from the back surface of the medicine ejection section 201 to a predetermined range to be selected, and the surface of the body organ 4 Is absorbed from.
  • medical agent injection apparatus 3 does not need to be attached to the body surface 6, For example, the structure embedded in a body and the structure arrange
  • the medicine ejection unit 201 has a three-layer structure including an upper layer 213, an intermediate layer 214, and a lower layer 215, and is bonded to each other.
  • the intermediate layer 214 is sandwiched between the upper layer 213 and the lower layer 215 and is made of a flexible biocompatible material such as silicon rubber, and is preferably a thick layer of 0.5 mm to 5 mm.
  • the upper layer 213 is made of a flexible biocompatible material, such as polyethylene, and is thinner than the intermediate layer 214, preferably a layer having a thickness of 0.05 mm to 0.3 mm.
  • the lower layer 215 is made of, for example, polysulfone, and is a flexible and biocompatible material that allows a drug to permeate.
  • the lower layer 215 is thinner than the intermediate layer 214, and preferably has a thickness of 0.05 mm to 0.3 mm.
  • the upper layer 213 has a protruding portion 217 from which the thin film is drawn to the tube 2 side.
  • a connector 216b is provided at the tip of the projecting portion 217, and is connected to the tube 2 by connecting the connector 216a and the connector 216b. That is, the connection between the connectors 216a and 216b allows the opening at the tip of the protrusion 217 to communicate with the internal passage of the tube 2.
  • a first opening 207, a second opening 208, and a flow path 209 communicating between the first opening 207 and the second opening 208 are formed inside the intermediate layer 214.
  • a protrusion 217 is disposed in the opening region of the first opening 207.
  • the first gate mechanism 211 that permits the flow of the drug in the initial state and prohibits the flow of the drug by receiving energy from the outside, and prohibits the flow of the drug in the initial state
  • a second gate mechanism 212 that accepts the energy of the medicine and permits the flow of the medicine. Note that only one of the first gate mechanism 211 and the second gate mechanism 212 may be provided. For convenience of explanation, in FIGS. 33 and 34, the first gate mechanism 211 and the second gate mechanism 212 are provided. A configuration in which both of the mechanisms 212 are arranged in the flow path 209 is shown.
  • the lower layer 215 may be a thin film in which only regions corresponding to the first opening 207 and the second opening 208 are opened, instead of the permeable membrane through which only the drug permeates.
  • the medicine supplied from the medicine injection device 3 is introduced into the protruding portion 217 of the upper layer 213 of the medicine ejection section 201 via the tube 2 and the connectors 216a and 216b, and further introduced into the first opening 207 of the intermediate layer 214. .
  • the drug introduced into the first opening 207 passes through the region of the lower layer 215 corresponding to the first opening 207 and permeates into the body from the surface of the internal organ 4.
  • the first gate mechanism 211 permits the flow of the medicine in the initial state, the medicine travels through the flow path 209 from the first opening 207 toward the second opening 208 side. Therefore, the second gate mechanism 212 that inhibits the flow of the drug prevents the flow of the drug, and the drug is not introduced into the second opening 208.
  • the medicine is supplied only to the surface of the internal organ 4 corresponding to the first opening 207.
  • the drug is supplied to the surface of the internal organ 4 from the corresponding region between the first opening 207 and the second gate mechanism 212 on the flow path 209, but is a linear region. The drug supply is negligible.
  • the flow path 209 includes the first opening 207 and the second flow path 209.
  • the medicine is supplied to the first opening 207 via the flow path 209, and the region of the lower layer 215 corresponding to the second opening 208 is communicated with the opening 208. It penetrates and is supplied to the surface of the internal organ 4. That is, the second opening 208 transitions from an inactive state in which medicine ejection is prohibited to an active state in which medicine is ejected. In this case, the medicine is also supplied from the surface of the internal organ 4 corresponding to the first opening 207.
  • the flow path 209 includes the first opening 207 and the second opening 208.
  • the drug supplied to the first opening 207 is supplied from the region of the lower layer 215 corresponding to the first opening 207 to the surface of the body organ 4 only. That is, the second opening 208 transitions from an active state in which the medicine is discharged to an inactive state in which the discharge of the medicine is prohibited. In this way, as a result, the dynamic change of the positional distribution of the drug amount can be easily performed.
  • the second gate mechanism 212 is a silica-alumina that breaks into a pair of recesses 219 provided facing the side surface of the flow path 209 by an ultrasonic shock wave or the like from the outside.
  • a cylindrical pellet 218 formed of ceramics realized by calcium phosphate ceramics is inserted. The pellet 218 closes the flow path 209 by being inserted into the recess 219 and locked to the flow path 209.
  • the pellet 218 is a member to be destroyed that is destroyed when receiving energy through the surface of the catheter 10 from the outside. Therefore, when the pellet 218 is destroyed, the second gate mechanism 212 allows the drug flow from a state in which the drug flow is prohibited.
  • the first gate mechanism 211 is formed with a recess 223 that locks the columnar pellet 220 on one side of the flow path 209 and at the recess 223.
  • a space 224 that is a recess for accommodating the elastic piece 225 is formed on the opposite side portion.
  • the elastic piece 225 is realized by a metal such as steel having a biocompatible coating, for example, and one end is cantilevered in the vicinity of the space 224 on the side of the flow path 209 in which the space 224 is formed. The other end is pressed by the pellet 220 and stored in the space 224.
  • the pellet 220 is formed with a communication hole 221 having an opening 222 penetrating from one side surface to the other side surface, and the pellet 220 is inserted into the flow channel 209 so that the communication direction of the communication hole 221 matches the flow direction of the flow channel 209. And locked.
  • the elastic piece 225 blocks the flow path 209 with its own elastic force and inhibits the flow of the drug when the pellet 220 is not present.
  • the first gate mechanism 211 is in a state where the elastic piece 225 presses the pellet 220 toward the concave portion 223 while the pellet 220 is locked to the flow path 209. It is installed to become.
  • the elastic piece 225 is an urging member that is urged by its own elastic force so as to move to a position where the flow path 209 is blocked and the flow of the medicine is prohibited. Therefore, instead of the elastic piece 225, a biasing member that biases by an extension spring or the like may be used.
  • the pellet 220 is formed of a member to be destroyed realized by ceramics or the like that breaks when receiving energy through the surface of the catheter 10.
  • the flow of the medicine is allowed.
  • the elastic piece 225 becomes elastic as shown in FIG. 37 (b). It moves to a position where the flow path 209 is closed by force, and closes the flow path 209.
  • the pellets 218 and 220 are not limited to ceramics, and may be realized with various materials such as glass and plastic in relation to energy supplied from the outside.
  • various wave energies such as sound waves, ultrasonic waves, electromagnetic waves including infrared rays and visible light, shock waves, and mechanical vibrations can be used.
  • it may be thermal energy transmitted by conduction. Heat can also be transmitted as wave energy by infrared rays.
  • pellets 218 and 220 may be deformable members that are deformed by external energy.
  • it may be a thermoplastic plastic that is deformed by thermal energy.
  • the pellet 218 may be formed by a balloon having a fluid such as air inside.
  • This balloon may be realized by bubbles.
  • a reversible gate mechanism that opens and closes the flow path 209 by expanding and contracting the fluid in the balloon without destroying the balloon may be used.
  • FIG. 38 is a schematic diagram illustrating a state in which wave energy such as a sound wave, an ultrasonic wave, and a shock wave is applied from outside the body.
  • the wave energy generator 231 generates wave energy based on the signal supplied from the driver 232 via the signal line 233.
  • the wave energy is collected by the wave lens 230 provided on the side of the gate mechanisms 218 and 220 of the wave energy generator 231 and is irradiated to the gate mechanisms 218 and 220.
  • the wave energy generation device 231 is realized by an ultrasonic transducer, a shock wave generation device, a sound wave source, or the like.
  • the energy generation unit of the energy generation device 235 is inserted into the body through the internal channel of the rigid endoscope 234, the energy generation unit is positioned in the vicinity of the gate mechanisms 218 and 220, and the energy generation unit to the gate mechanism 218. , 220 is supplied with energy.
  • the energy generation device 235 generates energy from the energy generation unit based on a signal supplied from the driver 240 via the signal line 241.
  • the energy for example, laser light by holmium / YAG laser, ultrasonic wave, high frequency, mechanical vibration, or the like is used. Of course, it may be heat transmitted by conduction.
  • FIG. 40 is a view of a medicine ejection unit 250, which is Modification 1 of the medicine ejection unit 201, as viewed from the back side.
  • the medicine ejection unit 201 has one second opening 208, but the medicine ejection unit 250 has a plurality of second openings 252.
  • the first opening 251 corresponding to the first opening 207 and the four second openings 252 are provided in a radial pattern, and each of the four flow paths is provided between the first opening 251 and the second opening 252.
  • a channel 209 is provided, and each channel 209 is provided with a first gate mechanism 211 and a second gate mechanism 212, respectively, similarly to the medicine ejection unit 201.
  • the lower layer 215 is not an osmotic membrane, but has an opening only in a region corresponding to the first opening 251 and the second opening 252.
  • the medicine in the initial state, the medicine is supplied only in the region corresponding to the first opening 261.
  • the drug supply distribution can be dynamically changed in detail.
  • a gate mechanism 212 may be appropriately combined, or a gate mechanism that performs reversible opening and closing may be used.
  • the gate mechanism is not limited to the node and may be provided on the flow path 209.
  • the flow path 209 is formed between the first opening and the second opening.
  • the first opening or the second opening is formed in an empty area of the flow path 209. It is preferable to arrange the openings densely.
  • a third opening is further provided, a flow path connecting the second opening and the third opening is further provided, and a gate mechanism is provided in the flow path so that the medicine supply distribution can be controlled more finely. Is preferred.
  • a plurality of gate mechanisms that open and close by different kinds of energy may be provided in one flow path 209.
  • a gate mechanism that is broken by a shock wave and a gate mechanism that is broken by heat may be provided.
  • the flow path 209 can be opened and closed in multiple stages, and the drug supply distribution can be dynamically changed more finely.
  • the drug is supplied directly to the surface of the internal organ 4 mainly using the sheet-like drug discharge units 201, 250, and 260.
  • a gate mechanism is provided. That is, as shown in FIG. 42, the catheter 270 of this modification 3 is provided with a branch unit 273 in the middle of the tube 2, and a plurality of tubes 271 are connected to the discharge side of the branch unit 273.
  • the medicine injection device 3 side of the branch unit 273 is connected by connectors 274a and 274b.
  • a puncture needle 272 having an opening for discharging a drug is connected to each tip of the plurality of tubes 271.
  • the branch unit 273 is installed on the body surface, and the puncture needles 272 connected through the tubes 271 are punctured into a plurality of internal organs to be treated and distributed.
  • the tubes 271 in the branch unit 273 are branched and connected through a common tube 275, and gate mechanisms 211 and 212 are provided on each tube 271, and on / off of each tube 271 is selectively controlled.
  • the dynamic medicine supply distribution can be easily changed.
  • FIG. 43 is an exploded perspective view showing the configuration of the gate mechanism of Modification 4 of Embodiment 5 of the present invention.
  • FIG. 44 is a diagram showing the operation of the gate mechanism shown in FIG. As shown in FIG. 43, this gate mechanism has a slider housing portion 305a, in which a metal slider 300 having an opening 301 corresponding to the cross section of the flow path 209 is formed on both sides of the flow path 209. It is slidably accommodated in 305b.
  • Slider drive chambers 303a and 303b are provided at the back of the slider accommodating portions 305a and 305b extending from the flow path 209, and magnets 304a and 304b are provided on the walls of the slider drive chambers 303a and 303b on the flow path 209 side, respectively. Is embedded.
  • balloons 302a and 302b are accommodated in the interior chambers separated from the flow path 209 of the slider drive chambers 303a and 303b, respectively.
  • the balloons 302a and 302b are made by covering a fluid such as pure water with an elastic film such as silicon rubber.
  • a fluid such as pure water
  • an elastic film such as silicon rubber.
  • the slider 300 is housed biased toward the slide housing portion 305a.
  • the opening 301 formed in the slider 300 is disposed at a position corresponding to the position of the flow path 209, and the medicine passing through the flow path 209 can freely flow through the opening 301.
  • the slider 300 is in a state in which one end thereof is attracted to the magnet 304b, and is in a stable state in which it does not move unless another force is applied.
  • the balloon 302a is cooled and the volume contracts to return to the original volume of the balloon 302a.
  • the slider 300 moves toward the slider drive chamber 303b by the attractive force of the magnet 304a. Stable when moved.
  • a gate mechanism is provided in the medicine ejection unit 201 as a pad, and the gate mechanism receives energy transmitted from the outside of the medicine ejection unit 201 to flow the medicine in the medicine ejection unit 201. Since the transition is made from one state that is allowed or allowed to the other state that is prohibited or permitted, the dose distribution can be dynamically changed according to the change in the affected area during drug administration.

Abstract

A catheter (10) to be attached to an internal organ of a mammal including a human being.  The catheter (10) is provided with a tube (2) which guides a medication from a medication supply source into the body and a sheet section (1) which is provided at the tip of the tube (2) and the rear surface of which at least partially adheres to the surface of the internal organ.  The sheet section (1) comprises apertures (12) communicating with the internal path of the tube (2), and the total area of the apertures (12) is set to be larger than the cross section area of the internal path.  As the result of this, the medication can simply and reliably be administered to a predetermined area in the vicinity of the surface of the internal organ.

Description

カテーテルcatheter
　この発明は、人間を含む哺乳類の体内臓器に取り付けられるカテーテルに関し、特に、体内臓器表面から体内臓器に薬剤を投与するカテーテルに関するものである。 The present invention relates to a catheter attached to a body organ of a mammal including human beings, and more particularly to a catheter for administering a drug from the surface of the body organ to the body organ.
　従来から、人間を含む哺乳類の体内臓器の内部に穿刺針を刺して薬剤を投与するカテーテルが知られている（特許文献１参照）。 Conventionally, a catheter that administers a drug by inserting a puncture needle into a body organ of a mammal including a human is known (see Patent Document 1).
特開平３－５７４５７号公報JP-A-3-57457 国際公開第０３／００７９８２号パンフレットWO03 / 007982 pamphlet
　従来のカテーテルは基本的に体内臓器内部の１点にのみに薬剤を投与するものであったため、ある程度の体積をもつ患部に薬剤を投与したい場合であっても、投与位置から離間した患部の部分には、あまり薬剤を行きわたらせることができなかった。 Since the conventional catheter basically administers the drug only to one point inside the internal organ, even if it is desired to administer the drug to the affected area having a certain volume, the part of the affected part separated from the administration position I wasn't able to spread the drug very much.
　特に、患部が体内臓器の表面や表面近傍に存在する場合には、穿刺針を刺す深さが不足して、穿刺針が抜けてしまう場合があり、このような場合、十分な薬剤投与を行うことができなかった。 In particular, when the affected part is present on the surface of the internal organ or in the vicinity of the surface, the depth of the puncture needle may be insufficient and the puncture needle may come off. In such a case, sufficient drug administration is performed. I couldn't.
　これに対し、このように体内臓器の表面や表面近傍に患部がある場合、薬剤をしみこませたシートやゲルを体内臓器表面に貼り付けることによって薬剤を投与していた（特許文献２参照）。 On the other hand, when there is an affected part on the surface of the internal organ or in the vicinity of the surface as described above, the drug is administered by sticking a sheet or gel soaked with the drug on the surface of the internal organ (see Patent Document 2).
　しかし、この場合、薬剤の交換や補充に開腹手術が必要であり、患者および医師にかかる負担が大きいという問題があった。また、この場合、薬剤の投与量を一定に保つことも難しかった。 However, in this case, a laparotomy is required for exchanging and replenishing the drug, and there is a problem that the burden on the patient and doctor is great. In this case, it is also difficult to keep the dose of the drug constant.
　この発明は、上記に鑑みてなされたものであって、簡易かつ確実に、体内臓器表面近傍の所定領域に薬剤を投与することができるカテーテルを提供することを目的とする。 The present invention has been made in view of the above, and an object of the present invention is to provide a catheter capable of easily and reliably administering a drug to a predetermined region near the surface of a body organ.
　上述した課題を解決し、目的を達成するために、この発明にかかるカテーテルは、人間を含む哺乳類の体内臓器に取り付けられるカテーテルであって、薬剤供給源から体内に薬剤を導く管路と、前記管路の最先端に設けられた、少なくとも裏面の一部が前記体内臓器表面に密着するパッドと、を備え、前記パッドは、前記管路の内部通路と連通する１つまたは複数の開口を形成し、前記１つまたは複数の開口の総面積は、前記内部通路の断面積より広いことを特徴とする。 In order to solve the above-described problems and achieve the object, a catheter according to the present invention is a catheter attached to a body organ of a mammal including a human, and a conduit for guiding a drug from a drug supply source into the body; A pad provided at the forefront of the duct, at least a part of the back surface of which is in close contact with the surface of the internal organ, and the pad forms one or more openings communicating with the internal passage of the duct The total area of the one or more openings is wider than the cross-sectional area of the internal passage.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッドは、柔軟なシート部であり、前記１つまたは複数の開口は、前記パッドの裏面に設けられていることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the pad is a flexible sheet portion, and the one or more openings are provided on the back surface of the pad.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部の裏面は、前記体内臓器表面に密着する密着領域と、前記体内臓器表面に密着しない非密着領域とが形成され、前記１つまたは複数の開口は、前記非密着領域に設けられることを特徴とする。 In the catheter according to the present invention, in the above invention, the back surface of the sheet portion is formed with a close contact area that is in close contact with the surface of the internal organ and a non-adhesion area that is not in close contact with the surface of the internal organ. Alternatively, the plurality of openings are provided in the non-contact region.
　また、この発明にかかるカテーテルは、上記の発明において、前記密着領域表面は平滑に形成され、前記非密着領域表面は前記密着領域よりも粗く形成されていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the surface of the close contact area is formed smoothly, and the surface of the non-contact area is formed rougher than the close contact area.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部の裏面に、前記１つまたは複数の開口が位置する非密着領域とは別に、前記１つまたは複数の開口が位置しない非密着領域が少なくとも１つ形成され、前記シート部の裏面が前記体内臓器表面に密着した状態で、前記１つまたは複数の開口が位置する非密着領域と前記１つまたは複数の開口が位置しない非密着領域とを接続する流路が形成されることを特徴とする。 Further, the catheter according to the present invention is the above-described invention, wherein the one or more openings are not positioned separately from the non-contact area where the one or more openings are positioned on the back surface of the sheet portion. A non-contact area where the one or more openings are located and a non-contact area where the one or more openings are not located in a state where at least one area is formed and the back surface of the sheet portion is in close contact with the surface of the internal organ A flow path connecting the region is formed.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記シート部の裏面に形成された溝であることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a groove formed on a back surface of the sheet portion.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記シート部内部に形成された気泡による前記シート部裏面側への突起形成によって前記シート部裏面に形成された溝であることを特徴とする。 In the catheter according to the present invention, in the above invention, the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the sheet portion. It is characterized by that.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記シート部内部に形成されたルーメンであることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-described invention, the flow path is a lumen formed in the seat portion.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記シート部内部に形成されたルーメンであって該ルーメン内が多孔形状となっていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a lumen formed inside the seat portion, and the inside of the lumen is porous.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部裏面と前記体内臓器表面との間に配設されるスペーサをさらに備え、前記スペーサは、側壁と、前記シート部側に形成される上部開口と、前記体内臓器側に形成される下部開口とを有し、少なくとも前記下部開口に覆われる前記体内臓器表面が前記非密着領域となることを特徴とする。 In the above invention, the catheter according to the present invention further includes a spacer disposed between the back surface of the sheet portion and the surface of the internal organ, and the spacer is formed on the side wall and the sheet portion side. An upper opening and a lower opening formed on the internal organ side, and at least a surface of the internal organ covered by the lower opening serves as the non-contact region.
