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WO1989006566A1 - Membrane a fibre creuse et appareil de traitement de fluide l'utilisant - Google Patents

Membrane a fibre creuse et appareil de traitement de fluide l'utilisant Download PDF

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Publication number
WO1989006566A1
WO1989006566A1 PCT/JP1989/000046 JP8900046W WO8906566A1 WO 1989006566 A1 WO1989006566 A1 WO 1989006566A1 JP 8900046 W JP8900046 W JP 8900046W WO 8906566 A1 WO8906566 A1 WO 8906566A1
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WO
WIPO (PCT)
Prior art keywords
hollow fiber
fiber membrane
hollow
blood
membrane
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/JP1989/000046
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English (en)
Japanese (ja)
Inventor
Hiroyuki Nakamaru
Hitoshi Miyazaki
Yukio Seita
Ken Tatebe
Shoichi Nagaki
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Terumo Corp
Original Assignee
Terumo Corp
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
Application filed by Terumo Corp filed Critical Terumo Corp
Publication of WO1989006566A1 publication Critical patent/WO1989006566A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D69/00—Semi-permeable membranes for separation processes or apparatus characterised by their form, structure or properties; Manufacturing processes specially adapted therefor
    • B01D69/08—Hollow fibre membranes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D69/00—Semi-permeable membranes for separation processes or apparatus characterised by their form, structure or properties; Manufacturing processes specially adapted therefor
    • D—TEXTILES; PAPER
    • D01—NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
    • D01D—MECHANICAL METHODS OR APPARATUS IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS
    • D01D5/00—Formation of filaments, threads, or the like
    • D01D5/24—Formation of filaments, threads, or the like with a hollow structure; Spinnerette packs therefor

Definitions

  • the present invention relates to a hollow fiber membrane and a fluid treatment apparatus such as an artificial kidney and an artificial lung using the same, and more particularly to a hollow fiber membrane capable of generating a turbulent flow in a flow of a fluid such as blood. And a fluid treatment device using the same.
  • the peripheral wall has a material selective permeability, and a hollow portion continuously penetrating therethrough is provided in the longitudinal direction. That is, a patient's blood flows into the hollow inside of the hollow fiber membrane, and a dialysate flows along the outside, that is, the surface of the hollow fiber membrane, and dialyzes through the hollow fiber membrane. This removes waste products in the blood and corrects the electrolyte concentration, and gives a pressure difference between the inside and outside of the hollow fiber membrane, and the excess water in the blood is removed by ultrafiltration. It removes the minute.
  • a hollow fiber oxygenator is used in an extracorporeal circulation circuit to introduce a patient's blood outside the body, add oxygen to the blood, and remove carbon dioxide.
  • Hollow fiber membranes are also used in artificial lungs.
  • this hollow fiber membrane can only detect blood from the blood. It is also used to separate or remove certain components from the blood to treat autoimmune diseases and the like.
  • a hollow fiber membrane one having a wall thickness of several m to 60 m and an outer diameter of 10 / xm to several hundred um is used.
  • a high molecular compound such as cellulose ester and cellulose is used as an artificial kidney, and polypropylene is used as an artificial lung. Etc. are used.
  • An artificial kidney or the like using such a hollow fiber membrane is formed, for example, in a tubular housing having an inflow port and an outflow port near both ends, respectively. It is manufactured by storing a bundle of thread membranes and then tightly fixing both ends of the tubular housing together with both ends of a tubular housing with resin such as polyurethane. .
  • the hollow fiber membrane has a wall thickness of several m to about 60 ⁇ , and thus is not sufficiently strong, and has a large number of bundles to form a tubular housing. Because of the tight mounting of the hollow fiber membrane, the hollow fiber membrane could be crushed depending on the mounting condition.
  • the present invention solves the above-mentioned problems of the conventional hollow fiber membrane, and for example, the dialysis effect is improved in the case of an artificial kidney, and the dialysis effect is improved in the case of an artificial lung.
