DE2603560A1 - DEVICE FOR EXCHANGING SUBSTANCES BETWEEN TWO FLUIDS - Google Patents

Description

P at ent notice

Device for exchanging materials between two shops

The invention relates to a device with permeable hollow fibers having a penetration zone in a housing contains a bundle of hollow fibers, and in which certain substances are selectively passed through the permeable walls of the hollow Fibers formed membranes can penetrate, between one of the gaps between the fibers of the bundle flowing through the fluid and a second fluid flowing through the hollow fibers Osmosis, dialysis, ultrafiltration, reverse osmosis or the like. represent.

A device designed in a known manner with permeable hollow fibers is used, for example _, in an artificial kidney for dialysis of blood, in which toxic substances are removed from the blood of a patient suffering from kidney failure or poisoning. Furthermore, such devices are used in artificial lungs used, in which oxygen and carbon dioxide are exchanged with each other to increase the oxygen content of the blood.

In order to characterize the state of the art in more detail, an example which is designed in a known manner is first used below Device with permeable hollow fibers described

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ORIGINAL INSPECTED

Fig «, 1 shows a suitable for use as an artificial kidney, overall with 10 designated blood dialyzer with hollow fibers of known construction, which has a cylindrical housing 1, which consists e.g. of a synthetic resin and is open at both ends. The housing 1 is at the top and bottom End provided with adjoining cylindrical sections 37 and 38 of larger diameter. To this extended Sections 38 and 37 are an inlet pipe 2 and an outlet pipe 3 for the. Dialysate

connected so that they are diametrically opposite each other. At their outer ends are the expanded housing sections 37 and 38 each provided with an external thread 8.

An existing in the housing 1. penetration zone 25 is filled by a hollow fiber bundle 6, which is composed of numerous closely spaced hollow fibers 5, the Z ₀ B ₀ are made of cellulose and are substantially as long as the housing 1. Normally, 6 contains the fiber bundle about 10,000 to 15,000 hollow fibers 5 with a diameter of about 0.3 mm · The total membrane area of the hollow fibers 5 »which is available for dialysis is here about 1 m ² .

The end portions of the fiber bundle 6 are sealed with a potting material 7, which is z "B ₀ is polyurethane, a silicone resin or an epoxy resin. According to FIG. 1, upper and lower cover disks 13 are in contact with the outer edge portions of the upper and lower end faces of the potting material 7 in the upper and lower end of the housing 1, respectively which are screwed onto the external thread 8 so that the potting material 7 and the cover disks 13 are held between the respective ends of the housing 1 and inwardly protruding flanges 19 of the union nuts 17 and 18 to the bundle 6 of hollow fibers 5 at both ends of the housing 1

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gain. The upper and lower ends of the hollow fibers 5 are cut so that they are in alignment with the smooth upper and lower end faces of the potting material 7. The union nuts 17 and 18, for example, consist _o of a synthetic resin.

A blood inlet pipe 14 and / or a blood outlet pipe 15 are connected to the upper and lower cover disks 13. The middle ones Portions 13A of the cover disks 13 are arranged along the axis of the device 10 so that they are close to the inlet pipe 14 and the outlet pipe 15 each delimit a round chamber 20 which is in communication with the channels of the hollow fibers 5.

If blood is to be dialyzed with the aid of the device 10, the dialysate 35 is fed to the housing 1 via the inlet tube 2, while the blood 36 to be dialyzed is supplied from an artery of the patient from the housing 1 via the inlet tube 14 will. The dialysate 35 is distributed in an annular space 22 within the housing extension 38 and then flows into the gaps of the bundle 6 of hollow fibers 5 a. In these gaps, the dialysate 35 flows from bottom to top between the hollow fibers 5 through to an annular space 23 formed by the housing extension 37, and then around the housing 1 via the outlet pipe 3 The blood 36, on the other hand, is directed to the openings the upper ends of the hollow fibers 5 because it enters the upper chamber 20 from the mouth 24 of the inlet tube 14. The blood 36 flows in countercurrent to the dialysate 35 from top to bottom through the hollow fibers 5 to the housing 1 finally the lower chamber 20 and the outlet pipe 15 can be left again via the lower openings of the hollow fibers 5

The blood 36 is through the membrane walls of the hollow fibers 5 due to the action of the dialysate 35 dialyzed ₀ In this way it is possible, for example, to transfer metabolic waste ₀ urea, uric acid and creatinine from the blood 36 in the dialysate 35th The purified blood 36 from escaping from the housing 1 and the patient through a vein returned to ₀ If

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the dialysate 35 is pumped out via the outlet pipe 3, it is compared to the blood 36 under a negative pressure, so that between the dialysate 35 and the blood 36 an ultrafiltration is brought about to remove excess water from the blood.

In the blood dialyzer 10, the hollow fibers 5 form a relatively large effective membrane area, and therefore this device can be used make them smaller than the known dialyzers, in which pipe coils or plate-shaped membranes are present sindo As a result, it is possible to reduce the volume of blood to be taken up by the device, which is the case with the Dialysis had a beneficial effect on the patient In addition, the device 10 and the hollow fibers 5 are easier to handle withstand the pressure better, and they are more suitable for ultrafiltration

Although the dialyzer 10 offers the advantages mentioned, which is why it has been increasingly accepted in recent times, it still adheres certain disadvantages, which will be discussed in more detail below ο

Since the hollow fibers 5 of the bundle containing approximately 10,000 to 15,000 fibers lie tightly against one another in the housing 1, it is difficult to achieve that the dialysate 35 uniformly penetrates all parts of the bundle 6 circumference of the bundle 6 near the inner wall of the housing is higher, and that the rate of dialysis of the bundle in the central part is extremely low _o It was also found that 5 boundary layers forming the outer and inner surfaces of the hollow fibers through which the efficiency of the Dialysis is decreased.

The invention is based on the object of creating a device with permeable hollow fibers in which in a housing

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at least one zone of larger cross-section is present in order ^{to generate a flow component hereinafter} referred to as "cross flow 11 such that the flow moves transversely to the bundle of hollow fibers" so that the flow through the central part of the fiber bundle is promoted, and thus it is possible, the boundary layers to destroy effectively on the surface of the hollow fibers ₀ Furthermore, a device of said type is to be created is present in a zone of enlarged cross-section that is shaped in a particular way and dimensioned such that said cross-flow is formed , in which the cross-section of the housing has such a shape that the creation of a cross flow is encouraged, and in which it is finally possible to return a fluid through the housing in order to increase the permeability «.

The invention provides a device for solving this problem has been created with permeable hollow fibers, which has a housing with a penetration zone, furthermore a at least a bundle arranged in this penetration zone made of hollow fibers with permeable walls, at least one inlet tube for supplying a first fluid to the housing such, that this fluid can enter the spaces between the hollow fibers, at least one outlet pipe for drawing off the first fluid from the housing, with at least a portion of the housing in the penetration zone compared to the hollow fiber bundle has an enlarged cross-section to define a space between the hollow fiber bundle and a wall of the housing, in which at least a portion of the first fluid can enter on its way from the inlet pipe to the outlet pipe, as well as one Means for passing a second fluid through the hollow fibers such that the walls of the hollow fibers selectively from certain substances can be penetrated,

The invention and advantageous details of the invention are described below with reference to schematic drawings of exemplary embodiments explained in more detail «It shows:

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1 shows a longitudinal section, partially drawn as a view, of a known blood dialyzer for an artificial one Kidney;

Fig. 2 is a partially exploded perspective view Representation of a first embodiment a r device according to the invention in the form of a horizontally arranged blood dialyzer;

Fig. 3 is a section along the line III-III in Figure 2 _0;

4A to 4C each show an enlarged partial section through a further development of an enlarged cross section having part of a device according to Fig. 2 or Fig. 3, in which the flow course of the Dialysate is indicated;

Fig. 5 is a graph showing the relationship between the rate of dialysis of urea and the shape of a band portion of the enlarged cross-section part illustrates;

6 is a graph showing the relationship between the dialysis rate for urea and the shape of another end portion of the larger cross-section part;

7A to 7F each show an enlarged partial section through parts having a larger cross section to which the invention does not relate, the direction of flow of the dialysate being indicated in each case;

Fig ₀ 8 is a graph illustrating the relationship between the efficiency of the dialysis one hand, and the molecular weight and the flow rate of the dialysate on the other hand;

9 shows a graphic representation to illustrate the relationship between the degree of efficiency of dialysis on the one hand and the molecular weight and the circulation

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speed of dialysate on the other hand;

Fig. 10 is a partially exploded perspective view Representation of a further development of the device according to FIG. 2, in which the method for feeding and withdrawing the dialysate is modified;

_O 11A to 11E are each an enlarged fragmentary section or _{o 0} Figure 3, wherein the direction of flow of the dialysate is indicated by FIG an alternative embodiment of an enlarged cross section comprising part of the apparatus of FIG. 2;

12 and 13 each show a longitudinal section of a further development a device according to FIG. 2 or FIG. 3, in which the housing is curved in a generally sinusoidal wave shape Owns walls;

14 and 15 each show an enlarged partial section through another embodiment of an enlarged one Cross-section having part of a device according to Figure 2 or 3;

16 shows a longitudinal section through a second embodiment a blood dialyzer;

Fig. 17 is a longitudinal section through an important part of a third embodiment of a blood dialyzer;

Fig. 18 is a longitudinal section through a major part of a further embodiment of the apparatus of FIG ₀ 17 »

19 shows a longitudinal section through a fourth embodiment the invention in the form of a standing blood dialyzer;

FIG. 20 shows a section along the line XX-XX in FIG. 19; FIG.

FIGS. 21 through 23 are each a graphical representation for illustrative purposes the relationship between dialysis

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rate and shape of the penetration zone;

24 shows a partially broken away perspective illustration of a further development of the device according to Figo 19;

25 is a partially exploded perspective view Illustration of a fifth embodiment of a blood dialyzer;

FIG. 26 shows a section along the line XXVI-XXVI in FIG. 25; FIG.

27 and 28 each show a longitudinal section, partially drawn as a view, of a "further development of the device." according to Fig. 25;

29A to 29H each show a cross section of a further development of a housing of a device according to the invention;

30 to 33 each show a perspective illustration or a longitudinal section of a further development of the device according to Fig. 25;

FIG. 34 is a section along the line XXXIV-XXXIV in FIG _o 33; 35 shows a section along the line XXXV-XXXV in FIG. 33;

FIG. 36 is a cross section of a further embodiment of the housing of the device of Figure 25 _e;

37 is a partially exploded perspective view Illustration of a sixth embodiment of a blood dialyzer;

38 shows a section along the line XXXVIII-XXXVIII in FIG. 37;

39 the partially as a section along the line XXXIX-XXXIX FIG. 37 shows a front view of the device according to FIG. 37;

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40 shows the front view, partially drawn as a longitudinal section, of a further development of the one enlarged A cross-sectional part of the device according to FIG. 37;

41 shows a partial section, partially drawn as a view, of an important section of another further development of the part of the device according to FIG. 37 having an enlarged cross section;

Fig. 42 the front of an important part of another Further development of the part of the device according to FIG. 37 having an enlarged cross section;

43 is a partially exploded perspective view Representation of a further development of the device according to FIG. 37;

FIG. 44 shows the partially sectioned front view of the device according to FIG. 43; FIG.

