|Publication number||USRE31029 E|
|Application number||US 06/212,081|
|Publication date||Sep 14, 1982|
|Filing date||Dec 1, 1980|
|Priority date||Aug 24, 1975|
|Also published as||DE2542438A1, DE2542438B2, DE2542438C3, US4141836|
|Publication number||06212081, 212081, US RE31029 E, US RE31029E, US-E-RE31029, USRE31029 E, USRE31029E|
|Original Assignee||Dr. Eduard Fresenius Chemisch-Pharmazeutische Industrie Kg, Apparatebau Kg|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Referenced by (12), Classifications (8)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The invention relates to a dialyser, in particular for haemodialysis, which comprises a housing with inflow and outflow pipes for blood and dialysis solution and open hollow filaments arranged in the housing and joined to one another at their ends, as well as to a dialyser cartridge, as well as a method for the manufacture of such a dialyser.
Haemodialysis requires a membrane of large surface area, some 1-1.5 m2 in size and 10-20 μm thick, of a material capable of acting as a dialytic permeable membrane, for example, cellulose acetate, polyacrylonitrile and similar materials are capable to act as separating layer between the blood and the suitably composed dialysis solution. The membrane is relatively easily permeable for water and low molecular weight constituents of the blood, including also substances contained in urine. High molecular weight and corpuscular constituents are however almost completely retained.
Under the term dialysers for haemodialysis can be recognised spool or coil dialysers, plate dialysers and also capillary or hollow filament dialysers, in which the membrane is formed from a large number (e.g. 10,000) of hollow filaments having a diameter of about 150 μm. In the hitherto usual arrangement the hollow filaments are collected into a loose bundle of parallel filaments and arranged in a cylindrical housing. The ends of the bundle of hollow filaments are sealed off and packed against the housing. The inflow and outflow of the blood stream is effected by connecting pieces screwed onto the ends of the housing. The dialysis solution flows, in countercurrent, along the outside of the capillaries or hollow filaments, inflow and outflow occurring via lateral connections in the vicinity of the ends of the housing.
In designing a hollow filament dialyser great efforts are made to achieve as great an effectiveness as possible, i.e. a flow distribution as uniform as possible is necessary in order to fully utilize the membrane surface. High flow velocities are also desirable since this reduces the diffusion resistance in the blood and dialysis solution. Furthermore, the blood filling volume should be as small as possible and the blood flow resistance should be low. A hollow filament dialyser in principle provides the necessary prerequisites in order to meet these requirements.
In view of the above, it is the aim of the invention to achieve the following objects, singly or in combination:
to provide a dialyser of the afore-mentioned type which optimally meets the above requirements and which furthermore can be manufactured in an advantageous manner;
to provide a dialyser in which the hollow filaments are in the form of a ring with the inflow and outflow of the medium flowing in the interstices from the middle thereof;
to provide a dialyser cartridge that is replaceable within a housing, having inflow and outflow pipes associated therewith especially for blood dialysis; and
to provide a method for manufacturing of a dialyser cartridge and/or housing.
In order to solve this problem the invention provides a dialyser in which the hollow filaments are arranged in the form of a ring and the inflow and outflow of the medium flowing in the interstices between the hollow filament pieces takes place from the middle. The flow conditions are thereby favorably influenced, and in addition this also provides the possibility of manufacturing the unit consisting of hollow filaments in a particularly convenient manner.
A further embodiment of the invention accordingly proposes that the hollow filaments are wound on the core and that the ends of the wound hollow filament body are then impregnated with a cast resin and the end regions are cut off, after solidification, in such a way that the front surfaces of the individual hollow filament pieces are open.
In this connection, the hollow filaments can be wound inclined or parallel to the axis of the core, winding being carried out with devices known per se.
In order that the invention may be clearly understood, it will now be described, by way of example, with reference to the accompanying drawings, wherein:
FIG. 1 is a sectional view through a dialyser according to the invention;
FIG. 2 is a perspective view of a hollow filament body with the hollow filament windings inclined to the core axis; and
FIG. 3 is a perspective view of a hollow filament body with windings parallel to the core axis.
Referring now to the drawings dialyser 1 according to the invention, is illustrated in FIG. 1, and consists of a two-part housing 2 in which a hollow filament body or cartridge 3 is located. The hollow filament body consists of a core 4, on which a body or hollow filament 5 consists of cellulose acetate or polyacrylonitrile is wound in accordance with FIG. 2 or 3.