　また、この発明にかかるカテーテルは、上記の発明において、前記管路と前記シート部とを接続する接続部材を有し、前記管路と前記シート部とは、前記接続部材によって着脱可能に連結されることを特徴とする。 In the above invention, the catheter according to the present invention includes a connection member that connects the conduit and the seat portion, and the conduit and the seat portion are detachably coupled by the connection member. It is characterized by that.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部裏面は、前記体内臓器表面と分子間力によって密着していることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the back surface of the sheet portion is in close contact with the surface of the internal organ by intermolecular force.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部は、前記管路側に前記管路と連結し、前記管路の内部通路の断面積より広い断面積をもち前記体内臓器表面と接する空室を形成する連結部を備えたことを特徴とする。 In the catheter according to the present invention, in the above invention, the seat portion is connected to the conduit on the conduit side, and has a cross-sectional area wider than the cross-sectional area of the internal passage of the conduit, It has the connection part which forms the empty room which contact | connects, It is characterized by the above-mentioned.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部は、空気抜きの弁が設けられていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the seat portion is provided with an air vent valve.
　また、この発明にかかるカテーテルは、上記の発明において、前記シート部は、通気性を有する部材で形成されていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the sheet portion is formed of a member having air permeability.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッドは、前記体内臓器を巻回してサポータの機能を有する柔軟なサポータ部であり、前記１つまたは複数の開口は、前記パッドの裏面に設けられていることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the pad is a flexible supporter part that winds around the internal organs and has a supporter function, and the one or more openings are on the back surface of the pad. It is provided in.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部は、複数の連結バンドを有し、該連結バンドで前記体内臓器を囲むことによって前記体内臓器表面に対して位置固定されることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the supporter portion has a plurality of connection bands, and the position is fixed with respect to the internal organ surface by surrounding the internal organs with the connection bands. It is characterized by.
　また、この発明にかかるカテーテルは、上記の発明において、前記連結バンドの先端部にホックが設けられていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, a hook is provided at a distal end portion of the connection band.
　また、この発明にかかるカテーテルは、上記の発明において、前記連結バンドの先端部にコードが設けられており、該コードの締め付けを調整して前記サポータ部の前記体内臓器への固着を調整することを特徴とする。 Further, in the catheter according to the present invention, in the above invention, a cord is provided at a distal end portion of the connection band, and adjustment of tightening of the cord to adjust fixation of the supporter portion to the internal organ. It is characterized by.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部は、前記体内臓器に対する固着強度を調整する調整部を備えたことを特徴とする。 Further, the catheter according to the present invention is characterized in that, in the above-mentioned invention, the supporter part includes an adjustment part for adjusting the adhesion strength to the internal organ.
　また、この発明にかかるカテーテルは、上記の発明において、前記調整部は、分散配置された複数のバルーンであることを特徴とする。 Further, the catheter according to the present invention is characterized in that, in the above invention, the adjusting section is a plurality of balloons arranged in a distributed manner.
　また、この発明にかかるカテーテルは、上記の発明において、前記調整部は、分散して形成された複数の開口であることを特徴とする。 Further, the catheter according to the present invention is characterized in that, in the above-mentioned invention, the adjustment portion is a plurality of openings formed in a dispersed manner.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部の裏面は、前記体内臓器表面に密着する密着領域と、前記体内臓器表面に密着しない非密着領域とが形成され、前記１つまたは複数の開口は、前記非密着領域に設けられることを特徴とする。 Further, in the catheter according to the present invention, in the above invention, the back surface of the supporter portion is formed with a close contact area that is in close contact with the surface of the internal organ and a non-adhesion area that is not in close contact with the surface of the internal organ. Alternatively, the plurality of openings are provided in the non-contact region.
　また、この発明にかかるカテーテルは、上記の発明において、前記密着領域表面は平滑に形成され、前記非密着領域表面は前記密着領域よりも粗く形成されていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the surface of the close contact area is formed smoothly, and the surface of the non-contact area is formed rougher than the close contact area.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部の裏面に、前記１つまたは複数の開口が位置する非密着領域とは別に、前記１つまたは複数の開口が位置しない非密着領域が少なくとも１つ形成され、前記サポータ部の裏面が前記体内臓器表面に密着した状態で、前記１つまたは複数の開口が位置する非密着領域と前記１つまたは複数の開口が位置しない非密着領域とを接続する流路が形成されることを特徴とする。 Further, the catheter according to the present invention is the above-described invention, wherein the one or more openings are not located on the back surface of the supporter part, apart from the non-contact area where the one or more openings are located. A non-contact region where the one or more openings are located and a non-contact region where the one or more openings are not located in a state where at least one region is formed and the back surface of the supporter is in close contact with the surface of the internal organ A flow path connecting the region is formed.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記サポータ部の裏面に形成された溝であることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the flow path is a groove formed on a back surface of the supporter portion.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記サポータ部内部に形成された気泡による前記シート部裏面側への突起形成によって前記シート部裏面に形成された溝であることを特徴とする。 In the catheter according to the present invention, in the above invention, the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the supporter portion. It is characterized by that.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記サポータ部内部に形成されたルーメンであることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the flow path is a lumen formed inside the supporter portion.
　また、この発明にかかるカテーテルは、上記の発明において、前記流路は、前記サポータ部内部に形成されたルーメンであって該ルーメン内が多孔形状となっていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the flow path is a lumen formed inside the supporter portion, and the inside of the lumen has a porous shape.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部裏面と前記体内臓器表面との間に配設されるスペーサをさらに備え、前記スペーサは、側壁と、前記サポータ部側に形成される上部開口と、前記体内臓器側に形成される下部開口とを有し、少なくとも前記下部開口に覆われる前記体内臓器表面が前記非密着領域となることを特徴とする。 In the above invention, the catheter according to the present invention further includes a spacer disposed between the back surface of the supporter portion and the surface of the internal organ, and the spacer is formed on the side wall and the supporter side. An upper opening and a lower opening formed on the internal organ side, and at least a surface of the internal organ covered by the lower opening serves as the non-contact region.
　また、この発明にかかるカテーテルは、上記の発明において、前記管路と前記サポータ部とを接続する接続部材を有し、前記管路と前記サポータ部とは、前記接続部材によって着脱可能に連結されることを特徴とする。 In the above invention, the catheter according to the present invention includes a connection member that connects the conduit and the supporter portion, and the conduit and the supporter portion are detachably coupled by the connection member. It is characterized by that.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部裏面は、前記体内臓器表面と分子間力によって密着していることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the back surface of the supporter is in close contact with the surface of the internal organ by intermolecular force.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部は、前記管路側に前記管路と連結し、前記管路の内部通路の断面積より広い断面積をもち前記体内臓器表面と接する空室を形成する連結部を備えたことを特徴とする。 The catheter according to the present invention is the catheter according to the above invention, wherein the supporter portion is connected to the duct on the duct side and has a cross-sectional area wider than the cross-sectional area of the internal passage of the duct, It has the connection part which forms the empty room which contact | connects, It is characterized by the above-mentioned.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部は、空気抜きの弁が設けられていることを特徴とする。 Further, the catheter according to the present invention is characterized in that, in the above invention, the supporter part is provided with an air vent valve.
　また、この発明にかかるカテーテルは、上記の発明において、前記サポータ部は、通気性を有する部材で形成されていることを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the supporter part is formed of a member having air permeability.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッド内には、前記パッドの外部から伝わるエネルギーを受けて、前記パッド内の薬剤の流れを許容または禁止する一方の状態から禁止または許容する他方の状態に遷移するゲート機構を備えたことを特徴とする。 Further, in the catheter according to the present invention, in the above invention, the pad is prohibited or permitted from one state in which the pad receives energy transmitted from the outside of the pad and permits or prohibits the flow of the drug in the pad. And a gate mechanism for transitioning to the other state.
　また、この発明にかかるカテーテルは、上記の発明において、前記エネルギーは、カテーテル表面を経由してカテーテル内に伝搬するエネルギーである。そして、前記ゲート機構の状態遷移は、前記ゲート機構周辺のカテーテル表面から侵入したエネルギーによって惹起される。このようなエネルギーは、たとえば、外部から照射される波動エネルギーであることを特徴とする。ここで、波動エネルギーとは、波動の形式で進行するエネルギーであり、音波、超音波、電磁波（電波、赤外線、可視光、紫外線を含む）、衝撃波、機械的振動を含むがこれに限定されず、パルスも波動に含まれる。このようなエネルギーの印加によって、ゲート機構の部材の破壊、変形（溶融や膨張など）等が惹起され、この結果、ゲート機構の遷移状態が起こる。 Also, in the catheter according to the present invention, in the above invention, the energy is energy that propagates into the catheter via the catheter surface. The state transition of the gate mechanism is caused by the energy that has entered from the catheter surface around the gate mechanism. Such energy is, for example, wave energy irradiated from the outside. Here, wave energy is energy that travels in the form of waves, including but not limited to sound waves, ultrasonic waves, electromagnetic waves (including radio waves, infrared rays, visible light, ultraviolet rays), shock waves, and mechanical vibrations. Pulses are also included in the wave. Application of such energy causes destruction, deformation (melting, expansion, etc.) of the members of the gate mechanism, and as a result, a transition state of the gate mechanism occurs.
　また、この発明にかかるカテーテルは、上記の発明において、前記ゲート機構は、前記波動エネルギーの照射を受けて破壊される被破壊部材を有し、該被破壊部材の破壊によって前記状態が遷移することを特徴とする。 Further, in the catheter according to the present invention, in the above invention, the gate mechanism has a member to be destroyed that is destroyed by the irradiation of the wave energy, and the state is changed by the destruction of the member to be destroyed. It is characterized by.
　また、この発明にかかるカテーテルは、上記の発明において、前記被破壊部材は、前記薬剤の流れを禁止する部材であり、前記ゲート機構は、前記波動エネルギーの照射を受けて該被破壊部材が破壊されることによって前記薬剤の流れを禁止する状態から許容する状態に遷移させることを特徴とする。 Further, in the catheter according to the present invention, in the above invention, the member to be destroyed is a member that prohibits the flow of the medicine, and the gate mechanism receives the irradiation of the wave energy and destroys the member to be destroyed. In this case, the medicine flow is changed from a state in which the medicine flow is prohibited to a state in which the medicine is allowed to flow.
　また、この発明にかかるカテーテルは、上記の発明において、前記被破壊部材は、前記薬剤の流れを許容する部材であり、前記薬剤の流れを禁止する位置に移動する方向に付勢され、前記被破壊部材によって前記移動が阻まれる付勢部材を有し、前記ゲート機構は、前記波動エネルギーの照射を受けて前記被破壊部材が破壊されることによって前記付勢部材を前記薬剤の流れを禁止する位置に移動させ、前記薬剤の流れを許容する状態から禁止する状態に遷移させることを特徴とする。 In the catheter according to the present invention, in the above invention, the member to be destroyed is a member that allows the flow of the medicine, and is biased in a direction to move to a position that prohibits the flow of the medicine, The gate mechanism has an urging member that is prevented from moving by a breaking member, and the gate mechanism inhibits the urging member from flowing the drug by receiving the wave energy and destroying the member to be broken. It is moved to a position to make a transition from a state in which the medicine flow is allowed to a state in which it is prohibited.
　また、この発明にかかるカテーテルは、上記の発明において、前記被破壊部材は、セラミックスであることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the member to be destroyed is ceramic.
　また、この発明にかかるカテーテルは、上記の発明において、前記ゲート機構は、前記エネルギーを受けて変形する変形部材を有し、該変形部材の変形によって前記状態が遷移することを特徴とする。 Further, the catheter according to the present invention is characterized in that, in the above-mentioned invention, the gate mechanism has a deformable member that is deformed by receiving the energy, and the state is changed by deformation of the deformable member.
　また、この発明にかかるカテーテルは、上記の発明において、前記ゲート機構は、前記エネルギーを受けて前記変形部材が変形することによって前記薬剤の流れを禁止する状態から許容する状態に遷移させることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the gate mechanism makes a transition from a state in which the flow of the medicine is prohibited to a state in which the flow of the medicine is permitted by receiving the energy and deforming the deformable member. And
　また、この発明にかかるカテーテルは、上記の発明において、前記変形部材は、前記薬剤の流れを許容する部材であり、前記薬剤の流れを禁止する位置に移動する方向に付勢され、前記変形部材によって前記移動が阻まれる付勢部材を有し、前記ゲート機構は、前記エネルギーを受けて前記変形部材が変形することによって前記付勢部材を前記薬剤の流れを禁止する位置に移動させ、前記薬剤の流れを許容する状態から禁止する状態に遷移させることを特徴とする。 In the catheter according to the present invention, in the above invention, the deformation member is a member that allows the flow of the medicine, and is biased in a direction to move to a position that prohibits the flow of the medicine, and the deformation member And the gate mechanism moves the urging member to a position where the flow of the medicine is prohibited by the deformation of the deforming member upon receiving the energy. It is characterized by making a transition from a state in which the flow is allowed to a state in which it is prohibited.
　また、この発明にかかるカテーテルは、上記の発明において、前記変形部材は、熱可塑性のプラスチックであることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the deformable member is a thermoplastic plastic.
　また、この発明にかかるカテーテルは、上記の発明において、前記波動エネルギーは、音波、超音波、赤外線と可視光とを含みかつ高周波を含む電磁波、衝撃波、機械振動のうちの１または複数を組み合わせたエネルギーであることを特徴とする。 In the catheter according to the present invention, in the above invention, the wave energy is a combination of one or more of an electromagnetic wave including a sound wave, an ultrasonic wave, an infrared ray and visible light, including a high frequency, a shock wave, and a mechanical vibration. It is characterized by energy.
　また、この発明にかかるカテーテルは、上記の発明において、前記波動エネルギーは、レーザ装置から出力されるエネルギーであることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the wave energy is energy output from a laser device.
　また、この発明にかかるカテーテルは、上記の発明において、前記波動エネルギーは、超音波振動子から出力されるエネルギーであることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the wave energy is energy output from an ultrasonic transducer.
　また、この発明にかかるカテーテルは、上記の発明において、前記波動エネルギーは、衝撃波発生装置から出力されるエネルギーであることを特徴とする。 Further, in the catheter according to the present invention, the wave energy is energy output from a shock wave generator.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッド内には、前記薬剤を吐出する薬剤吐出部を有し、前記薬剤吐出部および前記ゲート機構は、複数であり、少なくとも１つの薬剤吐出部は、前記ゲート機構によって前記薬剤を吐出する活性状態と薬剤を吐出しない不活性状態との遷移が行われることを特徴とする。 Further, the catheter according to the present invention is the above-described invention, wherein the pad has a drug discharge unit for discharging the drug in the pad, the drug discharge unit and the gate mechanism are plural, and at least one drug The ejection unit is characterized in that the gate mechanism makes a transition between an active state in which the medicine is ejected and an inactive state in which the medicine is not ejected.
　また、この発明にかかるカテーテルは、上記の発明において、前記ゲート機構は、シート状の前記パッドの内部に設けられることを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the gate mechanism is provided inside the sheet-like pad.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッドは、浸透膜を有し、該浸透膜を介して前記薬剤を前記体内に吐出することを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the pad has an osmotic membrane, and the drug is discharged into the body through the osmotic membrane.
　また、この発明にかかるカテーテルは、上記の発明において、前記パッドは、開口が形成され、該開口を介して前記薬剤を前記体内に吐出することを特徴とする。 The catheter according to the present invention is characterized in that, in the above-mentioned invention, the pad has an opening, and the drug is discharged into the body through the opening.
　また、この発明にかかるカテーテルは、上記の発明において、前記管路は、先端に穿刺針が設けられ、該穿刺針を介して前記薬剤を体内に吐出し、前記ゲート機構は、前記管路の途中に設けられることを特徴とする。 Further, in the catheter according to the present invention, in the above invention, a puncture needle is provided at a distal end of the conduit, and the drug is discharged into the body through the puncture needle, and the gate mechanism is connected to the conduit. It is provided in the middle.
　また、この発明にかかるカテーテルは、上記の発明において、前記管路は、前記薬剤の供給側の１つの通路から複数の通路に分岐する分岐部を有し、前記ゲート機構は、前記分岐部に複数設けられ、前記分岐部から分岐した少なくとも１つの通路は、前記ゲート機構によって該通路に薬剤を流す活性状態と該通路に薬剤を流さない不活性状態との状態遷移を行うことを特徴とする。 In the catheter according to the present invention as set forth in the invention described above, the conduit has a branch portion that branches from one passage on the drug supply side to a plurality of passages, and the gate mechanism is connected to the branch portion. A plurality of at least one passage branched from the branching portion performs a state transition between an active state in which a drug is caused to flow through the passage and an inactive state in which the agent is not caused to flow through the passage by the gate mechanism. .
　また、この発明にかかるカテーテルは、上記の発明において、前記分岐部は、網状の通路であることを特徴とする。 The catheter according to the present invention is characterized in that, in the above invention, the branch portion is a mesh-like passage.
　この発明によれば、人間を含む哺乳類の体内臓器に取り付けられるカテーテルであって、薬剤供給源から体内に薬剤を導く管路と、前記管路の最先端に設けられた、少なくとも裏面の一部が前記体内臓器表面に密着するパッドと、を備え、前記パッドは、前記管路の内部通路と連通する１つまたは複数の開口を形成し、前記１つまたは複数の開口の総面積は、前記内部通路の断面積より広くなるようにしているので、簡易かつ確実に、体内臓器の表面近傍の所定領域に薬剤を投与することができる。 According to the present invention, a catheter attached to a body organ of a mammal including a human, a conduit for guiding a drug from a drug supply source into the body, and at least a part of the back surface provided at the forefront of the conduit Wherein the pad forms one or more openings that communicate with the internal passage of the duct, and the total area of the one or more openings is Since it is made wider than the cross-sectional area of the internal passage, it is possible to easily and reliably administer the drug to a predetermined region near the surface of the internal organ.
