WO2006103951A1 - Liquid-supplying tube for medical use provided with deaeration module, assembly of medical machines using the liquid-supplying tube for medical use, deaeration module and method of supplying liquid - Google Patents

Abstract

A deaeration module whereby a gas dissolved in a liquid to be used in a therapeutic treatment or an examination in vivo is removed; a liquid-supplying tube for medical use which has this deaeration module; an assembly of various medical machines using the liquid-supplying tube for medical use; and a method of supplying a liquid. By applying a water molecule-activation means, whereby movements of water molecules are activated, to a liquid, it is intended to continuously supply a liquid, from which gases dissolved therein have been removed, in a stable state to a medical machine for conducting a therapeutic treatment or an examination in vivo to thereby ensure the safety of a patient and stable and continuous operation of the machine without exerting any undesirable effects on the performance by an operator.

Description

 Specification

 Medical liquid supply tube with deaeration module, medical device assembly, deaeration module and liquid supply method using the medical liquid supply tube

 Technical field

 [0001] The present invention relates to a degassing module for removing dissolved gas contained in a liquid used for treatment or examination in a living body, a medical liquid feeding tube having the degassing module, and the medical liquid feeding pipe. The present invention relates to various medical device assemblies and liquid feeding methods.

 Background art

 In recent years, medical devices using ultrasonic waves, microwaves, infrared rays, lasers, or the like as mediators have been developed for treatment or diagnosis in human blood vessels, and some have already been put into practical use. This medical device is used in, for example, computerized tomography (CT), angiography or magnetic resonance imaging (MRI), and is difficult to observe in minute blood vessels that are difficult to identify, or in surgery. Demonstrates excellent effects in crushing and excision of lesions in areas where the physical burden on the patient is large!

 Many of these medical devices are filled or circulated with a predetermined liquid such as physiological saline. Therefore, when a high-power laser or the like is irradiated in the liquid, moisture molecules in the liquid The movement of the air is activated and the dissolved air bubbles. The bubble formation of dissolved air in medical devices can be broadly classified according to the cause, either due to heat generation or due to cavitation.

 [0004] For example, when the former is due to heat generation, heat is generated at the emitting part that irradiates a laser or the like, or friction that occurs when a fiber that guides an ultrasonic wave or laser in a medical device rotates at high speed or moves back and forth at high speed. There are cases where bubbles are generated directly due to heat, etc., and some of the medical devices generate heat indirectly due to reflection or condensing of lasers, etc., or heaters installed in the liquid supply tube. is there.

[0005] In the latter case, the pressure applied to the liquid is locally reduced, thereby lowering the boiling point of water, and even if the water temperature does not rise, bubbles containing dissolved gas are generated. It is a phenomenon, but also in this case, high-speed rotation of the optical fiber in the liquid of the medical device, When a bubble is formed directly by pressure increase / decrease generated locally by ultrasonic vibration, a part of the medical device resonates due to ultrasonic waves, etc., or the liquid supply tube is locally increased / decreased by driving the pump. Indirect bubbles may occur.

 [0006] Such bubble formation of dissolved air causes the following various problems.

 [0007] (1) When liquid is fed into a living body, the generated bubbles flow together with the liquid feeding, causing blood vessel occlusion, and depending on the occluded part, there is a risk of causing serious damage to the body.

[0008] (2) Causes of obstructing the transmission of ultrasonic waves, lasers, etc. regardless of the liquid delivery to the living body, preventing accurate in-vivo information collection due to the occurrence of noise, or destabilizing the output It becomes.

 [0009] (3) When the liquid feeding is used for cooling a medical device, if the air bubbles remain in the medical device, the cooling efficiency of the medical device may decrease.

[0010] (4) Cavitation is known to give a huge impact to the part where the liquid comes into contact with the generation or collapse of bubbles, but this impact may damage the medical device.

 [0011] (5) In an infusion system or peritoneal dialysis system, when the temperature of an infusion solution or dialysate is increased, bubbles generated due to pressure increase / decrease of the drive unit of the liquid pump are detected by the bubble sensor. Infusion may stop, or it may cause adverse effects on dialysis therapy using a large amount of dialysate.

 [0012] For this reason, conventionally, when using medical devices, when performing so-called priming that fills the medical device with a liquid such as physiological saline, a previously degassed liquid is used and removed. A method has also been proposed in which even if there is some dissolved air that is difficult to solve, this is taken into the liquid (see Patent Document 1 below).

 [0013] However, in a medical device provided with a means for activating the movement of water molecules, if the liquid feeding is not performed smoothly, the gas in the atmosphere is dissolved again, and this is bubbled with the operation of the medical device. Therefore, it is incomplete as a means for removing air, and preparing a degassed liquid beforehand imposes unnecessary effort on the part of the operator.

[0014] In addition, as a method for removing dissolved air, there are a method using a permeable membrane, a method using boiling or reduced pressure, an inert gas publishing method, an ultrasonic deaeration method, a reduction reaction method, etc. 317 There is also a method of removing dissolved oxygen with a hollow fiber membrane (see the summary of JP-A-11 9902, see FIG. 1).

 [0015] However, the liquid deaerated by such a method is used after being sealed in a gas-permeable low-pressure container and then using the container-powered liquid when the medical device is used. This has a limited capacity and is not preferred for long-term use of medical devices. In addition, the liquid to be injected into the living body may be altered by boiling, and even if it does not change, preparing a degassed liquid in advance is a heavy burden for medical professionals. Furthermore, even if degassed and stored in a storage container, air (gas) in the atmosphere may dissolve into the liquid during storage, movement, or storage container power.

 [0016] In particular, in medical devices, it is important that degassing from the liquid does not adversely affect the operability and handling of the operator who operates the medical device, and ensuring patient safety and operation. It can only be used once all problems have been resolved, such as ensuring stable continuity of operation status and combination with other equipment. There is no utility as a device.

 Disclosure of the invention

 Problems to be solved by the invention

[0017] An object of the present invention is to apply a liquid to a water molecule activation means that activates the movement of water molecules, so that the liquid from which dissolved gas is removed is stable even in a medical device that performs treatment or diagnosis of a living body. It is intended to ensure the patient's safety and stable continuity of driving conditions without adversely affecting the operability of the operator.

[0018] Further, another object of the present invention is to provide a deaeration module for removing liquid force dissolved air or bubbles, which is smaller and simpler than a conventional structure. There is.

 Means for solving the problem

[0019] The medical liquid supply tube with a deaeration module of the present invention that achieves the above object is a medical device having water molecule activation means that directly or indirectly activates the movement of water molecules in the liquid. In a medical liquid delivery tube that is connected to the water molecule and forms a flow path for applying a predetermined liquid containing water molecules to the water molecule activating means, a dissolved gas contained in the liquid in a part of the flow path Alternatively, a deaeration module for removing bubbles is provided.

 [0020] The medical device assembly of the present invention that achieves the above-mentioned object is

 A medical device having a water molecule activation means for directly or indirectly activating movement of water molecules in a liquid;

 A liquid delivery pipe for applying the liquid to the water molecule activation means;

 A degassing module provided with a porous membrane that is provided in a part of the liquid supply pipe and removes dissolved gas or bubbles contained in the liquid;

 A liquid supply device connected to the liquid supply pipe and having a flow rate control device for controlling the flow rate of the liquid.

[0021] A degassing module of the present invention that achieves the above object is a degassing module that removes dissolved gas or bubbles contained in a liquid,

 A module body in which the distal end opening and the proximal end opening are in communication with each other;

 A mounting portion for liquid-tightly attaching the tip opening side of the module body to a liquid storage portion containing a liquid to be degassed;

 A plurality of bundles are bent in a U-shape, and the U-shaped curved portions are disposed in the module body or are exposed to the outside from the tip opening, and are opposite to the curved portions. A porous hollow fiber membrane potted in the vicinity of the proximal end opening so that the portion maintains an open state,

 Pressure is applied to the base end opening of the module body, and the dissolved gas or bubbles contained in the liquid are transmitted through the porous hollow fiber membrane from the U-shaped curved portion that comes into contact with the liquid in the liquid storage portion. And removing it.

[0022] The liquid-feeding method of the present invention that achieves the above-mentioned object is a medical treatment or examination in vivo having a water molecule activating means that directly or indirectly activates the movement of water molecules in the liquid. Dissolved liquid or bubbles contained in the liquid while controlling the flow rate of the liquid passing through the deaeration module provided with the porous membrane when the liquid from the liquid supply device is sent to the medical device using the liquid feeding pipe Is a liquid feeding method in which liquid is fed after the membrane area Sx (cm ² ) of the porous membrane of the deaeration module and the flow rate L (mlZh) of the liquid flowing through the liquid feeding pipe are: S x≥L / 40, preferably Sx≥L / 20, more preferably Sx≥LZlO The flow rate L (ml / h) of the liquid is controlled.

