WO2000057996A1 - Dispositif comprenant au moins une membrane preexistant sous la forme d'une fibre creuse pour filtrer les fluides corporels - Google Patents

Dispositif comprenant au moins une membrane preexistant sous la forme d'une fibre creuse pour filtrer les fluides corporels Download PDF

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Publication number
WO2000057996A1
WO2000057996A1 PCT/EP2000/002166 EP0002166W WO0057996A1 WO 2000057996 A1 WO2000057996 A1 WO 2000057996A1 EP 0002166 W EP0002166 W EP 0002166W WO 0057996 A1 WO0057996 A1 WO 0057996A1
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WO
WIPO (PCT)
Prior art keywords
hollow fibers
hollow fiber
membrane
hollow
outside
Prior art date
Application number
PCT/EP2000/002166
Other languages
German (de)
English (en)
Inventor
Hans-Dieter Lehmann
Siegfried Kaiser
Melanie Krebs
Original Assignee
Jostra Medizintechnik Ag
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
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Application filed by Jostra Medizintechnik Ag filed Critical Jostra Medizintechnik Ag
Publication of WO2000057996A1 publication Critical patent/WO2000057996A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1621—Constructional aspects thereof
    • A61M1/1623—Disposition or location of membranes relative to fluids
    • A61M1/1625—Dialyser of the outside perfusion type, i.e. blood flow outside hollow membrane fibres or tubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/02—Blood transfusion apparatus
    • A61M1/0281—Apparatus for treatment of blood or blood constituents prior to transfusion, e.g. washing, filtering or thawing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/3403—Regulation parameters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
    • A61M1/3633—Blood component filters, e.g. leukocyte filters
    • A61M1/3635—Constructional details
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow

Definitions

  • the invention relates to a device with at least one semi-permeable, wettable, in particular hydrophilic membrane in the form of a hollow fiber with the outside and lumens for ultrafiltering body fluids, in particular blood.
  • Devices of the aforementioned type are generally known from the prior art.
  • the known devices are used to filter body fluids with corpuscular ingredients, such as blood.
  • semipermeable membranes generally separate two areas that are sealed from one another: the liquid to be filtered flows into one area and leaves it as enriched retentate after the filtrate has been separated off, which flows out of the other area after passing through the semipermeable membrane.
  • the pore size for such ultrafilters is below 0.1 ⁇ m in diameter, so that albumin can no longer pass through the membrane, but the low-molecular substances and electrolytes dissolved in the liquid can.
  • the body fluid to be filtered is passed through the lumen of the hollow fibers with laminar flow.
  • the filtrate is then separated from the liquid to be filtered by a pressure gradient across the membrane, emerges from the outer walls of the hollow fibers and is drained off from there.
  • such devices are used as hemofilters, hemoconcentrators or plasma filters for the treatment of blood.
  • Semipermeable membranes suitable for these devices are described, for example, in DE 34 26 331 AI or WO 98/52683.
  • a membrane is semipermeable when it no longer allows molecules of a certain size to pass.
  • semipermeable is understood here to mean that, for example, molecules which do not at least have the size of albumin dissolved in the blood cannot pass through the membrane.
  • the driving force for the separation of low-molecular substances is a concentration gradient between the liquid to be filtered in the lumen of the hollow fiber and the dialysis solution that flows around the outside of the hollow fiber.
  • An essential feature of the hollow fibers used in conventional filters is the arrangement of a separating layer on the respective inside of these hollow fibers, so that the filtrate first passes through this inner separating layer when it is filtered, then traverses the membrane and finally emerges on the outside of the hollow fiber.
  • a conventional filter of the type described above is known for example from EP 0 294 737 B1.
  • a filter which consists of a plurality of bundled polysulfone hollow fiber membranes which are arranged in a housing, the two ends of the hollow fiber bundles being fixed to the housing with a curable resin, but remaining open. With these filters, too, the body fluids are passed through the lumen of the hollow fibers, the filtrate escaping on the outside and being drained off.
  • the semipermeable membranes used here which are used for blood purification, have an inside dense skin layer with a pore size of less than 10 nm. With plasma filters, however, conventional membranes with pore sizes down to the micrometer range are used.