図１は、この発明の実施の形態１にかかるカテーテルが人体に適用された状態を示す模式図である。FIG. 1 is a schematic diagram showing a state where the catheter according to the first embodiment of the present invention is applied to a human body. 図２は、図１に示したカテーテルの体内臓器近傍の設置状態を示す模式図である。FIG. 2 is a schematic view showing an installation state of the catheter shown in FIG. 1 in the vicinity of the internal organ. 図３は、図１に示したカテーテルの体内臓器近傍の設置状態を示す平面図である。FIG. 3 is a plan view showing an installed state of the catheter shown in FIG. 1 in the vicinity of the internal organ. 図４は、図１に示したカテーテルの変形例の構成を示す断面図である。FIG. 4 is a cross-sectional view showing a configuration of a modified example of the catheter shown in FIG. 図５は、図１に示したカテーテルのシート部の変形例を示す平面図である。FIG. 5 is a plan view showing a modification of the sheet portion of the catheter shown in FIG. 図６は、図１に示したカテーテルのシート部の変形例を示す平面図である。FIG. 6 is a plan view showing a modification of the seat portion of the catheter shown in FIG. 図７は、図６に示したカテーテルの流路の構成を示す断面図である。7 is a cross-sectional view showing the configuration of the flow path of the catheter shown in FIG. 図８は、図６に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 8 is a cross-sectional view showing a configuration of a modified example of the flow path of the catheter shown in FIG. 図９は、図６に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 9 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG. 図１０は、図６に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 10 is a cross-sectional view illustrating a configuration of a modified example of the flow path of the catheter illustrated in FIG. 6. 図１１は、この発明の実施の形態２であるカテーテルの設置態様を示す模式図である。FIG. 11 is a schematic diagram showing an installation mode of the catheter according to the second embodiment of the present invention. 図１２は、この発明の実施の形態２であるカテーテルのスペーサの変形例の構成を示す模式図である。FIG. 12 is a schematic diagram showing a configuration of a modified example of the spacer of the catheter according to the second embodiment of the present invention. 図１３は、この発明の実施の形態２であるカテーテルのスペーサの変形例の構成を示す模式図である。FIG. 13 is a schematic diagram showing a configuration of a modification of the catheter spacer according to the second embodiment of the present invention. 図１４は、この発明の実施の形態３にかかるカテーテルが人体に適用された状態を示す模式図である。FIG. 14 is a schematic diagram showing a state in which the catheter according to the third embodiment of the present invention is applied to a human body. 図１５は、図１４に示したカテーテルの体内臓器近傍の設置状態を示す模式図である。FIG. 15 is a schematic diagram showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ. 図１６は、図１４に示したカテーテルの体内臓器近傍の設置状態を示す平面図である。FIG. 16 is a plan view showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ. 図１７は、図１４に示したカテーテルの変形例の構成を示す断面図である。FIG. 17 is a cross-sectional view showing a configuration of a modified example of the catheter shown in FIG. 図１８は、図１４に示したサポータ部の変形例を示す斜視図である。FIG. 18 is a perspective view showing a modification of the supporter unit shown in FIG. 図１９は、図１４に示したサポータ部の変形例を示す斜視図である。FIG. 19 is a perspective view showing a modification of the supporter unit shown in FIG. 図２０は、図１４に示したサポータ部に複数のバルーンを設けた変形例を示す斜視図である。FIG. 20 is a perspective view showing a modification in which a plurality of balloons are provided on the supporter unit shown in FIG. 図２１は、図２０に示したバルーンの変形状態を示す断面図である。21 is a cross-sectional view showing a deformed state of the balloon shown in FIG. 図２２は、図１４に示したサポータ部に複数の開口を形成した変形例を示す斜視図である。FIG. 22 is a perspective view showing a modified example in which a plurality of openings are formed in the supporter part shown in FIG. 図２３は、図１４に示したカテーテルのサポータ部の変形例を示す平面図である。FIG. 23 is a plan view showing a modification of the supporter portion of the catheter shown in FIG. 図２４は、図１４に示したカテーテルのサポータ部の変形例を示す平面図である。FIG. 24 is a plan view showing a modification of the supporter portion of the catheter shown in FIG. 図２５は、図２４に示したカテーテルの流路の構成を示す断面図である。25 is a cross-sectional view showing the configuration of the flow path of the catheter shown in FIG. 図２６は、図２４に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 26 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG. 図２７は、図２４に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 27 is a cross-sectional view showing a configuration of a modified example of the flow path of the catheter shown in FIG. 図２８は、図２４に示したカテーテルの流路の変形例の構成を示す断面図である。FIG. 28 is a cross-sectional view showing a configuration of a modification of the flow path of the catheter shown in FIG. 図２９は、この発明の実施の形態４であるカテーテルの設置態様を示す模式図である。FIG. 29 is a schematic diagram showing an installation mode of the catheter according to the fourth embodiment of the present invention. 図３０は、この発明の実施の形態４であるカテーテルのスペーサの変形例の構成を示す模式図である。FIG. 30 is a schematic diagram showing a configuration of a modified example of the spacer of the catheter according to the fourth embodiment of the present invention. 図３１は、この発明の実施の形態４であるカテーテルのスペーサの変形例の構成を示す模式図である。FIG. 31 is a schematic diagram showing a configuration of a modification of the catheter spacer according to the fourth embodiment of the present invention. 図３２は、この発明の実施の形態５にかかるカテーテルが人体に適用された状態を示す模式図である。FIG. 32 is a schematic diagram illustrating a state in which the catheter according to the fifth embodiment of the present invention is applied to a human body. 図３３は、図３２に示したカテーテルの薬剤吐出部を裏面側からみた図である。FIG. 33 is a view of the drug discharge portion of the catheter shown in FIG. 32 as seen from the back side. 図３４は、図３２に示したカテーテルの薬剤吐出部の構成を示す分解斜視図である。FIG. 34 is an exploded perspective view showing the configuration of the medicine discharge section of the catheter shown in FIG. 図３５は、第２のゲート機構の構成を示す斜視図である。FIG. 35 is a perspective view showing the configuration of the second gate mechanism. 図３６は、第１のゲート機構の構成を示す斜視図である。FIG. 36 is a perspective view showing the configuration of the first gate mechanism. 図３７は、第１のゲート機構の動作を示す模式図である。FIG. 37 is a schematic diagram showing the operation of the first gate mechanism. 図３８は、外部からカテーテルの表面を介してゲート機構にエネルギーを供給する機構の一例を示す模式図である。FIG. 38 is a schematic diagram showing an example of a mechanism for supplying energy to the gate mechanism from the outside via the surface of the catheter. 図３９は、外部からカテーテルの表面を介してゲート機構にエネルギーを供給する機構の一例を示す模式図である。FIG. 39 is a schematic diagram showing an example of a mechanism for supplying energy to the gate mechanism from the outside via the surface of the catheter. 図４０は、薬剤吐出部の変形例１を裏面側からみた模式図である。FIG. 40 is a schematic view of Modification 1 of the medicine ejection unit viewed from the back side. 図４１は、薬剤吐出部の変形例２を裏面側からみた模式図である。FIG. 41 is a schematic diagram of Modification 2 of the medicine ejection unit viewed from the back side. 図４２は、カテーテルの変形例３の構成を示す斜視図である。FIG. 42 is a perspective view showing a configuration of Modification Example 3 of the catheter. 図４３は、この発明の実施の形態５の変形例４のゲート機構の構成を示す分解斜視図である。FIG. 43 is an exploded perspective view showing the configuration of the gate mechanism of Modification 4 of Embodiment 5 of the present invention. 図４４は、図４３に示したゲート機構の動作を示す図である。FIG. 44 is a diagram illustrating the operation of the gate mechanism shown in FIG.
　以下、図面を参照して、この発明にかかるカテーテルの好適な実施の形態を詳細に説明する。なお、この実施の形態によってこの発明が限定されるものではない。 Hereinafter, preferred embodiments of a catheter according to the present invention will be described in detail with reference to the drawings. The present invention is not limited to the embodiments.
（実施の形態１）
　図１は、この発明の実施の形態１にかかるカテーテルが人体に適用された状態を示す模式図である。また、図２は、図１に示したカテーテルの体内臓器近傍の設置状態を示す模式図である。さらに、図３は、図１に示したカテーテルの体内臓器近傍の設置状態を示す平面図である。図１では、たとえば、肝臓などの体内臓器４の表面に対して数十ｍｌ程度の抗癌剤などの薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与する場合を示している。なお、ここでいう薬剤には、液状およびゲル状の薬剤を含む。 (Embodiment 1)
FIG. 1 is a schematic diagram showing a state where the catheter according to the first embodiment of the present invention is applied to a human body. FIG. 2 is a schematic diagram showing an installed state of the catheter shown in FIG. 1 in the vicinity of the internal organ. Further, FIG. 3 is a plan view showing an installation state of the catheter shown in FIG. FIG. 1 shows a case where, for example, about several tens ml of anticancer drug or the like is continuously and intensively discharged over a long period of about one week on the surface of a body organ 4 such as the liver for planned administration. ing. In addition, the chemical | medical agent here contains a liquid and a gel-form chemical | medical agent.
　図１～図３において、カテーテル１０は、チューブ（管路）２とシート部１とを有する。チューブ２は、体表６に取り付けられた薬剤投入装置３に接続され、本発明のパッドに対応するシート部１は、臓器支持組織５によって体内で支えられている体内臓器４表面に密着して該体内臓器４に固着される。薬剤投入装置３は、上述したように体内臓器４の表面に対して数十ｍｌ程度の薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与するものであり、たとえば、薬剤リザーバ内に蓄積された薬剤を、電気浸透流ポンプなどによって微量に押し出し、カテーテル１０を介して投与する。すなわち、薬剤投入装置３から規定された量の薬剤がチューブ２を通って体内に導入され、薬剤は、シート部１の裏面に設けられた開口１２からシート部１の裏面側の所定範囲に拡散し、体内臓器４にその表面から吸収される。なお、薬剤投入装置３は、体表６に取り付けてある必要はなく、例えば、体内に埋め込む構成や、体外に離間して配置する構成が可能である。 1 to 3, the catheter 10 has a tube (pipe) 2 and a sheet portion 1. The tube 2 is connected to a drug injection device 3 attached to the body surface 6, and the sheet portion 1 corresponding to the pad of the present invention is in close contact with the surface of the internal organ 4 supported by the organ supporting tissue 5 in the body. It is fixed to the internal organ 4. As described above, the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week. The medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10. That is, a prescribed amount of medicine is introduced from the medicine feeding device 3 into the body through the tube 2, and the medicine diffuses from the opening 12 provided on the back surface of the sheet portion 1 to a predetermined range on the back surface side of the sheet portion 1. And absorbed by the internal organ 4 from its surface. In addition, the chemical | medical agent injection apparatus 3 does not need to be attached to the body surface 6, For example, the structure embedded in a body and the structure arrange | positioned apart from the body are possible.
　シート部１は、シート状で、柔軟な生体適合性のある素材、例えばＰＶＤＣ（ポリ塩化ビニリデン）フィルム、ポリエチレンフィルム、シリコンゴム等で形成される。また、チューブ２は、シート部１の表面から延伸し、ポリエチレン等の柔軟な生体適合性のある素材で形成される。 The sheet portion 1 is a sheet-like material made of a flexible biocompatible material, such as a PVDC (polyvinylidene chloride) film, a polyethylene film, or silicon rubber. The tube 2 extends from the surface of the sheet portion 1 and is formed of a flexible biocompatible material such as polyethylene.
　チューブ２は、シート部１の裏面に、チューブ２の内部通路と連通する開口１２が形成される。チューブ２のシート部１側には、連結部１１が設けられ、この連結部１１および体内臓器４の臓器表面８によって囲まれる空室２３が形成される。この空室２３下部の開口１２は、チューブ２の内部通路の断面積より広い面積で体内臓器４の表面である臓器表面８の領域Ｅ２に接している。 In the tube 2, an opening 12 communicating with the internal passage of the tube 2 is formed on the back surface of the sheet portion 1. A connecting portion 11 is provided on the sheet portion 1 side of the tube 2, and an empty chamber 23 surrounded by the connecting portion 11 and the organ surface 8 of the internal organ 4 is formed. The opening 12 below the vacant chamber 23 is in contact with the region E2 of the organ surface 8 that is the surface of the internal organ 4 in an area wider than the cross-sectional area of the internal passage of the tube 2.
　ここで、シート部１は、裏面の体内臓器４に接する領域の少なくとも一部の表面が平滑に形成されており、分子間力によって体内臓器４に密着する。図２および図３では、シート部１の連結部１１を除いた周縁部分の裏面が平滑に形成され、密着領域２１を形成し、体内臓器４の領域Ｅ１と密着している。なお、体内臓器４の表面にある粘膜９がこの密着領域２１との密着を促進する。また、連結部１１の裏面は、粗い表面とすることが好ましく、たとえば多孔性材であることが好ましく、これによって空室２３が形成し易くなる。 Here, at least a part of the surface of the sheet portion 1 in a region in contact with the internal organ 4 on the back surface is formed smoothly, and is in close contact with the internal organ 4 by intermolecular force. In FIG. 2 and FIG. 3, the back surface of the peripheral portion excluding the connecting portion 11 of the sheet portion 1 is formed smoothly, forms a close contact region 21, and is in close contact with the region E 1 of the body organ 4. The mucous membrane 9 on the surface of the internal organ 4 promotes close contact with the close contact region 21. Moreover, it is preferable that the back surface of the connection part 11 is made into the rough surface, for example, it is preferable that it is a porous material, for example, and it becomes easy to form the empty room 23 by this.
　すなわち、図３に示すように、開口１２の上部は、臓器表面８に密着しない非密着領域２２となり、空室２３が形成されるとともに、この空室２３の周囲が臓器表面８に密着する密着領域２１となる。 That is, as shown in FIG. 3, the upper part of the opening 12 becomes a non-contact region 22 that does not adhere to the organ surface 8, and a vacancy 23 is formed, and the periphery of the vacancy 23 adheres closely to the organ surface 8. It becomes area 21.
　チューブ２を通って薬剤投入装置３から導入された薬剤７は、連結部１１内部に形成される空室２３に流入する。空室２３に流入した薬剤７は、この空室２３に浸透・充満し、臓器表面８に接する領域Ｅ２（開口１２）から体内臓器４内に吸収される。このため、薬剤７は、チューブ２の内部通路の断面よりも大きな面積をもつ臓器表面８の領域Ｅ２（開口１２）から投与され、かつカテーテル１０が体内臓器４に密着固定されているため、比較的長期にわたって安定した薬剤投与を簡易に行うことができる。 The medicine 7 introduced from the medicine feeding device 3 through the tube 2 flows into the vacant chamber 23 formed inside the connecting portion 11. The drug 7 that has flowed into the vacant chamber 23 penetrates and fills the vacant chamber 23 and is absorbed into the internal organ 4 from the region E2 (opening 12) in contact with the organ surface 8. For this reason, since the medicine 7 is administered from the region E2 (opening 12) of the organ surface 8 having an area larger than the cross section of the internal passage of the tube 2, and the catheter 10 is closely fixed to the body organ 4, the comparison is made. Stable drug administration can be easily performed over a long period of time.
　なお、密着領域２１は、その密着性を高めるため、たとえば、エポキシ化ジエン系ブロック共重合体を１００重量部に対して水添ジエン系ブロック共重合体を１０～１００重量部配合した重合体組成物を用いるようにしてもよい。 In order to improve the adhesion, the adhesion region 21 is, for example, a polymer composition in which 10 to 100 parts by weight of a hydrogenated diene block copolymer is blended with 100 parts by weight of an epoxidized diene block copolymer. You may make it use a thing.
　また、シート部１と体内臓器４の密着は、分子間力に限定されるものではなく、密着部分のジェルの塗布や、縫合や、フィブリン糊などによる接着によって実現してもよい。 Further, the close contact between the sheet portion 1 and the internal organ 4 is not limited to intermolecular force, and may be realized by applying gel at the close contact portion, adhering with sutures, fibrin glue or the like.
　さらに、図４に示すように、チューブ２とシート部１との間を、各端部に設けた流体ソケットや流体コンセントなどによって実現される接続部３０ａ，３０ｂ（３０）によって着脱可能とするようにしてもよい。 Further, as shown in FIG. 4, the tube 2 and the seat portion 1 can be detachably attached by connecting portions 30a and 30b (30) realized by a fluid socket or a fluid outlet provided at each end portion. It may be.
　また、図４に示すように、連結部１１に空室２３内の空気抜きのための空気抜き弁３１を設けるようにしてもよい。この空気抜き弁３１は、空気は外部に通過することができるが、薬剤などは通過できないフィルタが設けられている。空室２３内では、薬剤７の流入により、空室２３内に残留していた空気が押圧されるが、この空気抜き弁３１によって内部空気が外部に放出され、薬剤の投与を確実に行うことができる。なお、空気抜き弁３１に替えて、シート部１あるいは連結部１１の材質を、空気のみが通過できる通気性の材質によって形成するようにしてもよい。 Further, as shown in FIG. 4, an air vent valve 31 for venting the air in the empty chamber 23 may be provided in the connecting portion 11. The air vent valve 31 is provided with a filter through which air can pass to the outside but no medicine or the like can pass. In the vacant chamber 23, the air remaining in the vacant chamber 23 is pressed by the inflow of the drug 7, but the internal air is released to the outside by the air vent valve 31, so that the drug can be reliably administered. it can. Instead of the air vent valve 31, the material of the seat part 1 or the connecting part 11 may be formed of a breathable material through which only air can pass.
　さらに、上述した実施の形態１では、図３に示すように、非密着領域２２が密着領域２１に囲まれた閉領域であったが、これに限らず、図５に示すように、非密着領域２２の一部に、外部と通じる開口領域２２ａを設けるようにしてもよい。この場合、空室２３に対応する空室２３ａに流入した薬剤７は、空室２３ａ内で加圧状態とならず、圧力解放によってチューブ２を介した薬剤７の流入をスムーズに行うことができる。なお、投入される薬剤７は、微量であり、薬剤の体内臓器４への吸収に対応する投与量に調整することにより、薬剤が非密着領域２２を大きく越えて投与されることが防止される。また、微量であれば、薬剤７が非密着領域２２を越えて広がってもよい。 Furthermore, in Embodiment 1 described above, as shown in FIG. 3, the non-contact region 22 is a closed region surrounded by the contact region 21, but not limited thereto, as shown in FIG. An opening region 22 a that communicates with the outside may be provided in a part of the region 22. In this case, the medicine 7 that has flowed into the vacant room 23a corresponding to the vacant room 23 is not in a pressurized state in the vacant room 23a, and the medicine 7 can be smoothly introduced through the tube 2 by releasing the pressure. . Note that the amount of the drug 7 to be introduced is very small, and by adjusting the dose corresponding to the absorption of the drug into the body organ 4, it is possible to prevent the drug from being greatly administered beyond the non-contact region 22. . Moreover, if it is a trace amount, the medicine 7 may spread beyond the non-contact region 22.
　また、図６に示すように、シート部１内の異なる領域に非密着領域２２ｂ，２２ｃを形成して空室２３ｂ，２３ｃを設けてもよい。この場合、チューブ２側の開口１２は、一方の非密着領域２２ｂに配置され、非密着領域２２ｂ，２２ｃ間は、互いに連通する流路３２が設けられる。これによって、異なった位置にある複数の患部に対して１つのカテーテル１０で一度に薬剤を投与することができる。 Further, as shown in FIG. 6, the non-contact regions 22b and 22c may be formed in different regions in the sheet portion 1 to provide the vacancies 23b and 23c. In this case, the opening 12 on the tube 2 side is disposed in one non-contact area 22b, and a flow path 32 communicating with each other is provided between the non-contact areas 22b and 22c. As a result, a single catheter 10 can administer a drug to a plurality of affected areas at different positions at a time.
　この流路３２は、たとえば、図７に示すように、シート部１裏面の流路形成領域３３を、表面が粗い材質としておくことによって実現される。この流路形成領域３３は、臓器表面８から浮いた状態となり、流路３２が形成されることになる。 The flow path 32 is realized, for example, by setting a flow path forming region 33 on the back surface of the sheet portion 1 as a material having a rough surface, as shown in FIG. This flow path forming region 33 is in a state of floating from the organ surface 8, and the flow path 32 is formed.
　また、図８に示すように、流路形成領域のシート部１内部に気泡３５を形成し、少なくともシート部１の裏面側を凸部とし、この凸部側面のシート部１を臓器表面８から離間させ、このシート部１と臓器表面８との間の空間を流路３２としてもよい。なお、この気泡３５の形成は、シート部１内部の流路形成領域に対応して切れ目を入れておき、この切れ目に空気を注入することによって実現できる。この切れ目は、積層の形成によって実現できる。また、シート部１内部の流路形成領域に、光あるいは熱に反応して発泡する発泡剤を注入しておき、この発泡剤に光あるいは熱を照射することによって膨張させて気泡を形成するようにしてもよい。 Further, as shown in FIG. 8, bubbles 35 are formed inside the sheet portion 1 in the flow path forming region, and at least the back side of the sheet portion 1 is a convex portion, and the sheet portion 1 on the side surface of the convex portion is separated from the organ surface 8. The space between the sheet portion 1 and the organ surface 8 may be separated and used as the flow path 32. The formation of the bubbles 35 can be realized by making a cut corresponding to the flow path forming region inside the sheet portion 1 and injecting air into the cut. This break can be realized by forming a laminate. Further, a foaming agent that reacts with light or heat is injected into the flow path forming region inside the sheet portion 1 and is expanded by irradiating the foaming agent with light or heat to form bubbles. It may be.