FIG. 45 is a partially-drawn as a sectional end view of the device according to Fig _o 44; '

Fig. 46 is a cross-section along the line XXXXVI-XXXXVI in Fig. 44;

47 shows the partially sectioned front view of another further development of the device Fig. 37;

FIG. 48 shows a partially sectioned front view of the device according to FIG. 47; FIG.

Figure "49 is a section along the line XXXXIX-XXXXIX in figure 47 _o;

50 is an exploded perspective view another development of the device according to FIG. 37;

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Figo 51 is a section along the line XXXXXI-XXXXXI in Fig _o 50; and

FIG _o 52 is an exploded perspective view of another embodiment of the device according to FIG »37th

The following are preferred embodiments of the invention described for use in connection with an artificial kidney, in which those parts which are based on Fig. 1 correspond to parts of the known device 10 described, each denoted by the same reference numerals are, so that a more detailed explanation should be unnecessary.

In Figs. 2 to 18 is a first embodiment of the invention shown.

Figo 2 and 3 shows a blood dialyzer 10 having a housing 1 of generally elongate cross-sectional shape whose narrow sides have a semicircular cross-section "The volume defined by the covers 13 chambers 20 have a similar cross-sectional shape as the housing 1, d _o h _o the chambers do not have any angled Corners in which blood could stagnate so that the blood to be dialyzed can flow through the housing 1 without forming lumps or clots. Alternatively, the housing 1 could an elliptical cross section or a rectangular cross section with four rounded corners have _e In another embodiment, a square cross section with rounded or angled corners could be present.

The flat sides 50 and 51 of the housing 1 facing away from one another each have a plurality of cross-sectional expansions that extends over the entire width W of these flat sides. In the embodiment described here, there are on the flat side 50 three cross-sectional enlargements 52, 53 and 54 present, which are separated by longitudinal distances d, and the other

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Flat side 51 is similarly provided with three cross-sectional enlargements 66, 67 and 68, which are also separated by distances d. Referring to FIG. 3, the upper cross-sectional enlargements 66, 67, 68 along the axis of the apparatus 10 with the lower cross-sectional enlargements 52, 53 »54 arranged alternately every six cross-sectional enlargements have the same shape ₀ Considering Z ₀ B _{0 is} the cross-sectional widening 67 'can be seen that this includes a curved wall 55, to which a substantially flat or to a lesser extent concave wall 56 is connected. The length of the cross-sectional widening 67 corresponds to FIG. 3, the distance D measured in the longitudinal direction of the bundle 6 of hollow fibers 5 _o The amount of the cross-sectional widening 67 corresponding to the measured at right angles to the longitudinal axis of the fiber bundle 6 distance L. If the fiber bundle by flat intermediate sections 57 of the housing 1 supported, the length of which corresponds to the distance d

The cross-sectional extensions 52, 53 '54, 66, 67 and 68 have the task to cause the dialysate to flow through the fiber bundle 6 transverse to its longitudinal axis, alternately in the one and the other direction _o the relationship between the length D of the cross-sectional enlargements, the The transverse dimension A 'of the fiber bundle 6 and the length d of the planar support sections 57 correspond to the following equations:

1/4 A <L <4A .0.0.00000 (1)

A < U <ι c- A .0 * 000000. \ ^ -)

O <d <T JJ 0000.00000 \ J>)

It has been found that it is possible considerably enhance the cross-flow of the dialysate, if the above equations are satisfied _o In the embodiment of Figure "2 and 3, the distance L approximately equal to the distance A, the distance D is approximately equal to 3A, and this distance is also approximately equal to 2d _o

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The planar support sections 57 are each arranged between adjacent cross-sectional enlargements 66 and 67 or 67 and 68 or 52 and 53 or ₀ 53 and 54.

3, the housing 1 is provided with an outlet pipe 28 for dispensing the dialysate to the left of the cross-sectional widening 66 and on the right next to the cross-sectional widening 54 with an inlet pipe 27 for supplying the dialysate Feed slot 88 formed or detachably fastened so that returned dialysate can be introduced into the cross-sectional widening 68 in a tangential direction. An inlet pipe 29 is connected to the inlet connection 64. In a corresponding manner, an outlet connection 65 for the circulating dialysate with an inlet slot 87 is formed or releasably attached so that the recirculated dialysate, which is fed to the cross-sectional widening 52 in the tangential direction, can be removed. At the outlet port 65 is a discharge pipe 26 attached because the inlet connection 64 and outlet connection 65 each have a slot 88 or having _o 87 and not approximately circular openings, it is possible that dialysate laminar so as to be guided by the fiber bundle 6 that the fiber bundle alternately flowed through in one direction and the other to the outlet pipe 26 is shown in FIG. 2 is a return line 73 is connected, which leads to the inlet pipe 29, and in which a check valve 74, a circulation pump 75 and a flow control valve are turned 76 _o the circulation pump 75 can be designed as a centrifugal pump, axial pump, piston pump or gear pump.

According to FIG. 2, a pipeline 77 is attached to the outlet pipe 28 connected to dispense the dialysate. In the line 77, which leads to a dialysate dispensing container, not shown, are a check valve 78 and a flow control valve 79

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switched on A feed line 80 for supplying dialysate is connected to the inlet pipe 27 according to FIG a check valve 81 and a flow control valve 82 are switched on, and connected to a dialysate reservoir, not shown connected. The lines 73, 77 and are made of a synthetic resin such as polyvinyl chloride. The inner surfaces these lines can be covered with silicone.

As mentioned, the housing 1 has an elongated cross section, so that the two end sections of the fiber bundle 6 and also the potting material 7 have a similar elongated cross-sectional shape, also the two covers 13 and the associated Fastening parts 17 and 18 have a cross-sectional shape corresponding to the shape of the housing 1. The two ends of the case 1 are each provided with a groove 70 on their outside, and on the inner surfaces of the fastening parts 17 and 18 mating beads 71 are formed so that the two fastening parts can slide onto the associated ends of the housing until their bulges 71 snap into the grooves 70, as shown in Fig. 3, the potting material 7 and the covers 13 between the housing on the one hand and the fastening parts 17 and 18, on the other hand, the ends of the housing 1 and the fasteners 17 and 18 have one circular cross-section, threaded connections can be provided between them. In this case the fiber bundle fits 6 between the ends of the housing 1 of the cross-sectional shape of Penetration zone 25 within the housing, the one has an elongated cross-section, since the fiber bundle is flexible.

The relationship between the width W of the penetration zone 25 and its thickness A is preferably such that the expression W = kA, where k is greater than 1 but less than 40 expediently between 1.5 and 20 and preferably between 2 and 10 _o the cross-sectional area

2 of the penetration zone 25 is about 15 to 30 cm and can

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2
be about 20 cm, for example. The hollow fibers 5 take about 10 to 60 by volume of ^ o the penetration zone 25 and in a particular embodiment, for example, about 35 vol $ a _o Therefore, stands for the dialysate in the penetration zone 25, a space ratio of about 40 to 90 by volume of ^ and the case mentioned of about 65 VoI- ^ o available.

The cross-sectional enlargements 52, 53 »54, 66, 67 and 68 have a specific cross-sectional shape in order to generate the desired cross-flow in the longitudinal direction, which is described below with reference to the cross-sectional enlargement 67 with reference to FIGS. 4A to 4C where various embodiments are shown.

In FIGS. 4A to 4C, a point Q is designated at which the curved wall 55 of the cross-sectional expansion 67 intersects the flat support section 57 of the housing 1, or, more precisely, the line defining the inner surface of the curved wall 55 intersects the inner surface of the flat one Support section 57 defining line intersects. The point R denotes the point at which the flat wall 56 of the cross-sectional expansion 67 intersects the next flat support section 57 of the housing, or, more precisely, at which the line defining the inner surface of the flat wall 56 intersects the line defining the inner surface of the flat support section. The point P lies in the middle between the points Q and R _0. FIG. 4A is a section along a plane which is determined by the longitudinal axis of the fiber bundle 6 and the height of the cross-sectional enlargement 67 ₀ There is a line in this plane A1 drawn, which extends from the center point P at an angle of 10 to the flat support section 57 to the left, ie in the direction of flow of the dialysate 35, and another line A2 is drawn, which extends from the center point P from under a angle of 20 ° to the planar support portion 57 extends leftward _o Further, 4A in FIG. applied to the curved wall 55 at an arbitrarily selected point S 'between the lines A1 and A2 a tangent B "between the tangent B, and the

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In a similar way, a line C1 is drawn in the above-mentioned plane, which extends from the center point P at an angle of 10 to the flat support section 57 to the right against the flow direction of the dialysate 35 , and a further line C2 is drawn in, which extends from the center point P at an angle of 20 ° to the flat support section 57 to the right _β Finally, there is a further tangent D to the flat wall 56 at an arbitrarily selected point T on it Wall created between lines C1 and C2. There is an angle θ between the tangent D and the planar support portion 57.

Extensive studies have shown that there is a cross flow can be achieved to a very high degree if the angles ot and θ are chosen according to the following equations will:

30 ° <ot <90 ° ..O.O ... O. (4)

5 ° <θ <80 ° .. "o.e .... (5)

If angles are chosen which lie in the stated ranges, the extent of the channeling ^{11 of} the dialysate 35 along the wall of the housing 1 is effectively restricted, so that the flow component of the dialysate which moves transversely to the fiber bundle 6 is increased will be discussed in more detail below on the basis of test results.

If the angle <* in the range of 45 ° to 90 °, particularly good results can be achieved _o Referring to FIG _e 4A flows the dialysate 35 along the inner surface of the cross-sectional widening 67, then 6 to traverse the fiber bundle at a desired angle to its longitudinal axis " The closer the angle ot approaches an angle of 90 °, the stronger the cross-flow component of the dialysate _o Since the dialysate here is the

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Fiber bundle 6 alternately in one respect and the other crossed, there is an increase in efficiency dialysis. Since the dialysate flow 35 on the outer surfaces of the When hollow fibers 5 impinge, there is also turbulence, see above that it is possible to destroy boundary layers forming on the outer surfaces of the hollow fibers, leave this way there are large differences in the concentration values of the substances in question between the outer and inner surfaces of the Maintain hollow fibers, which promotes the flow of dialysis.

Particularly good results can also be achieved if the angle θ is in the range from 5 ° to 60 °. According to Fig. 4A can that of the preceding cross-sectional expansion 54 incoming dialysate quickly enter the widened cross-section 67, since it is not opposed to any resistance. The direction of flow of the dialysate is changed along the inner surface of the cross-sectional enlargement 67, and finally flows the deflected dialysate in the transverse direction through the fiber bundle 6, as described above.

Since a strong cross flow can be achieved if the angles <* and θ correspond to the above equations (4) and (5), the shape of the cross-sectional enlargement 67 is preferably selected in accordance with these equations. However, it is directed the extent to which the angle oc contributes to the generation of a cross flow, according to the size of the angle Θ. The results become the better, the further the angle becomes right Angle approximates.

Fig. 4B shows an embodiment in which the angles oc and θ have the smallest value that corresponds to equations (4) and (5). An effective cross flow can even be found in the Achieve arrangement according to Fig. 4B. Fig. 4C shows an embodiment, at which the angles oc and θ according to equations (4) and (5) each have the largest value within the relevant Area have. With this arrangement, too, can

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achieve a strong cross flow.