  • the aim is therefore that the liquid to be filtered covers the shortest possible path in the fiber lumen, which can only be achieved by increasing the number of hollow fibers with the same effective membrane area.
  • the proportion of usable membrane area in the total membrane area decreases due to the increase in the number of fibers with a concomitant shortening of the fiber length.
  • the proportion of membrane area used for the sealing at the ends of the fibers with increasing number of fibers also increases and is not available for filtration.
  • a compromise between the length and number of hollow fibers must be found in the conventional filters, which, however, can never be completely satisfactory.
  • the inflow and outflow surfaces of the conventional filters pose a risk of thrombus formation, because here the porous substructures of the hollow fiber membranes are cut transversely in the pouring area and therefore represent a foreign surface with great roughness, which in turn causes thrombus formation in the blood offers.
  • the larger the number of hollow fibers in the conventional device the larger this area and thus the risk of thrombus formation.
  • With long-term use of such blood filters because of the increased foreign surface there is also a greater risk that the patient will show an immune reaction against the filter.
  • DE 38 23 858 AI describes a technical filtering based on the dead-end principle with a microporous membrane constructed from hollow fibers.
  • the flow of the hollow fibers is carried out on the outside, so that the filtration takes place from the outside into the lumen of the hollow fibers.
  • well-known filtering works according to the dead-end principle, well-known ones are formed here Way a filter cake on the outside of the hollow fibers, so that the filter capacity of the known filter is quickly exhausted.
  • the known filtering is not suitable for the filtration of body fluid, in particular blood, inter alia because it would clog up very quickly. When filtering blood, this dead-end filtration would press red blood cells into the pores of the microporous membrane and hemolyze immediately.
  • this object is achieved according to the invention in that the filtration takes place from the outside into the lumen.
  • the inventors of the present application have in fact recognized that a se ipermeable, wettable, in particular hydrophilic hollow fiber, which is not permeable to albumin, can be used for ultrafiltration, in which the liquid to be filtered flows against the outside of the hollow fiber.
  • a very small pressure drop between the inlet opening for the liquid to be filtered and the locations of the membranes where the actual one Filtration takes place so that there is only a slight pressure drop across the entire system of the filter.
  • the pressure drop in a tested filter device according to the invention is less than a third of the pressure drop in a conventional comparative filter. This means that almost the entire pressure at the inlet opening of the filter is available as a driving force on the membranes for the filtration.
  • a turbulent flow against the membranes can be achieved by the flow of the hollow fibers on the outside, whereby the so-called concentration polarization can be avoided.
  • concentration polarization can be avoided.
  • Another advantage of the new device is that the entire membrane surface contacted by the liquid to be filtered is available for filtration. It is also advantageous that there are no porous hollow fiber gates in the inflow or outflow region of the filter, so that the porosity known from the prior art, which can lead to thrombus formation in the filtration of blood, is also absent.
  • the length of the hollow fibers is also not limited by the pressure drop in the hollow fibers. It is therefore not necessary to use many short fibers in which - as stated above - a relatively large proportion of the effective membrane area is lost through the sealing. at the new device has no usable membrane surface that comes into contact with the liquid to be filtered.
  • Another economic advantage of the new device is that the improved effectiveness compared to conventional systems means that filters with comparable efficiency can be produced more cost-effectively because less hollow fiber material has to be used. In this way, a filtration rate comparable to a conventional filter is achieved with less than a third of the usual membrane area. This also makes it possible to further reduce the foreign surface with the advantages already mentioned.
  • the inventors of the present application have also recognized that the wall thickness of an externally incident fiber can be made thicker compared to an internally flowed fiber, since the inside diameter of the fiber can be kept very small due to the low-viscosity filtrate flowing therein. If, in conventional filters, a viscous liquid, such as blood, is to be passed through the lumen of the fiber, then the inside diameter must be larger, since otherwise high pressures with a high pressure drop must be used in order to achieve a sufficient flow.
  • the hollow fibers can be manufactured with greater strength than conventional • hollow fibers because, for the reasons mentioned above, the lumen can be kept small in diameter with the same external dimensions, since it is only for the outflow of the aqueous filtrate serves. While maximum tear strengths of 20-30 g per fiber were measured on conventional hollow fiber membranes made of the same material, tear strengths of 60-120 g per fiber can be set for the hollow fiber membranes used according to the invention. This enables the processing of the membranes in the form of e.g. knitted hollow fiber mats and thus e.g. the production of ordered structures in the filter with defined fiber distances. For such processing techniques, very long hollow fibers with high tear strength are a basic requirement.