  • An object of the present invention is to provide a membrane and a fluid treatment device using the same.
  • a hollow fiber membrane according to the present invention has a hollow portion continuously penetrating in a longitudinal direction, and a fluid flows through the hollow portion in the hollow fiber membrane.
  • a protrusion for generating turbulence in the flow of the fluid is provided on the inner wall surface of the hollow portion.
  • the hollow fiber membrane according to the present invention further has at least one ridge provided spirally on the outer surface of the hollow fiber membrane in the longitudinal direction. It is characterized by the following.
  • the fluid treatment apparatus is configured such that the hollow fiber membrane is housed in a housing as a fluid treatment membrane.
  • the protruding portion is at least one protruding ridge spirally formed in the longitudinal direction of the hollow portion.
  • the porous hollow fiber membrane according to the present invention has a hollow portion continuously penetrating in the longitudinal direction, and the oxygen-containing gas flows through the hollow portion, and blood flows along the outer wall surface.
  • the oxygenator is characterized in that the porous hollow fiber membrane is housed in a housing as a gas exchange membrane.
  • the fluid flowing in the hollow portion flows in a turbulent state due to the presence of the projecting portion, particularly the spiral ridge. Therefore, when this hollow fiber membrane is used for, for example, an artificial kidney, the dialysis efficiency is improved, and when it is used for a hollow fiber type artificial lung, the gas exchange capacity is improved. A smaller membrane area is required, which makes it possible to reduce the module's priming volume. In addition, since the strength is improved by the presence of the protruding portion, there is no danger of being crushed by the adjacent hollow fiber membrane. Further, when the porous hollow membrane having a projecting portion on the outer wall surface is used for a so-called external perfusion type artificial lung, the same effect as the above-described artificial lung can be obtained.
  • FIG. 1 is a perspective view showing a cross section of a hollow fiber membrane according to a first embodiment of the present invention
  • FIG. 2 is a cross sectional view taken along the line II--II of FIG. 1
  • FIG. FIG. 4 is a side view showing an artificial kidney using the hollow fiber membrane shown in FIG. 4 as a cross section.
  • FIG. 4 is a perspective view showing an example in which an outer wall of the hollow fiber membrane shown in FIG.
  • the figure is a perspective view showing the porous hollow fiber membrane according to the second embodiment
  • FIG. 6 is a schematic configuration diagram showing the manufacturing process of the hollow fiber membrane shown in FIG. 5, and FIGS.
  • FIG. 5 is a side view showing a partial cross section of the artificial lung using the hollow fiber membrane of FIG.
  • FIG. 1 shows a hollow fiber membrane 1 according to a first embodiment of the present invention
  • FIG. 2 shows a cross-sectional configuration along a line II-II in FIG.
  • the hollow fiber membrane 1 is used for, for example, an artificial kidney, and is made of a polymer compound having a substance-selective permeability.
  • Such high molecular compounds include, for example, cellulose, cellulose ester, polyamide, polyacrylonitrile, and polymethylmethacrylate.
  • Preferred are cellulose, polyvinyl alcohol, polycarbonate, copolymers thereof, and mixtures thereof, and particularly preferred are cellulose and cellulose esters.
  • This hollow fiber membrane 1 continuously penetrates over the entire fiber length.
  • a hollow portion 2 is formed. Blood flows inside the hollow part 2 as a fluid.
  • the hollow fiber membrane 1 wall thickness l ⁇ 4 0 / im of the peripheral wall 3, is rather to preferred. 8 to 3 0 iz m der is, and the outer diameter d 2 is 5 0 ⁇ ; L 0 0 0 m, It is preferably 150 to 700 im.
  • a spiral ridge 4 for generating turbulent blood flow is formed on the inner wall surface of the hollow portion 2.
  • the ridges 4 are formed at a certain angle, for example, at an angle of 15 ° with respect to the longitudinal direction of the hollow fiber membrane 1.
