JPH11137670A - Internal indwelling type purification device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an internal indwelling type purification device which lessens the patient's burden by the extracoporeal circulation of blood at the time of blood purification, improves operability for treatment, is capable of easily executing a blood purification therapy, is small in size and is directly insertable into the intracerebral blood vessels or the parenchymal organs, such as cerebral ventricle and liver. SOLUTION: This internal indwelling type purification device 1 consists of at least one piece of hollow fiber membranes 2 of which the outer peripheral surfaces are contactable with the blood, a supply port 51 which supplies a treating liquid to the internal cavity parts 21 of the hollow fiber membranes 2 and a discharge port 91 which discharges the treating liquid past the internal cavity parts 21 of the hollow fiber membranes 2. The supply port 51 and discharge port 91 described above are preferably disposed on one end side of the hollow fiber membranes 2.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a device for purifying a blood vessel or the like in a body.

[0002]

2. Description of the Related Art Conventionally, blood filtration, hemodiafiltration, hemodialysis and the like have been widely applied to clinical practice as blood purification methods.

[0003] Hemofiltration uses a membrane having pores to remove a substance (toxin substance) by a pressure difference applied between the membranes.
Is a method of removing and moving a blood plasma component containing from the blood side to the other side through the pores of the membrane. Substances that pass through the pores of the membrane (toxins) are regulated by their own size and pore size and allow for selective removal by sieving the membrane. In hemofiltration, it is usually necessary to replenish the patient with a replenisher in which the electrolyte and the like have been adjusted by the amount of water removed by filtration.

[0004] Hemodialysis is a method in which blood is applied to one side through a semipermeable membrane.
On the other hand, a dialysate in which electrolytes and the like are adjusted is flowed, and a toxin substance in blood is removed by utilizing a diffusion phenomenon caused by a difference in concentration of solute (substance) between blood and dialysate at a semipermeable membrane. It is.

[0005] Hemodiafiltration is a therapy in which the above-mentioned hemodialysis and hemofiltration are performed simultaneously, and similarly to hemofiltration, it is usually necessary to replenish the patient with a replenisher.

[0006] Since these blood purification methods are usually therapies in which blood is once taken out of the body and processed, that is, extracorporeal circulation therapy, the burden on the circulatory system is reduced for the patient by reducing the amount of blood circulation in the body. Is big. If the blood flow rate or the amount of solute removal per unit time is set too high, the patient will be overloaded.

[0007] Furthermore, treatment for treatment such as installation of an extracorporeal circulation circuit, priming operation, and handling of a blood circulation device and a dialysate recirculation device are many and complicated.

[0008] Therefore, continuous blood purification therapy for gradually removing toxin substances from patients over a long period of time has been developed by ICU, CC.
U and other intensive care units.

[0009] However, continuous blood purification therapy has a problem that the treatment operation is complicated. In addition, the device is large, and is not suitable for purifying blood in a fine intracerebral blood vessel or the like.

[0010]

SUMMARY OF THE INVENTION An object of the present invention is to reduce the burden of extracorporeal circulation of blood, improve the operability for treatment, and simplify the treatment, especially for the above-mentioned severe patients. An object of the present invention is to provide an in-vivo purifying device capable of performing blood purification therapy.

It is still another object of the present invention to provide an in-vivo purifying apparatus which is small and can purify blood even in complicated and minute blood vessels such as blood vessels in the brain.

It is another object of the present invention to provide an in-vivo purifying apparatus which can be inserted directly into a real organ such as a liver to purify a body fluid such as a tissue fluid.

[0013]

This and other objects are achieved by the present invention which is defined below as (1) to (14).

(1) An in-vivo purifying apparatus for indwelling in a blood vessel and selectively separating and removing a specific substance in blood in the blood vessel, wherein at least one purifying apparatus whose outer peripheral surface can come into contact with blood is provided. A body having a hollow fiber membrane, a supply port for supplying a processing liquid to the inner cavity of the hollow fiber membrane, and an outlet for discharging the processing liquid that has passed through the inner cavity of the hollow fiber membrane. Detention type purification device.

(2) The in-vivo purifying apparatus according to (1), wherein the supply port is provided at one end of the hollow fiber membrane, and the discharge port is provided at the other end of the hollow fiber membrane. .

(3) The in-vivo purifying apparatus according to (1), wherein the supply port and the discharge port are provided at one end of the hollow fiber membrane.