  • the outside of the hollow fiber determines its permeability and selectivity.
  • Selectivity is understood to mean the property of the membrane to let molecules up to a certain maximum size pass.
  • a high permeability ie a low total resistance of the membrane, determines its filtration performance.
  • the pressure gradient across the membrane is the driving force for the filtration process. This driving force should be as large as possible in all parts of the filter in order to ensure a high efficiency of the filter. Because this pressure gradient is reduced when If a high pressure drop occurs in the feed path or in the filtrate path, such a pressure drop should be kept as low as possible. In conventional ultra filters with a separating layer in the lumen of the hollow fibers, this pressure drop is given by the length of the hollow fibers, ie by the length of the feed path and by the concentration polarization increasing along the path. The feed is not swirled in the laminar flow of the feed in the lumen of conventional hollow fibers.
  • a liquid particle to be filtered can only reach the membrane by diffusion through the layer of retained particles and colloids enriched there.
  • the hollow fiber has pores whose average clear width on the outside is smaller than on a luminal side of the hollow fiber.
  • this measure has the advantage that it is a parameter that can be easily determined in the production of the hollow fiber.
  • the clear width of the pores, which determines the permeability of the membrane, can be monitored by electron micrographs.
  • the hollow fiber comprises on its outside at least one separating layer which determines the permeability of the membrane and which is an integral part of the membrane.
  • the separating layer can be produced in one process together with the hollow fiber. This can be done, for example, by spinning the initially liquid polymer solution from which the hollow fiber is produced into a precipitation bath which contains certain substances which influence the precipitation of the membrane in such a way that the separating layer forms in the outer region of the hollow fiber . Larger quantities of hollow fibers of the same permeability can thus be produced very inexpensively.
  • the above-mentioned specific substances which influence the properties of the inner or outer surfaces of the hollow fiber membrane are on the one hand the solvent of the polymer and on the other hand at least two precipitants with a high and a low precipitation potential for the polymer.
  • Polysulfone or other polymers suitable for membrane production preferably use aprotic dipolar solvents as solvents, e.g. Dimethylacetamide, dimethylformamide, N-methylpyrrolidone, dimethyl sulfoxide or the like
  • solvents e.g. Dimethylacetamide, dimethylformamide, N-methylpyrrolidone, dimethyl sulfoxide or the like
  • a precipitant with a very high precipitation potential for this and similar polymers from these solvents is e.g. Water; Precipitants with far lower potential are e.g. Alcohols.
  • the compositions of the outer precipitation bath and the liquid in the lumen of the spinneret are therefore selected so that there is a large precipitation potential in the precipitation bath and a very small precipitation potential in the center liquid.
  • water in the precipitation bath of e.g. Isopropanol can be used to control the separation properties and the permeability of the hollow fiber membranes according to the invention with an outer separation layer.
  • the hollow fiber comprises on its outside at least one separating layer which determines the permeability of the membrane and which is a separate component of the membrane.
  • a separate component is understood here to mean that the separating layer is applied in a second step.
  • the hollow fibers are arranged in such a way that there are predominantly non-laminar flow conditions on the hollow fibers during filtration.
  • This arrangement has the advantage that the transmembrane pressure difference which is effectively available for filtration is greater than in the case of an arrangement in which the liquid to be filtered flows past the hollow fibers in a laminar flow. This measure therefore results in a more effective filtration.
  • the device comprises a plurality of hollow fibers acting in parallel, which are arranged in layers.
  • the hollow fibers are arranged in a housing which separates a first space comprising the lumens of the hollow fibers from a second space which is connected to the outer sides of the hollow fibers.
  • the liquid to be filtered can flow through the second space, while the entire filtrate of all the hollow fibers acting in parallel can be derived from the first space.
  • This has the advantage that it is possible with such a housing, for example, to increase the transmembrane pressure difference, which is decisive for the efficiency of the filtration, in that the pressure in the first space is reduced by the application of a vacuum. If blood is the liquid to be filtered, this method enables effective filtration that is much gentler on the blood and its cellular components than would be possible by increasing the pressure on the blood.