  • the blood flowing from one end to the other end in the hollow part 2 is disturbed by the presence of the spiral ridge '4. It flows in a so-called turbulent state. Therefore, compared to the conventional case of a hollow fiber membrane that flows in a laminar flow state, the blood flow that flows without contacting the wall of the hollow portion 2 is remarkable. As a result, the dialysis effect is remarkably improved when used in artificial kidneys.
  • the strength of the peripheral wall 3 is improved by the presence of the ridges 4. Therefore, even when a large number of bundles are bundled and tightly attached to the tubular housing to produce an artificial kidney, the hollow fiber membrane 1 itself does not have the possibility of collapse.
  • the ridge 4 may be substantially parallel to the longitudinal direction of the hollow fiber membrane 1 or may have an angle.
  • the helix angle in the case of having the angle of the ridge 4 is: It is 40 ° or less, preferably 20 ° or less. If the angle is larger than 40 °, the ratio of the ridges 4 to the fixed area of the hollow fiber membrane 1 increases, and accordingly, the film thickness becomes thicker, so that the material exchange ability decreases. In addition, thrombus may occur. Also, this angle may vary rather than be constant, but it is practical to be constant in terms of blood flow stability and manufacturing.
  • the height and width of the ridge 4 can be appropriately selected according to the inner diameter and the thickness of the hollow fiber membrane 1, and the range is 2 to 150 ix m. I want to be. In addition, the height and width may be constant or varied, but it is desirable that the blood flow is stable and that it is constant in terms of manufacturing. If the ridges 4 are larger than the above range, the wall thickness of the hollow fiber membrane 1 increases, and on the contrary, the dialysis efficiency decreases. Further, if the ridge 4 is smaller than the above range, the effect of generating turbulent blood flow cannot be sufficiently obtained.
  • FIG. 3 shows a specific configuration of an artificial kidney made by using the hollow fiber membrane 1 described above.
  • blood flows from the blood inflow port 5a provided in the housing 7 to the outflow port 5b, and the dialysate inflow port 6a.
  • Blood flows through the hollow portion 2 of the hollow fiber membrane 1 and dialysate flows outside the dialysate by the dialysate flowing from a to the dialysate outflow bottle 5b. .
  • the blood and the dialysate come into contact with each other via the wall surface of the hollow fiber membrane 1, whereby waste and excess water in the blood can be removed.
  • the spiral ridges 4 are formed in the hollow fiber membrane 1 as described above, the blood flow changes from a laminar flow state to a turbulent flow state, as described above. The dialysis effect is significantly improved.
  • a spinning solution of the hollow fiber membrane 1 for example, copper ammonia cellulose is extruded from an annular spinning hole of a spinning nozzle into an organic solvent.
  • a non-coagulating liquid for the spinning dope for example, IMP (isopropyl myristinic acid) is introduced and filled into the center of the spinning dope spun in a linear shape, and discharged. Spin while maintaining the hollow state.
  • a small hole is provided at the inlet of the non-coagulable liquid (that is, the center of the spinning nozzle), and a melt of the same material is extruded from here, and a spinneret for extruding the melt of the material
  • a helical shape that continuously wraps around the inner wall of the hollow part 2 by extruding and fusing at a high speed tangentially the inside of the hollow fiber directly coming out of the hollow hole of the chile A ridge 4 can be formed.
  • one ridge 4 for generating turbulence is used, but two or more ridges may be used.
  • the number is too large, the effect of reinforcing the wall surface increases, but the effect of generating turbulence does not increase so much.
  • the average wall thickness of the hollow fiber membrane 1 increases, and on the contrary, It is not preferable because dialysis efficiency is reduced. Therefore, Articles 1 to 8 are appropriate as the number of ridges 4.
  • the helical protrusion for generating turbulence is not limited to the ridge 4, The protrusions may be formed discontinuously, may be formed in any shape without being formed spirally, and may be in a state where turbulence of blood occurs. It should be.