　さらに、図９に示すように、シート部１内の流路形成領域に連通孔３６であるルーメンを形成して流路３２としてもよい。また、図１０に示すように、このルーメン内に多孔質材３７を充填して流路３２を形成してもよい。この多孔質材３７は、たとえば、人工腎臓などに用いられる内径１００μｍ程度の中空糸（ホローファイバ）を束ねたもので実現される。この中空糸は、再生セルロース（キュプロファン、アセチルセルロースなど）、ポリメチルメタクリレート、ポリビニルアルコールエチレン共重合体、ポリスルフォンなどによって実現される。さらに、塩化ビニルなどの素材を一部に有するシート部１に対して、目的のルーメン形状に沿って紫外線を焦点し、塩化ビニルの架橋構造を破壊して、多孔構造を形成させてもよい。 Furthermore, as shown in FIG. 9, a lumen that is a communication hole 36 may be formed in the flow path forming region in the sheet portion 1 to form the flow path 32. In addition, as shown in FIG. 10, the flow path 32 may be formed by filling the lumen with a porous material 37. The porous material 37 is realized by, for example, a bundle of hollow fibers (hollow fibers) having an inner diameter of about 100 μm used for artificial kidneys and the like. This hollow fiber is realized by regenerated cellulose (such as cuprophan or acetyl cellulose), polymethyl methacrylate, polyvinyl alcohol ethylene copolymer, polysulfone, or the like. Further, the sheet portion 1 having a material such as vinyl chloride in part may be focused on ultraviolet rays along the target lumen shape to destroy the crosslinked structure of vinyl chloride, thereby forming a porous structure.
（実施の形態２）
　つぎに、この発明の実施の形態２について説明する。この実施の形態２では、さらにシート部１と体内臓器４との間に、スペーサを設け、空室２３に対応する空室を確実に形成できるようにしている。 (Embodiment 2)
Next, a second embodiment of the present invention will be described. In the second embodiment, a spacer is further provided between the seat portion 1 and the internal organ 4 so that an empty chamber corresponding to the empty chamber 23 can be reliably formed.
　図１１は、この発明の実施の形態２であるカテーテルの設置態様を示す模式図である。図１１に示すように、この実施の形態２では、シート部１と体内臓器４との間で、シート部１に覆われるスペーサ４０を設ける。このスペーサ４０は、図３に示した空室２３を確実に形成するためのものであり、側壁４２と、側壁４２の周縁であって体内臓器４側に形成されたフランジ４１とを有する。側壁４２は、空室２３に対応する空室４５を囲むように形成する。この側壁４２が形成する円筒には、シート部１側の上部開口４３と、体内臓器４側の下部開口４４とが形成されている。上部開口４３には、シート部１が覆われるが、この際、チューブ２が結合するシート部１のチューブ２側の開口が、上部開口４３内に位置するように覆う。一方、フランジ４１の裏面は、密着領域２１と同様に滑らかな表面となっており、体内臓器４の臓器表面８と密着してスペーサ４０を固着する。 FIG. 11 is a schematic diagram showing an installation mode of the catheter according to the second embodiment of the present invention. As shown in FIG. 11, in the second embodiment, a spacer 40 covered with the sheet part 1 is provided between the sheet part 1 and the internal organ 4. This spacer 40 is for reliably forming the empty chamber 23 shown in FIG. 3, and includes a side wall 42 and a flange 41 formed on the side of the body organ 4 at the periphery of the side wall 42. The side wall 42 is formed so as to surround the empty room 45 corresponding to the empty room 23. The cylinder formed by the side wall 42 is formed with an upper opening 43 on the seat portion 1 side and a lower opening 44 on the body organ 4 side. The upper opening 43 covers the sheet portion 1. At this time, the opening on the tube 2 side of the sheet portion 1 to which the tube 2 is coupled is covered with the upper opening 43. On the other hand, the back surface of the flange 41 has a smooth surface like the contact area 21, and is in close contact with the organ surface 8 of the internal organ 4 to fix the spacer 40.
　最終的に、図１１（ｂ）に示すように、スペーサ４０が所定の容積をもつ空室４５を確保しつつ、シート部１の周縁の密着領域２１によってさらに閉空間としての空室４５を確実にしている。すなわち、シート部１の開口１２は、実質的にスペーサ４０下部の開口１２ａとなる。このスペーサ４０を用いることによって、空室４５を確実に確保することができ、しかも、開口１２ａを介して、薬剤の投与領域を確実に広く得ることができる。特に、経時的に非密着領域２２の一部が密着領域２１に変化したり、密着領域２１の一部が非密着領域２２に変化したりする領域境界の不安定さが軽減され、安定して必要な非密着領域２２を確保できる。 Finally, as shown in FIG. 11 (b), the spacer 40 secures the vacant chamber 45 having a predetermined volume, and the vacant chamber 45 as a closed space is further ensured by the contact region 21 at the periphery of the seat portion 1. I have to. In other words, the opening 12 of the sheet portion 1 is substantially the opening 12 a below the spacer 40. By using this spacer 40, the vacant chamber 45 can be reliably ensured, and the medicine administration region can be reliably widened through the opening 12a. In particular, the instability of the region boundary in which a part of the non-contact region 22 changes to the contact region 21 or a part of the contact region 21 changes to the non-contact region 22 with time is reduced, and stable. The necessary non-contact area 22 can be secured.
　なお、図１２に示すように、図５に対応した非密着領域２２および空室２３ａを形成できるスペーサ５０としてもよい。この場合も、チューブ２側の開口が、上部開口５３に位置するように、シート部１が覆われる。また、シート部１は、側面開口５５を覆わないことが好ましいが、覆ってもよい。なお、スペーサ５０は、上部開口５３を有するシート部１側の上面と、体内臓器４側に形成される下部開口５４と、側壁５２と、側面開口５５とによって空室を形成する。 In addition, as shown in FIG. 12, it is good also as the spacer 50 which can form the non-contact | adherence area | region 22 and the empty room 23a corresponding to FIG. Also in this case, the sheet portion 1 is covered so that the opening on the tube 2 side is located in the upper opening 53. Moreover, although it is preferable that the sheet | seat part 1 does not cover the side surface opening 55, you may cover it. The spacer 50 forms an empty space by the upper surface on the sheet portion 1 side having the upper opening 53, the lower opening 54 formed on the body organ 4 side, the side wall 52, and the side surface opening 55.
　さらに、図１３に示すように、図６に対応した非密着領域２２および空室２３ｂ，２３ｃを形成できるスペーサ６０としてもよい。この場合、チューブ２側の開口が上部開口６４に位置するように、シート部１が覆われる。ここで、空室２３ｂ，２３ｃに対応する空室６９ｂ，６９ｃを形成するために、側壁６２，６３およびフランジ６１が設けられ、さらに下部開口６５，６７が形成され、空室６９ｂ，６９ｃ間を接続するためのブリッジ部６８が設けられている。このブリッジ部６８に、各空室６９ｂ，６９ｃ間を連通させる流路を形成してもよいし、形成しなくてもよい。また、流路を設けた場合、上部開口６６を塞ぐようにしてもよい。 Further, as shown in FIG. 13, a spacer 60 capable of forming the non-contact region 22 and the vacant spaces 23b and 23c corresponding to FIG. 6 may be used. In this case, the sheet portion 1 is covered so that the opening on the tube 2 side is located in the upper opening 64. Here, in order to form the empty chambers 69b and 69c corresponding to the empty chambers 23b and 23c, the side walls 62 and 63 and the flange 61 are provided, and further the lower openings 65 and 67 are formed, and the space between the empty chambers 69b and 69c is formed. A bridge portion 68 for connection is provided. The bridge portion 68 may or may not be formed with a flow path that communicates between the vacancies 69b and 69c. Further, when the flow path is provided, the upper opening 66 may be blocked.
　なお、上述した実施の形態２では、フランジ４１，５１，６１の各裏面などによってスペーサ４０，５０，６０を体内臓器４に密着固定するようにしていたが、これに限らず、縫合、接着等によってスペーサ４０，５０，６０を体内臓器４に固定するようにしてもよい。 In the above-described second embodiment, the spacers 40, 50, 60 are closely fixed to the internal organ 4 by the back surfaces of the flanges 41, 51, 61. However, the present invention is not limited to this, and stitching, adhesion, etc. The spacers 40, 50, 60 may be fixed to the internal organ 4.
　この実施の形態１，２では、パッドとしてシート状のシート部を用いるようにしているので、簡易な構成で、臓器表面に広範囲に薬剤を投与することができる。 In Embodiments 1 and 2, since a sheet-like sheet portion is used as a pad, a drug can be administered over a wide range on the organ surface with a simple configuration.
（実施の形態３）
　つぎに、この発明の実施の形態３について説明する。図１４は、この発明の実施の形態３にかかるカテーテルが人体に適用された状態を示す模式図である。また、図１５は、図１４に示したカテーテルの体内臓器近傍の設置状態を示す模式図である。さらに、図１６は、図１４に示したカテーテルの体内臓器近傍の設置状態を示す平面図である。図１４では、たとえば、肝臓などの体内臓器４の表面に対して数十ｍｌ程度の抗癌剤などの薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与する場合を示している。なお、ここでいう薬剤には、液状およびゲル状の薬剤を含む。 (Embodiment 3)
Next, a third embodiment of the present invention will be described. FIG. 14 is a schematic diagram showing a state in which the catheter according to the third embodiment of the present invention is applied to a human body. FIG. 15 is a schematic diagram showing an installation state of the catheter shown in FIG. 14 in the vicinity of the internal organ. Further, FIG. 16 is a plan view showing an installed state of the catheter shown in FIG. 14 in the vicinity of the internal organ. FIG. 14 shows, for example, a case where a drug such as an anticancer drug of about several tens ml is continuously and intensively discharged over a long period of about one week on the surface of a body organ 4 such as the liver for planned administration. ing. In addition, the chemical | medical agent here contains a liquid and a gel-form chemical | medical agent.
　図１４～図１６において、カテーテル１０は、チューブ２とサポータ部１０１とを有する。チューブ２は、体表６に取り付けられた薬剤投入装置３に接続され、本発明のパッドに対応するサポータ部１０１は、臓器支持組織５によって体内で支えられている体内臓器４表面を取り囲み、体内臓器４表面に対して位置が固定される。薬剤投入装置３は、上述したように体内臓器４の表面に対して数十ｍｌ程度の薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与するものであり、たとえば、薬剤リザーバ内に蓄積された薬剤を、電気浸透流ポンプなどによって微量に押し出し、カテーテル１０を介して投与する。すなわち、薬剤投入装置３から規定された量の薬剤がチューブ２を通って体内に導入され、薬剤は、サポータ部１０１の裏面に設けられた開口１２からサポータ部１０１の裏面側の所定範囲に拡散し、体内臓器４にその表面から吸収される。なお、薬剤投入装置３は、体表６に取り付けてある必要はなく、例えば、体内に埋め込む構成や、体外に離間して配置する構成が可能である。 14 to 16, the catheter 10 has a tube 2 and a supporter 101. The tube 2 is connected to the drug injection device 3 attached to the body surface 6, and the supporter unit 101 corresponding to the pad of the present invention surrounds the surface of the internal organ 4 supported in the body by the organ supporting tissue 5, The position is fixed with respect to the organ 4 surface. As described above, the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week. The medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10. That is, a prescribed amount of medicine is introduced from the medicine injection device 3 into the body through the tube 2, and the medicine diffuses from the opening 12 provided on the back surface of the supporter unit 101 to a predetermined range on the backside of the supporter unit 101. And absorbed by the internal organ 4 from its surface. In addition, the chemical | medical agent injection apparatus 3 does not need to be attached to the body surface 6, For example, the structure embedded in a body and the structure arrange | positioned apart from the body are possible.
　サポータ部１０１は、シート状で、柔軟な生体適合性のある素材、例えばＰＶＤＣ（ポリ塩化ビニリデン）フィルム、ポリエチレンフィルム、シリコンゴム等で形成される。また、チューブ２は、サポータ部１０１の表面から延伸し、ポリエチレン等の柔軟な生体適合性のある素材で形成される。 The supporter unit 101 is formed of a sheet-like, flexible biocompatible material, such as a PVDC (polyvinylidene chloride) film, a polyethylene film, or silicon rubber. The tube 2 extends from the surface of the supporter 101 and is formed of a flexible biocompatible material such as polyethylene.
　チューブ２は、サポータ部１０１の裏面に、チューブ２の内部通路と連通する開口１２が形成される。チューブ２のサポータ部１０１側には、連結部１１が設けられ、この連結部１１および体内臓器４の臓器表面８によって囲まれる空室２３が形成される。この空室２３下部の開口１２は、チューブ２の内部通路の断面積より広い面積で体内臓器４の表面である臓器表面８の領域Ｅ２に接している。 In the tube 2, an opening 12 communicating with the internal passage of the tube 2 is formed on the back surface of the supporter 101. A connecting part 11 is provided on the supporter 101 side of the tube 2, and an empty chamber 23 surrounded by the connecting part 11 and the organ surface 8 of the internal organ 4 is formed. The opening 12 below the vacant chamber 23 is in contact with the region E2 of the organ surface 8 that is the surface of the internal organ 4 in an area wider than the cross-sectional area of the internal passage of the tube 2.
　ここで、サポータ部１０１は、裏面の体内臓器４に接する領域の少なくとも一部の表面が平滑に形成されており、分子間力によって体内臓器４に密着する。図１５および図１６では、サポータ部１０１の連結部１１を除いた周縁部分の裏面が平滑に形成され、密着領域２１を形成し、体内臓器４の領域Ｅ１と密着している。なお、体内臓器４の表面にある粘膜９がこの密着領域２１との密着を促進する。また、連結部１１の裏面は、粗い表面とすることが好ましく、たとえば多孔性材であることが好ましく、これによって空室２３が形成し易くなる。 Here, the supporter part 101 has at least a part of the surface in contact with the body organ 4 on the back surface formed in a smooth manner, and is in close contact with the body organ 4 by intermolecular force. In FIG. 15 and FIG. 16, the back surface of the peripheral portion excluding the connecting portion 11 of the supporter portion 101 is formed smoothly, forms a close contact region 21, and is in close contact with the region E 1 of the internal organ 4. The mucous membrane 9 on the surface of the internal organ 4 promotes close contact with the close contact region 21. Moreover, it is preferable that the back surface of the connection part 11 is made into the rough surface, for example, it is preferable that it is a porous material, for example, and it becomes easy to form the empty room 23 by this.
　すなわち、図１６に示すように、開口１２の上部は、臓器表面８に密着しない非密着領域２２となり、空室２３が形成されるとともに、この空室２３の周囲が臓器表面８に密着する密着領域２１となる。 That is, as shown in FIG. 16, the upper portion of the opening 12 becomes a non-contact area 22 that does not adhere to the organ surface 8, and a vacancy 23 is formed, and the periphery of the vacancy 23 adheres closely to the organ surface 8. It becomes area 21.
　チューブ２を通って薬剤投入装置３から導入された薬剤７は、連結部１１内部に形成される空室２３に流入する。空室２３に流入した薬剤７は、この空室２３に浸透・充満し、臓器表面８に接する領域Ｅ２（開口１２）から体内臓器４内に吸収される。このため、薬剤７は、チューブ２の内部通路の断面よりも大きな面積をもつ臓器表面８の領域Ｅ２（開口１２）から投与され、かつカテーテル１０が体内臓器４に密着固定されているため、比較的長期にわたって安定した薬剤投与を簡易に行うことができる。 The medicine 7 introduced from the medicine feeding device 3 through the tube 2 flows into the vacant chamber 23 formed inside the connecting portion 11. The drug 7 that has flowed into the vacant chamber 23 penetrates and fills the vacant chamber 23 and is absorbed into the internal organ 4 from the region E2 (opening 12) in contact with the organ surface 8. For this reason, since the medicine 7 is administered from the region E2 (opening 12) of the organ surface 8 having an area larger than the cross section of the internal passage of the tube 2, and the catheter 10 is closely fixed to the body organ 4, the comparison is made. Stable drug administration can be easily performed over a long period of time.
　なお、密着領域２１は、その密着性を高めるため、たとえば、エポキシ化ジエン系ブロック共重合体を１００重量部に対して水添ジエン系ブロック共重合体を１０～１００重量部配合した重合体組成物を用いるようにしてもよい。 In order to improve the adhesion, the adhesion region 21 is, for example, a polymer composition in which 10 to 100 parts by weight of a hydrogenated diene block copolymer is blended with 100 parts by weight of an epoxidized diene block copolymer. You may make it use a thing.
　また、サポータ部１０１と体内臓器４の密着は、分子間力に限定されるものではなく、密着部分のジェルの塗布や、縫合や、フィブリン糊などによる接着によって実現してもよい。 Further, the close contact between the supporter 101 and the internal organ 4 is not limited to the intermolecular force, and may be realized by applying gel at the close contact portion, adhering by suturing, fibrin glue or the like.
　さらに、図１７に示すように、チューブ２とサポータ部１０１との間を、各端部に設けた流体ソケットや流体コンセントなどによって実現される接続部３０ａ，３０ｂ（３０）によって着脱可能とするようにしてもよい。 Furthermore, as shown in FIG. 17, the connection between the tube 2 and the supporter 101 is made detachable by connecting portions 30a and 30b (30) realized by a fluid socket or a fluid outlet provided at each end. It may be.
　また、図１７に示すように、連結部１１に空室２３内の空気抜きのための空気抜き弁３１を設けるようにしてもよい。この空気抜き弁３１は、空気は外部に通過することができるが、薬剤などは通過できないフィルタが設けられている。空室２３内では、薬剤７の流入により、空室２３内に残留していた空気が押圧されるが、この空気抜き弁３１によって内部空気が外部に放出され、薬剤の投与を確実に行うことができる。なお、空気抜き弁３１に替えて、サポータ部１０１あるいは連結部１１の材質を、空気のみが通過できる通気性の材質によって形成するようにしてもよい。 Further, as shown in FIG. 17, an air vent valve 31 for venting the air in the empty chamber 23 may be provided in the connecting portion 11. The air vent valve 31 is provided with a filter through which air can pass to the outside but no medicine or the like can pass. In the vacant chamber 23, the air remaining in the vacant chamber 23 is pressed by the inflow of the drug 7, but the internal air is released to the outside by the air vent valve 31, so that the drug can be reliably administered. it can. Instead of the air vent valve 31, the supporter 101 or the connecting part 11 may be made of a breathable material through which only air can pass.
　ここで、図１４に示したサポータ部１０１は、体内臓器４に、体内臓器４の一端から体内臓器４に嵌め込むことによって体内臓器４表面を囲むようにしていたが、図１８に示すように、複数の連結バンド１０１ａ～１０１ｅを持たせることが好ましい。連結バンド１０１ａ～１０１ｅの先端部には、それぞれ対応する先端部に雌雄のホック１１１が設けられ、体内臓器４表面を覆った後にホック１１１で体内臓器４に対する位置の固定を行うようにしている。この場合、臓器支持組織５が存在しても、体内臓器４に対してサポータ部１０１の位置を容易に固定することができる。 Here, the supporter unit 101 shown in FIG. 14 surrounds the surface of the internal organ 4 by fitting the internal organ 4 into the internal organ 4 from one end of the internal organ 4, but as shown in FIG. It is preferable to provide the connecting bands 101a to 101e. A male and female hook 111 is provided at the corresponding distal end of each of the connecting bands 101a to 101e, and the position of the internal organ 4 is fixed by the hook 111 after the surface of the internal organ 4 is covered. In this case, even if the organ supporting tissue 5 is present, the position of the supporter 101 can be easily fixed with respect to the internal organ 4.