The angles co and θ are determined by the tangents B and D, but it has been shown that the shape of the cross-sectional enlargement 67 between the line A1 and the planar support section 57 and between the line C1 and the associated planar support section 57 only has little influence on the generation of a transverse flow, so that these parts of the cross-sectional _{widening can have} a flat, concave or convex shape, for example.The shape of the cross-sectional widening 67 is preferably convex between the lines A2 and C2 compared to the fiber bundle 6 so that the dialysate 35 can flow rapidly along the inner surface of the widened cross-section and can be deflected by it _o

Referring to FIG ₀ 3, the fiber bundle 6 between the upper cross-sectional enlargements 66, 67 and 68 on the one hand and the lower cross-sectional enlargements 52, 53 and 54 is located on the other hand, the offset in pairs in the longitudinal direction against each other Sindo Thus tends emerging from a cross-sectional widening dialysate 35 to be after the crossing of the fiber bundle 6 to enter the next opposite cross-sectional widening, so that it swiftly flowed through the fiber bundle in the housing 1 alternately in one and the other direction

The following is a method of operating a blood dialyzer in the form of the first embodiment 10 of the invention described ο

Fresh dialysate 35 is shown in FIG. 2 the inlet connection Via the feed line 80, the check valve 81 and the flow control valve 82 from a dialysate storage container fed. The dialysate throughput is e.g. 82 adjusted to a value of about 200 ml / min «. That Dialysate 35 is fed to the housing 1 according to FIG. 3 via the opening 85 of the inlet connection 27, whereupon it is the

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- 18 houses along a zigzag path flowed through _o

As soon as the housing 1 is sufficiently filled with dialysate, the circulating pump 75 is put into operation, so that the housing Further dialysate is continuously supplied via the feed line 80. This is the amount of dialysate that is discharged from the outlet port 28 is released per unit of time, equal to the dialysate throughput of the inlet port 27. The dialysate is via the check valve 78 and the flow control valve 79 delivered to a collecting container, not shown

The dialysate 35 flows under the influence of the circulation pump 75 from the inlet nozzle 29 according to FIG. 2 from right to left through the penetration zone 25 to then over the outlet opening 87 and the outlet connection 26 to the recirculation line 73, whereupon the dialysate is the housing 1 via the check valve 74, the circulation pump 75 and the flow control valve 76 and the inlet connection 29 again fed ,, The throughput speed of the recirculated Dialysate can be about 5000 ml / min »

The dialysate 35 enters via the inlet opening 88 according to FIG. 3 first into the cross-sectional widening 68 in order to then flow over the inner surface of this cross-sectional widening. On that the dialysate penetrates the fiber bundle 6 in order to reach the widened cross-section 54, since this widened cross-section the flow opposes less resistance than the penetration zone 25. The dialysate now flows along the inner surface of the cross-sectional enlargement 54, whereupon it again flowed through the fiber bundle 6 Ba the various Cross-sectional enlargements are offset from one another in the longitudinal direction, the dialysate follows in the housing as a whole an undulating path, and it moves in countercurrent to the blood 36 flowing through the hollow fibers 5. The dialysate flow has a considerable transverse component at right angles to the longitudinal axis of the fiber bundle 6.

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Since the inlet opening 88 of the inlet connection 29 as a slot is formed, which extends over the entire width of the penetration zone 25, a uniform flow can be of the dialysate compared to the fiber bundle. Since the mouth 57 of the outlet pipe 26 extends over the whole Width of the penetration zone 25 forms extending slot, the dialysate can be uniformly collected and discharged from the housing 1, and therefore all parts of the fiber bundle the dialysate flows through in the transverse direction.

The fresh dialysate 35 is supplied to the housing 1 via the inlet opening 85 and from the housing via the outlet opening 86 at essentially the same throughput rate derived. The cross-flow formed by the dialysate, which emanates from the inlet connector 27, hits the hollow fibers 5 »so that turbulent flows develop.

According to the description above, a very effective cross-flow of the dialysate is produced in the housing 1, so that the boundary layers developing on the membranes formed by the hollow fibers 5 are caused by the turbulent flow be destroyed. Therefore, it is possible, as desired, to make a substantial difference in concentration certain substances in the blood 36 and the dialysate 35 with the two liquids being kept separate by the membranes. Therefore, a high Achieve dialysis efficiency. The cross-flow formed by the dialysate penetrates the at high speed middle part of the fiber bundle 6, so that a turbulent flow is formed therein. The flow rate of the The dialysate 35 passing through the middle part of the fiber bundle can be considerably higher than in the case of the known device according to Fig. 1 "

If the reverse circulation speed of the dialysate is increased, the dialysate flows considerably faster through the penetration

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supply zone 25, so that the boundary layers formed on the membranes formed by the hollow fibers to a greater extent be destroyed. One can measure the extent of this destruction of the boundary layers by changing the recirculation speed accordingly of the dialysate. "

In the following, the relationships between the angles cc and θ and the degree of effectiveness of the dialysis on the basis of test results.

The experimental conditions were as follows:

Hollow fibers

Material: "Cuprophane" (cellulose) Outside diameter (dry): 247 micrometers Inside diameter (dry): 215 micrometers Effective length: 190 mm

Number of fibers: 7800

2 Total membrane area of the hollow fiber bundle: 1 m

casing

Cross-section at right angles to the hollow fibers:

2
73 mm χ 17 »5 mm = 12.8 cm

Packing density of the hollow fibers (volume of the hollow fibers swollen by the dialysate compared to the volume of the penetration zone to be filled by the hollow fibers):
42 vol%

Penetration zone
Length D: 38 mm
Height L: 12 mm
Distance d between adjacent cross-sectional extensions:

23 mm

The dialysis efficiency D is according to Wolff by the following Expressing formula:

- ^Q b Cbi - Cdi 609832 / ÜÖ68

(6)

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Herein, Db denotes a dialysis efficiency for blood, Qb the blood flow rate, Cbi the concentration of the blood at the inlet opening, Cdi the concentration of the Dialysate at the inlet and Cbo the concentration of the blood at the outlet.

The dialysis efficiency Dd for the dialysate is as follows Given formula:

vyu _ r \ f3 L'CLO "" OO-i ο ·· ο · οοοοο \ IJ

^ut) - ^{inter alia} Cbi - Cdi

Here, Qd denotes the throughput rate of the dialysate and Cdo the concentration of the dialysate at the outlet opening. Usually the size Db is used mainly

At Qb = 200 ml / min and Qd = 500 ml / min, tests led to the following results:

OC (degree)

17 17 17 20 20 30 30 30 40 40 40 50 50 50 60

θ (degree) Dialysis efficiency
with urea
(ml / min) 40 139 12th 141 30th 141 45 137 4th 139 4th 141 40 160 90 133 40 169 45 167 110 140 4th 148 45 170 110 144 4th 156

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oc (degree) θ (degree) 60 36 60 10 70 5 70 32 70 10 85 4th 85 35 85 105 90 5 90 30th 90 90 100 30th 100 45 100 110

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Dialysis efficiency with urea (ml / min)

172 170 148 175 150 149 176 141 162 180 150 150 142 130

The above results are shown graphically in FIG _o 5 and 6, FIG. 5 illustrates the relationship between the angle Ot and the dialysis efficiency at urea for angle θ between 5 and 80. In FIG. 5, the circles indicate the above experiment results, while the blackened dots represent the results of other experiments "Figo 6 illustrates the relationship between the angle θ and the dialysis efficiency at urea for angle Ot is in the range of 30 ° to 90 ° _o in Fig. 6, the circles again denote the above test results, while the blackened points apply to the results of other tests or _similar

According to Figure 5, ₀ outstanding values of the dialysis efficiency of greater than about 150 ml / min can be achieved when the angle ot between 30 ° and 90 °, while the angle θ is between 5 ° and 80 °. If you choose a value between 45 ° and 90 ° for the angle OC, excellent results can be achieved.

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Zieleno According to Fig. 6, excellent dialysis efficiencies are achieved achieved when the angle θ is between 5 ° and 80 ° and the angle cc is between 30 ° and 90 ° «, particularly good results are achieved achieved when the angle 9 is between 5 ° and 60 ° and in particular between 10 ° and 45 °.

Thus it has been proved by experiments that we obtain a dialyzer with a high efficiency when the angle oC and θ the equations (4) and (5) satisfies _e other hand, it has been found that the dialysis efficiency is reduced when the angular 06 and θ are outside the ranges specified by equations (4) and (5). 7A to 7F show examples of arrangements in which the dialysate flows through the widened cross-section of the housing 1 in an unfavorable manner. In the arrangements according to Fig _o 7A and 7B, in which the angle O ^ is too small, there is a danger of the so-called ₀ "channeling". In the arrangements according to Fig _o 7B and 7C, in which the angle θ is too large or ₀ is too small, there is a risk of occurrence of a turbulent flow in the cross-sectional widenings of the housing, so that the desired effective cross-flow can not be obtained, "in 7D to 7F, in which the angle O ^ is too large and the angle θ too large or too small, vortices arise at the outlet end and / or at the inlet end of the cross-sectional widening 67 »so that the cross-flow component is reduced and a "Channeling" of the dialysate adjusts.

It has been shown that there is a very effective cross flow in the cross-sectional enlargements 52, 53 »54, 66, 67 and 68 of the housing can be achieved if the height L and the length D (Fig <> 3) of the cross-sectional enlargements in the equations (1) and (2) specific areas.

Fig ₀ 11A shows a case in which the equation (1) is not satisfied, because the height L 1/4 of the distance A is less than. The height of the cross-sectional enlargements 52, 53, 66 and 67 varies only relatively little in this case, and therefore the flow

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Dialysate 35 almost in the direction of the longitudinal axis of the fiber bundle 6, and the cross-flow component with respect to the fiber bundle is very small, although the dialysate actually also enters the widened cross-section _{or the like}

FIG _o 11B shows a case in which the equation (2) is not satisfied, since the length D is smaller than the distance A. The dimensions of the cross-sectional enlargements 53 »66 and 67 are compared to those of the fiber bundle 6 is very small, and therefore, the cross flow formed by the dialysate 35 cannot reach the central part of the fiber bundle, resulting in unfavorable effects

Fig. 11C shows a case where the equation (1) is not satisfied because the height L is more than four times the distance A. is equivalent to. Since the height L of the cross-sectional extensions 53, 66 and 67 is relatively large, according to FIG. 11C, vortices are formed in parts of the three cross-sectional enlargements, so that the dialysate 35 the device is not flowing through quickly and the extent of the cross flow is reduced compared to the fiber bundle "

11D shows a case in which equation (2) is not fulfilled because the length D is greater than twelve times the distance A ₀ yields to the flow which forms along the fiber bundle 6, so that the dialysate cannot effectively flow through the fiber bundle in the transverse direction _o

Fig. 11E shows a case where equations (1) and (2) are satisfied, but the arrangement of equation is not (B) corresponds because the distance d is greater than the distance D. In this arrangement, part of the dialysate hits 35, which flows from the widened cross-section 53 from bottom to top through the fiber bundle 6, to the left end of the flat support portion of the housing 1, whereby of course the

60983 ^ / 08 6 8

£ 603560

The direction of flow is changed _{o It is} therefore not possible to allow the entire dialysate flow to pass quickly from the widened cross-section into the widened cross-section 66. This interferes with the generation of an intensive cross-flow of the dialysate through the widened cross-section 66. It is therefore preferable to meet the requirements of equation (3) so that an effective cross-flow is formed.