  • the layers are arranged next to one another and offset one above the other.
  • This arrangement has the advantage that the liquid to be filtered is passed through the hollow fiber layers in such a way that it comes into contact with the largest possible membrane area without laminar flow conditions. This measure thus brings about a further increase in efficiency.
  • the device according to the invention has at least two hollow fibers which are not arranged parallel to one another. With this arrangement, laminar flow conditions are also avoided, which brings with it the advantages already mentioned.
  • the device has at least two hollow fibers which are arranged essentially parallel to one another.
  • this arrangement has the advantage of being simpler in terms of production technology and therefore more economical to implement than an arrangement of hollow fibers which do not run in parallel.
  • the device according to the invention has at least one inlet for the liquid to be filtered with at least one outlet opening between the layered hollow fibers.
  • This measure has the advantage that part of the liquid to be filtered does not first have to penetrate many layers of hollow fibers in order to penetrate to a membrane which has not yet reduced its performance due to deposits and / or concentration polarization. In addition, this measure reduces the resistance and thus the pressure drop in the entire device.
  • the device according to the invention has at least one outlet for the filtered liquid with at least one opening between the layered hollow fibers. This measure also has the advantage of keeping the pressure drop in the entire device as low as possible, because this prevents the filtered liquid from being blocked.
  • FIG. 1 shows a highly schematic sectional illustration of an exemplary embodiment of a device according to the invention
  • Fig. 2a shows a sectional view of the device shown in Fig. 1 along the line II-II in Fig. 1;
  • FIG. 2b shows a greatly enlarged schematic sectional illustration of a possible exemplary embodiment of a hollow fiber from FIG. 2a;
  • FIG. 2c shows a greatly enlarged schematic sectional illustration of a further possible exemplary embodiment of a hollow fiber from FIG. 2a;
  • 3a shows a highly schematic sectional illustration of a further exemplary embodiment of the device according to the invention;
  • FIG. 3b shows a greatly enlarged schematic sectional illustration of the region of the open hollow fiber ends from FIG. 3a together with a further development according to the invention
  • FIG. 4 shows a highly schematic top view of the central plate from FIG. 3;
  • FIG. 5a shows a top view of a center plate in a further embodiment and on a smaller scale than in FIG. 4 with a winding diagram indicated by way of example;
  • FIG. 5b shows a top view of a middle plate as in FIG. 5a with a further winding diagram indicated by way of example;
  • 6a shows a sectional illustration of a hollow fiber package with an inlet and an outlet
  • 6b shows a highly schematic top view of an exemplary embodiment of a sequence according to the invention.
  • FIG. 6c shows a highly schematic sectional illustration of the sequence shown in FIG. 6 along the line VI-VI in FIG. 6b.
  • 10 denotes a device for ultrafiltering body fluids, with a housing 11.
  • a plurality of membranes in the form of hollow fibers 12 are arranged in the housing 11 in such a way that they span the interior of the housing 11, through which a liquid to be filtered flows, which is indicated by an arrow a.
  • the hollow fibers 12 are sealed against the housing 11 and against one another by a casting compound 13.
  • the hollow fibers 12 each have a lumen 14, which connects two filtrate collecting spaces 16 in the housing 11 to one another via two opposite, open hollow fiber ends 15. These filtrate collecting spaces 16 are separated by the potting compounds 13 from a space 17 through which the liquid to be filtered can flow, and each have a filtrate outlet opening 18.
  • the retentate is indicated by an arrow b and the filtrate by arrows c, d.
  • this liquid flows through an inlet opening 19 into the space 17 spanned by the hollow fibers 12, flows around the hollow fibers 12 and leaves the space 17 through a retentate outlet opening 20.
  • Low-molecular constituents can thereby escape of the liquid to be filtered pass through the membranes, collect in the lumens 14 of the hollow fibers 12 and flow out of these lumens 14 through the open hollow fiber ends 15 into the filtrate collecting spaces 16 and leave them through the filtrate outlet openings 18, as indicated by the horizontal arrows c, d .
  • An opening 21 is used for ventilation.
  • Fig. 2a shows a sectional view along the line II-II in Fig. 1.