　また、図１９に示すように、連結バンド１０１ａ～１０１ｅの先端部を相互にコード１１２を用いて結合させることによって、体内臓器４に対してサポータ部１０１の位置を固定するようにしてもよい。この場合、コード１１２の締め具合を調節することによって、体内臓器４に対するサポータ部１０１の固着強度を調整できる。なお、このコード１１２には、紐、糸、ワイヤ等が含まれる。 Further, as shown in FIG. 19, the position of the supporter 101 may be fixed with respect to the internal organ 4 by connecting the distal ends of the connecting bands 101a to 101e to each other using the cord 112. In this case, by adjusting the tightness of the cord 112, it is possible to adjust the fixing strength of the supporter 101 to the internal organ 4. The cord 112 includes a string, a thread, a wire, and the like.
　さらに、図２０に示すように、サポータ部１０１に分散配置されたバルーン１０３を形成するようにしてもよい。このバルーン１０３内には、図２１に示すように、空気や生理食塩水などの流体１０４が満たされており、このバルーン１０３の存在によって、体内臓器４に対するサポータ部１０１の固着強度を高めることができる。この固着強度の調整は、図２１に示すように、所望のバルーン１０３に対して穿刺針１０５等を穿刺することによってバルーン１０３を破り、バルーン１０３内の流体１０４を流出させ、バルーン１０３の容積を減少させて、バルーン１０３が存在したサポータ部１０１の領域が広がることによって固着強度を減少させることができる。もちろん、固着強度を一層高めたい場合には、穿刺針１０５等による流体の吹き込みと穿刺部の閉塞とによってバルーン１０３を新たに形成するようにしてもよい。 Furthermore, as shown in FIG. 20, the balloons 103 distributed in the supporter unit 101 may be formed. As shown in FIG. 21, the balloon 103 is filled with a fluid 104 such as air or physiological saline, and the presence of the balloon 103 can increase the fixing strength of the supporter 101 to the internal organ 4. it can. As shown in FIG. 21, the fixation strength is adjusted by puncturing the desired balloon 103 with a puncture needle 105 or the like to break the balloon 103 and causing the fluid 104 in the balloon 103 to flow out. By reducing the width of the supporter 101 where the balloon 103 is present, the fixing strength can be reduced. Of course, when it is desired to further increase the fixing strength, the balloon 103 may be newly formed by blowing fluid with the puncture needle 105 or the like and closing the puncture portion.
　また、図２２に示すように、サポータ部１０１に分散配置された開口１０６を持たせておき、隣接する開口１０６間に切れ目を入れて切断部１０７を形成することによって、固着強度を調整するようにしてもよい。 Further, as shown in FIG. 22, the fixing strength is adjusted by providing openings 106 dispersedly arranged in the supporter part 101 and forming a cut part 107 by making a cut between the adjacent openings 106. It may be.
　さらに、上述した実施の形態３では、図１６に示すように、非密着領域２２が密着領域２１に囲まれた閉領域であったが、これに限らず、図２３に示すように、非密着領域２２の一部に、外部と通じる開口領域２２ａを設けるようにしてもよい。この場合、空室２３に対応する空室２３ａに流入した薬剤７は、空室２３ａ内で加圧状態とならず、圧力解放によってチューブ２を介した薬剤７の流入をスムーズに行うことができる。なお、投入される薬剤７は、微量であり、薬剤の体内臓器４への吸収に対応する投与量に調整することにより、薬剤が非密着領域２２を大きく越えて投与されることが防止される。また、微量であれば、薬剤７が非密着領域２２を越えて広がってもよい。 Furthermore, in Embodiment 3 described above, as shown in FIG. 16, the non-contact region 22 is a closed region surrounded by the contact region 21, but not limited to this, as shown in FIG. An opening region 22 a that communicates with the outside may be provided in a part of the region 22. In this case, the medicine 7 that has flowed into the vacant room 23a corresponding to the vacant room 23 is not in a pressurized state in the vacant room 23a, and the medicine 7 can be smoothly introduced through the tube 2 by releasing the pressure. . Note that the amount of the drug 7 to be introduced is very small, and by adjusting the dose corresponding to the absorption of the drug into the body organ 4, it is possible to prevent the drug from being greatly administered beyond the non-contact region 22. . Moreover, if it is a trace amount, the medicine 7 may spread beyond the non-contact region 22.
　また、図２４に示すように、サポータ部１０１内の異なる領域に非密着領域２２ｂ，２２ｃを形成して空室２３ｂ，２３ｃを設けてもよい。この場合、チューブ２側の開口１２は、一方の非密着領域２２ｂに配置され、非密着領域２２ｂ，２２ｃ間は、互いに連通する流路３２が設けられる。これによって、異なった位置にある複数の患部に対して１つのカテーテル１０で一度に薬剤を投与することができる。 Further, as shown in FIG. 24, the non-contact regions 22b and 22c may be formed in different regions in the supporter 101 to provide the vacancies 23b and 23c. In this case, the opening 12 on the tube 2 side is disposed in one non-contact area 22b, and a flow path 32 communicating with each other is provided between the non-contact areas 22b and 22c. As a result, a single catheter 10 can administer a drug to a plurality of affected areas at different positions at a time.
　この流路３２は、たとえば、図２５に示すように、サポータ部１０１裏面の流路形成領域３３を、表面が粗い材質としておくことによって実現される。この流路形成領域３３は、臓器表面８から浮いた状態となり、流路３２が形成されることになる。 25. For example, as shown in FIG. 25, the flow path 32 is realized by setting a flow path forming region 33 on the back surface of the supporter 101 as a material having a rough surface. This flow path forming region 33 is in a state of floating from the organ surface 8, and the flow path 32 is formed.
　また、図２６に示すように、流路形成領域のサポータ部１０１内部に気泡３５を形成し、少なくともサポータ部１０１の裏面側を凸部とし、この凸部側面のサポータ部１０１を臓器表面８から離間させ、このサポータ部１０１と臓器表面８との間の空間を流路３２としてもよい。なお、この気泡３５の形成は、サポータ部１０１内部の流路形成領域に対応して切れ目を入れておき、この切れ目に空気を注入することによって実現できる。この切れ目は、積層の形成によって実現できる。また、サポータ部１０１内部の流路形成領域に、光あるいは熱に反応して発泡する発泡剤を注入しておき、この発泡剤に光あるいは熱を照射することによって膨張させて気泡を形成するようにしてもよい。 In addition, as shown in FIG. 26, bubbles 35 are formed inside the supporter part 101 in the flow path forming region, and at least the back side of the supporter part 101 is a convex part, and the supporter part 101 on the side surface of the convex part is separated from the organ surface 8. The space between the supporter 101 and the organ surface 8 may be separated and used as the flow path 32. The formation of the bubbles 35 can be realized by making a cut corresponding to the flow path forming region inside the supporter 101 and injecting air into the cut. This break can be realized by forming a laminate. In addition, a foaming agent that foams in response to light or heat is injected into the flow path forming region inside the supporter 101, and the foaming agent is expanded by irradiating light or heat to form bubbles. It may be.
　さらに、図２７に示すように、サポータ部１０１内の流路形成領域に連通孔３６であるルーメンを形成して流路３２としてもよい。また、図２８に示すように、このルーメン内に多孔質材３７を充填して流路３２を形成してもよい。この多孔質材３７は、たとえば、人工腎臓などに用いられる内径１００μｍ程度の中空糸（ホローファイバ）を束ねたもので実現される。この中空糸は、再生セルロース（キュプロファン、アセチルセルロースなど）、ポリメチルメタクリレート、ポリビニルアルコールエチレン共重合体、ポリスルフォンなどによって実現される。さらに、塩化ビニルなどの素材を一部に有するサポータ部１０１に対して、目的のルーメン形状に沿って紫外線を焦点し、塩化ビニルの架橋構造を破壊して、多孔構造を形成させてもよい。 Further, as shown in FIG. 27, a lumen that is a communication hole 36 may be formed in the flow path forming region in the supporter 101 to form the flow path 32. In addition, as shown in FIG. 28, the lumen 32 may be filled with a porous material 37 to form the flow path 32. The porous material 37 is realized by, for example, a bundle of hollow fibers (hollow fibers) having an inner diameter of about 100 μm used for artificial kidneys and the like. This hollow fiber is realized by regenerated cellulose (such as cuprophan or acetyl cellulose), polymethyl methacrylate, polyvinyl alcohol ethylene copolymer, polysulfone, or the like. Furthermore, the supporter 101 having a part of a material such as vinyl chloride may focus on ultraviolet rays along a target lumen shape to destroy the crosslinked structure of vinyl chloride, thereby forming a porous structure.
（実施の形態４）
　つぎに、この発明の実施の形態４について説明する。この実施の形態４では、さらにサポータ部１０１と体内臓器４との間に、スペーサを設け、空室２３に対応する空室を確実に形成できるようにしている。 (Embodiment 4)
Next, a fourth embodiment of the present invention will be described. In the fourth embodiment, a spacer is further provided between the supporter 101 and the internal organ 4 so that a vacancy corresponding to the vacancy 23 can be reliably formed.
　図２９は、この発明の実施の形態４であるカテーテルの設置態様を示す模式図である。図２９に示すように、この実施の形態４では、サポータ部１０１と体内臓器４との間で、サポータ部１０１に覆われるスペーサ４０を設ける。このスペーサ４０は、図１６に示した空室２３を確実に形成するためのものであり、側壁４２と、側壁４２の周縁であって体内臓器４側に形成されたフランジ４１とを有する。側壁４２は、空室２３に対応する空室４５を囲むように形成する。この側壁４２が形成する円筒には、サポータ部１０１側の上部開口４３と、体内臓器４側の下部開口４４とが形成されている。上部開口４３には、サポータ部１０１が覆われるが、この際、チューブ２が結合するサポータ部１０１のチューブ２側の開口が、上部開口４３内に位置するように覆う。一方、フランジ４１の裏面は、密着領域２１と同様に滑らかな表面となっており、体内臓器４の臓器表面８と密着してスペーサ４０を固着する。 FIG. 29 is a schematic diagram showing an installation mode of the catheter according to the fourth embodiment of the present invention. As shown in FIG. 29, in the fourth embodiment, a spacer 40 covered with the supporter unit 101 is provided between the supporter unit 101 and the internal organ 4. This spacer 40 is for reliably forming the empty space 23 shown in FIG. 16, and has a side wall 42 and a flange 41 formed on the side of the body organ 4 at the periphery of the side wall 42. The side wall 42 is formed so as to surround the empty room 45 corresponding to the empty room 23. An upper opening 43 on the supporter 101 side and a lower opening 44 on the body organ 4 side are formed in the cylinder formed by the side wall 42. The upper opening 43 covers the supporter part 101. At this time, the opening on the tube 2 side of the supporter part 101 to which the tube 2 is coupled is covered with the upper opening 43. On the other hand, the back surface of the flange 41 has a smooth surface like the contact area 21, and is in close contact with the organ surface 8 of the internal organ 4 to fix the spacer 40.
　最終的に、図２９（ｂ）に示すように、スペーサ４０が所定の容積をもつ空室４５を確保しつつ、サポータ部１０１の周縁の密着領域２１によってさらに閉空間としての空室４５を確実にしている。すなわち、サポータ部１０１の開口１２は、実質的にスペーサ４０下部の開口１２ａとなる。このスペーサ４０を用いることによって、空室４５を確実に確保することができ、しかも、開口１２ａを介して、薬剤の投与領域を確実に広く得ることができる。特に、経時的に非密着領域２２の一部が密着領域２１に変化したり、密着領域２１の一部が非密着領域２２に変化したりする領域境界の不安定さが軽減され、安定して必要な非密着領域２２を確保できる。 Finally, as shown in FIG. 29 (b), the spacer 40 ensures a vacant chamber 45 having a predetermined volume, and the vacant chamber 45 as a closed space is further ensured by the contact region 21 at the periphery of the supporter 101. I have to. That is, the opening 12 of the supporter portion 101 is substantially the opening 12 a below the spacer 40. By using this spacer 40, the vacant chamber 45 can be reliably ensured, and the medicine administration region can be reliably widened through the opening 12a. In particular, the instability of the region boundary in which a part of the non-contact region 22 changes to the contact region 21 or a part of the contact region 21 changes to the non-contact region 22 with time is reduced, and stable. The necessary non-contact area 22 can be secured.
　なお、図３０に示すように、図２３に対応した非密着領域２２および空室２３ａを形成できるスペーサ５０としてもよい。この場合も、チューブ２側の開口が、上部開口５３に位置するように、サポータ部１０１が覆われる。また、サポータ部１０１は、側面開口５５を覆わないことが好ましいが、覆ってもよい。なお、スペーサ５０は、上部開口５３を有するサポータ部１０１側の上面と、体内臓器４側に形成される下部開口５４と、側壁５２と、側面開口５５とによって空室を形成する。 In addition, as shown in FIG. 30, it is good also as the spacer 50 which can form the non-contact | adherence area | region 22 and the empty room 23a corresponding to FIG. Also in this case, the supporter 101 is covered so that the opening on the tube 2 side is located in the upper opening 53. Further, the supporter unit 101 preferably does not cover the side opening 55, but may cover it. The spacer 50 forms an empty space by the upper surface on the supporter 101 side having the upper opening 53, the lower opening 54 formed on the body organ 4 side, the side wall 52, and the side surface opening 55.
　さらに、図３１に示すように、図２４に対応した非密着領域２２および空室２３ｂ，２３ｃを形成できるスペーサ６０としてもよい。この場合、チューブ２側の開口が上部開口６４に位置するように、サポータ部１０１が覆われる。ここで、空室２３ｂ，２３ｃに対応する空室６９ｂ，６９ｃを形成するために、側壁６２，６３およびフランジ６１が設けられ、さらに下部開口６５，６７が形成され、空室６９ｂ，６９ｃ間を接続するためのブリッジ部６８が設けられている。このブリッジ部６８に、各空室６９ｂ，６９ｃ間を連通させる流路を形成してもよいし、形成しなくてもよい。また、流路を設けた場合、上部開口６６を塞ぐようにしてもよい。 Furthermore, as shown in FIG. 31, a spacer 60 that can form the non-contact region 22 and the vacant spaces 23b and 23c corresponding to FIG. In this case, the supporter unit 101 is covered such that the opening on the tube 2 side is located in the upper opening 64. Here, in order to form the empty chambers 69b and 69c corresponding to the empty chambers 23b and 23c, the side walls 62 and 63 and the flange 61 are provided, and further the lower openings 65 and 67 are formed, and the space between the empty chambers 69b and 69c is formed. A bridge portion 68 for connection is provided. The bridge portion 68 may or may not be formed with a flow path that communicates between the vacancies 69b and 69c. Further, when the flow path is provided, the upper opening 66 may be blocked.
　なお、上述した実施の形態４では、フランジ４１，５１，６１の各裏面などによってスペーサ４０，５０，６０を体内臓器４に密着固定するようにしていたが、これに限らず、縫合、接着等によってスペーサ４０，５０，６０を体内臓器４に固定するようにしてもよい。 In the above-described fourth embodiment, the spacers 40, 50, 60 are tightly fixed to the internal organ 4 by the back surfaces of the flanges 41, 51, 61. However, the present invention is not limited to this, and stitching, adhesion, etc. The spacers 40, 50, 60 may be fixed to the internal organ 4.
　この実施の形態３，４では、パッドとして、体内臓器を巻回するサポータとして機能するサポート部を用いているので、臓器表面への薬剤投与を安定かつ確実に行うことができる。 In the third and fourth embodiments, since the support portion functioning as a supporter for winding the body organ is used as the pad, it is possible to stably and reliably administer the drug to the organ surface.
（実施の形態５）
　　つぎに、この発明の実施の形態５について説明する。図３２は、この発明の実施の形態５にかかるカテーテルが人体に適用された状態を示す模式図である。また、図３３は、図３２に示したカテーテルの薬剤吐出部を体内臓器側からみた図である。さらに、図３４は、図３２に示したカテーテルの薬剤吐出部の分解斜視図である。図３２では、たとえば、肝臓などの体内臓器４の表面に対して数十ｍｌ程度の抗癌剤などの薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与する場合を示している。なお、ここでいう薬剤には、液状およびゲル状の薬剤を含む。 (Embodiment 5)
Next, a fifth embodiment of the present invention will be described. FIG. 32 is a schematic diagram illustrating a state in which the catheter according to the fifth embodiment of the present invention is applied to a human body. FIG. 33 is a view of the drug discharge portion of the catheter shown in FIG. 32 as viewed from the internal organ side. Further, FIG. 34 is an exploded perspective view of the medicine discharge section of the catheter shown in FIG. FIG. 32 shows a case where, for example, a planned dosing is performed by continuously and intensively discharging a drug such as an anticancer drug of about several tens of ml to the surface of a body organ 4 such as the liver over a long period of about one week. ing. In addition, the chemical | medical agent here contains a liquid and a gel-form chemical | medical agent.
　図３２～図３４において、カテーテル１０は、薬剤通路であるチューブ２とシート状の薬剤吐出部２０１とを有する。チューブ２は、体表６に取り付けられた薬剤投入装置３に接続されるとともに、コネクタ２１６ａを介して薬剤吐出部２０１に接続される。薬剤吐出部２０１は、本発明のパッドに対応し、臓器支持組織５によって体内で支えられている体内臓器４表面に密着して該体内臓器４に固着され、薬剤投入装置３からチューブ２を介して供給される薬剤を体内臓器４表面に浸透させる。薬剤投入装置３は、上述したように体内臓器４の表面に対して数十ｍｌ程度の薬剤を、１週間程度の長期間にわたり連続的かつ集中的に吐出して計画投与するものであり、たとえば、薬剤リザーバ内に蓄積された薬剤を、電気浸透流ポンプなどによって微量に押し出し、カテーテル１０を介して投与する。すなわち、薬剤投入装置３から規定された量の薬剤がチューブ２を通って体内に導入され、薬剤は、薬剤吐出部２０１の裏面から、選択される所定範囲に拡散し、体内臓器４にその表面から吸収される。なお、薬剤投入装置３は、体表６に取り付けてある必要はなく、例えば、体内に埋め込む構成や、体外に離間して配置する構成が可能である。 32 to 34, the catheter 10 includes a tube 2 that is a drug passage and a sheet-like drug discharge unit 201. The tube 2 is connected to the medicine injection device 3 attached to the body surface 6 and is connected to the medicine ejection unit 201 via the connector 216a. The drug discharge unit 201 corresponds to the pad of the present invention, is in close contact with the surface of the internal organ 4 supported in the body by the organ support tissue 5, and is fixed to the internal organ 4. The drug to be supplied is penetrated into the body organ 4 surface. As described above, the drug injection device 3 is a device that plans and administers several tens of ml of drug to the surface of the internal organ 4 continuously and intensively over a long period of about one week. The medicine accumulated in the medicine reservoir is pushed out in a minute amount by an electroosmotic flow pump or the like and administered through the catheter 10. That is, a prescribed amount of medicine is introduced from the medicine injection device 3 into the body through the tube 2, and the medicine diffuses from the back surface of the medicine ejection section 201 to a predetermined range to be selected, and the surface of the body organ 4 Is absorbed from. In addition, the chemical | medical agent injection apparatus 3 does not need to be attached to the body surface 6, For example, the structure embedded in a body and the structure arrange | positioned apart from the body are possible.