  • the ridges 4 are formed inside the hollow portion 2 so that turbulent flow is generated in the blood flowing inside.
  • a similar ridge 8 may be provided on the outer wall surface of the hollow fiber membrane 1.
  • FIG. 5 shows a porous hollow fiber membrane 11 according to a second embodiment of the present invention.
  • This porous hollow fiber membrane 11 is used for human lungs, and has two ridges 13 a. 13 spirally extending in the longitudinal direction on the inner wall surface of the hollow portion 12. b is given.
  • the hollow fiber membrane 11 has an inner diameter of 100 to 400 am, preferably 150 to 300 um, and an outer diameter of 160 to 500 wm. It is between 180 and 380 um.
  • the ridges 13a and 13b each have a height and width of 2 to 50 mm, preferably 5 to 45 ii m. Each pitch of these ridges 13a and 13b is 1-2 Ocm, preferably 5 era.
  • the blood flow is disturbed by the ridges 13 a and 13 b, and the diffusion speed of gas in the blood is dramatically improved.
  • the gas exchange capacity of the oxygenator is significantly improved. Therefore, the membrane area of the oxygenator module can be reduced. The blood volume in the human lungs can be reduced, and the burden on the patient can be reduced.
  • FIG. 6 is a schematic view showing a process for producing the porous hollow fiber membrane 11. That is, first, a mixture 14 of a polyolefin, an organic filler, and a crystal nucleating agent is supplied from a hopper 15 to a kneading machine, for example, a single-screw extruder 16 to supply the mixture. After melt-blending 14 and extruding it, it is sent to the spinning device 17 and discharged into the gaseous atmosphere, for example, air from the deformed annular hole 18 by a highly quantitative gear pump.
  • a kneading machine for example, a single-screw extruder 16
  • a spiral groove is provided in the outer cylinder of the die of the irregularly shaped hole 18, and nitrogen gas, carbon dioxide gas, Gases such as um, argon and air, or heat-resistant liquids such as silicones are introduced. Therefore, a hollow object 19 having a hollow inside and a helical ridge formed on the inner wall surface is discharged from the irregular shaped hole 18. Then, after the discharged hollow material 19 travels 1 to 100 mm, the hollow material 19 is introduced into a cooling tank 21 containing a cooling solidified liquid 20, and the cooled solidified liquid 20 is formed. It is cooled by contacting, and the cooled solidified liquid 20 flowing down through the flow pipe 22 is received in the solidification tank 23 and stored, and is also hollowed therein. Material 19 is introduced and solidified.
  • the accumulated cooling solidified liquid 20 is discharged from the circulation line 24 and returned to the cooling tank 21 by the circulation pump 25.
  • the cooled and solidified hollow fiber membrane 26 is deflected by the deflection rod 27. After that, the mixture is guided to an extraction step (not shown) via a dry roll 28, and the organic filler is further removed. After being subjected to a heat treatment, the porous hollow fiber membrane is formed. It is wound up.
  • Polyolefin used as the above-mentioned raw material includes propylene homopolymer, ethylene homopolymer, and other materials containing propylene as a main component.
  • a block polymer with a mer, etc. but those with a melt index of 5 to 70 are preferred.
  • an organic filler it can be uniformly dispersed in the above-mentioned polyrefin under melting of the above-mentioned polyrefin, and can be used for the extract. It must be highly soluble.
  • organic fillers include liquid paraffin, ⁇ -methyl olefin oligomer, propylene oligomer, ethylene propylene oligomer, and paraffin.
  • raffin wax, various hydrocarbons, etc. and it is preferably a liquid paraffin.
  • the mixing ratio of the polyolefin and the organic filler is preferably 35 to 170 parts by weight, more preferably 100 to 100 parts by weight of the polyolefin, and is preferably 50 to L50 parts by weight. That is, if the amount of the organic filler is less than 35 parts by weight, a porous hollow fiber membrane having sufficient gas permeability cannot be obtained, while if the amount exceeds 170 parts by weight, the viscosity becomes low. Too large to hold the deformed shape. Such kneading of the raw materials is performed using an extruder such as a twin-screw extruder, for example.
