JPH0299067A - Hollow fiber type fluid treatment apparatus - Google Patents

Abstract

PURPOSE:To prevent channeling and to reduce pressure loss by winding a hollow fiber sheet formed into a reed screen shape around porous inner cylinder and receiving the same in a porous outer cylinder. CONSTITUTION:The blood introduced into a porous inner cylinder 3 from a blood inlet 11 flows in a gas exchange chamber from the openings bored in the porous inner cylinder 3 to flow in the outer peripheral direction thereof and flows out from the blood outlet 12 provided to the upper side wall of a cylindrical housing 1. The gas introduced into hollow fibers from a gas inlet 10 flows toward the lower part of the cylindrical housing 1. In this external perfusion type artificial lung, a reed screen like hollow fiber sheet is wound around the porous inner cylinder 3 and received in an outer cylinder 4. In this case, one hollow fiber sheet formed into a reed screen shape from hollow yarns arranged in parallel or bundles 41 each composed of a plurality of hollow fibers by longitudinal yarns 40 may be continuously wound around the porous inner cylinder 3 or two reed screen like hollow fiber sheets may be wound around the porous inner cylinder 3 in such a state that the hollow fibers of the upper and lower sheets are superposed so as to have an angle alternately.

Description

DETAILED DESCRIPTION OF THE INVENTION (Industrial Application Field) The present invention relates to a fluid treatment device using a membrane, particularly to a device suitable for treating m-liquid.

This type of device is generally used in blood permeators, oxygenators, plasma separators, humidifiers, and the like.

For convenience of explanation, a case where this is applied to an oxygenator will be explained.

(Prior Art) Artificial lungs have been studied as an auxiliary means for surgical procedures, and various types have been developed. Among the functions of biological lungs, these artificial lungs perform the gas exchange function of adding oxygen to blood and removing carbon dioxide, and bubble oxygenators and model oxygenators are currently in practical use. .

Bubble oxygenators are widely used clinically, but because oxygen is injected directly into the blood, they tend to cause hemolysis, protein denaturation, blood coagulation, microthrombi formation, and activation of white blood cells and complement.
Moreover, when used for a long time, the antifoaming effect becomes weaker, and there is a possibility that microbubbles may be mixed into the blood.

The model oxygenator makes contact between venous blood and gas through a membrane.
Because it absorbs oxygen into the venous blood and releases carbon dioxide into the gas at the same time, it is more physiological than a bubble-type oxygenator, and has advantages such as less blood damage and a smaller priming volume. It has gradually come to be used clinically in recent years.

The model artificial lungs currently being developed use porous hollow fibers made of hydrophobic polymers such as polyolefins or gas-permeable homogeneous hollow fibers such as Noricon to bring gas and blood into contact through the hollow fiber surface. The internal perfusion type (JP-A-62-106770, JP-A-59-57661, etc.) allows blood to flow into the hollow part of the hollow fiber and gas to flow outside the hollow fiber. ) and, conversely, an external perfusion type (Japanese Patent Laid-Open Nos. 5,957,963, 60-28,806, etc.) in which gas is passed through the hollow part of the hollow fiber and blood is allowed to flow outside.

(Problem to be solved by the invention) In the former method, if blood is distributed and supplied evenly to a large number of hollow fibers, there is no channeling of blood (unbalanced flow), but the blood flowing inside the hollow fibers is a completely laminar flow. Therefore, in order to increase the gas exchange capacity (gas transfer rate per unit membrane area), it is necessary to reduce the inner diameter of the hollow fibers. For this purpose, hollow fibers having an inner diameter of about 150 to 300 μm have been developed for use in oxygenators.