 The invention's effect

 [0023] In the present invention, when a liquid is applied to the water molecule activating means and treatment or inspection is performed in a living body, a degassing module is provided in a liquid supply pipe through which the liquid flows, so that a dissolved gas is previously generated from the liquid. The liquid can be fed with stable continuity while removing the water.

 [0024] Therefore, even when an operator who does not need to prepare a degassed liquid in advance and does not impose unnecessary effort, the liquid is in direct contact with the water molecule activation means. However, it is possible to prevent the dissolved gas from being bubbled, and to safely perform treatment in the living body without allowing bubbles to flow into the living body, generating noise caused by the generated bubbles, unstable output, and cooling due to liquid feeding. Degradation due to failure can be suppressed, in-vivo information can be collected accurately, stable performance can be demonstrated, and accurate inspection can be performed.

 [0025] For example, resonance in a medical device due to generated ultrasonic waves, lasers, or the like, heat generation in a part of the medical device due to heat conduction, heat generation in a reflection portion, or rapid pressure increase / decrease of liquid due to liquid vaporization Some sputums can suppress the formation of bubbles in dissolved gas even if a reduced pressure space occurs due to rapid liquid feeding in the lumen and high-speed rotation of sensors, etc., and it is safe without injecting bubbles into the living body. In-vivo treatment can be performed at the same time, and noise caused by bubbles generated, output instability, deterioration due to cooling failure due to liquid feeding, etc. are suppressed, and accurate in-vivo information collection and stable performance are obtained. Accurate inspection is possible.

 [0026] Further, in the present invention, a plurality of bundled porous hollow fiber membranes are potted in the vicinity of the base end opening of the module main body while one end of the porous hollow fiber membrane is maintained in an open state, and the other end is Since the structure is arranged in the module main body with the lumen closed or is exposed to the outside from the tip opening, the membrane area for contacting the liquid that has been deaerated even with a small amount of hollow fiber membrane Enough can be secured. Therefore, since the amount of the hollow fiber membrane used can be suppressed, the module can be reduced in size and is easily manufactured without being limited to the use provided in the middle of the liquid feeding pipe.

 [0027] Still other objects, features and characteristics of the present invention will become apparent by referring to the following description and preferred embodiments exemplified in the accompanying drawings.

Brief Description of Drawings FIG. 1 is a schematic front view showing a first embodiment of the present invention.

 2 is an enlarged cross-sectional view of the main part of FIG.

 FIG. 3 is an enlarged cross-sectional view of a portion A in FIG.

 FIG. 4 is an enlarged cross-sectional view of part B in FIG.

 FIG. 5 is a schematic cross-sectional view showing a first modification of the first embodiment of the present invention.

 FIG. 6 is a schematic sectional view showing a second modification.

 FIG. 7 is a schematic sectional view showing a third modification.

 FIG. 8 is a schematic sectional view showing a fourth modification.

 FIG. 9 is a schematic sectional view showing a fifth modification.

 FIG. 10 is a schematic sectional view showing a sixth modification.

 FIG. 11 is a schematic cross-sectional view showing a means for closing the end of the porous hollow fiber membrane.

 FIG. 12 is a schematic sectional view showing Modification Example 7.

 FIG. 13 is a schematic cross-sectional view of the relevant part showing Modification 8.

 FIG. 14 is a main part schematic cross-sectional view showing Modification 9;

 FIG. 15 is a schematic cross-sectional view showing a second embodiment of the present invention.

 FIG. 16 is a schematic cross-sectional view showing a third embodiment of the present invention.

 FIG. 17 is a schematic sectional view showing Modification 1 of the third embodiment.

 FIG. 18 is a schematic perspective view showing a modified example of the installation positions of the liquid supply pipe and the exhaust pipe of Modification 1

FIG. 19 is a schematic sectional view showing a second modification of the third embodiment.

 FIG. 20 is a schematic front view showing a fourth embodiment of the present invention.

 BEST MODE FOR CARRYING OUT THE INVENTION

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.

[0030] The present invention is basically a deaeration module using a hollow fiber membrane, and when this is provided in a liquid feeding tube, water molecule activation that directly activates the movement of water molecules in the liquid. Each medical device assembly will be described below because it can be incorporated into various medical device assemblies having means.

[0031] <First embodiment> As a medical device assembly according to this embodiment, there is a laser-induced liquid jet generating device for treating thrombosis. Recently, as a means of treating thrombosis in which human blood vessels are blocked, a liquid jet flow generated by irradiating laser light in a liquid is jetted toward the thrombus, and the liquid jet flow is applied with pressure. Methods have been developed to physically disrupt the thrombus and resume blood flow. This treatment method is expected to have an extremely high therapeutic effect because it enables early blood flow resumption without the need to administer a large amount of a thrombolytic agent with serious side effects.

 [0032] In this medical device, a liquid is irradiated with laser light, and a part of water molecules of the liquid is vaporized by the energy of the laser light to generate bubbles in the liquid, thereby creating a liquid jet flow. Therefore, the part that irradiates the laser beam is one of the water molecule activation methods that directly activate the motion of water molecules in the liquid.

 FIG. 1 is a schematic front view showing a first embodiment of the present invention, FIG. 2 is an enlarged cross-sectional view of the main part of FIG. 1, and FIG. 3 is an enlarged cross-sectional view of FIG. 4 is an enlarged cross-sectional view of a portion B surrounded by an alternate long and short dash line in FIG.

 As shown in FIG. 1, the medical device assembly of the present embodiment includes a laser oscillator 1, a main body 2 of a medical device connected to the laser oscillator 1, and a category connected to the tip of the main body 2. 1, 3, a laser irradiation unit 4, which is a water molecule activating means provided in the main body 2, and a flow path for supplying a predetermined liquid W containing water molecules to the laser one irradiation unit 4. The liquid pipe 6 and a porous membrane provided in a part of the liquid feed pipe 6 are provided for removing dissolved gas or bubbles (indicated by broken line arrows, hereinafter abbreviated as gas etc. K) contained in the liquid W. Connected to the degassing module 13 and the liquid supply pipe 6 to control and supply the flow rate of the liquid W, and connected to the degassing module 13 to suck the gas K etc. removed from the liquid W And a decompressor 20.

[0035] Further details will be described. As shown in FIG. 2, the main body 2 is a cylindrical tube having a lumen through which the laser irradiation unit 4 can pass, and has a high melting point and rigidity capable of withstanding the heat generated by the optical fiber 9 described later. It is made of a certain material, for example, stainless steel, aluminum alloy or the like, and a branch pipe 14 for connecting the liquid feeding pipe 6 is projected from the side. The main body 2 can be inserted and removed with the catheter 3 at the distal end and the guide wire G indicated by a broken line at the rear end side. The so-called Y connector 5 is attached. Υ Connector 5 is a well-known one, so avoid detailed explanation.

 As shown in FIGS. 1 and 2, the laser irradiating unit 4 transmits the pulsed laser light guided from the laser oscillator 1 through the optical fiber 9 to the liquid in the main body 2 from the tip 9a of the optical fiber 9. This is the part that irradiates pulsed toward W, vaporizes the liquid, and suddenly generates bubbles (Bubble B), but the optical fiber 9 is projected from the laser oscillator 1 side and inserted inside the Y connector 5 Supported in a ferrule 10 that passes through.

 As shown in FIG. 3, the distal end portion 9a of the optical fiber 9 protrudes from the ferrule 10 and is irradiated with a laser having a wavelength that is easily absorbed by the force liquid. The outer periphery of the tip 9a is preferably covered with a polymer film 11 for protection. Since the laser oscillator 1 belongs to the public knowledge, the description thereof is omitted.

 As shown in FIGS. 1 and 2, the liquid feeding pipe 6 has one end connected to the main body 2 of the medical device and the other end connected to the liquid supply device 12. W is guided to the catheter 3 through the space 2 a of the main body 2. One end of the liquid feeding pipe 6 is connected to the branch pipe 14 protruding from the main body 2 via the connector C1 (connecting means C), and the other end is provided with a connector C2 (connecting means C). The tip of the liquid supply device 12 is inserted in a liquid-tight manner inside.

 [0039] If the branch pipe 14 of the main body 2 and the liquid feeding pipe 6 are connected via the connector C1, the distance between the degassing module 13 and the main body 2 described later becomes extremely short, and the liquid after degassing is immediately supplied to the main body 2 So that air does not enter the liquid again. Further, if the connectors C1 and C2 are provided at both ends of the liquid feeding pipe 6, it is easy to attach and detach the main body 2 and the liquid supply device 12, and workability is improved.

 [0040] The position of the branch pipe 14 is preferably a position toward the distal end portion 9a of the liquid force optical fiber 9 from the liquid feeding pipe 6. This is for reliably cooling the heat generated by the laser irradiation unit 4. Further, one end of the liquid feeding tube 6 may be integrally connected to the main body 2 of the medical device. In this way, the operability is improved so that there is no bending or stopping of liquid feeding when the main body 2 is operated.