  • a crystal nucleating agent to be mixed in the raw material a polyrefin having a melting point of 150 ° C or more and a gel point is used. Is an organic heat-resistant substance having a temperature equal to or higher than the crystallization start temperature.
  • the mixing ratio of the polyolefin and the crystal nucleating agent is such that the amount of the crystal nucleating agent is 0 with respect to 100 parts by weight of the polyolefin. 1 to 5 parts by weight, preferably 0.2 to: 1.0 parts by weight.
  • the hollow solidified material 19 cooled and solidified is drawn off by the drive roller 28, and the kneading material discharged from the irregular shaped hole 18 is pulled out at this drawing speed.
  • the ratio of the discharge linear velocities to 1 to 100, a stable hollow fiber membrane can be manufactured. In other words, if it is less than 1, the hollow article 19 cannot be stably manufactured because no tension is applied to it, and if it exceeds 100, it becomes difficult to maintain an irregular shape. .
  • the cooling solidification liquid 20 use a substance which does not dissolve the polyolefin and the organic filler and has a relatively high boiling point.
  • the cooling temperature is between 10 and 90, preferably between 20 and 5 ° C. In other words, if the temperature is less than 10 " ⁇ , the cooling and solidification rate is too high, and most of the thick part becomes a dense layer, so that the gas exchange capacity is reduced, while the temperature exceeds 90 ° C. In this case, the crystallization rate of the polyrefin becomes slow, and when used in an artificial lung, the pore size becomes too large, which may cause blood leakage.
  • FIGS. 7 and 8 each show a specific configuration of an artificial lung made using the porous hollow fiber membrane 11, and FIG. 7 shows a hollow fiber bundle at the center.
  • a type having a constricted portion 30 is shown in FIG. 8, and FIG. 8 shows a type of oxygenator having no constricted portion.
  • reference numeral 31 denotes a housing.
  • the oxygen-containing gas flows from the gas inflow port 33a to the gas outflow port 33b, so that blood flows inside the hollow fiber membrane 11 and An oxygen-containing gas flows outside.
  • gas exchange is performed between carbon dioxide in the blood and oxygen in the gas via the holes of the hollow fiber membrane 11.
  • the spiral ridges 13a and 13b are formed in the porous hollow fiber membrane 11, the blood flow is changed from a laminar flow state to a turbulent flow state. And the gas exchange efficiency is improved.
  • the porous hollow fiber membrane according to the present embodiment is used for a so-called externally perfused artificial lung, and has 2 to 8 helical protrusions on the outer wall surface of the hollow portion in the longitudinal direction. Articles have been enacted.
  • the hollow fiber membrane has an inner diameter of 100 to 400 / m, preferably 150 to 300 / xm, and an outer diameter of 160 to 500 ILm, It is preferably 180-380 wm.
  • the ridges 13a and 13b have a height and width of 2 to 50 Um, preferably 5 to 45 wm, respectively.
  • the pitch of each of these ridges is 1-20 cm, preferably 5 cm.
  • the ridges disturb the blood flow, and the gas diffusion rate in the blood increases dramatically. Improve and As a result, the gas exchange capacity of the oxygenator is significantly improved. In addition, the spacing between the hollow fibers is kept uniform by the ridges, so blood comes into contact with all the hollow fibers without channeling, so gas exchange efficiency is improved. Increases.
  • a mixture 14 of a polyolefin, an organic filler, and a crystal nucleating agent is supplied from a hopper 15 to a kneading machine, for example, a single screw extruder 16, and the mixture 1 4 is melt-kneaded and extruded, and then sent to a spinning device 17 and discharged into a gaseous atmosphere, for example, air from the irregular shaped hole 18 by a highly quantitative gear pump.
  • a spiral groove is provided in the out die of the modified annular hole 18, and nitrogen gas, carbon dioxide gas, and helium are provided in the center of the inside of the modified rectangular hole 18.