However, even if the inner diameter is made smaller, as long as blood flows in a laminar flow state, gas exchange performance will not be dramatically improved. At present, the required amount for adult treatment is 200~
In order to achieve a gas exchange capacity of 300 cc/min, an internal perfusion oxygenator requires a membrane area of approximately 6 m''. Therefore, an internal perfusion oxygenator is large, heavy and difficult to handle, and the blood filling volume is limited. In order to make oxygenators smaller and make them easier to handle, the inner diameter of the hollow fibers is made even thinner, resulting in clotting (a phenomenon in which the hollow part is blocked by blood clots). Moreover, this type of oxygenator has the problem that head perfusion cannot be applied because the resistance on the blood flow path side is large, making it difficult to apply a pulsatile flow type blood pump.

In addition, - In artificial lungs for boat fishing, thousands to tens of thousands of hollow fibers are used in bundles, and it is difficult to sufficiently distribute and supply gas to each of these many hollow fibers. Special consideration is required for distributed supply. When the distributed supply of gas is insufficient, the carbon dioxide removal ability (carbon dioxide transfer rate per unit membrane area) decreases.

On the other hand, in the latter method, although gas distribution is good and turbulence can be expected to occur in the blood flow, there are problems such as insufficient oxygenation due to blood channeling or a tendency for blood clots to occur in the retention area. An artificial lung with sufficient performance has not yet been realized.

(Means for Solving the Problems) The present inventors focused on externally perfused oxygenators, which have low pressure loss and are expected to improve gas exchange capacity per unit area, and identified the drawbacks of externally perfused oxygenators. Blood channeling and blood retention are achieved by using a cloth-like hollow fiber sheet, and then winding the cloth-like hollow fiber sheet around a porous inner cylinder and storing it in a cylindrical housing. I tried to resolve it by doing this. However, simply accommodating a laminated body of wound cloth-like hollow fiber sheets in a cylindrical housing resulted in problems such as increased blood channeling and a decrease in gas exchange capacity per unit membrane area. . The present inventors found that this problem was caused by the swaying of the laminate of wound cloth-like hollow fiber sheets in the blood flow, and as a result of further study, the present invention was arrived at. .

That is, in the present invention, a laminate of hollow fiber sheets is wound around a porous inner cylinder and housed in a porous outer cylinder, and the hollow fiber sheet is housed in a cylindrical housing. is supported by partition walls that close both ends of the housing so that both ends thereof are open, and a first fluid inlet or outlet communicating with the internal space of the hollow fiber is provided at the upper end of the housing, and a first fluid inlet or outlet is provided at the upper end of the housing, and the porous inner cylinder is an upper boat having a second fluid inlet or outlet communicating with the interior; and a lower head cover having a first fluid outlet or inlet communicating with the interior of the hollow fiber at the lower end of the housing; This is a hollow fiber type fluid treatment device characterized in that a first fluid outlet or inlet is provided on the upper side wall of the housing.

(Function) In the fluid treatment device of the present invention, a hollow fiber sheet formed in a compact shape is wound around a porous inner cylinder, and this is housed in a porous outer cylinder. The resulting laminate of hollow fiber sheets is sandwiched between the inner tube and the outer tube. Therefore, a flow path regulated by the warp fibers and the hollow fibers is formed between the stacked hollow fibers, so that channeling can be prevented and pressure loss can be reduced.

(Example) Next, an example of the hollow fiber type fluid treatment device of the present invention will be described with reference to the drawings.

FIG. 1 shows a sectional view of an artificial lung, which is an example of the fluid treatment device of the present invention. The oxygenator has a cylindrical housing 1
A gas exchange chamber is formed inside.

In the gas exchange chamber, a hollow fiber sheet in which a bundle of one or more hollow fibers was formed into a shape with warp threads was wound around a porous inner cylinder 3 and housed in a porous outer cylinder 4. A laminate 5 of hollow fiber sheets is housed.

The hollow fibers are supported and fixed by partition walls 6.6'' that close both ends of the housing so that both ends thereof are open. The upper end of the housing has a gas inlet IO communicating with the interior space of the hollow fiber and a blood population 1 communicating with the interior of the porous inner cylinder 3.
It is covered with an upper head cover 7 having a diameter of 1. Further, the lower end of the housing is covered with a rad cover 8, which has a gas outlet 13 communicating with the inner space of the hollow fiber. In an artificial lung, the lower head cover 8 does not necessarily need to be provided.