[0041] The illustrated liquid supply apparatus 12 is a syringe pump having a drive unit 12a and a syringe 12b. The plunger of the syringe 12b is pushed at a substantially constant speed by the drive unit 12a, thereby supplying the liquid W to the liquid feeding pipe 6 at a substantially constant flow rate. The drive unit 12a is, for example, the series The liquid W may be supplied at a preset flow rate, such as a pump or injector, but a flow rate control device that changes the supply flow rate of the liquid W when using a medical device that uses only this is provided. It can be a thing.

 In particular, in the present embodiment, a deaeration means is provided so as to close a part of the axis of the long liquid feeding pipe 6. As the deaeration means, any means may be used as long as it has a porous membrane having air permeability that passes through the gas K etc. in the liquid W and a means for sucking the gas etc. K that has passed through the porous membrane. The deaeration module 13 is incorporated using a part of the liquid feeding pipe 6. Providing the deaeration module 13 using a part of the liquid supply pipe 6 will not unnecessarily increase the size of the device, and will not affect the peripheral devices. It is extremely advantageous.

 [0043] The degassing module 13 is installed at a position close to the laser irradiation unit 4 serving as a means for activating water molecules, and degass the gas, etc. K in the liquid W before the liquid W flows into the main body 2. It is preferable to do. In this way, the liquid W deaerated by the deaeration module 13 is immediately introduced into the main body 2, so that the gas does not re-dissolve during the liquid feeding process.

 Specifically, as shown in FIG. 2, a T-shape having a straight outer pipe 17 constituting a part of the liquid feeding pipe 6 and a branch pipe 19 branched from the outer pipe 17 is provided. A tubular body is used, and the porous membrane is a potting agent (adhesive) in which a large number of porous hollow fiber membranes 18 having air permeability are bundled in the outer tube 17 while maintaining the open state at both ends of the hollow fiber membrane. Potting with the agent)!

 [0045] The suction means is such that the decompression device 20 is communicated with the branch pipe 19 via the connector C3 (connecting means C) and the exhaust pipe 21, and the suction pipe 19a is opened from the side surface of the outer pipe 17. Aspiration of gas trapped in hollow fiber membrane 18 Examples of the decompression device 20 used here include a vacuum pump, an aspirator, and a roller pump.

 [0046] Needless to say, a plurality of intake ports 19a may be provided instead of only one. The deaeration module 13 shown in FIG. 2 is a so-called internal perfusion type, but is not limited to this, and can be used regardless of whether it is an internal perfusion type or an external perfusion type.

[0047] If a predetermined liquid is fed at a rapid flow rate with the hollow fiber membrane 18 exposed to the outside air without attaching the pressure reducing device 20 or the cap to the intake port 19a, the inside of the hollow fiber membrane 18 is negatively affected. Pressure There is a risk that outside air may be sucked into the deaeration module 13. The cap can be provided for the purpose of solving such problems and for preventing contamination and damage of the hollow fiber membrane before use.

 Next, the operation of this embodiment will be described.

 [0049] First, the catheter 2 is attached to the main body 2 and the so-called Y connector 5 that allows the guide wire G to be inserted and removed is attached to the rear end side. Connect one end of 6. When the liquid supply pipe 6 is integrated with the main body 2, this connecting work is not necessary, and workability is improved.

 [0050] The other end of the liquid feeding pipe 6 is connected to the liquid supply device 12. That is, the tip end of the syringe pump 12b is inserted into the connector C2. In addition, one end of the exhaust pipe 21 is connected to the branch pipe 19 provided in the outer pipe 17 of the liquid feeding pipe 6, and the other end is connected to the decompression device 20.

 [0051] When the medical device assembly is assembled in this manner, so-called priming is performed. The liquid supply device 12 is operated to start liquid feeding, and the decompression device 20 is operated. The liquid W is filled into the main body 2 and the catheter 3 which are connected only in the liquid feeding tube 6. The liquid feeding is performed until the liquid W flows out of the distal end force of the catheter 3.

 [0052] The liquid W used here is a solution obtained by adding a small amount of a thrombolytic agent to physiological saline or the like that can be vaporized by absorbing the energy of laser light. Depending on the thrombus hardness, you can use only saline without using a thrombolytic agent!

 [0053] Since the deaeration module 13 shown in FIG. 2 is an internal perfusion type, when the liquid W (solid line arrow) passes through the liquid feeding pipe 6 and reaches the deaeration module 13 part, it is porous. The external force of the hollow fiber membrane 18 is also sucked by the decompression device 20, so that the potting agent 22 (see FIG. 4) is filled, and the hollow fiber membrane 18 has numerous fine pores. The gas, etc. K is trapped, the gas, etc. K in the liquid is separated from the liquid, and the gas, etc. K is taken out of the hollow fiber membrane 18.

[0054] Since the degassed liquid W is immediately guided to the space 2a of the main body 2 through the liquid feeding pipe 6, air or the like is re-approached before reaching the laser irradiation section 4 which is a water molecule activation mechanism. It does not dissolve. Further, since the degassed liquid W is continuously supplied to the catheter 3 through the space 2a of the main body 2, it is necessary to prepare or store the degassed liquid W in advance. There is no unnecessary burden on the surgeon.

 [0055] Then, using the Y connector 5, the guide wire G is passed through the main body 2 and passed through the catheter 3, and only the guide wire G is inserted into the blood vessel while protruding from the distal end of the catheter 3. When the tip reaches the nearest position of the affected part such as a thrombus, the position is held. This insertion is performed while X-ray irradiation is performed and the position of the guide wire G in the living body is confirmed with an X-ray impermeable marker.

 [0056] Subsequently, the catheter 3 is advanced along the guide wire G. When the distal end of the catheter 3 reaches the affected area, the guide wire G is removed with the position fixed, and the optical fiber 9 is inserted into the main body 2. The tip of the optical fiber 9 is fixedly held at a predetermined position.

 [0057] The optical fiber 9 is connected to the laser oscillator 1 to perform laser irradiation. When the laser oscillator 1 operates, the laser light is irradiated in a pulsed manner toward the liquid W through the optical fiber 9. Irradiation is performed in the main body 3, and a part of the liquid W is rapidly vaporized by absorbing the energy of the laser beam. Bubbles B generated by this vaporization expand rapidly and generate a rapid jet, so-called liquid jet.

 [0058] The liquid jet flow is a force injected from the injection port 8 of the main body 2 toward the catheter 3. Since the main body 2 and the catheter 3 are filled with the liquid W, the force of the liquid jet flow is the liquid W Is transmitted to the tip of the catheter 3, and when it collides with a thrombus in front, the thrombus is broken.

 [0059] When the reopening of the blood vessel is confirmed, the laser irradiation is stopped. The crushed thrombus is taken out together with the liquid W through the catheter 3 by a suction device (not shown) provided separately. In order to ensure this removal, the supply of liquid and the removal and suction of the thrombus are continued for a predetermined time, and then the operation is stopped and the catheter 3 is removed from the body.

 As described above, in the present embodiment, heat generated by the generated laser light, resonance in the medical device, heat generation in a part of the medical device due to heat conduction, heat generation in the reflection portion, and abrupt liquid discharge accompanying liquid vaporization. Even if pressure is increased or decreased, or rapid liquid delivery in the lumen occurs, the gas, etc., in the liquid W is removed in advance, so that bubbles of the dissolved gas can be suppressed. It is possible to safely perform treatment without injecting air bubbles.

[0061] When various conditions regarding the degassing module 13 are specifically examined by experiments, the following conditions are obtained. It has been found that those having are preferred.

 [0062] (1) Filling density of hollow fiber membrane

 When potting the porous hollow fiber membrane 18 into the tube body 17, the inner diameter of the hollow fiber membrane 18 with respect to the packing density of the hollow fiber membrane 18, that is, the cross-sectional area perpendicular to the axis of the lumen of the tube body 17. The ratio of the total cross-sectional area perpendicular to the axis of the hollow fiber membrane 18 containing is 40% to 70%, more preferably 50% to 70%.

 [0063] If the range is exceeded, potting into the tube body 17 may become difficult. If the range is below this range, in order to obtain a membrane area that can be effectively degassed, the low filling rate is compensated. In addition, the diameter of the pipe body 17 needs to be increased, and production efficiency and transportability may be deteriorated.

 [0064] The packing density (%) as described above is

 (Cross-sectional area of hollow fiber membrane) Z (Module lumen area) X 100

 Is calculated by The “occupied cross-sectional area of the hollow fiber membrane” is the total area of the hollow fiber membrane including the area of the hollow fiber membrane lumen.