  • a hollow object 19 having a hollow inside and a spiral ridge formed on the outer wall surface is discharged from the modified ring-shaped hole 18. Then, after the discharged hollow object 19 is caused to travel 1 to 100 mm, the hollow object 19 is introduced into a cooling tank 21 containing a cooling solidified liquid 20, and the cooled solidified liquid 2 is introduced.
  • the cooling solidified liquid 20 flowing down through the flow pipe 22 is received and stored in the solidification tank 23, and is cooled by bringing the solidified liquid into contact with the solidified liquid 23.
  • the hollow material 19 is introduced therein and solidified.
  • the accumulated cooling solidified liquid 20 is discharged from the circulation line 24 and returned to the cooling tank 21 by the circulation pump 25. Cooled and solidified
  • the hollow fiber membrane 26 is diverted by the deflecting rod 27, and then guided to an extraction step (not shown) via the drive roller 28, and furthermore, to the organic layer. After the filler is removed and heat-treated, it is wound up as a hollow fiber membrane.
  • the artificial kidney and the artificial lung have been described using the fluid flowing through the hollow fiber membranes 1 and 11 as blood, but the present invention is not limited to this. Needless to say, it can be used for other fluid treatment devices, for example, water purifiers.
  • the hollow fiber membrane 1 according to the first embodiment was manufactured, and the dialysis effect was examined using a conventional hollow fiber membrane without the ridges 4 as a comparative example.
  • the outer diameter d 2 has produced a 2 5 0 ii m Doa emissions monitor Aseru B over scan made of hollow fiber membranes.
  • a single protrusion having a height and a width of about 30 wm is formed in the hollow portion of the hollow fiber membrane at a pitch of about 4 cm, about 10 ° with respect to the longitudinal direction of the hollow fiber membrane.
  • the hollow fiber membrane (A) of the present invention formed at an angle and the hollow fiber membrane (B) without the ridges 4 have the same cross-sectional area as a tubular housing of the same size.
  • the dialysis performance was measured with an impitro. The results are shown in Tables 11 (a) and 11 (b). As a result As is clear from the above, the dialysis effect of the hollow fiber membrane of the present invention was significantly improved as compared with the conventional one.
  • the wall thickness d 1 is 1 5 ii m
  • outer diameter d 2 is 2 3 0 um
  • about 3 era pitch middle hollow fiber longitudinal to the direction in pairs to about 1 0 beta angle formed by the present onset Ming hollow fiber membrane (C)
  • the hollow fiber membrane had set only Do a ridge 4
  • Table 2-(a) and Table 2-(b) show the results of dialysis performance in which (D) and were compared in the same manner as in Experimental Example 1 described above, respectively. As is clear from these results, the hollow fiber membrane of the present invention was used.
  • the porous hollow fiber membrane (E) of the present invention obtained in this manner is provided with eight protrusions having a height of 40 iLim and a width of 25 wm in the hollow portion in a spiral shape. It was a bad thing.
  • This porous hollow fiber membrane 4 effective length 1 have use a cm, membrane area 5.
  • In 4 m 2, to create a packing ratio 5 4% of the oxygenator module, the flow inside the porous hollow fiber membrane blood The oxygen gas addition ability and the carbon dioxide gas exclusion ability in this case were measured. The results are shown in Table 3.
  • a porous nozzle was formed by the same method as described above except that the spinning nozzle was formed in a concentric shape and the ratio between the drawing speed and the discharge linear speed was set to 170.
  • a hollow fiber membrane (F) was obtained.
  • the porous hollow fiber membrane obtained in this manner was a straight hollow fiber membrane having an inner diameter of 200 ix m and a wall thickness of 45 mm. And have use of porous hollow fiber membranes of this creates an effective length 1 4 cm, membrane area 5. Filling rate 4 m 2 5 4% of the oxygenator modular Yu Lumpur, Shi flow inside the hollow fiber membrane blood Carbon dioxide Gas addition ability and carbon dioxide elimination ability were measured. The results are shown in Table 3.