The distance D can also be shortened to zero. 12 shows such an arrangement. Here, between the cross-sectional extensions 52 and 53 and the cross-sectional extensions 54 and 54 on the underside 50 of the housing 1, there are curved sections 83 which adjoin the cross-sectional extensions 52, 53 and 54 in such a way that through Spaces limited to a sinusoidal curve are accordingly curved sections 84 between the cross-sectional enlargements 66 and 67 and the cross-sectional enlargements 67 and 68 on the top 51 of the housing, which also adjoin the cross-sectional enlargements so that spaces are present through a sinusoidally curved wall The support sections 57 of the curved sections 83 and 84, which support the fiber bundle 6, are opposite the corresponding apices of the cross-sectional enlargements 52, 53, 54, 66, 67 and 68, therefore the dialysate 35 can quickly enter the cross-sectional enlargements and from these the fiber bundle 6 is the same moderate flow _o

13 shows a modification of the arrangement according to FIG. 12, in which the cross-sectional enlargements are each composed of an only slightly curved section 89 and a more strongly curved section 90. Here, the dialysate 35 is guided along the slightly curved sections 89 and then through the more curved sections 90 suddenly deflected so that the fiber bundle 6 in the transverse direction flowed through can thus be in the arrangement of Fig. 13 also produce an effective cross-flow _o

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Normally, the dialysis efficiency varies depending on the throughput rate of the dialysate and the molecular weight of the substances to be dialyzed. "Fig. 8 illustrates the relationship between four different high throughput rates V1 to V4 of the dialysate, the molecular weight of the substances to be dialyzed and the efficiency of the dialysis. Referring to FIG _o 8, the dialysis efficiency decreases with decreasing molecular weight of the materials to be dialyzed. The higher the throughput rate of the dialysate, the higher the degree of efficiency, which applies in particular to substances with a lower molecular weight. It has been shown, however, that the effect of this phenomenon, which has a detrimental effect on the well-being of the patient because an uneven dialysis occurs, can be eliminated by recirculating most of the dialysate so that only part of the Dialysate is discharged _o FIG. 9 illustrates the effect of a renewed circulation of the dialysate on the efficiency of the dialysis. In Fig. 9, curve L1 is for the case that the dialysate flows through the device only once at the high speed, corresponding to the throughput speed V4 of FIG _o 8 ,, the resembles The relationship between the dialysis efficiency and the molecular weight to be dialyzed substance of corresponding relationship of Figure 8. The graph shows. N1 in Figure 9 _o that a particular material is dialyzed the faster, the lower its molecular weight isto

If the dialysate is recirculated in the device, the concentration of a substance with a lower molecular weight increases in the circulated dialysate. Therefore, the concentration difference between the blood and the dialysate in the Substance with the lower molecular weight is smaller, which practically prevents too rapid dialysis of this substance so that the differences in dialysis efficiency for substances of different molecular weights get compensated.

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In certain embodiments of the invention, the cross-flow components and therefore the dialysis efficiency increase as the flow rate of the circulated dialysate is increased _o In addition, the differences in the efficiency of the dialysis due to differences in molecular weight decrease as the flow rate of the circulated dialysate increases, as shown in FIG Figure 9 is illustrated by curves N2, N3 and N4.

Thus, it is possible by appropriately controlling the supply, the discharge and the circulation of dialysate to dialyze different substances in each case in the desired manner and the dialysis efficiency per unit volume of the dialysate to climb rn _o

In Figure "8 and 9 it is assumed that the substances contained in the blood of different molecular weight are present in almost equal amounts, and that the substances in question are not initially included in the dialysate ₀

In comparison to dialyzers with pipe coils or plates, the known device described at the beginning achieve good dialysis efficiency with hollow fibers for dialyzing blood. In view of this has been up to now an increase in the throughput rate of the dialysate not seriously taken into account, because differences in the degree of dialysis efficiency with different substances occur increasingly when one considers the throughput speed of dialysate increased. In addition, in the known blood dialyzer with hollow fibers, the so-called "channeling" occurs more and more Be careful when the throughput rate is increased so that a large amount of the dialysate is wasted ”.

Further, it has hitherto been assumed that the dialysis efficiency reduced when the dialysate is circulated again,

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because the concentration of the dialyzed substances in the dialysate increases, and this increases the concentration differences between the blood and the dialysate decreased in size.

In devices according to the invention, in which a cross-flow of the dialysate occurs, the "described" channeling "is avoided, and this leads to an improvement in the dialysis efficiency and the dialysis equilibrium, although the dialysate is circulated to adverse effects on the patient resulting, for the imbalance of the dialysis at different substances is equalized. it is also possible to control the imbalance of dialysis by adjusting the Rückumwälzgeschwindigkeit according to the physical condition of the patient, d _o h., the patient may accordingly its symptoms are treated.

The throughput rate of the dialysate flowing through the housing is expediently between approximately 200 and 10,000 ml / min and is preferably about 400 to 5000 ml / min. It is useful here for the relationship between the throughput speed of the supplied fresh dialysate and that of the circulated dialysate have a value of about 1:50 to 1: 0.5 and preferably from about 1:30 to 1: 1 to be selected. Here you can regenerate the dialysate by having it passes through an adsorbent and feed it back to the dialyzer without fresh dialysate being added.

The methods for supplying and removing the fresh dialysate are not limited to the description given with regard to the device according to FIG. FIG _o 10 shows a further development of the device according to Figo 2, wherein the exhaust pipe 77 branched from the circulation line 73, while the feed line 80 is connected to the Rückumwälzleitung 73rd Thus, the device is simplified by changes in the connections of the exit line 77 and the feed line 80, but

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it can be operated in the same way as the device according to FIG. 2.

Furthermore, the widened cross-section 67 according to FIG. 4A can be modified in the manner shown in FIG. 14. According to FIG. 14, a flat or straight section 58 is present between the cross-sectional widening 66, which takes up a considerable amount of space, and the flat section 57 supporting the fiber bundle 6, so that a larger amount of dialysate can be introduced into the cross-sectional widening 66. The flat section 58 defines an introduction zone. With this arrangement, a stronger cross flow can be achieved. The flat section 58 is inclined to the longitudinal axis of the fiber bundle 6 at the angle β and intersects the flat support section 57 at the point U _0. Along the fiber bundle 6, the flat section 58 has the length m ₀ The length of the flat support section 57, i.e., ho the distance between the point U and the point Q on the adjacent cross-sectional widening 67 is given by the distance η, which corresponds to the above-mentioned length d. The distances m and η as well as the angle ß should preferably satisfy the following equations:

1/3 A <m < 6A · Οοοο οο ·· vöy 1/3 A ^ η ^ 6A • ••• οο οο V -ζ / 0.1 <n / m < 10 · Ο ·· οοο οο \ I vJ / 2 ° <ß < 20 ° • · ο ·· οο ··· \ M /

Are herein referred to A of FIG ₀ 15 the depth of the penetration zone 25ο In this case, it is assumed that the equations (1) and (2) that apply to the height L and the length D ¹ of the cross-sectional enlargement 66 of FIG. 15 met, . Preferably m is between 1/2 A and 6A, while η is between 1/2 A and 6A, _o

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According to FIG. 15, in a region 59, which is formed by the flat support section 57, the flat section 58 and the dashed line Line 59 is surrounded, and which is adjacent to an area in which, according to FIG. 3, the uuerstströmung forms, the dialysate 35 guided through the inlet zone delimited by the flat section 58 in such a way that it quickly enters the cross-sectional widening 66, thereby increasing the cross flow will ο

In the devices according to FIGS. 3 and 4A, the dialysate 35 cannot be effectively introduced into the widened cross-section 66 in the region 59 in which only a slight cross flow occurs. In the device of Fig 14 _o the dialysate in the range 59, however, can of FIG. Be well collected in the cross-sectional widening 66 15 since the flat introductory portion exists 58th

If the distance m does not correspond to equation (8), ie if the flat section 58 is too long or too short, it is difficult to introduce the dialysate from the region 59 into the cross-sectional enlargement 66 in an effective manner _o corresponds to the distance η does not correspond to equations (9) and (10), there is a similar disadvantage. If the correct length of the distances m and η is to be determined, equation (10) must be taken into account. Ss is the angle is too small, that is, it does not correspond to the equation (11), the device corresponds to Fig. 15 to that of FIG. 4A ₀ is the angle ß too large, d _o h. if it does not correspond to equation (11), it proves difficult to achieve the desired cross flow. In the case of the cross-sectional expansion 66, the angle β is preferably smaller than the angle Θ. The flat section 58 does not need to be flat in every case in the manner shown in FIG. 14, but it could also be made concave or convex.

A second embodiment of the invention is shown in FIG.

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posed, which are related to the first embodiment the design of the cross-sectional enlargements and the process for circulating the dialysate differ “Those parts of the The device according to FIG. 16, which corresponds to parts of the first embodiment, are denoted by the same reference numerals, so that a new description should be superfluous.

Over the length of the housing 1 are four lower cross-sectional expansions 100, 101, 102 and 103 as well as three upper cross-sectional extensions 104, 105 and 106, which alternate in the longitudinal direction are offset from one another and between the side walls 50 and 51 over the entire width of the housing extend .. The side wall 50 of the housing has between the Cross-sectional extensions 101 and 102 have an opening or nozzle 107 which extends over the entire width of the side wall 50. The cross-sectional extensions 100, 101 and 102 each have the same shape, and the cross-sectional extensions 104 and 106 are symmetrical to one another. Each of the cross-sectional extensions 100 to 106 has one associated therewith the plane wall 56, which is closer to the nozzle 107, and a rounded or curved wall 55 < > The cross-sectional expansion 105 is composed of two rounded or curved walls 108 and 109 together. The middle part of the widened cross-section 105 is opposite the mouth 88 of the nozzle 107 for feeding of the dialysate 35 arranged. There are also outlet pipes 110 and 111 with slot-like openings 87 are present, which on the left side of the cross-sectional enlargement 104 and the are arranged on the right side of the cross-sectional expansion 106 of the housing ο

The inlet pipe for the circulated dialysate 35 is connected to the nozzle 107. The outlet tube 26 for the dialysate is connected to the pipe socket 110 and 111. According to FIG. 16, the outlet pipe 26 is branched and the dialysate is discharged deducted from the middle part of this tube. The outlet nozzle 28 for discharging the dialysate is at the cross-section widening

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tion 103 opposite the outlet pipe 111 is formed. The inlet pipe 27 for supplying dialysate forms part of the widened cross-section 100 and lies opposite the outlet pipe 110.

The cross-sectional extensions 100, 101, 102, 103, 104 and 106 are shaped so that, as shown in FIG. 4A, the angles oe and θ die Satisfy equations (4) and (5). The tangents B and D omitted in FIG. 16 are the ends of the cross-sectional expansion 105 assigned. The angles <x and θ between the support section 57 and the line B and between the support section and the line C satisfy equations (4) and (5). aside from that the cross-sectional enlargements (1), (2) and (3) correspond to 0

The dialysate 35 flows through the housing 1 essentially in the same way as in the first embodiment ₀ The circulated dialysate supplied via the nozzle 107 flows through the fiber bundle 6 and is introduced into the widened cross-section 105, in which the dialysate flow is divided into two partial flows, which are diverted to the left or to the right. The dialysate then flows in the manner indicated by arrows in FIG. 16 to the outlet openings 87 in order to escape through the outlet pipe 26 and to be fed again by the circulation pump to the inlet pipe 29 and thus circulated.