In this case, the gas is discharged directly to the atmosphere through the end openings of the hollow fibers embedded in the partition wall.

A blood outlet 12 is also provided on the upper side wall of the cylindrical housing 1. FIG. 1 shows an example in which the tip of the blood inlet 11 passes through the partition wall 6 that closes the upper part of the hollow core tube 2 and opens into the inside of the porous inner cylinder 3. Further, as shown in FIG. 2, the blood inlet is provided by dividing the inside of the upper head cover 7 into two by a dividing piece 14, and opening the blood inlet 11 in the inner space of the divided head cover. An opening 15 may be provided in the partition wall 6 that closes off the head cover 7 to communicate the inner space of the head cover 7 with the inside of the porous inner cylinder. Furthermore, as shown in FIG.
The blood guide device 16 may be inserted and fixed in a liquid-tight manner into the porous inner cylinder from the 6° partition wall that closes the lower end of the blood guide device 16.

The laminate 5 of the hollow fiber sheets is shown in FIG. 4 along A-A in FIG.
As shown in the cross-sectional view, a knotted hollow fiber sheet is wound around a porous inner cylinder 3, a two-part porous outer cylinder 4 is placed around it, and the joints of the outer cylinder are bonded by ultrasonic bonding. The adhesive is integrally colored.

Blood introduced into the porous inner cylinder 3 from the blood inlet 11 flows into the gas exchange chamber through an opening formed in the porous inner cylinder, flows toward the outer circumference of the gas exchange chamber, and forms a cylindrical shape. Blood flows out from an outlet 12 provided in the upper side wall of the housing 1. On the other hand, the gas introduced into the hollow fiber from the gas population 10 flows toward the bottom of the cylindrical housing.

In such an externally perfused oxygenator, the porous inner cylinder 2
For example, as shown in FIG. 5, the knotted hollow fiber sheet is wound around the outer tube 4 and is housed in the outer cylinder 4. For example, as shown in FIG. One hollow fiber sheet formed in the shape of a hollow fiber can be continuously wound around the porous inner cylinder, or two knotted hollow fiber sheets can be wrapped around the upper and lower parts as shown in Fig. 6. It is also possible to wrap the hollow fibers around the porous inner cylinder in a state in which the hollow fibers are alternately stacked at an angle. In this case, adjacent hollow fibers can cross each other, further improving blood channeling. Figure 7 (
a) and (b) are cross-sectional views of the knotted hollow fiber sheet;
In Figure (a), one hollow fiber is used, and in Figure 7 (b)
This shows an example using a bundle of three hollow fibers. To make hollow fibers into a warp shape,... 9J4J Hollow fibers may be braided with warp threads, or warp threads may be bonded to hollow fibers, but the method of braiding hollow fibers with warp threads is particularly preferred because it facilitates production of knotted sheets.

When using the device of the present invention for emergency treatment, it is necessary to select warp yarns and adhesives that will not damage blood. What kind of knitting method can be used to braid the hollow fibers in a yield-like manner with the warp threads? As shown in Figure 7 (a) and (b), each hollow fiber is knitted one by one with the warp threads. It is preferable to fix it with By fixing each hollow fiber with warp threads in this way, it is possible to prevent the hollow fibers from shifting due to blood flow when winding the hollow fiber sheet around the inner cylinder or during use, and the gap between adjacent hollow fibers is always maintained constant. channeling can be completely prevented.

The hollow fiber formed in a planar shape is not particularly limited as long as it is gas permeable, and for example, it may be made of a polyolefin-based material such as polyethylene or polypropylene, or a resin such as polytetrafluoroethylene, polysulfone, or silicone rubber. A porous or homogeneous hollow fiber with high oxygen gas permeability is used. Among these, hollow fibers made of polyolefin resin are preferable because even if the film thickness is thin, the hollow fibers are less likely to be crushed or deformed when formed into a planar shape.