 [0065] (2) Area of hollow fiber membrane

The area where the hollow fiber membrane comes into contact with the liquid is determined by the product area of the 1Z40 with respect to the flow rate (mlZh) from the viewpoint of increasing the deaeration efficiency by sufficiently bringing the liquid to be deaerated into contact with the porous membrane. It is preferable to have at least (cm ² ). More preferably, it is a product of 1/20, and more preferably a product of 1Z10. The upper limit of the membrane area is not particularly limited, but if the membrane area is too large, the deaeration module becomes too large and lacks transportability, the dead volume of a given liquid increases, the tube 17 and the hollow fiber membrane The air in the air increases, and there is a possibility that the suction capability of the decompression device having a limited capacity such as a vacuum tube 2 Oa described later may be impaired. Therefore, it is necessary to set the membrane area in consideration of these.

 [0066] As an experimental result on this point,

Regarding the liquid feed pump described in detail later, when the flow rate was 25 mlZh, degassing was possible at Sx = 3 (cm ² ).

[0067] Regarding thrombus removal by laser, when the flow rate was 120 mlZh, degassing was possible at Sx = 22 (cm ² ). When the flow rate was 300mlZh, degassing was possible even at Sx = 22 (cm ² ) [0068] Furthermore, regarding the peritoneal dialysis system described in detail later, when the flow rate was 12000 mlZh, degassing was possible at Sx = 300 (cm ² ).

 [0069] (3) Degree of vacuum

 Regarding the degree of vacuum when sucking gas etc., OmmHg to 300mmHg or less is preferable. More preferably, it is 0 to 150 mmHg. Above this range, the intake air is too weak and may not be sufficiently deaerated.

 [0070] (4) Porosity of hollow fiber membrane

 It has been found that the porosity of the hollow fiber membrane is preferably 10% to 50%, more preferably 35% to 45%. If this range is exceeded, there is a possibility that the liquid enters the pores of the hollow fiber membrane and flows into the suction side, and if it falls below this range, the dissolved air cannot be sucked into the opposite side of the hollow fiber membrane, and the dissolved air May be insufficiently degassed.

 [0071] (5) Average pore diameter of hollow fiber membrane

 The average pore diameter of the pores of the hollow fiber membrane is preferably 0.05 μm to 0.5 / z m, more preferably 0.05 / ζ πι to 0.15 / z m. If this range is exceeded, there is a possibility that the liquid enters the hole of the hollow fiber membrane and flows into the intake side, and if it falls below this range, gas or the like κ cannot be sucked into the opposite side of the hollow fiber membrane, and the gas Etc. K may be insufficiently degassed.

[0072] When such a degassing module 13 is used in the medical device 2 which is a laser-induced liquid jet generating device, the optical fiber diameter is 700 / ζ πι and the conventional laser conditions capable of crushing the thrombus are conventionally used. In this case, about 100 1 dissolved air per 10 minutes was discharged as well as the tip of the liquid delivery pipe 6.However, when the deaeration module 13 with the inner surface area of the hollow fiber membrane set to 22 cm ² was used, 90 mmHg The amount of dissolved air generated could be reduced to zero with the degree of vacuum. In addition, when 1200mlZh of air was exhausted in this degassing module 13, bubbles were not generated from the tip of the liquid pipe connector C1 at a vacuum level of 90mmHg. It was.

 [0073] (6) The material of the hollow fiber membrane is polypropylene.

[0074] (7) The inner and outer diameters of the hollow fiber membrane have an inner diameter of 200 ± 50 m and an outer diameter of 300 ± 50 m. [0075] Note that the porosity and average pore diameter of the hollow fiber membrane are measured. Is disclosed in JP-A-5-64663. It conforms to the measurement method disclosed in paragraph “0090”, and a silver silver press-fitting porosimeter type 2000 (manufacturer: CARLO ERBA INSTRUMENTS) was used as a measuring instrument.

 [0076] In the present invention, there are also modifications described below that are not limited to the deaeration module 13 described above.

 [0077] <Modification 1>

 FIG. 5 is a schematic sectional view showing a first modification of the present embodiment. As shown in FIG. 5, the liquid feeding pipe 6 of Modification 1 has liquid feeding tubes tl and t2 and an exhaust pipe 21 attached to both ends of the T-shaped outer pipe 17 and to the end of the branch pipe 19. Is.

 [0078] The liquid supply device 12 and the decompression device 20 which are syringe pumps are relatively heavy and are not preferable in terms of portability and mobility. In addition, it is not preferable that these devices exist in the vicinity of the main body 2 and the deaeration module 13 of the medical device in view of the operability of the operator. Furthermore, there is a space limitation regarding the operating table.

 [0079] Therefore, if the tubes tl, t2 and the exhaust pipe 21 are provided in the T-shaped outer pipe 17 as in the first modification, the lengths of the liquid supply tubes tl, t2 and the exhaust pipe 21 are appropriately set. By selecting, the distance between the main body 2 and the liquid supply device 12 or the decompression device 20 can be set to an appropriate length that is easy for the operator to operate. As a result, workability is improved.

 [0080] <Modification 2>

 FIG. 6 is a schematic sectional view showing a second modification of the present embodiment. The embodiment shown in FIG. 1 and the like described above can be directly detached from the main body 2 of the medical device 2 and the liquid supply device 12 to re-dissolve the gas from the degassing module 13 to the water molecule kinetic active substance. In order to minimize the distance between the degassing module 13 and the main body 2, the degassing module 13 and the main body 2 or the degassing air can be supplied to the main body 2 immediately after degassing. The module 13 and the liquid supply device 12 are connected by connectors CI and C2.

 However, as described above, the presence of the relatively heavy liquid supply device 12 and the decompression device 20 in the vicinity of the transportability surface, the medical device main body 2 and the deaeration module 13 may be There is also a space limitation with respect to an operating table in which the operability is not favorable.

[0082] Therefore, as shown in FIG. 6, the present modified example 2 includes an inlet side and an intake port of the deaeration module 13. If the liquid feeding tube t2 and the exhaust pipe 21 are attached to the part 19a, and the connector C1 is attached to the other end of the outer pipe 17, it is short from the degassing module 13 to the water molecule kinetic active substance. The other part becomes longer, and the operability becomes more preferable. Connectors C3 and C4 may be provided at both ends of the exhaust pipe 21, and the exhaust pipe 21 itself is preferably provided with a rigidity that can withstand vacuuming.

[0083] <Modification 3>

 FIG. 7 is a schematic sectional view showing a third modification of the present embodiment. As shown in FIG. 7, the deaeration module 13 of Modification 3 is provided with a branch pipe 19 on the side surface of the outer pipe 17, and a base end of a needle 23 is provided on the branch pipe 19 in a liquid-tight manner. 20 uses a sealed vacuum tube 20a

[0084] By inserting the cutting edge formed at the tip of the needle 23 into the plug 24 of the vacuum tube 20a, the deaeration module 13 and the vacuum tube 20a are communicated with each other, and the vacuum tube 20a is deaerated by reducing the pressure. Further, in order to ensure the support of the vacuum tube 20a, an inverted saddle-shaped decompression tube holding member 28 is provided.

 [0085] After the liquid supply device 12 starts liquid feeding and it is confirmed that a predetermined liquid has passed through the hollow fiber membrane, the needle 20 may be inserted into the plug 24 of the vacuum tube 20a. A two-way stopcock 25 is provided between the branch pipe 19 and the needle 23, and the needle 20 is inserted into the plug body 24 with the two-way stopcock 25 closed, and the deaeration module 13 and the vacuum tube 20a are communicated with each other. It is preferable to open the two-way stopcock 25 after confirming that a predetermined liquid has passed through the deaeration module 13.

 In any case, with this configuration, the connection between the deaeration module 13 and the vacuum tube 20a is extremely simple and the workability is improved.

 [0087] <Modification 4>

 FIG. 8 is a schematic sectional view showing a fourth modification of the present embodiment. The medical fluid supply tube 6 with the deaeration module described above is an internal perfusion type, but may be an external perfusion type.

As the external perfusion type deaeration module 13, for example, as shown in FIG. 8, a large number of porous hollow fiber membranes 18 (only a few are shown in the figure for simplicity) are used as hollow fiber membranes. Potting agent (adhesive) 22 is potted in the outer tube 17 so as to maintain the open state at both ends, and a liquid inlet 26 and outlet 27 are provided on the side of the outer tube 17. [0089] The liquid feeding pipe 6 is different from the above embodiment in that the decompression device 20 is communicated with both ends of the outer pipe 17, but the liquid W (solid arrow) passes through the inside of the outer pipe 17 from the inlet 26. Passing through the outlet 27 and discharging it, the decompression device 20 communicates with both ends of the outer pipe 17 and sucks it, so that the gas K in the liquid W enters the hollow fiber membrane 18 from the portion not filled with the potting agent 22. Can be taken up and removed from liquid W.