Since the nozzle 107 has the slot-like opening 88, which extends over the entire width of the penetration zone 25, the dialysate 35 can flow evenly through the fiber bundle 6 = Since the outlet openings 87 are also slit-like and extend over the entire width of the penetration zone, this can Dialysate can be collected evenly at these openings so that it flows evenly along a sinusoidal path through the fiber bundle 6 in the housing alternately in one and the other direction, with the desired cross flow being achieved _o

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The outlet openings are assigned to 87 for the to be circulated the dialysate to the ends of the housing 1 as in the embodiment of Fig. 16, while the inlet opening 88 to the central portion leads the housing, the dialysate is conveyed by suction to the two outlet openings 87 ₀ In this case, moves the dialysate flowing to the left in countercurrent to the supplied blood 36, while the dialysate flowing to the right moves in the same direction as the blood. The distance between the inlet opening 88 and the or each outlet port 87 is reduced compared to the apparatus of FIG. By half, so that a greater cross-flow can be formed as in the apparatus of FIG _o 3. Furthermore, decreases in the apparatus According to Fig. 16 the cross flow is not in the direction of the outlet openings 87, and the dialysate is introduced very evenly along the flat walls 56 into the various cross-sectional enlargements, in order then to be deflected by the curved walls 55 so that the fiber bundle 6 is almost in the at right angles to its longitudinal axis, which significantly improves the dialysis efficiency.

Also, in the apparatus in Fig. 16, the cross-sectional enlargements 100 are designed to 106 to satisfy the equations (1) to (5), so that the same operation can be achieved as in the first described Ausführungsfοrm _o In the device according F ^ g. 16 it is also possible to use only one flow path for the dialysate. In this case, the dialysate can be fed in via the inlet tube 29 and discharged from both ends of the housing 1 via the outlet tube 26. Here, the tubes 28 and 27 are omitted.

In the following 17 and 18 a third embodiment of the invention, with reference to FIG. Described which differ from the already embodiments discussed with respect to the design of the cross-sectional enlargements differs ₀ Those parts of the device according to Fig _o 17 and 18, which parts already described

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Bener embodiments correspond, are in each case with the same Reference numerals denoted so that a renewed description is unnecessary.

In this embodiment, cross-sectional expansions 129, 130, 131 and 132 formed in the interior of the housing 1 are composed of curved walls 120, 122, 124, 126 and 128 as well as flat walls 121, 123, 125 and 127, the adjacent cross-sectional expansions 129, 130 and 131, 132 are connected to one another by rectangular support sections 117 which extend over the entire width of the housing 1 «. The fiber bundle 6 is supported by the support sections 117. Since the cross-sectional enlargements 129 to 132 are shaped so that they satisfy equations (1) to (5), the dialysate 35 flows through the device in the manner indicated by arrows in FIG , d _o h. the desired cross flow is formed.

FIG. 18 shows a modification of the device according to FIG. 17, in which the cross-sectional extensions 129 to 132 are delimited by rectangular walls 120 to 128, so that the cross-sectional extensions each have an essentially trapezoidal cross-section _{or the like}

19 to 24 relate to a fourth embodiment of the invention, in turn parts, the parts already described Embodiments correspond, are each designated with the same reference numerals, so that a new Description should be superfluous.

The efficiency of dialysis depends largely on the shape of the housing. According to the invention, the relationships between the housing shape and the dialysis efficiency according to The definition given above has been investigated. It has been shown that the dialysis efficiency increases considerably leaves if the equation below is satisfied;

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¥ = kA (12)

Here, k is generally between 1 and 40, but expediently between 1.5 and 10 and preferably between 2 and 10, where ¥ according to FIG. 20 is the width of the penetration zone and A denotes the depth of the penetration zone. This means, that the penetration zone is a substantially flattened one Must have cross-sectional shape. The extent of the cross flow is directed largely according to the degree of flattening of the cross-section the penetration zone. It has been shown that dialysis The efficiency of the cross flow described can be increased considerably if the above equation (12) is satisfied will. It was also found that the dialysis effect can be further improved by using the cross flow, if you keep circulating the dialysate.

Referring to FIG ₀ 19 and 20, the housing 1 in turn comprises a bundle of hollow fibers 6 5> which is held by a potting material 7 in position. The inside of the housing is provided with almost rectangular, inclined guide walls 140 to 145 at regular longitudinal intervals, which are connected to the housing and offset from one another in the longitudinal direction. The angle of inclination of the guide walls may according to the shape of the fiber bundle are indeed arbitrarily selected 6, but it is preferable for practical reasons to choose an angle of inclination in the range of 15 ° to 75, and preferably between 30 ° and 60 _0, the free ends of the guide walls 140 to 145 are angled so that they form support sections 147 for the fiber bundle 6, which can be supported by the guide walls in such a way that it is secured against mechanical damage ₀

The guide walls 140 to 145 limit in the housing 1 a plurality of cross-sectional enlargements 149-156 _O The dialysate 35 is else fed to the cross-sectional enlargements in the manner already described ¥ and derived from them. According to Figo 20, the diameter

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Penetration zone 25 the width W and the depth A. The width ¥ is equal to the width of the housing 1, while the depth A is equal to the distance between the opposite Guide walls and thus equal to the thickness of the fiber bundle is.

In the following, the results are denoted by 1 to 16 Attempts received.

These tests were carried out under the following conditions:

Casing:

WxA = 15 cm (constant ^ W and A variable

Hollow fibers:

7000 hollow fibers made from "Cuprophane" produced using a copper-ammonia process. Effective length between the Potting material 7 at both ends: 150 mm. Inner diameter of the hollow fibers: 190 micrometers » Membrane thickness: 16 micrometers.

Guide walls:

Angle of inclination: 45

Distance between the fiber bundle 6 and the inner walls of the housing 1: 15 mm _o

To measure the efficiency of dialysis, an aqueous solution was used instead of blood, which contained common salt (molecular weight 58.5), urea (molecular weight 60), creatinine (molecular weight 113) and vitamin B ₁₂ (molecular weight 1355). Pure water was used as the dialysate

Was the dialysate is not recirculated, the outlet and the inlet tube 29 remained closed, ie _o it was just a flow path used in this method using only

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one flow path was operated with an average throughput rate Qb of the aqueous solution fed in via the inlet pipe 14 of 200 ml / min. The mean flow rate Qd of the pure water supplied through the inlet pipe 28 was 500 ml / min. The aqueous solution and the pure water were at a temperature of 37 C. The amount of common salt present was determined by measuring the electrical conductivity of the solution. The amounts of urea, creatinine and vitamin B _{12 present} were measured using a spectrometric method.

The results of these tests are summarized in Table I below.

W / A Qd Tabel 0 I. NaCl Dialysis efficiency
(ml / min) £ reatinin example (k) Qrd 1500 120 Urea 1 80 No. 0.33 (ml / min) (ml / min) 3000 132 131 93 1 0.33 500 5000 136 135 92 2 0.33 500 0 136 136 93 3 0.33 500 1500 124 137 90 4th 0.50 300 3000 134 132 94 5 0.50 500 5000 135 138 95 6th 0.50 500 0 138 138.5 96 7th 0.50 500 1500 132 140 90 8th 0.75 300 3000 143 135 98 9 0.75 500 5000 141 142 100 10 0.75 500 0 145 142 102 11 0.75 500 1500 133 143 98 12th 1.00 300 3000 148 140 106 13th 1.00 500 5000 149 147 107 14th 1.00 500 150 149 108 15th 1.00 500 150 16 300

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In the example above, where AxW = 15 cm, Qd denotes the throughput rate of the pure water supplied as fresh dialysate and Qrd the throughput rate of the pure water supplied as circulated dialysate.

According to Table I, the dialysis efficiency is then when k = W / A is less than 1, and when Qrd is not equal to zero _P with reverse circulation, is considerably higher than when Qrd is equal to zero, ie when none Recirculation takes place ,, Furthermore, the dialysis efficiency increases with the value of k. 21 illustrates the test results compiled in Table I in a graphical representation. According to FIG. 21, the dialysis efficiency suddenly increases sharply in the vicinity of k = 1.

In the following, the results are referred to by 17 to 28 Experiments entered In this case too, a dialysis machine according to FIGS. 19 and 20 was used, in which

2
W χ A = 20 cm, in which 10,000 hollow fibers 5 were present, and in which a throughput rate Qb of the aqueous solution of 280 ml / min was used. The experimental conditions were the same as before. In this case, the dialysis efficiency of vitamin B ^ S £ ^e ~ was measured ,, The results are in Table II below, total ammenge s shares.

Table II

Dialysis efficiency of vitamin B ₁₂ (ml / min)

24 24 22 22 0.50 500. 1500. 24

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example W / A Qd Qrd: 0 No. (k) (ml / min) (ml / min) 1500 17th 0.33 500 3000 18th 0.33 500 5000 19th 0.33 500 0 20th 0.33 300 21 0.50 500

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Example W / A Qd Qrd Dialysis efficiency of No. (k) (ml / min) (ml / min) Vitamin B ₁₂ (ml / min)

23 0.50 500 3000 25

24 0.50 300 5000 26

25 1.00 500 0 22

26 1.00 500 1500 28

27 1.00 500 3000 28

28 1.00 300 5000 30

In these examples, too, there is a considerable influence of the recirculation of the dialysate. The efficiency of dialysis increases with the value of k _o

In Figure 22 are the results summarized in Table II shown graphically, and it can be seen that the dialysis efficiency increases sharply in the vicinity of k = 1.

The following discusses the results of labeled 29-64 experiments in which also the dialyzer of FIG was used _o 19 and 20, wherein all values of k on were first These results are summarized in Table III below.

W / A Qd Tabel 0 III Dialysis efficiency
(ml / min) 119 example (k) Qrd 1500 Urea creatinine 122 No. ₀ 1.25 (ml / min) (ml / min) 3000 NaCl 153 124 29 1.25 500 5000 144 159 135 30th 1.25 500 0 154 165 117 31 1.25 500 1500 162 170 125 32 1.50 300 3000 166 158 133 33 1.50 500 5000 149 164 144 34 1.50 500 161 172 35 1.50 500 170 183 36 300 179

60 983; // Ex 68

W / A tid - 40 - 0 2603560 (ml / min; : Creatinine (k) 1500 Dialysis efficiency Ureas 121 example 2.00 Qrd 3000 160 128 No. 2.00 (ml / min) (ml / min) 5000 NaCl: 167 139 37 2.00 500 0 154 179 146 38 2.00 500 1500 162 188 120 39 3.00 500 3000 174 161 131 40 3.00 300 5000 186 171 140 41 3.00 500 0 156 183 149 42 3.00 500 1500 168 192 123 43 5.00 500 3000 181 163 133 44 5.00 300 5000 190 173 143 45 5.00 500 0 160 184 146 46 5.00 500 1500 170 195 124 47 10.00 500 3000 181 164 137 48 10.00 300 5000 192 176 148 49 10.00 500 0 159 187 156 50 10.00 500 1500 172 198 121 51 20.00 500 3000 182 161 137 52 20.00. 300 5000 191 176 149 53 20.00 500 0 159 187 158 54 20.00 500 1500 175 195 129 55 30.00 500 3000 185 169 136 56 30.00 300 5000 192 175 145 57 30.00 500 0 159 185 159 58 30.00 500 1500 173 197 124 59 40.00 500 3000 182 164 146 60 40.00 300 5000 195 196 158 61 40.00 500 161 186 158 62 40.00 500 175 187 63 500 183 64 300 196

Comparing Table I with Table III, it can be seen that the dialysis efficiency increases when k = 1 significantly increased. In Fig. 21 the in Table III

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The compiled results are shown graphically. According to Figure 21, the efficiency of dialysis _o decreases with respect to the urea with the increase in the throughput rate of the recirculating dialysate to. However, even if no dialysate is circulated, ie if Qrd = 0, the dialysis efficiency increases considerably at k = 1. From FIG. 21 it can be seen that k should expediently be between 1.5 and 20 and preferably between 2 and 10

In the following, the results are referred to as 65 to 91 Attempts were made in which also the dialyzer

2 according to FIGS. 19 and 20 was used. Here, ¥ χ A = 20 cm, 10,000 hollow fibers 5 were present, and the throughput rate Qd was 280 ml / min. The other conditions were the same as in the examples discussed above. The degree of dialysis efficiency of vitamin B ^ _{2 was} measured, and the results are compiled in Table IV below and shown graphically in FIG.