The outer diameter (D) of the hollow fiber is 50~2000μ, and the membrane thickness is 3~
It is 500μ. If the outer diameter or film thickness is smaller than this, yarn breakage or filament breakage is likely to occur when forming into a planar shape, and on the other hand, if it is larger than this, it is difficult to realize compactness of the device. Normally, the outer diameter (D) of the hollow fiber is 100 to 500μ, and the membrane thickness is 6 to 10μ.
0μ is preferable, and the outer diameter (D) is 175 to 400μ.
, those having a film thickness of 10 to 60 μm are more preferably used.

The effective length of the hollow fibers is usually 3 to 30 cI11. If the effective length is smaller than this, the cutting loss of the hollow fiber during the assembly process will be excessive and it will be uneconomical, while if it is larger than this, it will be difficult to make the device compact.

The hollow fibers are formed into a planar shape using a bundle of one or more hollow fibers as a unit system. When a bundle of a plurality of hollow fibers is formed into a planar shape, a bundle of 35 or less hollow fibers, preferably 24 or less hollow fibers is used. 1 for bundles of 35 or more hollow fibers
This is not preferable since each hollow fiber in the single fiber bundle may not be able to make sufficient contact with blood, which may reduce gas exchange efficiency.

Usually, a planar sheet is formed using each hollow fiber as a weft thread. In this case, approximately 100% of the surface area of each hollow fiber
% is not only utilized for gas exchange with the blood, but the blood is divided and mixed extremely efficiently in minute units by the small, almost square, uniform slits formed by the vertical and horizontal threads. An unexpectedly high gas exchange capacity can be achieved in terms of area, and pressure loss can be reduced.

The warp yarns forming the hollow fibers into a planar shape are not particularly limited, but for example, thin but strong yarns such as polyester, polyamide, polyimide, polyacrylonitrile, polyethylene, polypropylene, polyarylate, polyvinyl alcohol, etc. are used. Among them, 10 to 150 deniers made of multifilament, preferably 25 to 7
Since 5-denier polyester or polyamide yarns have both appropriate softness and mechanical strength, they are preferably used without damaging the hollow fibers when processed into planar shapes.

When using the device of the present invention for medical purposes such as an oxygenator, the use of oil on the warp threads should be avoided as much as possible, but if it is unavoidable, such as when forming into a planar shape, safety should be confirmed. It is necessary to use an oil that has been removed or that can be washed away.

The laminate in which the planar hollow fiber sheet is wound has a porous inner cylinder 3 and an outer cylinder 4 to prevent the hollow fibers from shaking due to blood flow during use.
It is held between the Such porous inner and outer cylinders are necessary to maintain the arrangement of the laminated hollow fiber sheets to form a blood flow path and to prevent saliva channeling, and are made of polyethylene, polypropylene, etc. Olefin resins, polystyrene, polyacrylate resins, polyamides, polycarbonate resins, thin metal plates, etc. are used. A cylindrical body made of polycarbonate, polyamide, or polyolefin resin with a thickness of usually 0.5 to 5++1 m is preferably used. The cylindrical body has a hole diameter of 1 to LQm.
A large number of m holes are drilled. The outer cylinder 4 is usually divided into two parts, and the hollow fiber sheet wound around the inner cylinder 3 is sandwiched between the outer cylinders 4 and the joined parts are glued together to integrate them.

It is preferable that the planar formed hollow fiber sheet to be accommodated in the gas exchange chamber of the oxygenator satisfies the following conditions.

First, the warp density W (lines/cm) of the cylindrical sheet has a high gas exchange ability, prevents blood stagnation and channeling, has low pressure loss, and allows reproducibility of external perfusion with low priming volume. For good implementation, it is preferable to satisfy 0.2≦W≦40.