  • a hollow object is extruded from the deformed circular spinning hole into the air at an air distance of 6 rara. Introduced into polyethylene glycol solution. At this time, the ratio between the take-off speed and the discharge linear speed was 50. Subsequently, the hollow material is brought into contact with 1.1.2—trichloro-1,2,2—trifluoroethane to extract and remove the liquid paraffin. After heat treatment, it was wound up.
  • the porous hollow fiber membrane (G) of the present invention obtained in this way has a spiral shape with eight protrusions having a height of 40 im and a width of 25 wm on its outer wall. It was a bad thing.
  • This porous hollow fiber membrane had use the in effective length 9 cm, membrane area 2.
  • a porous method was used in the same manner as described above except that the spinning nozzle was formed in a concentric shape and the ratio between the drawing speed and the discharge linear speed was set to 170. A hollow fiber membrane (H) was obtained.
  • the porous hollow fiber membrane obtained in this manner was a straight hollow fiber membrane having an inner diameter of 200 im and a wall thickness of 45 ⁇ . And have use of porous hollow fiber membranes of this creates an effective length 9 cm, membrane area 2. Filling rate 4 m 2 4 2% of the oxygenator modular Interview Lumpur, Shi flow outside of the hollow fiber membrane blood The ability to add carbon dioxide gas and the ability to eliminate carbon dioxide gas were measured. The results are shown in Table 4.
  • the hollow fiber membrane of the present invention has an oxygen gas adding ability and a carbon dioxide gas removing ability as compared with the conventional one. Remarkably improved
  • a single pass of bovine blood flows through the hollow fiber membrane module at a flow rate of 6.0 l / min, and pure oxygen flows out of the hollow fiber membrane at a flow rate of 6.0 nm / min. flushed with oxygenator inlet
  • PC 0 2 carbon dioxide partial pressure
  • P 0 2 oxygen gas partial pressure
  • a blood gas measuring device Radiometer Inc., BGA 3 type
  • Hematocrit value -353 ⁇ 4 (adjusted with physiological saline)
  • Hemoglobin concentration 12 soil 1 g / d ⁇
  • the hollow fiber membrane according to the present invention generates turbulence in the fluid flowing inside and outside the hollow portion or outside, so that the inner wall surface and the outside The flow rate of the fluid in contact with the wall surface is remarkably increased, so that it is suitably used for artificial kidneys and artificial lungs, and is also widely used for blood separation membranes and the like.
  • the module is formed by reducing the membrane area. Can reduce the volume of fluid flow, thus reducing the burden on the patient, for example, in an artificial lung. Can be reduced.

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  • Chemical & Material Sciences (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • Textile Engineering (AREA)
  • External Artificial Organs (AREA)

Abstract

Membrane à fibre creuse (1, 11) utilisée pour un rein artificiel, un poumon artificiel ou une membrane de séparation du plasma sanguin. Cette membrane présente une partie creuse (2) s'étendant en continu dans le sens de la longueur, et un fluide s'écoule à travers l'intérieur et/ou l'extérieur de la partie creuse (2). Des saillies (4, 8, 13a, 13b) sont créées sur la surface de la paroi interne et/ou sur la surface de la paroi externe de la partie creuse (2), de manière à produire un écoulement turbulent dans le fluide. Par conséquent, le fluide s'écoule en formant des turbulences à l'intérieur et/ou à l'extérieur de la partie creuse, ce qui augmente considérablement le débit du fluide entrant en contact avec la surface de la paroi. Lorsqu'on utilise cette membrane dans une rein artificiel, elle permet d'améliorer le rendement de la dialyse, et lorsqu'on l'utilise dans un poumon artificiel, elle permet d'augmenter la capacité d'échange gazeux. En outre, on peut accroître la résistance de la fibre creuse, de manière à éviter que la membrane ne soit écrasée par les membranes adjacentes.