The core 4 may be tubular having an outer wall or surface 4a and an inner wall or surface 4b with at least one radially extending separating wall 6 there between, as well as several passage openings 9 distributed on the periphery between the outer wall 4a and the inner wall 4b, adjacent the two ends 7 and 8 of the core 4. The wall 6 separates or divides the core 4 into a pair of chambers 6a that are sealed from each other by the separating wall 6. The two halves or sections 10 and 11 of the housing 2 each have together with the tubular shaped core 4 an aligned inflow conduit or pipe 12 and outflow conduit or pipe 13. The pair or set of pipes 12 and 13 may be in axial alignment with each other and having a terminal end 12a and 13a respectively. Each pipe 12 and 13 may extend into an enlarged passage 12b and 13b respectively, which are in alignment with the chambers 6a to provide a proper flow of fluid therethrough. Each half 10 and 11 further has another pair or set of pipes consisting of an inflow pipe 14 and outflow pipe 15 which open out into a guide channel 16 and 17 in the interior of the halves 10 and 11 of the housing 2. The width of the two channels 16 and 17 preferably corresponds to the layer of hollow filament pieces 18 arranged in the form of a ring on the core 4. The inflow pipe 14 has an outer end 14a, and the outflow pipe 15 has an outer end 15a. The inflow pipe 14 and outflow pipe 15 are provided in non-aligned relationship with respect to each other to provide the necessary flow length for the dialysis fluid.
Like the cylindrical core 4, the hollow filament body 3 also has a circular cross-section. A jacket 19 is arranged on the circumference of the hollow filament body 3, which not only holds together the external hollow filament pieces 18 but also serves for sealing purposes. The jacket 19 may extend the same axial length as the core 4 and coincide with the ends 7 and 8 thereof. As illustrated in FIG. 1 the guide channels 16 and 17 each include an inner edge or wall 16a and 17a that engages the ends 7 and 8 respectively, of the core 4 as well as each end of jacket 19. The core 4 and jacket 19 may be in co-axial alignment with each other.
The manufacture of the hollow filament body is carried out in accordance with FIGS. 2 and 3 in such a way that the hollow filament 5 is wound on the core 4 with an arbitrary number of windings 20, 21 and 22, the winding being performed so that the windings are either inclined or parallel to the longitudinal axis or plane of the core 4. During the winding procedure the hollow filament 5 is led back and forth so that after a certain angle of rotation of the winding device carrying the core 4, the said filament moves from one edge to the other edge. A compact or a lightly wound hollow filament body is thus obtained depending on the angle of inclination.
The ends of the hollow filament body 3 wound in this manner are then impregnated with a cast resin so that all interstices are filled and the windings of the hollow filaments 5 are firmly embedded. In a following operation the outermost end regions of the hollow filament body 3 impregnated by the cast resin are cut off along the dotted lines 23 and 24 in FIG. 2, with the result that hollow filament pieces 18 roughly corresponding to the length of the core 4 are formed, which are open and freely accessible at their front faces for a flow of fluid through the hollow filament pieces 18.
In the case of the hollow filament body 3 shown in FIG. 3, the hollow filament 5 is wound over the circumference and the front sides of the core 4 so that the hollow filament pieces 18 lie on the circumference of the core approximately parallel to the axis thereof.
During the winding the core 4 is slowly rotated about its longitudinal axis, which is at right angles to the winding axis. The angular displacement depends on the relationship between winding rate and the rotational velocity of the hollow filament body. The required distance or spacing between the hollow filament pieces 18 can be achieved by the simultaneous applying or winding of foil strips 25 and 26, which are wound in the direction of the circumference as can be seen from FIG. 3.
When the hollow filament body 3 has been impregnated with cast resin, hardened, and then cut at its edge or end regions, after the winding procedure, the jacket 19 is applied, following which the hollow filament body 3 can be inserted into the housing 2 consisting of practically equal sections of halves 10 and 11. After insertion, the two halves 10 and 11 or the housing are securely connected to one another in their flange region 27 and 28 in a conventional manner.
The dialysis solution enters the dialyser through the centrally arranged inflow pipe 12 in the direction of arrow 32, and first of all passes into one half, or chamber 6a, of the tube-shaped core 4, from which it then flows through the passage openings 9 in the direction of arrows 34, and splits up in the interstices between the hollow filament pieces 18. After the dialysis solution has flowed through the hollow filament body 3, it reenters the core 4 through the passage opening 9, in the direction of arrows 36, at the other end thereof into chamber 6a and then flows directly to the outflow pipe 13, in the direction of arrow 38.
The blood flows through the dialyser 1 in the opposite direction. It enters through the inflow pipe 14, in the direction of arrow 40 which opens out into the guide channel 16. From there the blood is distributed through the hollow filament pieces 18 from which it flows into the guide channel 17 in the other half 10 of the housing, which channel 17 collects the blood and passes it to the outflow pipe 15 in the direction of arrow 42.
FIG. 1 clearly illustrates the sealing function of the jacket 19, against the walls 16a and 17a which prevents any bypass for the dialysis solution parallel to the hollow filament pieces 18 and into the chamber 6a, or passages 12b or 13b.