That is, when the density W of the warp yarns is smaller than 02, the hollow fibers that fit between the warp yarns are long, and the hollow fibers tend to sag between the warp yarns. As a result, it becomes difficult to regulate the hollow fibers, which are weft threads, to be arranged in parallel at substantially constant intervals, and the distribution density of the hollow fibers becomes uneven, causing blood to sag in the hollow fibers when used as an oxygenator. There is a risk that high gas exchange performance may not be achieved by repairing many sparse areas with large amounts of gas.

When the density W is greater than 4.0, the hollow fibers are regulated in parallel at extremely uniform intervals, and as a result, the flow rate of blood flowing through the gaps between the hollow fibers is made uniform. However, as the warp density increases, the contact area between the warp and hollow fibers increases, the contact area between the hollow fiber membrane and blood (effective membrane area) decreases, and the contact area (weave) between the warp and hollow fibers decreases. Since it is difficult for the blood to flow, there is a risk that the diffusivity of dissolved gases on the blood side will decrease, that is, the gas exchange capacity will decrease and the pressure loss will increase.

Furthermore, the yarn density F (wood/cm) per unit length in the longitudinal direction of the hollow fibers, which are the wefts, and the lamination + per unit thickness of the laminated hollow fiber notebook! This is an important requirement due to the relationship between F and F (sheets/am), and according to the experiments of the present inventors, as F and/or I increase, the gas exchange capacity of the oxygenator clearly improves. However, at the same time, the pressure loss on the blood side also increases. Therefore, in order to realize an oxygenator with low pressure drop and high gas exchange efficiency, 0.73 1Q@/(3,QX D )'≦FXI≦108B...
・×D) It is preferable that the relationship of 2 exists.

If FXI is too small within this range, the gas exchange capacity will be too low, and if FXI is above this range, the pressure loss will be too large. In this equation, D is the outer diameter of the hollow fiber (μ
), when a bundle of multiple hollow fibers is used, it represents the outer diameter (μ) of a cylinder formed by a predetermined number of hollow fibers packed closely together to prevent crushing.

Another requirement of the present invention is that the stacked thickness T (cm) of the hollow fiber sort stacked between the porous inner and outer cylinders is in the range of 05≦T≦12.0. The thickness of the laminated notebook layer is particularly related to pressure loss, but if the thickness is greater than this, the pressure loss will be too large, which will be a problem when using a pulsatile flow pump. Moreover, if it is less than this, it becomes difficult to handle in terms of air removal during brimming, placement with an artificial heart-lung machine, connectivity, etc.

The anomalous hollow fiber notebook is wound around a porous inner tube, housed in a porous outer tube, and then housed in a cylindrical housing. The housing containing the laminate wound with the hollow fiber sort is assembled using a centrifugal bonding machine after the open ends of the hollow fibers are packed with a highly viscous wood fiber, or after the open ends of the hollow fibers are closed by heat rolls or crushing. Polyurethane, linicone, evokino resin, etc. are injected into both ends of the hollow fiber, and the hollow fiber is cured to a predetermined degree.The outer end of the cured resin is then cut to open the hollow fiber.

The oxygenator described above may have a built-in heat exchanger or blood reservoir. FIG. 8 is a sectional view of an oxygenator having a built-in heat exchanger, in which a porous inner cylinder 3 houses a heat transfer tube 20 wound in a coil shape. The heat exchanger tube 20 is supported by a heat exchanger tube support tube 21 inserted into the porous inner cylinder 3, with both ends buried in a partition wall 6.6° that closes both ends of the cylindrical housing. That's what I do. The heat transfer tube 20 is wound around the support tube 21 in a coil shape, and has one end opening at the top of the support tube and the other end opening at the bottom of the support tube.