 [0090] <Modification 5>

 FIG. 9 is a schematic sectional view showing Modification 5 of the present embodiment. Although the above-described medical fluid delivery pipe 6 with a deaeration module is different from the internal perfusion type or the external perfusion type, all use a straight porous hollow fiber membrane 18, but this modification 5 The porous hollow fiber membrane 18 is bent in a loop shape as shown in FIG.

 This liquid feeding tube 6 is an external perfusion type that takes in gas K or the like from the liquid W flowing outside the porous hollow fiber membrane 18.

 [0092] Normally, the configuration of the external perfusion type tends to be more complicated than the internal perfusion type, but the hollow fiber membrane is curved in a U shape or a loop shape, and the shape of the outer tube 17 is T-shaped or Y-shaped. By doing so, the bonding portion of the hollow fiber membrane 18 can be made one place, which is advantageous in terms of manufacturing.

 [0093] Further, the deaeration module 13 may be either an internal perfusion type or an external perfusion type, but the external perfusion type is more advantageous if the amount of the hollow fiber membrane in the portion other than the adhesive portion is the same. is there. The area of the hollow fiber membrane in contact with the liquid W can be increased, the liquid feeding resistance is lowered, and a high deaeration potential can be obtained.

 [0094] <Modification 6>

 Here, the degassing module 13 having a U-shaped or loop-shaped structure provided in the medical liquid feeding tube 6 of Modification 5 is not limited to an application provided in the middle of the liquid feeding pipe 6. It can also be used for deaeration that is applied to the industry and for the production of industrial deaeration water, and can also be used as a small deaeration module with a small membrane area.

 [0095] For this reason, the degassing module 13 can be used as a single degassing module as long as it is connected to the liquid storage part containing the liquid to be degassed.

FIG. 10 is a schematic cross-sectional view showing Modification 6 of the present embodiment. As shown in FIG. 10, the deaeration module 13 includes a module main body 29 in which the front end opening 30 and the base end opening 31 are in communication with each other, and a liquid storage unit containing the liquid W to be deaerated. 32 (corresponding to the outer tube 17) the mounting opening 33 (corresponding to the branch tube 19) where the tip opening side of the module body 29 is liquid-tightly attached, and a porous hollow fiber accommodated in the module body 29 And a film 18.

 [0098] A plurality of porous hollow fiber membranes 18 are bent in a U shape in a bundled state, and the U-shaped curved portion 18a is disposed in the tip opening 30 or externally from the tip opening 30. The both ends 18b of the porous hollow fiber membrane 18 that are arranged exposed to the opposite side of the curved portion 18a are potted by the potting agent 22 in the vicinity of the proximal end opening 31 while maintaining the open state. . The U-shaped curved portion 18a is exposed outside the tip opening 30 without being potted in the module main body 29, and is exposed to the outside from the inside of the tip opening 30.

 In the illustrated example, a luer taper surface 29 a is formed on the outer peripheral surface of the module main body 29, a taper surface 33 a is formed on the inner peripheral surface of the mounting portion 33, and the module main body 29 is inserted into the mounting portion 33. Only to be connected in an airtight manner. However, the connection between the mounting portion 33 and the module main body 29 may be a so-called lock adapter structure. That is, a male screw 33b is formed on the outer peripheral surface of the mounting portion 33, an adapter member 34 having a female screw formed on the inner surface thereof is screwed into this, and the mounting portion 33 and the module main body 29 are connected by screwing them together. It may be more reliable. Further, a sleeve 34a may be provided at the lower end of the adapter member 34 so that the exhaust pipe 21 can be securely held.

 [0100] In this deaeration module 13, the state in which the liquid W in the liquid storage portion 32 and the portion not filled with the potting agent including the U-shaped curved portion 18a of the porous hollow fiber membrane 18 are in contact with each other. Thus, when the decompression from the decompression device 20 is applied, the gas K contained in the liquid W permeates through the porous hollow fiber membrane 18 not filled with the potting agent 22 and is removed.

 [0101] Therefore, the degassing module 13 can reduce the amount of the hollow fiber membrane used while ensuring a large membrane area in contact with the liquid to be degassed. It can also be used for industrial degassing water production not only as a module, making it extremely practical.

[0102] Further, the deaeration module 13 has a U-shape or halfway in the middle of the straight porous hollow fiber membrane 18. It is possible to easily form the film simply by bending in a loop shape.

 [0103] Further, when it is not necessary to deaerate the predetermined liquid W flowing into the medical liquid delivery tube 6, the opening 19a of the mounting portion 33 is sealed with a cap or the like (not shown), and deaerated. Only when it is necessary to remove the cap, the degassing module 13 of the U-shaped hollow fiber membrane 18 having a pressure reducing device may be attached.

 FIG. 11 is a schematic cross-sectional view showing a means for closing the end of the porous hollow fiber membrane.

[0105] In Modification 6 described above, the force that is obtained by bending the porous hollow fiber membrane 18 into a U shape may be a straight shape that does not necessarily need to be bent into a U shape or a loop shape. . That is, as shown in FIG. 11, one end of a straight porous hollow fiber membrane 18 in a bundled state is connected to the base end of the module main body 29 with its inner cavity 18c kept open. Potting may be performed in the vicinity of the opening 31, and the other end may be disposed in the module main body 29 or exposed to the outside from the tip opening 30 so that the inner cavity 18c is closed.

Then, when pressure is applied to the base end opening 31 of the module main body 29, bubbles contained in the liquid W from the other end of the porous hollow fiber membrane 18 in contact with the liquid in the liquid storage portion 32, etc. K can be removed.

 Here, as means for forming the closed state of the other end, a heat-shrinkable tube (not shown) is put on the end of the straight porous hollow fiber membrane 18 in a bundled state. When heated, the adjacent porous hollow fiber membranes 18 are heat-sealed to form the heat-sealed portion 18d, and the lumen 18c can be easily closed.

 <Modification 7>

 FIG. 12 is a schematic sectional view showing Modification 7 of the present embodiment. In this modified example 7, the above-described plug body 24 of the vacuum tube 20a is punctured with a needle 23, and a plurality of porous hollow fiber membranes 18 curved in a U shape are potted. It is provided at the tip of 29. Also in the present modified example 7, in order to ensure the support of the vacuum tube 20a, a reverse pressure-shaped decompression tube holding member 28 may be provided on the module body 29.

[0109] In this way, the deaeration module 13 and the vacuum tube 20a are very easily connected, and the force is also hermetically connected simply by inserting the module body 29 into the branch tube 19, so The tube 17 and the deaeration module 13 can be easily attached and detached. [0110] Note that the deaeration module having the U-shaped curved portion according to the above-described modified examples 5 to 7 is used as a part of a medical liquid feeding tube, and is detached from a medical device. It can also be applied to a gas module, that is, an application for degassing a liquid before being applied to a medical device. In any case, the deaeration module of this embodiment can be easily manufactured and can secure a large membrane area in contact with the liquid while reducing the amount of the hollow fiber membrane itself, thereby reducing the size of the deaeration module. Very advantageous.

 [0111] Further, in the embodiment including the U-shaped curved portion, each of the bundled hollow fiber membranes is

It is not limited to a configuration composed of a single continuous hollow fiber membrane, and at the u-shaped curved portion, the ends of the two hollow fiber membranes are heat-sealed while maintaining their open state, A plurality of hollow fiber membranes may be connected to form a U-shaped curved portion.

 [0112] <Modification 8>

 In the above-described modified examples 5 to 7, the U-shaped curved portion is advantageous in that a force such as the suction side opening 30 is exposed and a large membrane area in contact with the liquid can be secured. The invention is not limited to this.

 FIG. 13 is a schematic cross-sectional view of the relevant part showing Modification Example 8. For example, as shown in FIG. 13, as long as the U-shaped curved portion 18a and the liquid W can come into contact with each other, it is provided in the module body 29, and the distal end of the curved portion 18a of the porous hollow fiber membrane 18 is the proximal end opening. It may be a structure that is retracted inside 31 (on the side close to the base opening 31 on the exhaust side). In FIG. 13, the potting portion is schematically shown with a broken line for convenience. Further, in this modified example, the hollow fiber membrane can be stretched relatively long in the module main body 29, thereby ensuring a large membrane area in contact with the liquid W.

 [0114] Furthermore, when it is not necessary to deaerate the predetermined liquid W flowing into the medical liquid delivery tube 6, the opening 19a of the mounting portion 33 is sealed with a cap or the like (not shown), and deaerated. Only when it is necessary to install the degassing module 13 of the hollow fiber membrane 18 having a U-shape having a decompression device, the operation of degassing the dissolved air becomes possible.

[0115] If a predetermined liquid is fed at a rapid flow rate without attaching the pressure reducing device 20 or the cap to the intake port 19a and the hollow fiber membrane 18 is exposed to the outside air, the inside of the hollow fiber membrane 18 is negatively affected. The outside air may be sucked into the deaeration module 13 due to the pressure. Cap solves this problem It can be provided for the purpose of determining and preventing the contamination and damage of the hollow fiber membrane before use.