　薬剤吐出部２０１は、図３４に示すように、上層２１３、中間層２１４、下層２１５からなる３層構造をなし、互いに接着される。中間層２１４は、上層２１３および下層２１５によって挟まれ、柔軟な生体適合性のある素材、例えばシリコンゴム等で実現され、好ましくは０．５ｍｍ～５ｍｍの肉厚な層である。上層２１３は、柔軟な生体適合性のある素材、たとえばポリエチレン等で実現され、中間層２１４に比して肉薄で、好ましくは０．０５ｍｍ～０．３ｍｍの層である。下層２１５は、たとえばポリスルホンによって実現され、薬剤を透過させる柔軟で生体適合性のある素材で、中間層２１４に比して肉薄で、好ましくは０．０５ｍｍ～０．３ｍｍの層である。 As shown in FIG. 34, the medicine ejection unit 201 has a three-layer structure including an upper layer 213, an intermediate layer 214, and a lower layer 215, and is bonded to each other. The intermediate layer 214 is sandwiched between the upper layer 213 and the lower layer 215 and is made of a flexible biocompatible material such as silicon rubber, and is preferably a thick layer of 0.5 mm to 5 mm. The upper layer 213 is made of a flexible biocompatible material, such as polyethylene, and is thinner than the intermediate layer 214, preferably a layer having a thickness of 0.05 mm to 0.3 mm. The lower layer 215 is made of, for example, polysulfone, and is a flexible and biocompatible material that allows a drug to permeate. The lower layer 215 is thinner than the intermediate layer 214, and preferably has a thickness of 0.05 mm to 0.3 mm.
　上層２１３は、薄膜がチューブ２側に引き出された突出部２１７を有する。突出部２１７の先端には、コネクタ２１６ｂが設けられ、コネクタ２１６ａとコネクタ２１６ｂとが接続されることによって、チューブ２に連結される。すなわち、コネクタ２１６ａ，２１６ｂの連結によって、突出部２１７の先端の開口とチューブ２の内部通路とが連通する。 The upper layer 213 has a protruding portion 217 from which the thin film is drawn to the tube 2 side. A connector 216b is provided at the tip of the projecting portion 217, and is connected to the tube 2 by connecting the connector 216a and the connector 216b. That is, the connection between the connectors 216a and 216b allows the opening at the tip of the protrusion 217 to communicate with the internal passage of the tube 2.
　中間層２１４の内部には、第１の開口２０７、第２の開口２０８、および第１の開口２０７および第２の開口２０８間を連通する流路２０９が形成されている。第１の開口２０７の開口領域には、突出部２１７が配置される。流路２０９内には、初期状態で薬剤の流れを許可し、外部からのエネルギーを受けて薬剤の流れを禁止する第１のゲート機構２１１と、初期状態で薬剤の流れを禁止し、外部からのエネルギーを受けて薬剤の流れを許可する第２のゲート機構２１２とが設けられている。なお、第１のゲート機構２１１および第２のゲート機構２１２は、いずれか一方のみが設けられればよく、説明の都合上、図３３および図３４では、第１のゲート機構２１１および第２のゲート機構２１２の双方を流路２０９内に配置した構成を示している。 Inside the intermediate layer 214, a first opening 207, a second opening 208, and a flow path 209 communicating between the first opening 207 and the second opening 208 are formed. A protrusion 217 is disposed in the opening region of the first opening 207. In the flow path 209, the first gate mechanism 211 that permits the flow of the drug in the initial state and prohibits the flow of the drug by receiving energy from the outside, and prohibits the flow of the drug in the initial state, And a second gate mechanism 212 that accepts the energy of the medicine and permits the flow of the medicine. Note that only one of the first gate mechanism 211 and the second gate mechanism 212 may be provided. For convenience of explanation, in FIGS. 33 and 34, the first gate mechanism 211 and the second gate mechanism 212 are provided. A configuration in which both of the mechanisms 212 are arranged in the flow path 209 is shown.
　なお、下層２１５は、薬剤のみが透過する浸透膜ではなく、第１の開口２０７および第２の開口２０８に対応する領域のみが開口した薄膜であってもよい。 Note that the lower layer 215 may be a thin film in which only regions corresponding to the first opening 207 and the second opening 208 are opened, instead of the permeable membrane through which only the drug permeates.
　薬剤投入装置３から供給される薬剤は、チューブ２、コネクタ２１６ａ，２１６ｂを介して薬剤吐出部２０１の上層２１３の突出部２１７に導入され、さらに中間層２１４の第１の開口２０７に導入される。第１の開口２０７に導入された薬剤は、第１の開口２０７に対応する下層２１５の領域を透過して体内臓器４表面から体内に浸透する。ここで、第１のゲート機構２１１は、初期状態で薬剤の流れを許可するため、薬剤は、第１の開口２０７から第２の開口２０８側に向けて流路２０９を進行するが、初期状態で薬剤の流れを禁止する第２のゲート機構２１２によって薬剤の流れが阻止され、薬剤は、第２の開口２０８には導入されない。この結果、薬剤は、第１の開口２０７に対応する体内臓器４の表面のみに供給されることになる。なお、流路２０９上であって、第１の開口２０７と第２のゲート機構２１２との間に対応する領域からも体内臓器４表面に薬剤が供給されるが、線状領域であるため、無視できる程度の薬剤供給である。 The medicine supplied from the medicine injection device 3 is introduced into the protruding portion 217 of the upper layer 213 of the medicine ejection section 201 via the tube 2 and the connectors 216a and 216b, and further introduced into the first opening 207 of the intermediate layer 214. . The drug introduced into the first opening 207 passes through the region of the lower layer 215 corresponding to the first opening 207 and permeates into the body from the surface of the internal organ 4. Here, since the first gate mechanism 211 permits the flow of the medicine in the initial state, the medicine travels through the flow path 209 from the first opening 207 toward the second opening 208 side. Therefore, the second gate mechanism 212 that inhibits the flow of the drug prevents the flow of the drug, and the drug is not introduced into the second opening 208. As a result, the medicine is supplied only to the surface of the internal organ 4 corresponding to the first opening 207. Note that the drug is supplied to the surface of the internal organ 4 from the corresponding region between the first opening 207 and the second gate mechanism 212 on the flow path 209, but is a linear region. The drug supply is negligible.
　その後、第２のゲート機構２１２が、外部からエネルギーを受けて、薬剤の流れを禁止する状態から薬剤の流れを許可する状態に遷移すると、流路２０９は、第１の開口２０７と第２の開口２０８との間が連通状態となり、第１の開口２０７に供給された薬剤は、流路２０９を介して第２の開口２０８に供給され、第２の開口２０８に対応する下層２１５の領域を透過して体内臓器４表面に供給される。すなわち、第２の開口２０８は、薬剤の吐出が禁止された不活性状態から薬剤を吐出する活性状態に遷移する。なお、この場合、第１の開口２０７に対応する体内臓器４表面からも薬剤が供給される。 Thereafter, when the second gate mechanism 212 receives energy from the outside and makes a transition from a state in which the flow of the medicine is prohibited to a state in which the flow of the medicine is permitted, the flow path 209 includes the first opening 207 and the second flow path 209. The medicine is supplied to the first opening 207 via the flow path 209, and the region of the lower layer 215 corresponding to the second opening 208 is communicated with the opening 208. It penetrates and is supplied to the surface of the internal organ 4. That is, the second opening 208 transitions from an inactive state in which medicine ejection is prohibited to an active state in which medicine is ejected. In this case, the medicine is also supplied from the surface of the internal organ 4 corresponding to the first opening 207.
　その後、さらに第１のゲート機構２１１が、外部からエネルギーを受けて、薬剤の流れを許可する状態から禁止する状態に遷移すると、流路２０９は、第１の開口２０７と第２の開口２０８との間が非連通状態となり、第１の開口２０７に供給された薬剤は、第１の開口２０７に対応する下層２１５の領域のみから体内臓器４表面に薬剤が供給される。すなわち、第２の開口２０８は、薬剤が吐出される活性状態から、薬剤の吐出が禁止された不活性状態に遷移する。このようにして、結果的に、薬剤量の位置的な分布の動的変化を簡易に行うことができる。 Thereafter, when the first gate mechanism 211 further receives energy from the outside and transitions from a state in which the medicine flow is permitted to a state in which the medicine is prohibited, the flow path 209 includes the first opening 207 and the second opening 208. The drug supplied to the first opening 207 is supplied from the region of the lower layer 215 corresponding to the first opening 207 to the surface of the body organ 4 only. That is, the second opening 208 transitions from an active state in which the medicine is discharged to an inactive state in which the discharge of the medicine is prohibited. In this way, as a result, the dynamic change of the positional distribution of the drug amount can be easily performed.
　ここで、第２のゲート機構２１２は、図３５に示すように、流路２０９の側面に対向して設けられた１対の凹部２１９に、外部からの超音波衝撃波などで破壊するシリカ・アルミナ・燐酸カルシウム系セラミックスなどによって実現されるセラミックスで形成された円柱状のペレット２１８が挿入されて構成される。ペレット２１８は、凹部２１９に挿入されて流路２０９に係止されることによって流路２０９を塞ぐ。 Here, as shown in FIG. 35, the second gate mechanism 212 is a silica-alumina that breaks into a pair of recesses 219 provided facing the side surface of the flow path 209 by an ultrasonic shock wave or the like from the outside. A cylindrical pellet 218 formed of ceramics realized by calcium phosphate ceramics is inserted. The pellet 218 closes the flow path 209 by being inserted into the recess 219 and locked to the flow path 209.
　ペレット２１８は、外部からカテーテル１０の表面を介してエネルギーを受けると破壊する被破壊部材である。したがって、ペレット２１８が破壊されることによって、第２のゲート機構２１２は、薬剤の流れを禁止する状態から薬剤の流れを許容する。 The pellet 218 is a member to be destroyed that is destroyed when receiving energy through the surface of the catheter 10 from the outside. Therefore, when the pellet 218 is destroyed, the second gate mechanism 212 allows the drug flow from a state in which the drug flow is prohibited.
　一方、第１のゲート機構２１１は、図３６および図３７に示すように、流路２０９の一方の側部に、円柱状のペレット２２０を係止する凹部２２３が形成されるとともに、凹部２２３に対向する側部に弾性片２２５を収納する凹部であるスペース２２４が形成される。弾性片２２５は、たとえば生体親和性のあるコーティングが施された鋼などの金属で実現され、一端が、スペース２２４が形成された流路２０９の側部であってスペース２２４近傍に片持ち支持され、他端が、ペレット２２０に押圧されてスペース２２４内に収納される。 On the other hand, as shown in FIG. 36 and FIG. 37, the first gate mechanism 211 is formed with a recess 223 that locks the columnar pellet 220 on one side of the flow path 209 and at the recess 223. A space 224 that is a recess for accommodating the elastic piece 225 is formed on the opposite side portion. The elastic piece 225 is realized by a metal such as steel having a biocompatible coating, for example, and one end is cantilevered in the vicinity of the space 224 on the side of the flow path 209 in which the space 224 is formed. The other end is pressed by the pellet 220 and stored in the space 224.
　ペレット２２０は、一方の側面から他方の側面に貫通する開口２２２を有した連通孔２２１が形成され、連通孔２２１の連通方向が、流路２０９の流れ方向に一致するように流路２０９に挿入され、係止される。一方、弾性片２２５は、図３７（ｂ）に示すように、ペレット２２０が存在しない場合に、自己の弾性力によって流路２０９を塞ぎ、薬剤の流れを禁止する。ここで、第１のゲート機構２１１は、図３７（ａ）に示すように、ペレット２２０が流路２０９に係止された状態で、弾性片２２５がペレット２２０を凹部２２３側に押圧する状態となるように設置される。すなわち、弾性片２２５は、流路２０９を塞いで薬剤の流れを禁止する位置に移動するように自己の弾性力によって付勢されている付勢部材である。したがって、弾性片２２５に替えて、伸張バネ等によって付勢する付勢部材であってもよい。 The pellet 220 is formed with a communication hole 221 having an opening 222 penetrating from one side surface to the other side surface, and the pellet 220 is inserted into the flow channel 209 so that the communication direction of the communication hole 221 matches the flow direction of the flow channel 209. And locked. On the other hand, as shown in FIG. 37 (b), the elastic piece 225 blocks the flow path 209 with its own elastic force and inhibits the flow of the drug when the pellet 220 is not present. Here, as shown in FIG. 37A, the first gate mechanism 211 is in a state where the elastic piece 225 presses the pellet 220 toward the concave portion 223 while the pellet 220 is locked to the flow path 209. It is installed to become. That is, the elastic piece 225 is an urging member that is urged by its own elastic force so as to move to a position where the flow path 209 is blocked and the flow of the medicine is prohibited. Therefore, instead of the elastic piece 225, a biasing member that biases by an extension spring or the like may be used.
　ここで、ペレット２２０は、ペレット２１８と同様に、カテーテル１０の表面を介してエネルギーを受けると破壊するセラミックスなどによって実現される被破壊部材によって形成される。そして、ペレット２２０が破壊されない図３７（ａ）の状態では、薬剤の流れを許可する状態となり、ペレット２２０が破壊されると、弾性片２２５が図３７（ｂ）に示すように、自己の弾性力によって流路２０９を塞ぐ位置に移動して、流路２０９を塞ぐ。 Here, similarly to the pellet 218, the pellet 220 is formed of a member to be destroyed realized by ceramics or the like that breaks when receiving energy through the surface of the catheter 10. In the state of FIG. 37 (a) where the pellet 220 is not broken, the flow of the medicine is allowed. When the pellet 220 is broken, the elastic piece 225 becomes elastic as shown in FIG. 37 (b). It moves to a position where the flow path 209 is closed by force, and closes the flow path 209.
　なお、ペレット２１８，２２０は、セラミックスに限らず、外部から供給されるエネルギーとの関係で、ガラスやプラスチック等の種々の材質で実現してもよい。同様に、ペレット２１８，２２０を破壊する外部から供給されるエネルギーも、音波、超音波、赤外線と可視光を含む電磁波、衝撃波、機械振動などの各種波動エネルギーを用いることができる。さらに、伝導によって伝わる熱エネルギーでもよい。なお、熱は、赤外線による波動エネルギーとして伝えることもできる。 The pellets 218 and 220 are not limited to ceramics, and may be realized with various materials such as glass and plastic in relation to energy supplied from the outside. Similarly, as the energy supplied from the outside that destroys the pellets 218 and 220, various wave energies such as sound waves, ultrasonic waves, electromagnetic waves including infrared rays and visible light, shock waves, and mechanical vibrations can be used. Furthermore, it may be thermal energy transmitted by conduction. Heat can also be transmitted as wave energy by infrared rays.
　また、ペレット２１８，２２０は、外部からのエネルギーによって変形する変形部材であってもよい。たとえば、熱エネルギーによって変形する熱可塑性のプラスチックであってもよい。 Further, the pellets 218 and 220 may be deformable members that are deformed by external energy. For example, it may be a thermoplastic plastic that is deformed by thermal energy.
　さらに、ペレット２１８は、内部に空気などの流体を有したバルーンなどによって形成してもよい。このバルーンは、気泡によって実現してもよい。また、バルーンを破壊せずに、バルーン内の流体の膨張・収縮を行うことによって、流路２０９の開閉を行う可逆性のゲート機構としてもよい。 Furthermore, the pellet 218 may be formed by a balloon having a fluid such as air inside. This balloon may be realized by bubbles. Further, a reversible gate mechanism that opens and closes the flow path 209 by expanding and contracting the fluid in the balloon without destroying the balloon may be used.
　ここで、図３８および図３９を参照して、外部からカテーテル１０の表面を介してゲート機構２１１，２１２にエネルギーを供給する機構の一例について説明する。図３８は、体外から音波、超音波、衝撃波などの波動エネルギーを照射する状態を示す模式図である。図３８において、波動エネルギー発生装置２３１は、ドライバ２３２から信号線２３３を介して供給される信号をもとに波動エネルギーを発生する。波動エネルギーは、波動エネルギー発生装置２３１のゲート機構２１８，２２０側に設けられた波動レンズ２３０によって集約され、ゲート機構２１８，２２０に照射される。なお、波動エネルギー発生装置２３１としては、超音波振動子、衝撃波発生装置、音波源などによって実現される。 Here, an example of a mechanism for supplying energy to the gate mechanisms 211 and 212 from the outside via the surface of the catheter 10 will be described with reference to FIGS. FIG. 38 is a schematic diagram illustrating a state in which wave energy such as a sound wave, an ultrasonic wave, and a shock wave is applied from outside the body. In FIG. 38, the wave energy generator 231 generates wave energy based on the signal supplied from the driver 232 via the signal line 233. The wave energy is collected by the wave lens 230 provided on the side of the gate mechanisms 218 and 220 of the wave energy generator 231 and is irradiated to the gate mechanisms 218 and 220. The wave energy generation device 231 is realized by an ultrasonic transducer, a shock wave generation device, a sound wave source, or the like.
　一方、図３９では、硬性鏡２３４の内部チャネルを通して、エネルギー発生装置２３５のエネルギー発生部を体内に挿入し、エネルギー発生部をゲート機構２１８，２２０の近傍に位置させ、エネルギー発生部からゲート機構２１８，２２０にエネルギーを供給する。なお、エネルギー発生装置２３５は、ドライバ２４０から信号線２４１を介して供給される信号をもとにエネルギー発生部からエネルギーを発生させる。なお、エネルギーとしては、たとえば、ホルミウム・ＹＡＧレーザによるレーザ光や、超音波、高周波、機械振動などが用いられる。もちろん、伝導によって伝わる熱であってもよい。 On the other hand, in FIG. 39, the energy generation unit of the energy generation device 235 is inserted into the body through the internal channel of the rigid endoscope 234, the energy generation unit is positioned in the vicinity of the gate mechanisms 218 and 220, and the energy generation unit to the gate mechanism 218. , 220 is supplied with energy. The energy generation device 235 generates energy from the energy generation unit based on a signal supplied from the driver 240 via the signal line 241. As the energy, for example, laser light by holmium / YAG laser, ultrasonic wave, high frequency, mechanical vibration, or the like is used. Of course, it may be heat transmitted by conduction.
（実施の形態５の変形例１）
　ここで、薬剤吐出部２０１の変形例について説明する。図４０は、薬剤吐出部２０１の変形例１である薬剤吐出部２５０を裏面側からみた図である。薬剤吐出部２０１は、第２の開口２０８が１つであったが、この薬剤吐出部２５０は、複数の第２の開口２５２を有している。すなわち、第１の開口２０７に対応する第１の開口２５１と、４つの第２の開口２５２とが放射状に設けられ、第１の開口２５１と第２の開口２５２との間にそれぞれ４つの流路２０９が設けられ、各流路２０９には、薬剤吐出部２０１と同様に、それぞれ第１のゲート機構２１１と第２のゲート機構２１２とが設けられている。なお、下層２１５は、ここでは、浸透膜ではなく、第１の開口２５１および第２の開口２５２に対応する領域のみに開口を有するようにしている。これによって、各流路２０９のゲート機構２１１，２１２に対してエネルギーを与えることによって各ゲート機構２１１，２１２がオンオフし、薬剤が供給される領域を動的に変化させることができる。 (Modification 1 of Embodiment 5)
Here, a modified example of the medicine ejection unit 201 will be described. FIG. 40 is a view of a medicine ejection unit 250, which is Modification 1 of the medicine ejection unit 201, as viewed from the back side. The medicine ejection unit 201 has one second opening 208, but the medicine ejection unit 250 has a plurality of second openings 252. In other words, the first opening 251 corresponding to the first opening 207 and the four second openings 252 are provided in a radial pattern, and each of the four flow paths is provided between the first opening 251 and the second opening 252. A channel 209 is provided, and each channel 209 is provided with a first gate mechanism 211 and a second gate mechanism 212, respectively, similarly to the medicine ejection unit 201. Here, the lower layer 215 is not an osmotic membrane, but has an opening only in a region corresponding to the first opening 251 and the second opening 252. Thus, by applying energy to the gate mechanisms 211 and 212 of each flow path 209, the gate mechanisms 211 and 212 are turned on and off, and the region to which the medicine is supplied can be dynamically changed.