Pipes are connected to the openings, respectively, and a hot water inlet 22 and a hot water outlet 23 are provided at the lower end of the housing. Alternatively, as shown in FIG. 9, the heat transfer tube 20 may be wound in a coil around the blood guiding device 16 provided inside the porous inner cylinder 3. Furthermore, as shown in FIG. 10, a heat exchanger tube 20 wound into a coil may be housed inside the porous inner cylinder.

FIG. 11 shows an artificial lung with a built-in blood reservoir, in which blood flows out from an opening 30 provided at the upper part of the housing between the outer wall of the housing and the outer periphery of a cylindrical housing l. I! 31 are provided. The blood storage tank 3
A blood outflow port 32 is provided at the bottom of 1. Further, it is also possible to provide an oxygenator having a built-in heat exchanger and a blood storage tank, which is a combination of an oxygenator with a built-in heat exchanger and a blood storage tank as shown in FIGS. 8 to 1O. FIG. 12 shows an example of an artificial lung incorporating a heat exchanger and a blood storage tank, in which a heat exchanger tube 20 wound in a coil is housed in a porous inner cylinder 3, and a blood storage tank 31 is placed on the outer periphery of the cylindrical housing 1. This is an example where . FIG. 13 shows an example in which a coiled heat transfer tube 20 is housed inside a blood storage tank 31, and this oxygenator is arranged in a type of oxygenator-blood storage Hiroichi heat exchanger.

The device of the present invention can be used for fluid treatment in many other applications, not just oxygenators. For example, in a translucent trough that transfers mass between two different types of liquids through a hollow fiber, it does not matter whether the two types of liquids flow inside or outside the hollow fiber, but in blood treatment, blood It is preferable to flow it inside the hollow fiber. When mass transfer is performed between gas and liquid through a hollow fiber to dissolve the gas in the liquid or to release gas, 2N gas is transferred inside or outside the hollow fiber. I don't care if it goes anywhere.

When a specific substance contained in a gas or liquid is separated by a hollow fiber, the liquid or gas may be flowed either inside or outside the hollow fiber. It is usually preferable to apply hollow fibers on the outside.

Next, the present inventors conducted various experiments in order to confirm the effects of the present invention. An example is shown below.

Experimental Example 1 As hollow fibers, polypropylene porous hollow fibers having an outer diameter of 360μ, an inner diameter of 280μ, and a porosity of about 50% were arranged one by one so that the density (F) in the length direction was 17 fibers/cm. ,
Using 30 denier (12 filament) polyester yarn as the warp, the density (W) is 1/C! ! The hollow fibers were braided in a yield shape to form a hollow fiber sheet shown in FIG. The number of laminated sheets per unit thickness (T) of this hollow fiber sheet is 30 sheets in a porous inner tube (2 cm in diameter) made of polypropylene with a thickness of 2.5 mm, in which a large number of holes with a diameter of 3 mm are bored at 8III+ intervals. /cm, wound so that the thickness (T) is 3 cm, and a porous outer shell made of polypropylene with a thickness of 2.5 mm, with a large number of holes of diameter 3 m + 11 bored at 81 intervals around the circumference. Tube (diameter 8.5c
m), and the joint portion of the nuclear outer cylinder was adhered by ultrasonic adhesion to form a hollow fiber notebook@liquid. The FXI of this laminate was 510, and the effective membrane area was 1.48 m'. This laminate was housed in a cylindrical housing with a diameter of 10cI11 and a thickness of 2.5mm.

Then, both ends of the hollow fiber were supported by partition walls made of polyurethane resin formed at both ends of the housing, thereby producing the device shown in FIG. 1. On the other hand, a device without a porous outer cylinder was separately manufactured. The effective length of the hollow system was then 7 cm.

Using bovine blood heated to 37°C, blood and pure oxygen were passed through the two types of devices mentioned above so that the ratio of oxygen flow rate to blood flow rate was 1.0. Table 1 shows the results of the tests conducted according to the Japanese Artificial Organ Association (Japan Artificial Organ Association). In addition, in the following evaluation, the maximum blood flow rate was 2000 CmQ1 min/m.
2) If the pressure drop is less than 300 (mmH9) or more than 300 (mmH9) when the blood flow ffi is 612/min, there is a practical problem and it is outside the scope of the present invention, and an asterisk (*) is marked on the right end.