 [0116] <Modification 9>

 FIG. 14 is a schematic cross-sectional view showing a main part of a ninth modification. In this modified example 9, the branch pipe 19 has a Y-shape instead of the T-shape as in the previous example, and the U-shaped curved portion 18a of the hollow fiber membrane 18 protrudes from the branch pipe into the liquid feed pipe. The extended configuration.

 [0117] In this way, it is possible to secure a larger membrane area of the hollow fiber membrane 18 without being restricted by the cross-sectional area of the intake port, and to connect the end of the hollow fiber membrane 18 to the Y-shaped branch pipe 19 By extending the obtuse angle to the side forming the obtuse angle, unlike the case of the T-shaped branch pipe, the load of bending the hollow fiber membrane 18 at a right angle can be eliminated. Also in FIG. 14, the potting portion is shown by a broken line for convenience.

 [0118] <Second Embodiment>

 The medical device assembly in which the liquid feeding tube according to the present embodiment is used is a laser irradiation apparatus that is inserted into a body cavity or an organ and irradiates energy to a lesioned part to treat a tumor such as cancer or a prostatic hypertrophy. .

 [0119] In general, the laser irradiation apparatus includes an optical fiber 9, a reflection mirror 40, and the like in a long and thin tubular main body 2, and a laser irradiation unit 4 that irradiates a laser guided by the optical fiber 9. The main body 2 is filled with cooling water in order to suppress the heat generation of the laser. However, when a single laser beam is irradiated, part of the laser energy is absorbed by the reflection mirror 40 and the reflection mirror 40 may generate heat. . In particular, when the laser output is increased to further improve the therapeutic effect, the reflection mirror 40 provided at the tip of the main body 2 of the medical device generates heat, and the liquid W around the reflection mirror 40 is heated and dissolved. Gas may be generated. Therefore, the laser irradiation unit 4 including the reflection mirror 40 is one of water molecule activation means for directly activating the movement of water molecules in the liquid.

 FIG. 15 is a schematic cross-sectional view showing a second embodiment of the present invention. In addition, the same code | symbol is used for the member which is functionally common with the said embodiment, and description is abbreviate | omitted.

As shown in FIG. 15, the laser irradiation apparatus of the present embodiment is incident from a laser oscillator 1, a long and thin tubular main body 2, and a base end of an optical fiber 9 provided inside the main body 2. Shi The laser beam emitted from the tip is reflected in a predetermined direction by the reflection mirror 40, and the laser irradiation unit 4 that irradiates from the laser beam transmission window 44, and the optical fiber 9 and the reflection mirror 40 are driven back and forth in the longitudinal direction of the main body 2. And a degassing module 13 having a porous membrane for removing dissolved gas or bubbles contained in the liquid. A liquid supply pipe 6, a liquid supply device 12 connected to one end of the liquid supply pipe 6, a drain pipe 42 for discharging cooling water, and a drain apparatus 43 connected to one end of the drain pipe 42. is doing. Reference numeral “45” in the figure is a base that supports the main body 2 and is provided with an endoscope (not shown).

 [0122] In the laser irradiation apparatus, first, the main body 2 is inserted into a distal-end force body cavity, and the distal end is positioned in the vicinity of the lesioned part. While observing the position of the tip directly with an endoscope, adjust the position by moving the body 2 or rotating it, and set and fix it so that it matches the direction of the target site. It is preferable that a balloon (not shown) that can be expanded and contracted is provided at the distal end portion of the main body 2, and the main body 2 is closely fixed in the body cavity by expanding the balloon. Then, the liquid supply device 12 is operated, and the liquid W such as cooling water is circulated in the main body 2 to cool the main body 2 that generates heat by one laser beam, the surface of the living tissue, and the like. This is to reliably prevent damage to the surface layer of the living tissue.

 [0123] After the position is fixed, the driving means 41 is driven simultaneously with the operation of the laser oscillator 1. The laser beam is guided by the optical fiber 9, reflected laterally by the reflection mirror 40, emitted from the laser light transmission window 44 of the main body 2, and applied to the target site. In this case, the reflection mirror 40 changes its reflection angle while reciprocating at a predetermined cycle in the axial direction, and the optical path axis of the laser beam is continuously changed, but all intersect at the target portion.

 [0124] As a result, the target site and its vicinity are heated by the laser beam to reach the desired temperature, but other than the target site, the amount of heat generated is kept at a relatively low temperature and high for the patient!ヽ Safety is ensured.

[0125] Also in such a laser irradiation apparatus, when the liquid W from the liquid supply apparatus 12 is removed from the gas K or the like by the deaeration module 13 of the liquid supply pipe 6, laser irradiation is performed, and the liquid around the reflection mirror 40 is discharged. Even if heated, the bubbling of dissolved gas is suppressed, and the bubbles stay in the vicinity of the laser light transmission window 44 of the main body 2 to prevent the transmission of the laser light, Stable output or performance without lowering the cooling efficiency of the body surface can be achieved.

 [0126] It goes without saying that the various modifications described above can also be used in this embodiment.

<Third embodiment>

 The medical device assembly in which the liquid feeding tube according to the present embodiment is used is a liquid feeding pump used for an infusion pump that dispenses a certain amount of a chemical solution, hemodialysis, or peritoneal dialysis.

 [0128] For example, in the case of an infusion system or peritoneal dialysis system, the temperature is lower than room temperature such as in a cold region or a refrigerator! However, it is usually used as it is without sufficiently raising the temperature to room temperature, in which case the dissolved air becomes supersaturated during the treatment. When this supersaturated liquid is used connected to an infusion line and a pump at room temperature, bubbles naturally occur when the temperature rises due to the heater, or indirectly at the liquid feed pump drive section via a liquid feed pipe. In addition, the liquid may be pressurized and decompressed, and the dissolved gas may become bubbles.

 [0129] In addition, when the motor or the like is insufficiently cooled due to the downsizing of the liquid feed pump, the liquid feed pump drive section generates heat and indirectly heats the liquid via the liquid feed pipe. In other words, the dissolved gas may become bubbles. In particular, peritoneal dialysis uses a large amount of dialysate. However, since the dialysate must be heated to a temperature close to the body temperature using a heater before being injected into the body, more bubbles are likely to be generated.

 [0130] In such an infusion system, in the infusion system, the bubble sensor of the infusion pump detects the bubble and the infusion stops, and in the absence of the bubble sensor, the bubble enters the body. Become. In the peritoneal dialysis system, a peritoneal dialysis solution in which dissolved gas is bubbled is used, which causes pain such as shoulders in the patient.

 [0131] Accordingly, the liquid feed pump and the heater are also one of the water molecule activation means for directly activating the movement of the water molecules in the liquid.

FIG. 16 is a schematic cross-sectional view showing a third embodiment of the present invention. In addition, the same code | symbol is used for the member which is common in the said embodiment, and description is abbreviate | omitted. As shown in FIG. 16, the liquid feed pump 50 of the present embodiment includes a plurality of rollers 52 provided on a rotating plate 51 that is rotated by a motor (not shown), and a roller 52 that rotates. The plate 51 is a so-called roller pump having one elastic liquid feeding pipe 6 installed between the crimping wall (not shown) provided around the plate 51, and the liquid feeding pipe 6 is connected to the crimping wall. The roller 52 serves as a transfer source that pumps the liquid W in the liquid supply pipe 6 at a controlled flow rate while being crushed between the rollers.

 [0134] One end of the liquid supply tube 6 is connected to and detached from a liquid reservoir 53 such as a chemical solution bag in which liquid W is stored, and the other end is detachably connected to a living body injecting unit 54 that is a dialysis unit. Has been. In the case of the peritoneal dialysis system, a heater 55 is provided in the middle of the liquid feeding tube 6.

 In the present embodiment, the degassing module 13 is provided in a part of the force feeding pipe 6 that is the liquid feeding pump 50 in which the decompression device 20 of the degassing module 13 is separately provided. Gas etc. K is removed. In particular, the deaeration module 13 is preferably provided at least before the liquid is injected into the living body injection unit 54, which is preferably located in the vicinity of the roller pump. In addition, the degassing module 13 that aims at degassing with the minimum required hollow fiber membrane to maintain the flow rate accuracy with a low liquid flow rate, such as an infusion solution, has a U-shaped curved portion as shown in FIGS. A degassing module 13 with is suitable.

 Note that the transfer source of the liquid W is not limited to the illustrated roller pump, and may be a diaphragm pump, a finger type pump or a peristal type pump, or a syringe.