（実施の形態５の変形例２）
　さらに、薬剤吐出部２０１の変形例について説明する。図４１に示した薬剤吐出部２６０では、さらに第２の開口２０８に対応した第２の開口２６２を、第１の開口２６１の周囲に１２個設けている。そして、第１の開口２６１と第２の開口２６２との間の流路２０９をネットワーク状にし、流路２０９が交差する交差部にゲート機構２１１を設けている。いわゆるネットワークにおけるノードの開閉を行うようにしている。なお、下層２１５は、薬剤のみを浸透する浸透膜ではなく、第１の開口２６１および第２の開口２６２に対応する領域のみが開口している。ゲート機構２１１は、エネルギーの供給によって破壊するものであるため、図４１では、初期状態において薬剤の供給は、第１の開口２６１に対応する領域のみとなる。これによって、きめ細かく薬剤供給分布を動的に変更することができる。なお、ゲート機構２１１に限らず、ゲート機構２１２を適宜組み合わせても良いし、可逆性のある開閉を行うゲート機構としてもよい。さらに、ゲート機構は、ノードに限らず、流路２０９上に設けてもよい。 (Modification 2 of Embodiment 5)
Furthermore, a modified example of the medicine ejection unit 201 will be described. In the medicine ejection unit 260 shown in FIG. 41, 12 second openings 262 corresponding to the second openings 208 are further provided around the first openings 261. The flow path 209 between the first opening 261 and the second opening 262 is networked, and a gate mechanism 211 is provided at an intersection where the flow paths 209 intersect. Nodes in the so-called network are opened and closed. Note that the lower layer 215 is not a permeable membrane that allows only the drug to permeate, and only the regions corresponding to the first opening 261 and the second opening 262 are open. Since the gate mechanism 211 is destroyed by the supply of energy, in FIG. 41, in the initial state, the medicine is supplied only in the region corresponding to the first opening 261. As a result, the drug supply distribution can be dynamically changed in detail. Not only the gate mechanism 211 but also a gate mechanism 212 may be appropriately combined, or a gate mechanism that performs reversible opening and closing may be used. Further, the gate mechanism is not limited to the node and may be provided on the flow path 209.
　なお、変形例１，２では、第１の開口と第２の開口との間に流路２０９が形成されるようにしているが、流路２０９の空き領域に第１の開口あるいは第２の開口を密に配置することが好ましい。また、第３の開口をさらに設けるとともに第２の開口と第３の開口とをつなぐ流路をさらに設けるとともに、この流路内にゲート機構を設け、薬剤供給分布をさらにきめ細かく制御可能にすることが好ましい。 In the first and second modified examples, the flow path 209 is formed between the first opening and the second opening. However, the first opening or the second opening is formed in an empty area of the flow path 209. It is preferable to arrange the openings densely. In addition, a third opening is further provided, a flow path connecting the second opening and the third opening is further provided, and a gate mechanism is provided in the flow path so that the medicine supply distribution can be controlled more finely. Is preferred.
　さらに、１つの流路２０９内に異種のエネルギーによって開閉するゲート機構を複数設けてもよい。たとえば、衝撃波によって破壊するゲート機構と熱によって破壊するゲート機構とを設けるようにしてもよい。この場合、流路２０９の開閉を多段階によって行うことができ、さらにきめ細かく薬剤供給分布を動的に変更することができる。 Furthermore, a plurality of gate mechanisms that open and close by different kinds of energy may be provided in one flow path 209. For example, a gate mechanism that is broken by a shock wave and a gate mechanism that is broken by heat may be provided. In this case, the flow path 209 can be opened and closed in multiple stages, and the drug supply distribution can be dynamically changed more finely.
（実施の形態５の変形例３）
　上述した実施の形態５では、主に体内臓器４表面にシート状の薬剤吐出部２０１，２５０，２６０を用いて直接薬剤を供給するものであったが、この変形例３では、チューブ２上にゲート機構を設けている。すなわち、この変形例３のカテーテル２７０は、図４２に示すように、チューブ２の途中に分岐ユニット２７３を設け、分岐ユニット２７３の吐出側に複数のチューブ２７１が接続される。分岐ユニット２７３の薬剤投入装置３側は、コネクタ２７４ａ，２７４ｂによって接続される。複数のチューブ２７１の各先端には、薬剤を吐出する開口を有した穿刺針２７２が接続されている。 (Modification 3 of Embodiment 5)
In the fifth embodiment described above, the drug is supplied directly to the surface of the internal organ 4 mainly using the sheet-like drug discharge units 201, 250, and 260. A gate mechanism is provided. That is, as shown in FIG. 42, the catheter 270 of this modification 3 is provided with a branch unit 273 in the middle of the tube 2, and a plurality of tubes 271 are connected to the discharge side of the branch unit 273. The medicine injection device 3 side of the branch unit 273 is connected by connectors 274a and 274b. A puncture needle 272 having an opening for discharging a drug is connected to each tip of the plurality of tubes 271.
　このカテーテル２７０は、分岐ユニット２７３が体表に設置され、各チューブ２７１を介して接続される穿刺針２７２が、複数に分散した処置対象である体内臓器などにそれぞれ穿刺された状態となっている。ここで、分岐ユニット２７３内のチューブ２７１は、共通のチューブ２７５を介して分岐接続され、各チューブ２７１上には、ゲート機構２１１，２１２が設けられ、各チューブ２７１のオンオフが選択制御される。 In this catheter 270, the branch unit 273 is installed on the body surface, and the puncture needles 272 connected through the tubes 271 are punctured into a plurality of internal organs to be treated and distributed. . Here, the tubes 271 in the branch unit 273 are branched and connected through a common tube 275, and gate mechanisms 211 and 212 are provided on each tube 271, and on / off of each tube 271 is selectively controlled.
　この変形例３では、チューブ２７１を介した穿刺針２７２による薬剤の吐出を選択的にオンオフ制御することができるので、動的な薬剤供給分布の変更を簡易に行うことができる。 In the third modification, since the discharge of the medicine by the puncture needle 272 via the tube 271 can be selectively turned on / off, the dynamic medicine supply distribution can be easily changed.
（実施の形態５の変形例４）
　上述した実施の形態５では、状態遷移が可逆性のないゲート機構を前提として説明した。すなわち、薬剤の流れを許容するまたは禁止する一方の状態から、薬剤の流れを許容するまたは禁止する他方の状態に遷移した場合には、再び、元の状態に遷移できないゲート機構であった。この変形例４では、薬剤の流れを許容するまたは禁止する一方の状態から他方の状態への遷移を繰り返し行うことができる可逆性のあるゲート機構を実現している。 (Modification 4 of Embodiment 5)
The above-described fifth embodiment has been described on the assumption that the state transition is not reversible. That is, the gate mechanism cannot be changed to the original state again when transitioning from one state permitting or prohibiting the flow of the drug to the other state permitting or prohibiting the flow of the drug. In the fourth modification, a reversible gate mechanism is realized that can repeatedly perform transition from one state that permits or prohibits the flow of medicine to the other state.
　図４３は、この発明の実施の形態５の変形例４のゲート機構の構成を示す分解斜視図である。また、図４４は、図４３に示したゲート機構の動作を示す図である。図４３に示すように、このゲート機構は、流路２０９の断面に対応した開口３０１が形成された金属製のスライダ３００が、流路２０９の途中の両側にそれぞれ形成されたスライダ収容部３０５ａ，３０５ｂにスライド可能に収容される。各スライダ収容部３０５ａ，３０５ｂが流路２０９から延在する奥にはスライダ駆動室３０３ａ，３０３ｂが設けられ、各スライダ駆動室３０３ａ，３０３ｂの流路２０９側の壁には、それぞれ磁石３０４ａ，３０４ｂが埋め込まれる。また、各スライダ駆動室３０３ａ，３０３ｂの流路２０９から離隔する奥側の室内には、それぞれバルーン３０２ａ，３０２ｂが収容される。 FIG. 43 is an exploded perspective view showing the configuration of the gate mechanism of Modification 4 of Embodiment 5 of the present invention. FIG. 44 is a diagram showing the operation of the gate mechanism shown in FIG. As shown in FIG. 43, this gate mechanism has a slider housing portion 305a, in which a metal slider 300 having an opening 301 corresponding to the cross section of the flow path 209 is formed on both sides of the flow path 209. It is slidably accommodated in 305b. Slider drive chambers 303a and 303b are provided at the back of the slider accommodating portions 305a and 305b extending from the flow path 209, and magnets 304a and 304b are provided on the walls of the slider drive chambers 303a and 303b on the flow path 209 side, respectively. Is embedded. In addition, balloons 302a and 302b are accommodated in the interior chambers separated from the flow path 209 of the slider drive chambers 303a and 303b, respectively.
　バルーン３０２ａ，３０２ｂは、純水などの流体をシリコンゴムなどの弾性膜で覆ったものであり、外部からのエネルギー照射（たとえば、レーザ光の照射）によって流体の温度が上がると、流体の気化によって体積が膨張する性質を有する。 The balloons 302a and 302b are made by covering a fluid such as pure water with an elastic film such as silicon rubber. When the temperature of the fluid rises due to external energy irradiation (for example, laser light irradiation), the fluid is vaporized. It has the property of expanding its volume.
　ここで、図４４（ａ）に示す状態では、スライダ３００がスライド収容部３０５ａ側に偏って収容されている。この状態で、スライダ３００に形成された開口３０１は、流路２０９の位置に対応した位置に配置され、流路２０９を通る薬剤は、開口３０１を通って自由に流れることができる。また、この状態では、スライダ３００は、その一端が磁石３０４ｂに引き付けられた状態となっており、他の力が作用しない限り移動しない安定した状態となっている。 Here, in the state shown in FIG. 44 (a), the slider 300 is housed biased toward the slide housing portion 305a. In this state, the opening 301 formed in the slider 300 is disposed at a position corresponding to the position of the flow path 209, and the medicine passing through the flow path 209 can freely flow through the opening 301. Further, in this state, the slider 300 is in a state in which one end thereof is attracted to the magnet 304b, and is in a stable state in which it does not move unless another force is applied.
　この状態で、バルーン３０２ａにレーザ光などを照射して外部エネルギーを与えると、バルーン３０２ａ内の流体が気化してバルーン３０２ａの体積が膨張する。この結果、図４４（ｂ）に示すように、スライダ３００は、スライダ駆動室３０３ｂ側に向かって押され、磁石３０４ｂの引き付け力に抗して解放され、スライダ駆動室３０３ｂ側に向けて移動する。このスライダ３００の位置では、スライダ３００の開口３０１は、流路２０９の位置に対応しておらず、流路２０９がスライダ３００によって塞がれた状態となる。この結果、薬剤の流れは、スライダ３００によって禁止される。また、この状態では、スライダ３００の他端が、磁石３０４ａに引き付けられており、他の力が作用しない限り移動しない安定した状態となっている。 In this state, when external energy is applied by irradiating the balloon 302a with laser light or the like, the fluid in the balloon 302a is vaporized and the volume of the balloon 302a expands. As a result, as shown in FIG. 44B, the slider 300 is pushed toward the slider drive chamber 303b, released against the attracting force of the magnet 304b, and moved toward the slider drive chamber 303b. . At the position of the slider 300, the opening 301 of the slider 300 does not correspond to the position of the flow path 209, and the flow path 209 is closed by the slider 300. As a result, the flow of medicine is prohibited by the slider 300. Further, in this state, the other end of the slider 300 is attracted to the magnet 304a and is in a stable state in which it does not move unless other force is applied.
　その後、図４４（ｃ）に示すように、バルーン３０２ａが冷えて、体積が収縮して元のバルーン３０２ａの体積にもどるが、スライダ３００は、磁石３０４ａの引き付け力によって、スライダ駆動室３０３ｂ側に移動した状態で安定している。 Thereafter, as shown in FIG. 44C, the balloon 302a is cooled and the volume contracts to return to the original volume of the balloon 302a. However, the slider 300 moves toward the slider drive chamber 303b by the attractive force of the magnet 304a. Stable when moved.
　この図４４（ｃ）に示す状態で、バルーン３０２ａと同様に、他方のバルーン３０２ｂに外部からエネルギーを与えれば、スライダ３００は、バルーン３０２ａの膨張によってスライダ駆動室３０３ａ側に移動し、流路２０９は、再び薬剤の流れを許容する状態に戻すことができる。 In the state shown in FIG. 44 (c), if energy is applied to the other balloon 302b from the outside in the same manner as the balloon 302a, the slider 300 moves to the slider drive chamber 303a side due to the expansion of the balloon 302a, and the flow path 209. Can return to a state that allows the flow of the drug again.
　この変形例４に示したゲート機構では、薬剤の流れを許容するまたは禁止する一方の状態から、薬剤の流れを禁止するまたは許容する他方の状態への遷移を可逆的に繰り返し行うことができる。 In the gate mechanism shown in the fourth modification, it is possible to reversibly and repeatedly perform transition from one state in which the flow of medicine is allowed or prohibited to the other state in which the flow of medicine is prohibited or allowed.
　この実施の形態５では、パッドとしての薬剤吐出部２０１内に、ゲート機構を設け、このゲート機構が、薬剤吐出部２０１の外部から伝わるエネルギーを受けて、薬剤吐出部２０１内の薬剤の流れを許容または因子する一方の状態から禁止または許容する他方の状態に遷移するようにしているので、薬剤投与中の患部の変化に応じて投与量分布を動的に変更することができる。 In the fifth embodiment, a gate mechanism is provided in the medicine ejection unit 201 as a pad, and the gate mechanism receives energy transmitted from the outside of the medicine ejection unit 201 to flow the medicine in the medicine ejection unit 201. Since the transition is made from one state that is allowed or allowed to the other state that is prohibited or permitted, the dose distribution can be dynamically changed according to the change in the affected area during drug administration.
　　　１　シート部
　　　２，２７１，２７５　チューブ
　　　３　薬剤投入装置
　　　４　体内臓器
　　　５　臓器支持組織
　　　６　体表
　　　７　薬剤
　　　８　臓器表面
　　　９　粘膜
　　１０，２７０　カテーテル
　　１１　連結部
　　１２　開口
　　２１　密着領域
　　２２，３３　非密着領域
　　２３，２３ａ，２３ｂ，２３ｃ，４５，６９ｂ，６９ｃ　空室
　　３０，３０ａ，３０ｂ　接続部
　　３１　空気抜き弁
　　３５　気泡
　　３６　連通孔
　　３７　多孔質材
　　４０，５０，６０　スペーサ
　　４１，５１，６１　フランジ
　　４２，５２，６２，６３　側壁
　１０１　サポータ部
　１０１ａ～１０１ｅ　連結バンド
　１１１　ホック
　１１２　コード
　１０３　バルーン
　１０４　流体
　１０５　穿刺針
　１０７　切断部
　２０１，２５０，２６０　薬剤吐出部
　２０７，２５１，２６１　第１の開口
　２０８，２５２，２６２　第２の開口
　２０９　流路
　２１１，２１２　ゲート機構
　２１３　上層
　２１４　中間層
　２１５　下層 DESCRIPTION OF SYMBOLS 1 Sheet | seat part 2,271,275 Tube 3 Drug injection device 4 Internal organ 5 Organ support tissue 6 Body surface 7 Drug 8 Organ surface 9 Mucosa 10,270 Catheter 11 Connection part 12 Opening 21 Contact | adherence area | region 22,33 Non-adhesion area | region 23, 23a, 23b, 23c, 45, 69b, 69c Vacant room 30, 30a, 30b Connection part 31 Air vent valve 35 Bubble 36 Communication hole 37 Porous material 40, 50, 60 Spacer 41, 51, 61 Flange 42, 52, 62, 63 Side wall 101 Supporter part 101a-101e Connection band 111 Hook 112 Code 103 Balloon 104 Fluid 105 Puncture needle 107 Cutting part 201,250,260 Drug discharge part 207,251,261 First opening 208,252,262 Second opening 209 channel 211 212 Gate mechanism 213 Upper layer 214 Intermediate layer 215 Lower layer

Claims (56)

  1. 　人間を含む哺乳類の体内臓器に取り付けられるカテーテルであって、
    　薬剤供給源から体内に薬剤を導く管路と、
    　前記管路の最先端に設けられた、少なくとも裏面の一部が前記体内臓器表面に密着するパッドと、
    　を備え、
    　前記パッドは、前記管路の内部通路と連通する１つまたは複数の開口を有し、前記１つまたは複数の開口の総面積は、前記内部通路の断面積より広いことを特徴とするカテーテル。     A catheter attached to the internal organs of mammals, including humans,
    A conduit that guides the drug from the drug source into the body,
    A pad provided at the forefront of the duct, at least a part of the back surface is in close contact with the internal organ surface;
    With
    The catheter has one or more openings communicating with an internal passage of the conduit, and the total area of the one or more openings is larger than the cross-sectional area of the internal passage.
  2. 　前記パッドは、柔軟なシート部であり、
    　前記１つまたは複数の開口は、前記パッドの裏面に設けられていることを特徴とする請求項１に記載のカテーテル。     The pad is a flexible seat part,
    The catheter according to claim 1, wherein the one or more openings are provided on a back surface of the pad.
  3. 　前記シート部の裏面は、前記体内臓器表面に密着する密着領域と、前記体内臓器表面に密着しない非密着領域とが形成され、前記１つまたは複数の開口は、前記非密着領域に設けられることを特徴とする請求項２に記載のカテーテル。 The back surface of the sheet part is formed with a close contact region that is in close contact with the surface of the internal organ and a non-adhesion region that is not in close contact with the surface of the internal organ, and the one or more openings are provided in the non-contact region. The catheter according to claim 2.
  4. 　前記密着領域表面は平滑に形成され、前記非密着領域表面は前記密着領域よりも粗く形成されていることを特徴とする請求項３に記載のカテーテル。 The catheter according to claim 3, wherein the surface of the close contact region is formed smoothly and the surface of the non-contact region is formed to be rougher than the close contact region.
  5. 　前記シート部の裏面に、前記１つまたは複数の開口が位置する非密着領域とは別に、前記１つまたは複数の開口が位置しない非密着領域が少なくとも１つ形成され、前記シート部の裏面が前記体内臓器表面に密着した状態で、前記１つまたは複数の開口が位置する非密着領域と前記１つまたは複数の開口が位置しない非密着領域とを接続する流路が形成されることを特徴とする請求項３に記載のカテーテル。 In addition to the non-contact region where the one or more openings are located, at least one non-contact region where the one or more openings are not formed is formed on the back surface of the sheet portion, and the back surface of the sheet portion is A flow path connecting the non-contact area where the one or more openings are located and the non-contact area where the one or more openings are not located is formed in close contact with the surface of the internal organ. The catheter according to claim 3.
  6. 　前記流路は、前記シート部の裏面に形成された溝であることを特徴とする請求項５に記載のカテーテル。 The catheter according to claim 5, wherein the flow path is a groove formed on a back surface of the sheet portion.
  7. 　前記流路は、前記シート部内部に形成された気泡による前記シート部裏面側への突起形成によって前記シート部裏面に形成された溝であることを特徴とする請求項５に記載のカテーテル。 The catheter according to claim 5, wherein the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the sheet portion.
  8. 　前記流路は、前記シート部内部に形成されたルーメンであることを特徴とする請求項５に記載のカテーテル。 The catheter according to claim 5, wherein the flow path is a lumen formed in the seat portion.
  9. 　前記流路は、前記シート部内部に形成されたルーメンであって該ルーメン内が多孔形状となっていることを特徴とする請求項５に記載のカテーテル。 The catheter according to claim 5, wherein the flow path is a lumen formed inside the sheet portion, and the inside of the lumen has a porous shape.