Experimental Example 2 Using the same hollow fiber sorting as in Experimental Example 1, four types of devices were fabricated with different stacking thicknesses (T) of the hollow fibers sandwiched between the porous inner cylinder and the outer cylinder. Table 2 shows the results of the same test as above.

Table Experimental Example 3 Four types of hollow fiber sorting with different warp densities (W) were made, and the stacking thickness T of the hollow fiber notebook was 3 as in Experimental Example 1.
Experimental Example 1
Table 3 shows the results of a similar test made using a similar device.

Using the same hollow fibers as in Experimental Example 1, the hollow fibers were arranged with different density (F) in the longitudinal direction and knotted so that the warp density (W) was 1/Cm as in Experimental Example 1. A device similar to Experimental Example 1 was prepared by forming a hollow fiber sort braided into a shape, and changing the number of laminated sheets per unit thickness of the hollow fiber notebook to form a laminate with a lamination thickness T of 3 cm. Table 4 shows the results of the same test.

Experimental Example 4 Experimental Example 5 A plurality of hollow fibers shown in Experimental Example 1 were bundled together, the arrangement of the hollow fiber bundles was changed, and the warp yarns were braided in the same manner as in Experimental Example 1 to form a hollow fiber sort. And the number of laminated sheets per laminated thickness I
A laminate with a thickness of 3 cm was obtained by changing the conditions. Using this laminate, a device similar to that in Experimental Example 1 was manufactured and the same tests were conducted. The results are shown in Table 5.

Experimental Example 6 Hollow fiber with an outer diameter of 250μ, an inner diameter of 210μ, and a porosity of 5
Using a laminate of hollow fiber notebooks in which one 0% polypropylene porous hollow fiber was bonded with a warp thread, four types of devices similar to those in Experimental Example 1 were fabricated, with each parameter changed as shown in Table 6. The results of a test similar to Experimental Example 1 are shown below.
6.

Experimental Example 7 Porous hollow fibers made of polyvinyl alcohol with an outer diameter of 510μ, an inner diameter of 320μ, and a porosity of about 50% were arranged one by one so that the density (F) in the length direction was 14 fibers/am, and the warp A hollow fiber notebook shown in FIG. 5 was formed by braiding the hollow fibers into a planar shape using polyester threads of 30 denier (12 filaments) at a density (W) of 1 thread/am. A device was fabricated in which this hollow fiber notebook was placed in a porous inner tube similar to Experimental Example 1, with the number of laminated sheets per unit thickness (1) of 22 sheets/cm and the thickness (T) of 4 cm. The FXr of this laminate is 308, and the effective area is 0.5.
It was 2m2. This laminate has a diameter of 12 cm and a thickness of 2.5 cm.
The device was housed in a cylindrical housing of mm in diameter, and the device shown in FIG. 1 was created.

A separate device was prepared using a hollow fiber sheet with a square density (W) of 0.125 fibers/cm and without a porous outer cylinder. The effective length of the hollow fiber at that time was 7 cm.

The above two types of devices were evaluated using bovine blood heated to 37°C. The blood flow rate was set to 100 mQ/min to the outside of the hollow fiber, and the liquid inside the hollow fiber was increased stepwise to 30 mQ/min.
The amount of J liquid a just before the transmembrane pressure difference sharply increases per minute was defined as the maximum overflow < Q F, , , ).