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Table I?

example W / A ad Qrd Dialysis efficiency No. (k) (ml / min) (ml / min) with vitamin B ^ 65 1.50 500 0 37 66 1.50 500 1500 45 67 1.50 500 3000 50 68 1.50 300 5000 60 69 2.00 500 0 41 70 2.00 500 1500 51 71 2.00 500 3000 58 72 2.00 300 5000 69 73 3.00 500 0 45 74 3.00 500 1500 55 75 3.00 500 3000 64 76 3.00 300 5000 76 77 5.00 500 0 46 78 5.00 500 1500 57 79 5.00 500 3000 69 80 5.00 300 5000 80 81 10.00 500 0 48 82 10.00 500 1500 59 83 10.00 500 3000 69 84 10.00 300 5000 82 85 30.00 500 0 48 86 30.00 500 1500 59 87 30.00 500 3000 70 88 30.00 300 5000 81 89 40.00 500 0 4β ■ 90 40.00 500 1500 • 60 91 40.00 300 5000 83

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From Fig. 22, which shows the results according to Tables II and IV, the dialysis efficiency for vitamin B ^ ₂ improves with a recirculation of the dialysate, and it suddenly increases with a recirculation as well as with only one pass at k = 1 to.

The following deals with the results of an experiment designated 92 using the same dialyzer became like before. In this case, Qd = 300 ml / min, Qrd = 2700 ml / min and Qb = 200 ml / min, and the temperature was 37 ° Co. The results are shown in Fig. 23 as solid lines Curve shown. It can be seen that the dialysis efficiency with urea increases sharply as soon as k becomes the value 1 The apparatus of FIGS. 19 and 20 can be modified in the manner described below.

The number of guide walls 140 to 145 can be varied and these walls can be curved. Furthermore, the guide walls can extend at right angles to the longitudinal axis of the fiber bundle 6. If the guide walls are inclined upward and inward according to FIG. 19, the direction of flow of the dialysate can be changed accordingly. The side walls of the housing 1 with the width A can have a semicircular or shark-elliptical shape. In this way, coagulation of the fluid flowing through the hollow fibers 5 blood can be avoided effectively "Although Fig the guide in accordance _o 19 walls 140 are added to 145 in the housing 1 in the longitudinal direction against each other, but could be arranged symmetrically with respect to the fiber bundle 6 also. Although the inlet pipes 28, 29 and the outlet pipes 27, 26 in the housing 1 are preferably arranged diagonally opposite one another, they could also be provided on the same side of the housing to facilitate manufacture and handling.

FIG. 24 shows a further development of the device according to FIG. and 20, in which the guide walls in particular have been modified,

6 09832/0868

The guide walls delimiting the cross-sectional enlargements 157 and 158 have a semi-cylindrical shape and are arranged obliquely opposite one another in the case 1. The lower sections of the guide walls 157 and 158 have openings 159 and 160 as passages for the dialysate 35. The openings 16O are formed in the middle of the lower portions of the guide walls 157 and 158 and are larger than the openings 159 too both sides of the central openings. The flow of dialysate can be regulated through openings 159 and 160. Of the From the lower guide wall 157, the dialysate 35 flows through the fiber bundle 6 to that through the upper guide wall 158 delimited area 161. Here, part of the dialysate flows through the openings 159 and 160 to the area 161 inside the guide wall 158. The flow is weakened by the smaller openings 159, while compared to this is reinforced by the larger opening 160 »This has to As a result, the flow velocity of the between the inner surfaces of the housing 1 and the fiber bundle 6 flowing through Dialysate is relatively low, while the dialysate flows through the middle part of the fiber bundle relatively quickly.

A fifth embodiment will now be described with reference to Figs of the invention described in which the dialysate is not recirculated, and in which various modifications are made on the cross-sectional enlargements.

According to FIGS. 25 and 26, in the blood dialyzer designated as a whole by 10, the upper and lower end portions of the Housing as in the known device of FIG. 1 has a cylindrical shape, while the cross section of the main part of the housing is square. The main part of the housing can also be given a different shape as described below The one side wall 50 of the housing 1 is provided with semi-cylindrical cross-sectional enlargements 170, 171 and 172, while the other side wall 51 semi-cylindrical cross-sectional extensions 173, 174 and 175, which in uniform longitudinal

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are spaced apart. The cross-sectional extensions 170 to 172 and 173-175 are offset in the longitudinal direction against each other and each extending over the entire width of the side walls 50 and 51. As shown in FIG _o 26 face each other similar semi-cylindrical portions which are formed by the cross-sectional enlargements 170 to 175, in compound with which the fiber bundle 6 containing penetration zone 25, which has a square cross-section _o hit the cross-sectional extension 170 is an outlet tube 3 is connected to the dialysate 35, and an inlet tube to the cross-sectional widening 175 closes 2 at the dialysate.

As well as upper and lower cover plates 13 and upper and lower attachment members are mounted 17 and 18 on the upper and lower end of the housing 1 in the apparatus according to Fig _o 1, and at both ends of the fiber bundle 6 is a sealing compound 7 is present. Since the upper and lower ends of the housing have a circular cross-section, the associated ends of the fiber bundle 6 together with the potting compound are also circular. However, the main part of the fiber bundle 6 adapts to the square cross section of the penetration zone 25, since the hollow fibers 5 are very flexible.

In the device according to FIGS. 25 and 26, there are no parts of the hollow fibers 5 in the areas 176 to 181 _{o delimited by the cross-sectional expansions 170 to 175}

The dialysate 35 is fed to the widened cross-section 121 via the inlet tube 2 with the mouth 22, so that the Dialysate flow is not locally concentrated on the fiber bundle 6, and that there is therefore only a very low risk that the fiber bundle is damaged by the dialysate flow.

Which according to FIG 25 _o circular shaped upper and lower end portions of the housing 1 could also get a square cross section. In this case, the covering

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washers 13 and the fasteners 17 and 18 a square Have shape. The blood receiving chambers 13A delimited by the cover disks 13 have a similar square shape Cross-sectional shape. The fasteners 17 and 18 are attached to the housing 1 mounted so that existing beads on its inside in associated grooves on the outside of the housing ends intervention.

27 shows a modification of the device according to FIGS. 25 and 26, in which the cross-sectional extensions 170, 171 and 172 on the side wall 50 of the housing compared to the device 25 and 26 are displaced downwards, while the cross-sectional enlargements 173, 174 and 175 at the other side wall 51 are shifted upwards. Here, the cross-sectional enlargements are on both sides of the housing offset from one another in the longitudinal direction. The inlet tube for the dialysate 35 is directly connected to the side 51 of the housing and not connected to the enlarged cross-section 175, and the outlet tube 3 for the dialysate closes immediately to the side wall 50 of the housing and not to the Cross-section expansion 170 at "

Thus, the device 10 according to FIG. 27 differs from that according to FIGS. 25 and 26 in that the dialysate 35 near the inlet opening 22 is not distributed so evenly over the entire width of the side wall 51 of the housing, and that it is near the outlet opening 23 is collected not so evenly over the entire width of the side wall 50 _o However, by also flows in the apparatus of FIG _o 27 the dialysate according to the arrows, the fiber bundle 6 repeated alternately in the one and the other direction, that is, the desired extent, a cross-flow achieved.

FIG. 28 shows another development of the device according to FIGS. 25 and 26, in which the cross-sectional enlargements 170 to 172 of the side wall 50 of the housing compared to the front

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27 are shifted slightly upwards, while the cross-sectional enlargements 173 to 175 of the other side wall 51 are correspondingly displaced downwards so that the cross-sectional enlargements are arranged symmetrically to the fiber bundle 6 are. The device according to FIG. 28 only differs externally from the device according to FIG 27, but the device according to FIG. 28 operates in a different manner than that which indicates the direction of flow of the dialysate Arrows corresponds.

29B to 29H show various developments of the device according to FIG. FIG. 29A is a section through the housing 1 along the line XXIXa-XXIXa in Fig. 26. Fig. 29B to 29H 29A various developments show in cross-section corresponding to FIG. Of the housing 1 _o The case of FIG. 29A to 29D have a rectangular Cross-section. In the housings according to FIGS. 29B and 29C, the cross-sectional extensions 172 and 174 are semi-cylindrical, as is also the case with the cross-sectional extensions of the housing according to FIG. 29A. In the case of the housing according to FIG. 29D, the cross-sectional enlargements are hemispherical.

In the apparatus according to Fig _o 29B is the length of the cross-sectional serweite runge η 178 and 180, which are in connection with the penetration zone 25 is relatively large compared to the cross sectional area of the penetration zone, that _o the penetration zone has a flat cross section, so that the Dialysate distributed in the cross-sectional widening 181 near the inlet opening 22 (FIG. 26) in the width direction, in order then to flow upwards through the fiber bundle 6 _o This type of distribution or dispersion of the dialysate proves to be very advantageous. The greater the value of the ratio between the length of the cross section of the penetration zone 25 and its width, the more effectively the dialysate is distributed. However, too large a value of this ratio turns out to be unfavorable from the standpoint of handling the device. In

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in practice it is expedient to have a value between 1.5 and 20 and preferably between 2 and 10 to choose.

The housings of FIGS. 29E to 29H have an elongated cross-sectional shape. The cross section of the housing according to Fig. 29F is circular. The housing according to Fig. 29G is hexagonal Cross-section, while the cross-sectional extensions 172 and 174 of the housing according to FIGS. 29E to 29G are hemispherical. The cross-sectional extensions 172 and 174 of the housing according to FIG. 29H have a triangular cross-section in the longitudinal direction.

The upper and lower end portions of the housing of FIGS. 29A to 29H can be circular or rectangular, while the Cross-sectional enlargements outside the penetration zone in may be given a different shape in the manner described below.

Fig. 30, 31 and 32 show further modifications of the device according to Fig _o 25 ".

In the device according to FIG. 30, the cross-sectional enlargements 170 to 175 have a triangular cross section and in the device according to FIG. 31 a trapezoidal cross section.

In the device according to FIG. 32, the cross-sectional enlargements 52, 53, 54, 66, 67 and 68 have the same shape as in the device according to FIG. 3, but the dialysate 35 is not circulated again, and therefore the device according to FIG. 32 not provided with the inlet pipe 27 and the outlet pipe 28 of FIG _o. In the device according to FIG. 32, the inlet pipe 29 of FIG. 3 for the dialysate to be circulated and the outlet pipe 26 for the dialysate serve as an inlet pipe or outlet pipe for the dialysate which in this case is not to be circulated. The transverse

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In the device according to FIG. ₀ 32, widened sections are formed in such a way that they correspond to equations (1) to (5) and equation (12), which will be discussed further. As with the first embodiment, it is possible to create an effective cross flow. In the apparatus according to Fig _o 32, it is also possible to circulate the dialysate 35 with the help of the inlet pipe 29 and the outlet pipe 26 again, and this supply and withdrawal can be brought about by the dialysate in the Rückumwälzkreis. For example, a small container connected to the circuit can be used for supplying and removing dialysate, or the method described with reference to FIG. 10 can be used.