  10. 　前記シート部裏面と前記体内臓器表面との間に配設されるスペーサをさらに備え、
    　前記スペーサは、側壁と、前記シート部側に形成される上部開口と、前記体内臓器側に形成される下部開口とを有し、少なくとも前記下部開口に覆われる前記体内臓器表面が前記非密着領域となることを特徴とする請求項３に記載のカテーテル。     Further comprising a spacer disposed between the back surface of the sheet part and the surface of the internal organs;
    The spacer has a side wall, an upper opening formed on the sheet portion side, and a lower opening formed on the body organ side, and at least the surface of the body organ covered by the lower opening is the non-contact region The catheter according to claim 3, wherein
  11. 　前記管路と前記シート部とを接続する接続部材を有し、
    　前記管路と前記シート部とは、前記接続部材によって着脱可能に連結されることを特徴とする請求項２に記載のカテーテル。     A connecting member for connecting the pipe line and the seat portion;
    The catheter according to claim 2, wherein the conduit and the seat portion are detachably coupled by the connecting member.
  12. 　前記シート部裏面は、前記体内臓器表面と分子間力によって密着していることを特徴とする請求項２に記載のカテーテル。 The catheter according to claim 2, wherein the back surface of the sheet portion is in close contact with the surface of the internal organ by intermolecular force.
  13. 　前記シート部は、前記管路側に前記管路と連結し、前記管路の内部通路の断面積より広い断面積をもち前記体内臓器表面と接する空室を形成する連結部を備えたことを特徴とする請求項２に記載のカテーテル。 The seat portion includes a connecting portion that is connected to the conduit on the conduit side, and that has a cross-sectional area wider than the cross-sectional area of the internal passage of the conduit and forms a cavity that contacts the surface of the internal organ. The catheter according to claim 2.
  14. 　前記シート部は、空気抜きの弁が設けられていることを特徴とする請求項２に記載のカテーテル。 3. The catheter according to claim 2, wherein the seat portion is provided with an air vent valve.
  15. 　前記シート部は、通気性を有する部材で形成されていることを特徴とする請求項２に記載のカテーテル。 The catheter according to claim 2, wherein the sheet portion is formed of a member having air permeability.
  16. 　前記パッドは、前記体内臓器を巻回してサポータの機能を有する柔軟なサポータ部であり、
    　前記１つまたは複数の開口は、前記パッドの裏面に設けられていることを特徴とする請求項１に記載のカテーテル。     The pad is a flexible supporter part having a supporter function by winding the internal organs,
    The catheter according to claim 1, wherein the one or more openings are provided on a back surface of the pad.
  17. 　前記サポータ部は、複数の連結バンドを有し、該連結バンドで前記体内臓器を囲むことによって前記体内臓器表面に対して位置固定されることを特徴とする請求項１６に記載のカテーテル。 The catheter according to claim 16, wherein the supporter portion has a plurality of connection bands, and the position is fixed with respect to the surface of the internal organs by surrounding the internal organs with the connection bands.
  18. 　前記連結バンドの先端部にホックが設けられていることを特徴とする請求項１７に記載のカテーテル。 The catheter according to claim 17, wherein a hook is provided at a distal end portion of the connection band.
  19. 　前記連結バンドの先端部にコードが設けられており、該コードの締め付けを調整して前記サポータ部の前記体内臓器への固着を調整することを特徴とする請求項１７に記載のカテーテル。 The catheter according to claim 17, wherein a cord is provided at a distal end portion of the connection band, and the fixation of the supporter portion to the internal organ is adjusted by adjusting tightening of the cord.
  20. 　前記サポータ部は、前記体内臓器に対する固着強度を調整する調整部を備えたことを特徴とする請求項１６に記載のカテーテル。 The catheter according to claim 16, wherein the supporter portion includes an adjustment portion that adjusts adhesion strength to the internal organ.
  21. 　前記調整部は、分散配置された複数のバルーンであることを特徴とする請求項２０に記載のカテーテル。 The catheter according to claim 20, wherein the adjustment unit is a plurality of balloons arranged in a distributed manner.
  22. 　前記調整部は、分散して形成された複数の開口であることを特徴とする請求項２０に記載のカテーテル。 21. The catheter according to claim 20, wherein the adjustment section is a plurality of openings formed in a dispersed manner.
  23. 　前記サポータ部の裏面は、前記体内臓器表面に密着する密着領域と、前記体内臓器表面に密着しない非密着領域とが形成され、前記１つまたは複数の開口は、前記非密着領域に設けられることを特徴とする請求項１６に記載のカテーテル。 The back surface of the supporter is formed with a close contact area that is in close contact with the surface of the internal organ and a non-contact area that is not in close contact with the surface of the internal organ, and the one or more openings are provided in the non-contact area. The catheter according to claim 16.
  24. 　前記密着領域表面は平滑に形成され、前記非密着領域表面は前記密着領域よりも粗く形成されていることを特徴とする請求項２３に記載のカテーテル。 24. The catheter according to claim 23, wherein the surface of the contact area is formed smoothly and the surface of the non-contact area is formed rougher than the contact area.
  25. 　前記サポータ部の裏面に、前記１つまたは複数の開口が位置する非密着領域とは別に、前記１つまたは複数の開口が位置しない非密着領域が少なくとも１つ形成され、前記サポータ部の裏面が前記体内臓器表面に密着した状態で、前記１つまたは複数の開口が位置する非密着領域と前記１つまたは複数の開口が位置しない非密着領域とを接続する流路が形成されることを特徴とする請求項２３に記載のカテーテル。 In addition to the non-contact area where the one or more openings are positioned, at least one non-contact area where the one or more openings are not formed is formed on the back surface of the supporter section, and the back surface of the supporter section is A flow path connecting the non-contact area where the one or more openings are located and the non-contact area where the one or more openings are not located is formed in close contact with the surface of the internal organ. The catheter according to claim 23.
  26. 　前記流路は、前記サポータ部の裏面に形成された溝であることを特徴とする請求項２５に記載のカテーテル。 The catheter according to claim 25, wherein the flow path is a groove formed on a back surface of the supporter portion.
  27. 　前記流路は、前記サポータ部内部に形成された気泡による前記シート部裏面側への突起形成によって前記シート部裏面に形成された溝であることを特徴とする請求項２５に記載のカテーテル。 26. The catheter according to claim 25, wherein the flow path is a groove formed on the back surface of the sheet portion by forming a protrusion on the back surface side of the sheet portion by bubbles formed inside the supporter portion.
  28. 　前記流路は、前記サポータ部内部に形成されたルーメンであることを特徴とする請求項２５に記載のカテーテル。 The catheter according to claim 25, wherein the flow path is a lumen formed inside the supporter portion.
  29. 　前記流路は、前記サポータ部内部に形成されたルーメンであって該ルーメン内が多孔形状となっていることを特徴とする請求項２５に記載のカテーテル。 The catheter according to claim 25, wherein the flow path is a lumen formed inside the supporter portion, and the inside of the lumen has a porous shape.
  30. 　前記サポータ部裏面と前記体内臓器表面との間に配設されるスペーサをさらに備え、
    　前記スペーサは、側壁と、前記サポータ部側に形成される上部開口と、前記体内臓器側に形成される下部開口とを有し、少なくとも前記下部開口に覆われる前記体内臓器表面が前記非密着領域となることを特徴とする請求項２３に記載のカテーテル。     A spacer disposed between the back surface of the supporter and the surface of the internal organ;
    The spacer has a side wall, an upper opening formed on the supporter side, and a lower opening formed on the body organ side, and at least the surface of the body organ covered by the lower opening is the non-contact region The catheter according to claim 23, wherein:
  31. 　前記管路と前記サポータ部とを接続する接続部材を有し、
    　前記管路と前記サポータ部とは、前記接続部材によって着脱可能に連結されることを特徴とする請求項１６に記載のカテーテル。     A connecting member for connecting the pipe line and the supporter part;
    The catheter according to claim 16, wherein the conduit and the supporter part are detachably coupled by the connection member.
  32. 　前記サポータ部裏面は、前記体内臓器表面と分子間力によって密着していることを特徴とする請求項１６に記載のカテーテル。 The catheter according to claim 16, wherein the back surface of the supporter is in close contact with the internal organ surface by intermolecular force.
  33. 　前記サポータ部は、前記管路側に前記管路と連結し、前記管路の内部通路の断面積より広い断面積をもち前記体内臓器表面と接する空室を形成する連結部を備えたことを特徴とする請求項１６に記載のカテーテル。 The supporter includes a connecting part that is connected to the pipe line on the pipe line side, and has a cross-sectional area wider than a cross-sectional area of an internal passage of the pipe line and forms an empty space in contact with the internal organ surface. The catheter according to claim 16.
  34. 　前記サポータ部は、空気抜きの弁が設けられていることを特徴とする請求項１６に記載のカテーテル。 The catheter according to claim 16, wherein the supporter part is provided with an air vent valve.
  35. 　前記サポータ部は、通気性を有する部材で形成されていることを特徴とする請求項１６に記載のカテーテル。 The catheter according to claim 16, wherein the supporter part is formed of a member having air permeability.
  36. 　前記パッド内には、前記パッドの外部から伝わるエネルギーを受けて、前記パッド内の薬剤の流れを許容または禁止する一方の状態から禁止または許容する他方の状態に遷移するゲート機構を備えたことを特徴とする請求項１に記載のカテーテル。 The pad is provided with a gate mechanism that receives energy transmitted from the outside of the pad and makes a transition from one state that permits or prohibits the flow of the drug in the pad to the other state that prohibits or allows the flow of medicine. The catheter according to claim 1.
  37. 　前記エネルギーは、外部から照射される波動エネルギーであることを特徴とする請求項３６に記載のカテーテル。 The catheter according to claim 36, wherein the energy is wave energy irradiated from outside.
  38. 　前記ゲート機構は、前記波動エネルギーの照射を受けて破壊される被破壊部材を有し、該被破壊部材の破壊によって前記状態が遷移することを特徴とする請求項３７に記載のカテーテル。 38. The catheter according to claim 37, wherein the gate mechanism has a member to be destroyed that is destroyed by the irradiation of the wave energy, and the state is changed by the destruction of the member to be destroyed.
  39. 　前記被破壊部材は、前記薬剤の流れを禁止する部材であり、
    　前記ゲート機構は、前記波動エネルギーの照射を受けて該被破壊部材が破壊されることによって前記薬剤の流れを禁止する状態から許容する状態に遷移させることを特徴とする請求項３８に記載のカテーテル。     The member to be destroyed is a member that prohibits the flow of the medicine,
    39. The catheter according to claim 38, wherein the gate mechanism makes a transition from a state in which the flow of the medicine is allowed to a state in which the medicine is allowed to flow by being destroyed by receiving the wave energy. .
  40. 　前記被破壊部材は、前記薬剤の流れを許容する部材であり、
    　前記薬剤の流れを禁止する位置に移動する方向に付勢され、前記被破壊部材によって前記移動が阻まれる付勢部材を有し、
    　前記ゲート機構は、前記波動エネルギーの照射を受けて前記被破壊部材が破壊されることによって前記付勢部材を前記薬剤の流れを禁止する位置に移動させ、前記薬剤の流れを許容する状態から禁止する状態に遷移させることを特徴とする請求項３８に記載のカテーテル。     The member to be destroyed is a member that allows the flow of the medicine,
    Biased in a direction to move to a position where the flow of the medicine is prohibited, and having a biasing member that is blocked by the member to be destroyed;
    The gate mechanism receives the wave energy irradiation and moves the urging member to a position where the flow of the medicine is prohibited by breaking the member to be destroyed, and is prohibited from a state where the flow of the medicine is allowed. 39. The catheter according to claim 38, wherein the catheter is shifted to a state to be performed.
  41. 　前記被破壊部材は、セラミックスであることを特徴とする請求項３８に記載のカテーテル。 The catheter according to claim 38, wherein the member to be destroyed is ceramic.
  42. 　前記ゲート機構は、前記エネルギーを受けて変形する変形部材を有し、該変形部材の変形によって前記状態が遷移することを特徴とする請求項３６に記載のカテーテル。 The catheter according to claim 36, wherein the gate mechanism has a deformable member that is deformed by receiving the energy, and the state is changed by deformation of the deformable member.
  43. 　前記ゲート機構は、前記エネルギーを受けて前記変形部材が変形することによって前記薬剤の流れを禁止する状態から許容する状態に遷移させることを特徴とする請求項４２に記載のカテーテル。 43. The catheter according to claim 42, wherein the gate mechanism makes a transition from a state in which the flow of the medicine is prohibited to a state in which the flow of the medicine is permitted by the deformation of the deformable member in response to the energy.
  44. 　前記変形部材は、前記薬剤の流れを許容する部材であり、
    　前記薬剤の流れを禁止する位置に移動する方向に付勢され、前記変形部材によって前記移動が阻まれる付勢部材を有し、
    　前記ゲート機構は、前記エネルギーを受けて前記変形部材が変形することによって前記付勢部材を前記薬剤の流れを禁止する位置に移動させ、前記薬剤の流れを許容する状態から禁止する状態に遷移させることを特徴とする請求項４２に記載のカテーテル。     The deformable member is a member that allows the flow of the medicine,
    Biased in a direction to move to a position where the flow of the medicine is prohibited, and having a biasing member that is blocked by the deformation member,
    The gate mechanism receives the energy and deforms the deforming member to move the biasing member to a position where the flow of the medicine is prohibited, and makes a transition from a state where the flow of the medicine is allowed to a prohibited state. 43. A catheter according to claim 42.
  45. 　前記変形部材は、熱可塑性のプラスチックであることを特徴とする請求項４２に記載のカテーテル。 43. The catheter according to claim 42, wherein the deformable member is a thermoplastic plastic.
  46. 　前記波動エネルギーは、音波、超音波、赤外線と可視光とを含みかつ高周波を含む電磁波、衝撃波、機械振動のうちの１または複数を組み合わせたエネルギーであることを特徴とする請求項３７に記載のカテーテル。 The said wave energy is the energy which combined one or more of the electromagnetic waves which contain a sound wave, an ultrasonic wave, infrared rays, and visible light, and contain a high frequency, a shock wave, and a mechanical vibration, The Claim 37 characterized by the above-mentioned. catheter.
  47. 　前記波動エネルギーは、レーザ装置から出力されるエネルギーであることを特徴とする請求項３７に記載のカテーテル。 The catheter according to claim 37, wherein the wave energy is energy output from a laser device.
  48. 　前記波動エネルギーは、超音波振動子から出力されるエネルギーであることを特徴とする請求項３７に記載のカテーテル。 The catheter according to claim 37, wherein the wave energy is energy output from an ultrasonic transducer.
  49. 　前記波動エネルギーは、衝撃波発生装置から出力されるエネルギーであることを特徴とする請求項３７に記載のカテーテル。 The catheter according to claim 37, wherein the wave energy is energy output from a shock wave generator.
  50. 　前記パッド内には、前記薬剤を吐出する薬剤吐出部を有し、
    　前記薬剤吐出部および前記ゲート機構は、複数であり、
    　少なくとも１つの薬剤吐出部は、前記ゲート機構によって前記薬剤を吐出する活性状態と薬剤を吐出しない不活性状態との遷移が行われることを特徴とする請求項３６に記載のカテーテル。     In the pad, there is a medicine discharge part for discharging the medicine,
    The medicine ejection part and the gate mechanism are plural,
    37. The catheter according to claim 36, wherein at least one medicine ejection unit is transitioned between an active state in which the medicine is ejected and an inactive state in which the medicine is not ejected by the gate mechanism.
  51. 　前記ゲート機構は、シート状の前記パッドの内部に設けられることを特徴とする請求項３６に記載のカテーテル。 The catheter according to claim 36, wherein the gate mechanism is provided inside the sheet-like pad.
  52. 　前記パッドは、浸透膜を有し、該浸透膜を介して前記薬剤を前記体内に吐出することを特徴とする請求項５１に記載のカテーテル。 52. The catheter according to claim 51, wherein the pad has an osmotic membrane, and the drug is discharged into the body through the osmotic membrane.
  53. 　前記パッドは、開口が形成され、該開口を介して前記薬剤を前記体内に吐出することを特徴とする請求項５１に記載のカテーテル。 52. The catheter according to claim 51, wherein an opening is formed in the pad, and the medicine is discharged into the body through the opening.
  54. 　前記管路は、先端に穿刺針が設けられ、該穿刺針を介して前記薬剤を体内に吐出し、
    　前記ゲート機構は、前記管路の途中に設けられることを特徴とする請求項３６に記載のカテーテル。     The conduit is provided with a puncture needle at the tip, and the drug is discharged into the body through the puncture needle,
    The catheter according to claim 36, wherein the gate mechanism is provided in the middle of the conduit.
  55. 　前記管路は、前記薬剤の供給側の１つの通路から複数の通路に分岐する分岐部を有し、
    　前記ゲート機構は、前記分岐部に複数設けられ、
    　前記分岐部から分岐した少なくとも１つの通路は、前記ゲート機構によって該通路に薬剤を流す活性状態と該通路に薬剤を流さない不活性状態との状態遷移を行うことを特徴とする請求項５４に記載のカテーテル。     The conduit has a branch portion that branches from one passage on the drug supply side into a plurality of passages,
    A plurality of the gate mechanisms are provided in the branch part,
    55. The at least one passage branched from the branch portion performs a state transition between an active state in which a drug flows through the passage by the gate mechanism and an inactive state in which the drug does not flow through the passage. The catheter described.
  56. 　前記分岐部は、網状の通路であることを特徴とする請求項５５に記載のカテーテル。 The catheter according to claim 55, wherein the branch portion is a mesh-like passage.
PCT/JP2009/065749 2008-11-28 2009-09-09 Catheter WO2010061680A1 (en)

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JP2008305499A JP2010125226A (en) 2008-11-28 2008-11-28 Catheter
JP2008-305501 2008-11-28
JP2008305501A JP2010125228A (en) 2008-11-28 2008-11-28 Catheter
JP2008305500A JP2010125227A (en) 2008-11-28 2008-11-28 Catheter
JP2008-305500 2008-11-28
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WO2012132482A1 (en) * 2011-03-30 2012-10-04 テルモ株式会社 Biological adhesive sheet and device for attaching biological adhesive sheet
US9555217B2 (en) 2012-01-31 2017-01-31 Terumo Kabushiki Kaisha Catheter
US10966641B2 (en) 2015-09-04 2021-04-06 Senzime Ab (Publ.) Microdialysis device comprising attachment sheet

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US20070156113A1 (en) * 2006-01-03 2007-07-05 Heartcor Organ shealth for percutaneous delivery of biological and pharmacological agents
JP2007534407A (en) * 2004-04-28 2007-11-29 スミス　アンド　ネフュー　ピーエルシー Device for aspirating, irrigating and / or cleaning wounds

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JPH02152469A (en) * 1988-12-02 1990-06-12 Olympus Optical Co Ltd Drug capsule
JP2002529207A (en) * 1998-11-17 2002-09-10 アンリ・メイエール Device for delivering an active substance directly into cellular tissue and means for embedding such a device and apparatus intended for injecting the active substance into the device
JP2007534407A (en) * 2004-04-28 2007-11-29 スミス　アンド　ネフュー　ピーエルシー Device for aspirating, irrigating and / or cleaning wounds
US20070156113A1 (en) * 2006-01-03 2007-07-05 Heartcor Organ shealth for percutaneous delivery of biological and pharmacological agents

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WO2012132482A1 (en) * 2011-03-30 2012-10-04 テルモ株式会社 Biological adhesive sheet and device for attaching biological adhesive sheet
JPWO2012132482A1 (en) * 2011-03-30 2014-07-24 テルモ株式会社 Bioadhesive sheet and bioadhesive sheet pasting device
JP5837050B2 (en) * 2011-03-30 2015-12-24 テルモ株式会社 Bioadhesive sheet and bioadhesive sheet pasting device
US9555217B2 (en) 2012-01-31 2017-01-31 Terumo Kabushiki Kaisha Catheter
US10966641B2 (en) 2015-09-04 2021-04-06 Senzime Ab (Publ.) Microdialysis device comprising attachment sheet
US11707212B2 (en) 2015-09-04 2023-07-25 Senzime Ab (Publ.) Microdialysis device comprising attachment sheet

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