 [0137] In using the liquid feed pump, first, the liquid feed pipe 6 is set between the roller 52 and the crimping wall, and the deaeration module 13 is arranged in the vicinity of the roller pump. One end of the liquid supply pipe 6 is connected to the liquid reservoir 53, and the other end is left open. Then, the roller-one pump is operated to cause the liquid W to flow out of the liquid reservoir 53 and fill the liquid feed pipe 6, and after priming, it communicates with the living body injector 54.

 [0138] In this state, when the roller pump is operated and the decompression device 20 is operated at the same time and degassing is performed by the degassing module 13, the liquid W from which bubbles and dissolved gas are degassed due to a temperature rise or the like becomes the living body injecting unit 54 Sent to. Therefore, there is no possibility that the infusion force S is stopped by the detection of the bubble sensor in the infusion system, or the effectiveness of dialysis is reduced in the peritoneal dialysis system.

[0139] Also in the present embodiment, various modifications of the deaeration module 13 described above should be used. Needless to say, you can. Further, the liquid feed pump 50 is a kind of the liquid supply device 12, but the flow rate of the liquid supply device 12 may be changed only by a pump that delivers a constant flow rate when the medical device assembly is used. When changing the flow rate, it is preferable to control so that the relational expression with the membrane area of the deaeration module 13 is satisfied.

[0140] In the present embodiment, as described above, the decompression device 20 of the deaeration module 13 is separately provided, but the liquid supply device 12 having the flow control device 12a and the decompression device 20 are combined into one. It can also be provided integrally in a unit case (not shown). In this way, handling, transportability, operability, etc. as a medical device assembly are improved.

[0141] Further, in such a liquid feed pump, it is possible to perform deaeration without suction by increasing the membrane area without providing the suction means as described in the first embodiment. That is, the range of temperature change of the infusion solution is 0 ° C to 40 ° C, and the flow rate of the infusion agent during continuous administration is 10 to as in the case of infusion pumps. The deaeration effect can be obtained simply by opening the intake port 19a of the deaeration module 13 which is not necessary. However, the method using the decompression device 20 described above also has a low deaeration effect, so it is necessary to make the membrane area of the deaeration module 13 rich so as to compensate for it, and a product area of 1Z10 or more is also secured. It is preferable. When the flow rate was lOOmlZh, degassing was possible without suction at Sx = 22 (cm ² ) and Sx = 13 (cm ² ).

[0142] <Variation 1>

 FIG. 17 is a schematic cross-sectional view showing a first modification of the third embodiment, and FIG. 18 is a schematic perspective view showing a modification of the installation positions of the liquid supply pipe and the exhaust pipe in the first modification.

 It is. In addition, the same code | symbol is used for the member which is common in the said embodiment, and description is abbreviate | omitted.

[0143] In the first modification, devices corresponding to the liquid supply device and the pressure reducing device are driven by the same drive source and incorporated in the same unit case 56.

[0144] As shown in Fig. 17, the liquid feed pump 50 of Modification 1 includes a liquid feed pipe 6 (first tube) and an exhaust pipe 21 (second tube) between the roller 52 and the crimping wall. It is installed and is composed of a tube cover that is relatively flexible in terms of V and displacement. One end of the liquid supply pipe 6 is detachably connected to the liquid reservoir 53 and the other end is connected to the biological injection part 54, and one end of the exhaust pipe 21 is connected to the deaeration module 13. The other end of the branch pipe 19 communicates with the other end. A heater 55 is provided adjacent to the liquid feeding pipe 6 in the vicinity of the roller 52.

[0145] In using the liquid feed pump 50, first, the liquid feed pipe 6 is set between the roller 52 and the crimping wall, and the deaeration module 13 is arranged in the vicinity of the roller pump. The exhaust pipe 21 is set between the roller 52 opposite to the set position and the crimping wall. After the liquid feeding pipe 6 and the exhaust pipe 21 are set, the roller pump is operated to perform priming, and the end part is communicated with the living body injection part 54.

 When the roller pump is operated in this state, liquid W starts to be fed on the liquid feed pipe 6 side, and at the same time, degassing is started from the degassing module 13 on the exhaust pipe 21 side. In this case, even if bubbles are generated when the temperature of the liquid W is raised to room temperature, or due to the temperature rise by the heater 55 or the heat of the liquid feed pump drive unit, the liquid W is deaerated through the exhaust pipe 21, The degassed liquid W is sent to the living body injection section 54 through the liquid feeding pipe 6.

 [0147] In this modification, infusion can be stopped by the detection of the bubble sensor in the infusion system, and wrinkles that reduce the effectiveness of dialysis can be prevented in the peritoneal dialysis system. Since the device 20 can be separated from the operating position, the operability is improved.

 In the first modification, the liquid feeding pipe 6 and the exhaust pipe 21 may be arranged on the same side of the liquid feeding pump 50 as shown in FIG.

 [0149] <Modification 2>

 FIG. 19 is a schematic cross-sectional view showing Modification 2 of the third embodiment. In addition, the same code | symbol is used for the member which is common in the said embodiment, and description is abbreviate | omitted.

As shown in FIG. 19, in the liquid feed pump of Modification 3, the liquid supply device 12 is a diaphragm pump 57, and a single liquid feed pipe 6 having elasticity is provided. One end of the liquid feeding pipe 6 is detachably connected to the liquid storage part 53 and the other end is connected to the living body injection part 54, respectively. One end of the exhaust pipe 21 communicates with the branch pipe 19 of the deaeration module 13, and the other end communicates with the syringe pump 58. The deaeration module 13 is disposed in the vicinity of the diaphragm pump 57, but the diaphragm pump 57 and the syringe pump 58 are installed in the unit case 55. Use a syringe pump 58 that automatically sucks. Is preferred.

 [0151] In using the liquid feed pump, the liquid feed pipe 6 in which the deaeration module 13 is disposed in the vicinity of the diaphragm pump 57 is used. Then, priming for filling the liquid feeding tube 6 with liquid is performed, and the end portion communicates with the living body injecting portion 54.

 In this state, when the diaphragm pump 57 is operated, the liquid feeding pipe 6 starts feeding the liquid W, and the degassing module 13 performs deaeration by the suction action of the syringe pump 58. Therefore, bubbles or dissolved gas generated due to a temperature rise or the like is degassed through the degassing module 13, and the degassed liquid W is sent to the living body injecting section 54 through the liquid feeding tube 6. The pressure reducing means is not limited to the illustrated roller pump, but may be a diaphragm pump, a finger type or a peristal type pump, or a syringe.

 <Fourth embodiment>

 The medical device assembly in which the liquid supply tube according to the present embodiment is used has a high-speed rotation of a sensor such as an ultrasonic wave or magnetism in order to check the result of diagnosis or treatment of a lesion in a blood vessel. It is the diagnostic device which acquires the information in.

 [0154] For example, an intravascular ultrasonic diagnostic device is used to diagnose unstable angina pectoris, acute myocardial infarction, etc. In this diagnostic device, an ultrasonic sensor is provided at the tip of the catheter, This is a high-speed rotational movement (radial scanning), which transmits ultrasonic waves while moving back and forth at high speed, receives the reflected waves to acquire a received signal, and modulates the amplitude of the received signal by luminance modulation etc. The tomographic images of the blood vessels were acquired, and the results after diagnosis and treatment of lesions inside the blood vessels were confirmed.

 [0155] Even in this diagnostic device, medical devices may be used in the case of frictional heat generated by the movement of an ultrasonic sensor, heat generation of a lead wire of an ultrasonic sensor, resonance of a part of a medical device due to ultrasonic waves, or vibration. The dissolved gas is bubbled by local pressure increase / decrease in the liquid. Therefore, the part where the ultrasonic sensor moves is one of the water molecule activation means that directly activate the movement of water molecules in the liquid.

FIG. 20 is a schematic front view showing the fourth embodiment of the present invention. In addition, the same code | symbol is used for the member which is functionally common with the said embodiment, and description is abbreviate | omitted. As shown in FIG. 20, the ultrasonic diagnostic apparatus of this embodiment includes a drive unit 60 incorporating a power source, an analysis device, and a rotation operation unit, a main body 2 connected to the drive unit 60, and a main unit 2 Long, thin, connected to the distal end of the tube, and connects the tubular catheter tube 61, the ultrasonic transmission / reception article 62 provided inside the distal end of the catheter tube 61, and the drive unit 60 and the ultrasonic transmission / reception article 62. A liquid feed having a degassing module 13 having a rotating member 63, a flow path for supplying a predetermined liquid W to the main body 2 and the catheter tube 61, and a porous film for removing dissolved gas or bubbles contained in the liquid A pipe 6 and a liquid supply device 12 connected to one end of the liquid feeding pipe 6 are provided.

 [0158] In the ultrasonic diagnostic apparatus, first, the catheter tube 61 is also inserted into the body cavity with the distal end force, and the distal end is positioned in the vicinity of the lesioned part. Then, the liquid supply device 12 is operated to supply liquid W such as cooling water into the main body 2.