FIGS. 33-34 and 35 show further modifications of the device according to FIG. 25, in which the main part of the penetration zone 25 has a triangular cross-section, and in which one first side wall 200 of the housing with widened cross-sections

190, 191 and 192 is provided. A second side wall 201 of the Housing has enlarged cross-sections 193, 194 and 195, while the third side wall 202 of the housing is provided with cross-sectional enlargements 196, 197 and 198? all cross-sectional extensions are evenly spaced along the length of the device. The cross-sectional expansion are along the housing 1 in the order 190, 196, 193,

191, 197, 194, 192, 198 and 195 arranged so that they are longitudinal a helix are spaced apart.

The dialysate 35, which is fed to the cross-sectional enlargement 195 via the inlet pipe 2, flows through the fiber bundle 6 in the direction of the arrows, ie _o clockwise _o Here, the dialysate follows a helical path, being repeatedly deflected so that it successively flows through the cross-sectional widenings 195, 198, 192, 194, 197, 191, 193, 196 and 190 so that it repeatedly crosses the fiber bundle 6

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36 shows a further modification of the device according to FIG 25, in which the penetration zone 25 has a cylindrical shape, and in which the housing 1 correspondingly on its circumference the arrangement of Figo 33 to 35 with hemispherical Cross-sectional enlargements 190 to 198 is provided »

It is true that in the device according to FIGS. 33 to 35 the cross-sectional enlargements 190 to 198 have a semi-cylindrical shape, but they could also have a triangular cross-section in longitudinal section obtain. Here you can circulate the dialysate 35 in such a way that the inlet tube for the dialysate with the cross-sectional enlargement 192 and the outlet tube for the dialysate connects to the cross-sectional enlargement 193, wherein the inlet pipe 2 and the outlet pipe 3 for circulating the dialysate is used. In this case too, the dialysate can pass through the housing from bottom to top along a helical line 1 and repeatedly cross the fiber bundle 6. The recirculation can be brought about in the same way as in the first embodiment.

In the following is described with reference to FIG _o 37 to 51, a sixth embodiment of the invention correspond with the parts corresponding to those described with reference -from Fig. 1 are again denoted by the same reference numerals.

In the device according to FIGS. 37 to 39, the housing 1 has a flattened, generally elongated cross-section with rounded ones End walls ,, However, there could also be a rectangular cross-section with four rounded corners. Needs If the housing is not to be flattened, one can also choose a square cross-section with four rounded corners.

The housing 1 is designed to be axially symmetrical as a whole. The side walls 50 and 51 of the housing are provided with cross-sectional extensions of trapezoidal cross-section, the extend over the entire width of the housing, the transverse

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_ ₅₁ _? 603560

section extension .210 is adjacent to the upper end of the side wall 50, while the cross section extension 211 is adjacent to the lower End of the side wall 51 is adjacent, so that the two cross-sectional enlargements lie on a diagonal of the housing. The inlet pipe 2 for the dialysate 35 is arranged horizontally, and connected to one end of the widened cross section 211. The outlet pipe 3 for the dialysate is also arranged horizontally and is connected to the widened cross section 210 The inlet pipe 2 and the outlet pipe 3 extend in opposite directions, which is advantageous an even distribution of the dialysate over the fiber bundle 6 has the effect. However, one could expand the cross-section to facilitate manufacture and handling also on the same side of the housing. The result of the cross-sectional expansion 210 and 211 demarcated areas 212 and 213 are in communication with the flattened penetration zone 25 »which the bundle 6 of hollow fibers 5 contains.

The dialysate is _o supplied to the housing via the inlet opening 22 of Figure 38 so that it first enters the cross-sectional widening 213 which opposes a considerably lower resistance to flow than the penetration zone 25, whereby the dialysate in which extends over the entire width of the side wall 51 of the housing extending cross-sectional enlargement 213 is evenly distributed in order to then flow through the fiber bundle 6 upwards. There is therefore only a very low risk that the part of the fiber bundle adjacent to the inlet opening 22 will be damaged by the incoming dialysate. The dialysis efficiency for urea that can be achieved with this device is indicated in FIG. 23 by the dashed curve. According to FIG. 23, the dialysis efficiency increases sharply in the vicinity of k = 1 _o

40 shows a further development of the device according to FIGS. 37 to 39, in which the cross-sectional extensions 210 and 211 have a have a semi-cylindrical shape. Here, the outlet pipe 3

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and the inlet tube 2 are each connected to the central part of the associated cross-sectional extension and L-shaped Apart from the just mentioned points corresponding to the "device of FIG ₀ 40 is substantially that of FIG. 37 to 39 and operates in substantially the same Way.

41 shows another development of the device according to FIG 37 to 39, which essentially correspond to the device according to FIG. 40, except that the cross-sectional enlargements 210 and 211 have an almost rectangular cross-section. The apparatus of Fig. 41 essentially operates in the same way as that according to Fig. 40 "

42 also shows a further development of the device according to FIGS. 37 to 39, in which the upper half of each cross-sectional enlargement 210 and 211 according to FIG. 41 has a rectangular cross-section, while the lower half is rounded according to FIG. 40. Arrangement and shape of the inlet tube 2 and the outlet tube 3 substantially correspond to the representation in FIGS. 37 through 39 _o The other construction is substantially the same. The device according to FIG. 42 is therefore essentially as effective as that according to FIGS. 37 to 39 _o

Fig. 43 to 46 also show a further development of the device according to Figs. 37 to 39, wherein the outlet pipe 3 and the intake pipe 2 in the narrow sides 214 and 215 of the housing 1 are installed on both sides of the penetration zone 25 _o The cross-section extensions 212 and 213 extend over the side walls 50 and 51 and the narrow sides 214 and 215, so that they have an L-shaped shape. In order to distribute the dialysate 35 supplied via the inlet pipe 2 to all parts of the cross-sectional widening 213, a weir part or a deflecting member 216 is attached to the inner surface of the narrow side 215 within the cross-sectional widening 213

609832 / U868

To discharge dialysate evenly via the outlet opening 23, a further weir part or deflection element 217 is on according to FIG attached to the inner surface of the narrow side 214 within the cross-sectional expansion 212. Weir parts 216 and 217 can have the same shape.

The blood inlet tube 14 and the blood outlet tube 15 are attached to the upper cover 13 and the lower cover 13 formed so that they each extend almost in the same direction as the outlet pipe 3 and the inlet pipe 2 for the Dialysate. The blood inlet port 24 of the inlet tube 14 and the blood outlet port 24 of the outlet tube 15 have a similar one Shape like the chambers 20 in the housing 1, so that the blood 36 flows rapidly from the inlet opening 24 to the outlet opening 24 can.

The outlet pipe 3 for the dialysate 35 and the inlet pipe 14 for the blood are adjacent to each other and almost extend in the same direction. Correspondingly, the inlet tube 2 for the dialysate and the outlet tube 15 for the blood are mutually exclusive adjacent and so arranged that they are almost in the same direction, as shown in FIG in a simple manner caps 218 on the blood inlet tube 14 and the dialysate outlet tube 3 or the blood outlet tube 15 and the like Put on the dialysate inlet tube 2, and this can be effected with the aid of an automatic machine, not shown.

Since the deflection members 216 and 217 are arranged in the L-shaped cross-sectional extensions 212 and 213, this is via the Dialysate 35 supplied to the inlet opening 22 is distributed uniformly over all parts of the widened cross-section 213 and in the Cross-sectional enlargement 212 uniformly collected in order to be fed to the outlet opening 23. Here concentrates the dialysate stream entering via the opening 22 does not affect a small part of the fiber bundle 6, so that no politeness damage to the fiber bundle in the vicinity of the

609832/0868

Inlet opening through a concentrated stream of dialysate consists of O

47 to 49 show a further modification of the device according to FIGS. 37 to 39 in the form of a horizontally arranged one Apparatus which is otherwise essentially similar to the apparatus according to FIGS. 43 to 46. According to FIGS. 47 and 49, this flows Dialysate 35 obliquely from the underside of the side wall 51 through the penetration zone 25 to the upper part of the side wall 50. Since the fiber bundle 6 is relatively short, the dialysate can effectively flow through it in the transverse direction so that a good dialysis efficiency can be achieved leaves.

In the device according to FIGS. 47 to 49, the cross-sectional enlargements 212 and 213 extend over the entire length the penetration zone 25. However, this cross-section Extensions also extend only over part of the length of the penetration zone, so that the dialysate passes through the penetration zone would flow through in a correspondingly different way.

50 and 51 show another development of the device 37 to 39, in which the upper and lower ends of the housing 1, which has a round cross-section, with semicircular cross-sectional extensions 210 and 211 provided are. The inlet pipe 2 and the outlet pipe 3 are enlarged with diametrically opposite cross-sections tied together. The mouth 22 of the inlet pipe 2 leads to the semicircular space 213 by the widened cross-section 211 is delimited, while the mouth 23 of the outlet pipe 3 to the by the cross-sectional enlargement 210 delimited space 212 adjoins. As with the device according to FIGS. 37 to 39, the cross-sections have widened sections 210 and 211 have a trapezoidal cross-section, but one could also have a rectangular or semicircular cross-section provide. The two cross-sectional extensions extend

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in the circumferential direction of the circular housing 1, respectively over an angular range of 180 ° and are offset from one another by 180 °. The dialysate 35 flows from the lower one Cross-sectional expansion or the space 213 from obliquely upwards through the penetration zone 25 through to the upper one Space 212 in the widened cross-section 210, so that the hollow fiber bundle 6 is flowed through in the transverse direction. The cross-sectional enlargements 210 and 211 can also be designed in this way be that they are in the circumferential direction of the round case 1 each extend over an angular range of 60 ° to 120 °.

FIG. 52 shows another development of the device according to FIG. 37, in which the housing 1 on one side with a is provided over the entire length of the fiber bundle 6 extending cross-sectional enlargement 220, which is a curved owns outer wall. The inlet pipe 2 and the outlet pipe 3 are attached to the opposite side of the housing. Because of the curvature of the outer wall of the cross-sectional enlargement 220, the dialysate is caused to flow from the inlet tube 2 from flowing in the transverse direction through the fiber bundle 6 and then escaping again via the outlet pipe 3.

While the foregoing are various preferred embodiments of the invention described, but there are ways to create further modifications that are also within the field of the appended claims.

In the exemplary embodiments described, the blood and the dialysate flow through the penetration zone in countercurrent. Since this countercurrent process in the described arrangements is combined with a cross flow, better dialysis can be achieved. However, it is also possible to use the blood and the dialysate in the same general direction of flow to pass through the penetration zone.

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If necessary, one can in the recirculation flow path for the dialysate turn on a small dialysate container In In this case, the small container is provided with an inlet opening and an outlet opening for replenishing the dialysate supply, and the recirculation line is connected to the tank

The housing of the device can have a plurality of inlet openings and a plurality of outlet openings. Furthermore, the openings can be arranged differently with respect to the housing. Finally, one can swap the inlet port and the outlet port at the described embodiments with one another, d _o h. the inlet opening can be used as an outlet opening and the outlet opening as an inlet opening.