  • the cross-sectional hollow fibers 12 are shown in addition to the housing 11 with the space 17, the inlet opening tion 19 and the retentate outlet opening 20, the cross-sectional hollow fibers 12 are shown. Two possible embodiments of these hollow fibers 12 are shown in FIGS. 2b and 2c as greatly enlarged schematic cross sections.
  • the hollow fiber 12 has pores 28 which have a larger clear width on a side 29 facing the lumen 14 than on an outer side 30.
  • the permeability of this hollow fiber 12 is due to the clear width of the pores 28 on the Outside 30 of the hollow fiber 12 determined.
  • the diameter of the pores 28 is less than 0.1 ⁇ m, preferably less than 0.05 ⁇ m.
  • the hollow fiber 12 comprises a separate separating layer 32.
  • This separate separating layer 32 lies on a hollow fiber formed by a porous basic structure 33, the pores 34 of which, however, are so large that they do not limit the permeability of the membrane in any relevant way.
  • the permeability on the outside 30 of the membrane is determined by small pores 35 of the separate separating layer 32.
  • a method for producing an integral separating layer on the luminal side of a hollow fiber is described in WO 98/52683. This method can also be used analogously to produce a separating layer on the outside of a hollow fiber.
  • 3a overall, 38 denotes an alternative embodiment of a device according to the invention for the ultrafiltration of body fluids, newly developed by the inventors of the present application.
  • 19 again designates the inlet opening through which, as indicated by a vertical arrow a, the liquid to be filtered can flow into the space 17 formed by the housing 11, in which there is a hollow fiber package 39 which is around a central plate 40 is arranged.
  • This middle plate 40 has openings 41 for the passage of liquid.
  • the ends of the hollow fibers 12 in the hollow fiber package 39 are sealed against one another and against the housing 11 by the sealing compound 13.
  • the lumens 14 of the hollow fibers 12 are connected via the cut hollow fiber ends 15 to an outer space which is separated from the space 17 by the potting compound 13.
  • the device shown has a rotationally symmetrical structure with respect to the vertical central axis.
  • the liquid entering through the inlet opening 19, indicated by the arrow a flows through the hollow fiber package 39 and thereby passes through the central plate 40 through the openings 41.
  • the filtered liquid leaves the housing 11, as indicated by a vertical arrow b, through the Retentate outlet opening 20.
  • low-molecular constituents penetrate the membranes and thus get into the lumens 14 of the hollow fibers 12, which they leave, as indicated by horizontal arrows c, d, through the open hollow fiber ends 15.
  • 11 denotes the housing of the device for ultrafiltration of body fluids
  • 12 the hollow fibers, which are the Form hollow fiber package 39 in space 17 and only six of which are shown for clarification
  • 13 the potting compound
  • 15 the open hollow fiber ends
  • 40 the middle plate
  • 41 the opening in the middle plate
  • 42 the filtrate collector
  • 16 the filtrate collecting chamber
  • 18 the filtrate outlet.
  • the filtrate collector 42 spans the entire device 38 for filtering liquids, so that the connected filtrate collection space 16 is located around the open hollow fiber ends 15.
  • the filtrate emerging from the open hollow fiber ends 15 collects in the filtrate collecting space 16 and flows out of it through the filtrate outlet opening 18.
  • FIG. 4 shows a top view of the central plate 40, which is shown in FIG. 3 in a sectional illustration.
  • the middle plate 40 has the basic shape of a regular octagon, the corners being each in the form of a horn 43.
  • the hollow fibers 12 extend in a parallel arrangement from one side 44 to an opposite side 45 of the octagon and between the other opposite sides. For reasons of clarity, only a few of these hollow fibers 12 are shown and in some cases not drawn continuously, but only hinted at.
  • Bundles of parallel hollow fibers 12 are arranged in layers on this central plate 40, each having an angle of 45 ° to the adjacent bundle of parallel hollow fibers 12. These bundles of parallel hollow fibers 12 in their entirety form the hollow fiber package 39 shown in FIG. 3a.
  • the croissants 43 in the middle plate 40 prevent individual hollow fibers from slipping off. ser 12 in production, in which the hollow fibers 12 are preferably wound on the central plate 40.
  • the circular openings 41 in the central plate 40 can also have any other shape and, for example, be in the form of slots. It is only important that these openings 41 allow the passage of liquid.