PCT/JP1989/000046 1988-01-20 1989-01-19 Membrane a fibre creuse et appareil de traitement de fluide l'utilisant Ceased WO1989006566A1 (fr)

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Application Number Priority Date Filing Date Title
JP1033788 1988-01-20
JP63/10337 1988-01-20

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Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1995034373A1 (fr) * 1994-06-10 1995-12-21 Baxter International Inc. Ecartement par monofilaments de membranes fibreuses et creuses et dispositifs d'oxygenation du sang comprenant ces membranes
KR19990027172A (ko) * 1997-09-29 1999-04-15 구광시 중공사막
WO2000001472A1 (fr) * 1998-07-06 2000-01-13 University Of Pittsburgh Systeme d'amelioration du transport via des membranes en fibres creuses et des molecules de membrane
EP1469934A4 (fr) * 2002-01-29 2005-09-07 Amersham Biosciences Membrane Membranes de fibres creuses a surface spiralee
JP2007283267A (ja) * 2006-04-20 2007-11-01 Kansai Electric Power Co Inc:The ガス分離方法及び装置
EP2143480A1 (fr) 2008-07-02 2010-01-13 Rheinisch-Westfälisch-Technische Hochschule Aachen Dispositif de membrane
JP2012527281A (ja) * 2009-05-19 2012-11-08 バスキュラー フロー テクノロジーズ リミテッド 血管移植片
GB2573265A (en) * 2018-03-12 2019-11-06 Brightwake Ltd Apparatus for treating blood
WO2021061955A1 (fr) * 2019-09-26 2021-04-01 Cardiacassist, Inc. Membrane de fibres d'oxygénateur à propriétés de surface modifiées

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JPS5766137A (en) * 1980-10-09 1982-04-22 Asahi Medical Co Hoolow fiber
JPS60110305A (ja) * 1983-11-21 1985-06-15 Teijin Ltd 中空繊維膜及びそれを用いた体液処理器
JPS6118404A (ja) * 1984-07-04 1986-01-27 Teijin Ltd 中空糸膜及びその製造方法

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WO1995034373A1 (fr) * 1994-06-10 1995-12-21 Baxter International Inc. Ecartement par monofilaments de membranes fibreuses et creuses et dispositifs d'oxygenation du sang comprenant ces membranes
KR19990027172A (ko) * 1997-09-29 1999-04-15 구광시 중공사막
WO2000001472A1 (fr) * 1998-07-06 2000-01-13 University Of Pittsburgh Systeme d'amelioration du transport via des membranes en fibres creuses et des molecules de membrane
EP1469934A4 (fr) * 2002-01-29 2005-09-07 Amersham Biosciences Membrane Membranes de fibres creuses a surface spiralee
JP2007283267A (ja) * 2006-04-20 2007-11-01 Kansai Electric Power Co Inc:The ガス分離方法及び装置
EP2143480A1 (fr) 2008-07-02 2010-01-13 Rheinisch-Westfälisch-Technische Hochschule Aachen Dispositif de membrane
JP2012527281A (ja) * 2009-05-19 2012-11-08 バスキュラー フロー テクノロジーズ リミテッド 血管移植片
US9067026B2 (en) 2009-05-19 2015-06-30 Vascular Flow Technologies Limited Vascular graft
TWI578975B (zh) * 2009-05-19 2017-04-21 泰塞德佛羅科技公司 人工血管
GB2573265A (en) * 2018-03-12 2019-11-06 Brightwake Ltd Apparatus for treating blood
GB2573265B (en) * 2018-03-12 2022-06-15 Tsi Tech Limited Apparatus for treating blood
US11911549B2 (en) 2018-03-12 2024-02-27 Tsi Technology Limited Plasmapheresis device
WO2021061955A1 (fr) * 2019-09-26 2021-04-01 Cardiacassist, Inc. Membrane de fibres d'oxygénateur à propriétés de surface modifiées

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