Although the various embodiments of the invention have been described for the case that dialysis is to be carried out between two liquids, the invention can also be used in cases in which substances are between a liquid and a gas or between two gas flows through the membranes forming hollow fibers are to be transported through. May continue to the devices described do not only use as a blood dialyzer in an artificial kidney, but also in an artificial lung for supplying oxygen to a blood stream, the blood is passed through the hollow fibers, while the oxygen-containing gas or _o an appropriate liquid, the outer surfaces of the hollow fibers sweeps ,, Finally, one may include such devices for desalting and purification of water by reverse osmosis, in methods for treating food, Z ₀ B ₀ for concentrating juices, removal of yeast from beer, etc use _0th

Expectations;

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Claims (1)

EXPECTATIONS Device with a housing, a bundle of hollow fibers with permeable walls arranged in the housing and with means for passing a first fluid and a second fluid through the housing such that the one fluid sweeps over the outer surfaces of the hollow fibers, while the other fluid flows through the hollow fibers, thereby characterized in that the housing (i) has several wall sections adjacent to the bundle (6) of hollow fibers (5) (52, 53, 54, 66, 67, 68) which are shaped so that they form cross-sectional enlargements of the housing in order to to contribute that the first Flud (35) flows through the fiber bundle transversely to the hollow fibers. 2. Device with a delimiting a penetration zone Housing, one filling at least this penetration zone Bundles of hollow fibers with permeable walls, at least one inlet tube for supplying a first fluid the housing in such a way that it flows through the gaps between the hollow fibers, at least one outlet pipe for discharging the first Fludes from the housing as well as devices that enable a second fluid to be passed through the hollow fibers, so that it is possible for certain substances to selectively penetrate the walls of the hollow fibers, characterized in that at least one part (52, 53, 54, 66, 67, 68) of the housing (1) within the penetration zone (25) opposite the bundle (6) of hollow fibers (5) forms a cross-sectional widening in such a way that between the hollow fiber bundle and a wall of the housing has a space into which at least a part of the first fiud (35) is on its way can enter from the inlet pipe (2) to the outlet pipe (3), and that the or each cross-sectional enlargement has such a shape that it helps to induce the first flud to flow through the hollow fiber bundle in the transverse direction «, 609832 / U868 3. Apparatus according to claim 2, characterized in that a plurality of cross-sectional enlargements are present which are arranged on opposite sides of the housing. 4. Apparatus according to claim 3 »characterized in that the cross-sectional enlargements on the two each other opposite sides of the housing between the inlet pipe and the outlet pipe alternately with each other and in the Are arranged offset from one another in the longitudinal direction. 5 o device according to claim 2, characterized in that the or _o each cross-sectional expansion of the housing is formed by an outwardly projecting part of a wall of the housing. 6 ₀ device according to claim 2, characterized in that the or each cross-sectional enlargement is formed by a guide plate part on an inner surface of the housing. 7. The device according to claim 2, characterized in that the shape of the or _o each cross-sectional expansion, the following equations 1/4 A <L <4A and A < D <12A corresponds to where A is a cross-sectional dimension of the hollow fiber bundle (6), L is the length of the cross-sectional expansion at right angles to the longitudinal axis of the hollow fiber bundle and D the Denotes the length of the cross-sectional expansion in the direction of the longitudinal axis of the hollow fiber bundle. 8 "Device according to claim 7" characterized in that that the shape of the or »each cross-sectional expansion corresponds to the equations 609832/0868 1/3 A <L <2A and
A <D <8A is equivalent to, 9. Apparatus according to claim 71, characterized in that that the length d of a planar support section of the housing which rests against the hollow fiber bundle (6) in order to support it, the equation 0 <d <D
is equivalent to. 1Oo device according to claim 2, characterized in that that there are several cross-sectional enlargements, and that an inlet zone inclined towards the longitudinal axis of the hollow fiber bundle (6) between adjacent cross-sectional expansions is arranged. 11. The device according to claim 10, characterized in that the or each introduction zone by a flat wall (58) is delimited, which is related to the associated cross-sectional expansion adjoins and is inclined to the longitudinal axis of the hollow fiber bundle (6). 12. The device according to claim 11, characterized in that adjacent cross-sectional expansions are each connected to one another by an inclined flat wall (58), which is adjoined by a flat support section (57), which is in contact with the hollow fiber bundle (6) to support it, 13. The device according to claim 12, characterized in that the angle of inclination (ß) of the wall (58) of the introduction zone, 609832/0868 the length (m) of the discharge zone in the direction of the longitudinal axis of the hollow fiber bundle (6) and the length (s) of the planar support section (57) in the direction of the longitudinal axis of the hollow fiber bundle correspond to the following equations: 1/3 A < m -c 6A,
1/3 £ η ^ 6A,
0.1 ^ n / mg 10 and 2 ^ ß ^ 20. 14o device according to claim 2, characterized in that that on opposite sides of the housing several cross-sectional widenings are present, which are opposite to the penetration zone (25) are curved in the shape of a sine wave. 15. The device according to claim 2, characterized in that the or each cross-sectional enlargement on its exit side opposite to the general direction of flow of the first Fludes (35) is shaped to match the equation 30 ° ^ CX- < 90 ° corresponds to, at which the angle <x is obtained if a first straight line (A1) and a second straight line (A2) in the direction of flow of the first fluid (35) at an angle of 10 or 20 ° to the longitudinal axis of the hollow fiber bundle from the center point (P) between the end of the cross-sectional enlargement facing the flow and that into the The end of the cross-sectional enlargement pointing in the direction of flow and a tangent (B) on the wall (55) of the cross-sectional enlargement at any point between the first and the second line, the angle oc being the angle which the 609832/0868 7603560 Forms tangent with the longitudinal axis of the hollow fiber bundle. 16 _O device according to claim 15 »characterized in that the angle oc corresponds to the following equation: 45 ° < Qt < 90 °. 17o device according to claim 15, characterized in that that the or each cross-sectional enlargement on its inlet side opposite the general direction of flow of the first Fludes (35) is shaped to match the equation 5 ° <Q <30 ° corresponds to at which the angle θ is obtained when one in the plane passing through the longitudinal axis of the hollow fiber bundle (6) and the dimension (L) measured at right angles to it the cross-sectional expansion is determined, a third straight Line (C1) and a fourth straight line (C2) opposite to that Direction of flow at an angle of 10 ° or 20 ° against the longitudinal axis of the hollow fiber bundle from the center point (P) between the entry side and the exit side of the Cross-sectional expansion and a tangent (D) to the wall (56) of the cross-sectional expansion at any point (T) that wall draws between the third and fourth straight lines, where the angle θ is the angle that this tangent makes forms with the longitudinal axis of the hollow fiber bundle. 18. The device according to claim 17, characterized in that that the angle θ corresponds to the following equation; 5 ° <θ <60 ° o 19ο Device according to claim 17, characterized in that that the angle θ corresponds to the following equation: 10 ° <9 <45 ° _E 609832/08 68 20. The device according to claim 2, characterized in that the penetration zone (25) is shaped so that it the equation ¥ = n / a corresponds, in which ¥ and A are the cross-sectional dimensions of the Denote penetration zone, where k is greater than 1. 21. The device according to claim 20, characterized in that k corresponds to the following equation: 1 <k <40. 22. The device according to claim 20, characterized in that k corresponds to the following equation: 1.5 <k <20. 23. The device according to claim 20, characterized in that k corresponds to the following equation: 2 <k <1O ₀ 24. The device according to claim 2, characterized in that the inlet pipe (27) and the outlet pipe (28) for the first Flud (35) connected to a recirculation circuit for the first Flud which leads through the housing (1), and that a further inlet pipe (29) and a further outlet pipe (26) are present are, which make it possible to supply the device with a fresh fluid of the same type as the first fluid and a Remove part of the first fluid from the device. 25 ο Device according to claim 24, characterized in that a container is switched into the return circuit in such a way that the one which escapes from the outlet pipe and is to be circulated again. first fluid (35) enters this container and then flows from the container to the inlet pipe, and that the other inlet 609832/0868 Let the tube and the other outlet pipe be connected to the container sindo 26. The device according to claim 24, characterized in that that the inlet pipe and the outlet pipe for circulating the first fluid diagonally opposite one another on opposite sides Sides of the housing are arranged, and that the other inlet pipe and the other outlet pipe for supply and discharge of the first fluid in the side walls of the housing opposite the inlet pipe and the outlet pipe for circulating the first Fludes are built in. 27. The device according to claim 24, characterized in that the outlet pipe is forked for circulating the first fluid is that two ends of the bifurcated outlet pipe are connected to the associated ends of a side wall of the housing, and that the inlet pipe for circulating the first fluid is built into the central part of the other side wall of the housing is. 28ο Device according to claim 24, characterized in that that the inlet pipe for circulating the first fluid is bifurcated, that two ends of the bifurcated inlet pipe with the associated Ends of a side wall of the housing are connected, and that the outlet pipe for circulating the first fluid in the middle part of the other side wall of the housing is installed. 29. The device according to claim 24, characterized in that the inlet pipe for supplying the first fluid has a branch of the inlet pipe for circulating the first fluid, and that the outlet pipe for discharging the first fluid forms a branch of the outlet pipe for circulating the first fluid. 3Oo device according to claim 2, characterized in that 609832/0868 7603560 that the inlet pipe and the outlet pipe are connected to means which serve to supply the first fluid to the housing feed and divert it from the housing in such a way that it flows through the housing only once and is not circulated again will. 31 ο Device according to Claim 30, characterized in that that the outlet pipe for discharging the first fluid is bifurcated, that two ends of the bifurcated outlet pipe in the associated Ends of a side wall of the housing are installed, and that the inlet pipe for feeding the first fluid into the middle part of the other side wall of the housing is installed. 32. Apparatus according to claim 30, characterized in that the inlet pipe for supplying the first fluid is bifurcated is that two ends of the bifurcated inlet pipe are built into the associated ends of a side wall of the housing, and that the outlet pipe for discharging the first fluid is built into the central part of the other side wall of the housing is. 33. Device according to claim 1, characterized in that that the inlet pipe and the outlet pipe serve to recirculate the fluid, and that the fluid is discharged via the outlet pipe, regenerated with the aid of an adsorbent and then fed back to the inlet pipe. 34. Apparatus according to claim 2, characterized in that at least one of the inlet and outlet pipes to the Cross-sectional enlargement is connected, and that a device is available which serves to the over the inlet pipe supplied first fluid in the cross-sectional enlargement essentially over all parts of a cross-sectional dimension of the To distribute the penetration zone and / or the first Flud in the associated cross-sectional expansion of essentially all 6 0983 2 / Obbö .65- 7603560 Dividing a cross-sectional dimension of the cross-sectional expansion to collect so that it can be discharged from the widened cross-section via the outlet pipe, 35ο device according to claim 27, characterized in that the penetration zone has a flattened cross-section, and that is disposed or _o any cross-sectional enlargement on the longer side of the cross section of the penetration zone, " 36, The apparatus of claim 34, characterized in that the length of the penetration zone in the direction of the longitudinal axis of the hollow fibers (5) is smaller than the measured at right angles to the longitudinal axis of the hollow fibers length of the longer side of the penetration zone, and in that the or along ₀ each cross-sectional widening the longer side of the cross section of the penetration zone is formed _o The patent attorney 609832/0868