 [0159] The drive unit 60 is operated, and the ultrasonic transmission receiver 62 is rotated at high speed or moved back and forth at high speed via the rotating member 63. The ultrasonic waves are reflected by the lesioned part inside the blood vessel and received by the ultrasonic transmission / reception object 62, and displayed as an image on an external monitor (not shown).

 [0160] In such an ultrasonic diagnostic apparatus as well, when dissolved gas or bubbles are removed from the liquid W fed from the liquid supply apparatus 12 by the degassing module 13 of the liquid feeding pipe 6, the ultrasonic transmission / reception object 62 is removed. Even if the surrounding liquid W is heated by the movement, resonance occurs in the device, or even if a local low pressure is generated by high-speed rotation, the bubble formation of dissolved gas and the generation of bubbles are suppressed. Stays in the vicinity of the ultrasonic transmission / reception object 62 and obstructs the transmission and reception of ultrasonic waves, thereby preventing the collection of high-definition images due to the generation of noise or causing unstable output. Stable output or performance will be demonstrated. Further, since the generated bubbles stay in the catheter tube 61, the cooling efficiency due to the liquid W feeding is not lowered, and the deterioration due to the cooling failure due to the liquid feeding is not caused.

 [0161] In the present embodiment, it is needless to say that the various modified examples described above can be used, but in the present embodiment, not only this but also a laser beam is used. It is effective even for equipment using microwaves or infrared rays.

 [0162] Industrial applicability

The present invention provides a water molecule activity that directly or indirectly activates the motion of water molecules in a liquid. It can be used for more accurate diagnosis and treatment by removing dissolved gas or air bubbles contained in the liquid of the medical device having the sexifying means.

 Furthermore, this application is based on Japanese Patent Application No. 2005-964 15 filed on Mar. 29, 2005, the disclosure of which is incorporated by reference in its entirety.

Claims

The scope of the claims

 [1] Connected to a medical device having a water molecule activation means that directly or indirectly activates the movement of water molecules in the liquid, and the water molecule activation means contains a predetermined liquid containing water molecules. A medical liquid delivery tube for forming a flow path to be applied, wherein a degas module for removing dissolved gas or bubbles contained in the liquid is provided in a part of the flow path. Liquid feeding tube.

 [2] The degassing module according to claim 1, wherein an air-permeable porous membrane that transmits dissolved air or bubbles in the liquid is provided in a tube body of the liquid feeding pipe. Medical feeding tube with degassing module.

 [3] The deaeration module is configured such that the porous membrane is constituted by a porous hollow fiber membrane, and a plurality of the porous hollow fiber membranes are bundled in the liquid feeding tube and potted with a potting agent. The medical liquid feeding tube with a deaeration module according to claim 1 or 2,

 [4] The deaeration module bundles a plurality of the porous hollow fiber membranes in a part along the axis of the liquid supply pipe and pots them using a potting agent, and the potting of the porous hollow fiber membranes is performed. The at least one inlet port for discharging dissolved air or bubbles that have permeated through the porous hollow fiber membrane is provided in the liquid supply pipe facing the portion not filled with the agent. The medical liquid feeding tube with a deaeration module according to any one of 1 to 3

[5] The deaeration module has a branch pipe continuously connected to at least one intake port provided on a side surface of the liquid feed pipe, and a distal end thereof is curved in a U shape in the branch pipe, and both ends of the base end A plurality of the porous hollow fiber membranes potted so that the portion maintains an open state is provided, and the tip of the porous hollow fiber membrane is disposed in the flow path of the liquid feeding tube The medical liquid feeding tube with a deaeration module according to any one of claims 1 to 3.

 6. The medical liquid supply tube with a deaeration module according to any one of claims 1 to 5, wherein one end of the liquid supply pipe is integrally connected to the medical device.

 7. The medical liquid feeding tube with a deaeration module according to any one of claims 1 to 5, wherein the liquid feeding pipe has at least one connecting means detachable from the medical device. .

[8] Water molecule activation means to directly or indirectly activate the movement of water molecules in a liquid A medical device with

 A liquid delivery pipe for applying the liquid to the water molecule activation means;

 A degassing module provided with a porous membrane that is provided in a part of the liquid supply pipe and removes dissolved gas or bubbles contained in the liquid;

 A liquid supply device connected to the liquid feeding pipe and having a flow rate control device for controlling the flow rate of the liquid;

 A medical device assembly for in-vivo treatment or examination, comprising:

 [9] The medical device assembly includes a decompression device that is connected to the degassing module and sucks dissolved gas or bubbles removed from the liquid. The flow control device and the decompression device are combined into a single unit. 9. The medical device assembly according to claim 8, wherein the medical device assembly is incorporated in the medical device assembly.

 [10] In the liquid supply device, one end is connected to the inlet side of the deaeration module and the other end is connected to a liquid supply source, and the first tube having elasticity is pressurized and deformed to pump the liquid. A flow rate control device, and a pressure reducing device that generates a negative pressure by pressurizing and deforming an elastic second tube having one end connected to the intake port side of the deaeration module and the other end opened. 10. The medical device assembly according to claim 8 or 9, wherein the medical device assembly is a medical device assembly.

 11. The medical device assembly according to claim 9, wherein the liquid supply device is configured to drive the flow rate control device and the decompression device with the same drive source.

 [12] The degassing module is characterized in that the membrane area Sx (cm2) of the porous membrane has a relationship of Sx≥L / 40 with respect to the flow rate L (mlZh) controlled by the flow rate control device. The medical device assembly according to any of claims 8 to 11, wherein

 [13] The degassing module is characterized in that the membrane area Sx (cm2) of the porous membrane has a relationship of Sx≥L / 20 with respect to the flow rate L (mlZh) controlled by the flow rate control device. The medical device assembly according to any of claims 8 to 11, wherein

 [14] In the degassing module, the membrane area Sx (cm2) of the porous membrane has a relationship of Sx≥L / 10 with respect to the flow rate L (mlZh) controlled by the flow rate control device. The medical device assembly according to any of claims 8 to 11, wherein

[15] Water molecule activation means to directly or indirectly activate the movement of water molecules in a liquid When the liquid from the liquid supply device is sent to a medical device for treatment or examination in a living body using a liquid feeding pipe, the flow rate of the liquid passing through the deaeration module having a porous membrane is controlled. A liquid feeding method for feeding after removing dissolved gas or bubbles contained in the liquid,

 The liquid flow rate (L) is set so that the membrane area Sx (cm2) of the porous membrane of the degassing module and the flow rate L (mlZh) of the liquid flowing through the liquid feeding pipe have a relationship of Sx≥LZ40. A liquid feeding method characterized by controlling.

[16] The liquid from the liquid supply device is sent to a medical device for treatment or examination in a living body having a water molecule activation mechanism that directly or indirectly activates the movement of water molecules in the liquid. This is a liquid feeding method in which liquid is fed after removing dissolved gas or bubbles contained in the liquid while controlling the flow rate of the liquid passing through the deaeration module having a porous membrane when liquid is fed using the liquid pipe. And

 The flow rate (L) of the liquid is adjusted so that the membrane area Sx (cm2) of the porous membrane of the degassing module and the flow rate L (mlZh) of the liquid flowing through the liquid feeding pipe have a relationship of Sx≥LZ20. A liquid feeding method characterized by controlling.

[17] The liquid from the liquid supply device is sent to a medical device for treatment or examination in a living body having a water molecule activation mechanism that directly or indirectly activates the movement of water molecules in the liquid. This is a liquid feeding method in which liquid is fed after removing dissolved gas or bubbles contained in the liquid while controlling the flow rate of the liquid passing through the deaeration module having a porous membrane when liquid is fed using the liquid pipe. And

 The flow rate L (ml / ml) of the porous membrane of the degassing module and the flow rate L (mlZh) of the liquid flowing through the liquid feeding pipe have a relationship of Sx≥LZlO. A liquid feeding method characterized by controlling h).

[18] A degassing module for removing dissolved gas or bubbles contained in a liquid,

 A module body in which the distal end opening and the proximal end opening are in communication with each other;

 A mounting portion for liquid-tightly attaching the tip opening side of the module body to a liquid storage portion containing a liquid to be degassed;

Potted in the vicinity of the base end opening with one end kept open, the other A plurality of bundled porous hollow fiber membranes arranged in the module main body with the end portion closed in the lumen or being exposed to the outside from the tip opening, Depressurizing the base end opening, and removing dissolved gas or bubbles contained in the liquid from the other end side contacting the liquid in the liquid container through the porous hollow fiber membrane. Features degassing module.

 [19] The deaeration module according to [18], wherein the porous hollow fiber membrane is curved in a U-shape, and the U-shaped curved portion constitutes the other end portion.

 20. The deaeration module according to claim 18, wherein the porous hollow fiber membrane forms a lumen closed state at the other end by heat fusion.