  • 50 designates overall a further embodiment of a center plate, which is shown in plan view.
  • 41 denotes the openings through which liquid can pass during filtration and 43 the croissants which prevent the hollow fibers 12 from slipping off when they are wound onto this central plate 50.
  • the hollow fibers 12 are wound up in layers in the manner of a star-shaped twisted thread.
  • the hollow fibers 12 can each be wound from a recess 51 between two croissants 43 to a directly opposite recess 52 between two croissants 43 (FIG. 5a) or also to a recess 53 that is not directly opposite (FIG. 5b), so that when a certain winding pattern is observed, there is a free space in the middle of the middle plate 50 which is not spanned by any hollow fiber 12 and which, when filtered, facilitates the penetration of the liquid to be filtered into the hollow fiber package 39 as well as the outflow of the filtered liquid the hollow fiber package 39.
  • the hollow fiber 12 can be wound back and forth several times between two specific recesses 51, 52, 53, so that a bundle of parallel hollow fibers 12 is formed, which is at a certain angle to a next bundle of parallel hollow fibers 12, which is in the same Way was wrapped.
  • the hollow fiber 12 can be stretched between two specific recesses 51, 52, 53 only once per layer, so that even if several layers are wound, no bundles of parallel hollow fibers 12 arise due to the underlying hollow fibers 12 and in the resulting hollow fiber package 39 no hollow fibers 12 run parallel to each other.
  • the hollow fibers 12 are wound onto the middle plate 50 in such a way that a recess remains in the center of the hollow fiber package 39, which has an inlet 61 and an outlet 63 on the other side of the middle plate 50 records.
  • Both the inlet 61 and the outlet 63 are designed in the form of a tube which has a plurality of openings 64 within the hollow fiber package 39.
  • the body fluid to be filtered flows, as indicated by a vertical arrow, laterally into the hollow fiber package 39 via the inlet 61 and the openings 64 contained therein.
  • the openings 64 facilitate the penetration of the liquid to be filtered into the hollow fiber package 39
  • the openings 64 facilitate the discharge of the filtered liquid, so that the pressure drop during filtration is kept low as a result of this measure.
  • 70 designates a further exemplary embodiment of a sequence, which is shown in a top view. 64 openings in the drain.
  • Fig. 6c shows a sectional view along the line VI-VI in Fig. 6b. 70 therein designates the outlet, 64 openings and 65 channels in the outlet 70.
  • This embodiment in which the openings 64 are made so recessed in the outlet 70 that they cannot be directly covered by the hollow fibers 12 of the hollow fiber package 39, avoids through the channels 65 that there is a congestion of the filtered liquid as it flows away is coming.
  • An inlet can also be designed analogously to this exemplary embodiment.
  • the channels 65 prevent the liquid to be filtered from jamming.

Abstract

Cette invention concerne un dispositif (10) comprenant au moins une membrane préexistant sous la forme d'une fibre creuse (12) constituée d'une face externe et d'une lumière (14), semi-perméable, mouillable, particulièrement hydrophile. Ledit dispositif est utilisé pour filtrer les fluides corporels, le filtrage s'effectuant de la face externe vers l'intérieur de la lumière (14).
PCT/EP2000/002166 1999-03-25 2000-03-11 Dispositif comprenant au moins une membrane preexistant sous la forme d'une fibre creuse pour filtrer les fluides corporels WO2000057996A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19913416.2 1999-03-25
DE1999113416 DE19913416A1 (de) 1999-03-25 1999-03-25 Vorrichtung mit mindestens einer in Form einer Hohlfaser vorliegenden Membran zum Filtrieren von Flüssigkeiten

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Publication Number Publication Date
WO2000057996A1 true WO2000057996A1 (fr) 2000-10-05

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WO (1) WO2000057996A1 (fr)

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Publication number Priority date Publication date Assignee Title
DE102004030878B4 (de) * 2004-06-25 2008-05-08 Dr. Lerche Kg Verfahren zum selektiven Konzentrieren und Sammeln chromatographisch getrennter Stoffe und Sammelvorrichtung für die Flüssig-Chromatographie
EP2383031B1 (fr) 2006-10-18 2016-05-25 Gambro Lundia AB Utilisation d'une membrane à fibre creuse pour le microdialyse

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