A further prerequisite for satisfactory operation is that the end regions 29 and 30 of the hollow filament body 3, which are sealed with a cast resin, are absolutely tight and impermeable since otherwise dialysis solution can pass into the two guide channels 16 and 17. The position of the passage openings 9 is chosen so that they are immediately adjacent to the end regions 29 and 30 impregnated with cast resin. In this manner the spacing between each hollow filament 18 is sealed preventing the escape from each end region 29 and 30, and yet permitting the flow of fluid through the individual filament pieces 18.
The dialysis solution or medium is distributed very rapidly over the whole cross-section of the circularly arranged hollow filament pieces 18 by virtue of the feed of dialysis solution from the centrally arranged core 4 into the interstices between the hollow filament pieces 18 which are in communicating relationship with inflow and outflow pipes 12 and 13. The transition zone from a uniformly "flushed" cross-section to a "non-flushed" cross-section is very short at the inflow and outflow, which is accompanied by an increase in the exchange efficiency on account of the better utilization of the incorporated hollow filament surface. This can be fully exploited by incorporating a correspondingly smaller amount of hollow filament material in the dialyser, any increase in efficiency being relinquished, and in addition the flow resistance on the blood side can be markedly reduced if the number of hollow filaments is increased and their length is reduced, the total surface area remaining the same. This provides one of the conditions in haemodialysis for driving the blood circulation outside the body without the use of blood pumps, the natural arterial-venous pressure drop being utilized. The invention is not limited to the examples of the embodiments illustrated in the figures, and indeed alterations can be carried out without departing from the basic ideas of the invention. Thus, for example, it is also possible to provide appropriate separating walls instead of the separating wall 6 immediately adjacent to the passage openings 9, so that the dialysis solution passes into the interior of the hollow filament body 3 via the shortest pathway. Furthermore, it may also be convenient if the manufacturing procedure described above is altered and the jacket 19 is applied before the ends of the hollow fiber body are impregnated with cast resin.
Although the invention has been described with reference to specific example embodiments, it is to be understood, that it is intended to cover all modifications and equivalents within the scope of the appended claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3228876 *||Sep 19, 1960||Jan 11, 1966||Dow Chemical Co||Permeability separatory apparatus, permeability separatory membrane element, method of making the same and process utilizing the same|
|US3422008 *||Oct 24, 1963||Jan 14, 1969||Dow Chemical Co||Wound hollow fiber permeability apparatus and process of making the same|
|US3852198 *||Feb 12, 1973||Dec 3, 1974||Plastic Kogaku Kenkyusho Kk||Dialyzing apparatus for artifical kidney|
|US3884814 *||Jul 23, 1973||May 20, 1975||Rhone Poulenc Sa||Apparatus for fractionating fluids|
|US3953334 *||Jun 26, 1974||Apr 27, 1976||Rhone-Poulenc, S.A.||Fluid fractionating apparatus|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US5290445 *||Jun 1, 1993||Mar 1, 1994||Pall Corporation||Filtering apparatus|
|US6635179 *||Dec 30, 1999||Oct 21, 2003||Nephros, Inc.||Sterile fluid filtration cartridge and method for using same|
|US7534349||Aug 31, 2006||May 19, 2009||Nephros, Inc.||Dual stage ultrafilter devices in the form of portable filter devices, shower devices, and hydration packs|
|US7775375||Jun 15, 2006||Aug 17, 2010||Medica S.R.L.||Redundant ultrafiltration device|
|US8323492||Aug 19, 2011||Dec 4, 2012||Baxter International Inc.||Hemodialysis system having clamping mechanism for peristaltic pumping|
|US8329030||Aug 19, 2011||Dec 11, 2012||Baxter International Inc.||Hemodialysis system with cassette and pinch clamp|
|US8343347||May 15, 2009||Jan 1, 2013||Nephros, Inc.||Dual stage ultrafilter devices in the form of portable filter devices, shower devices, and hydration packs|
|US8858488||Sep 17, 2010||Oct 14, 2014||Baxter International Inc.||Dialysis system including blood and dialysate cassette|
|US8882692||Aug 19, 2011||Nov 11, 2014||Baxter International Inc.||Hemodialysis system with multiple cassette interference|
|US9168333||Oct 10, 2014||Oct 27, 2015||Baxter International Inc.||Dialysis system including disposable cassette|
|US20070163943 *||Aug 31, 2006||Jul 19, 2007||Nephros, Inc.||Dual stage ultrafilter devices in the form of portable filter devices, shower devices, and hydration packs|
|US20090078625 *||Jun 15, 2006||Mar 26, 2009||Palumbo Giuseppe||Redundant ultrafiltration device|
|U.S. Classification||210/321.81, 210/456|
|International Classification||B01D63/02, A61M1/18|
|Cooperative Classification||B01D63/02, B01D63/021|
|European Classification||B01D63/02, B01D63/02B|