Experimental Example 8 Hollow fibers made of ethylene hinyl alcohol copolymer having an outer diameter of 225μ and an inner diameter of 175μ were arranged one by one so that the density (F) in the length direction was 24 fibers/am, and the warp was 30 denier. A hollow fiber notebook was formed by braiding the hollow fibers into a planar shape using a polyester yarn (12 filaments) at a density (W) of 1 fiber/am.The hollow fiber sheets were arranged at 4 mm intervals with a diameter of 2 mm. A porous inner tube made of polypropylene with a thickness of 2.5 mm with many holes of 0 mm in diameter (
The number of layers per unit thickness ([) is 45 for a diameter of 1 cm)
The laminate was wound into a cylindrical housing with a diameter of 9 cm and a thickness of 2.5 mm. Then, the device shown in FIG. 1 was created. The FXI of this laminate is 1080, and the loading membrane area is 15 m.
''. On the other hand, a separate apparatus was prepared using a hollow fiber sheet with a density (W) of 0.1 ICl11 without a porous outer cylinder. The effective length of the hollow fiber was gcm.

The above two types of devices were tested using bovine blood heated to 37°C, with blood flowing inside the hollow fibers and dialysate flowing outside the hollow fibers, in accordance with the Artificial Kidney Performance Evaluation Standards (Japan Artificial Organ Association). It is shown in Table-8.

(Effects of the Invention) As described above, the fluid treatment device of the present invention has a large amount of material exchange per unit area through the hollow fibers, almost no fluid channeling or stagnation, and excellent performance. I can demonstrate it. In addition, because it can be produced in a variety of ways, it is inexpensive and compact, so it has the advantage of reducing the amount of blood carried out of the body, especially as a device for processing blood, and reducing the burden on people. There is.

[Brief explanation of the drawing]

FIG. 1 is a sectional view of the fluid treatment device of the present invention, FIGS. 2 and 3 are sectional views showing other points, and FIG. 4 is a sectional view taken along line A-A in FIG. 1. Figure 5 is a perspective view showing a hollow fiber sort wound around a porous inner cylinder;
The figure is a perspective view showing the other side, and FIGS. 7(a) and (b)
is a cross-sectional view of a hollow fiber notebook braided into knots;
Figures to Figures 10 are cross-sectional views of the device with a built-in heat exchanger, Figure 1I is a cross-sectional view of the device with a built-in blood storage tank, and Figures 12 and 13 are cross-sectional views of the device with a built-in heat exchanger and blood storage tank. FIG. 3 is a cross-sectional view of the built-in device. l... Cylindrical housing 3... Porous inner tube 4... Porous outer tube 5... Hollow fiber laminate 6.6°... Partition wall 7... Upper head cover 8. ... Suspension of lower head cover drawing (no change in content) Fig. 1 Fig. Fig. Fig. Fig. Fig. Fig. Fig. Fig. Fig. (b) Patent Application No. 63-254651 No. 2, Title of the invention: Person who corrects hollow fiber type fluid treatment device Relation to the case Patent applicant: 1621-108 Sakazu, Kurashiki City Representative: Rira Shi Co., Ltd. Director Nao Nakamura Contents of the amendment (1) Detailed explanation of the invention in the specification ■ After “polypropylene” on page 11, line 10, “,
Poly-4-methylpentene-1' is inserted. ■Page 16, line 12 r 10”/ (3,OX D
)”≦F×■≦10”/ (0,93X D)’J to’/ (3,0×D)1≦F X ■< to
'/(0,93x D)'j. ■Table 4 on page 25 is corrected as follows.

Claims (1)

[Claims] 1. A laminate of hollow fiber sheets is wound around a porous inner cylinder and housed in a porous outer cylinder, and the laminate of the hollow fiber sheets is housed in a cylindrical housing. The housing is supported by partition walls that close both ends of the housing so as to be open, and a first fluid inlet or outlet that communicates with the inner space of the hollow fiber at the upper end of the housing communicates with the inside of the porous inner cylinder. an upper head cover having a second fluid inlet or outlet communicating with the interior space of the hollow fiber at the lower end of the housing; 1. A hollow fiber type fluid treatment device, characterized in that a second fluid outlet or inlet is provided in the hollow fiber type fluid treatment device.