(4) The in-vivo purifying apparatus according to (3), wherein a storage portion for storing the treatment liquid is provided at the other end of the hollow fiber membrane.

(5) The in-vivo purifying apparatus according to the above (3) or (4), further comprising a connecting pipe communicating the supply port or the discharge port with the storage section.

(6) A plurality of the hollow fiber membranes, wherein a part of the hollow fiber membrane and the remaining hollow fiber membrane have different flow directions of the treatment liquid in the inner cavity. The in-vivo purifying device according to any one of (5) and (5).

(7) An in-vivo purifying apparatus for indwelling in a blood vessel and selectively separating / removing a specific substance in blood in the blood vessel, wherein at least one purifying apparatus whose outer peripheral surface can come into contact with blood. An in-vivo purifying apparatus, comprising: a hollow fiber membrane; and an outlet communicating with an inner cavity of the hollow fiber membrane and discharging the specific substance that has passed through the hollow fiber membrane.

(8) The hollow fiber membrane has an inner diameter of 10 to 25.
The in-vivo purifying apparatus according to any one of the above (1) to (7), which is 0 μm.

(9) The hollow fiber membrane has a thickness of 1 to 60 μm.
m. The in-vivo purifying apparatus according to any one of the above (1) to (8), wherein m is m.

(10) The ultrafiltration rate of the hollow fiber membrane is 5 to 5.
The in-vivo purifying apparatus according to any one of the above (1) to (9), which has a flow rate of 300 ml / hr / m ² / mmHg.

(11) The total length of the hollow fiber membrane is 10 to 10
The in-vivo purifying apparatus according to any one of the above (1) to (10), which is 0 cm.

(12) The total membrane area of the hollow fiber membrane is 0.0
The in-vivo purifying apparatus according to any one of the above (1) to (11), which has a size of 5 cm ^{2 to 3} m ² .

(13) An in-vivo purifying apparatus for indwelling in a body and selectively separating / removing a specific substance in a body fluid in the body, wherein at least one hollow fiber whose outer peripheral surface is in contact with the body fluid A membrane, a supply port for supplying a treatment liquid to the inner cavity of the hollow fiber membrane, and an outlet for discharging the treatment liquid passing through the inner cavity of the hollow fiber membrane, wherein the in-vivo indwelling type is provided. Purification device.

(14) An in-vivo purifying device for indwelling in a body and selectively separating / removing a specific substance in a body fluid in the body, wherein at least one hollow fiber whose outer peripheral surface is in contact with the body fluid An in-vivo purifying apparatus, comprising: a membrane; and an outlet for discharging the specific substance that has passed through the hollow fiber membrane through the lumen of the hollow fiber membrane.

[0028]

BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a perspective view of a purifying apparatus according to the present invention.

FIG. 1 is a side sectional view and a cross-sectional view taken along the line AA of a first embodiment of an in-vivo purifying apparatus (in-vivo in-vivo blood purifying apparatus) according to the present invention.

As shown in the figure, an in-vivo purifying apparatus 1 (hereinafter referred to as “apparatus 1”) of the present invention is placed in a blood vessel.
At least one hollow fiber membrane 2 (hollow fiber membrane bundle 3) whose outer peripheral surface is capable of contacting with blood, selectively separating and removing a specific substance in blood in the blood vessel; 2
A supply port 51 for supplying the processing liquid to the inner cavity 21 of the hollow fiber membrane and an outlet 9 for discharging the processing liquid having passed through the inner cavity 21 of the hollow fiber membrane 2.
And 1.

The hollow fiber membrane 2 used in the apparatus 1 of the present invention is a microporous membrane having a large number of pores communicating between the inside and the outside of the membrane, and having a molecular weight cut off of 10,000 to 6
Those which are at 000 daltons are preferred.

The constituent material of the hollow fiber membrane 2 is not particularly limited as long as it has biocompatibility and can be used for blood purification. For example, regenerated cellulose, ethyl cellulose, cellulose acetate, propion Hollow fibers made of synthetic polymer materials such as cellulose, such as acid cellulose, polysulfone, polyacrylonitrile, polymethyl methacrylate, ethylene vinyl alcohol copolymer, polyamide, polypropylene, and polycarbonate are preferred. Further, it can be used by imparting hydrophilicity as required. Further, the surface of the hollow fiber membrane can be coated with a polymer compound having biocompatibility (blood) and used.

Further, in order to bring the hollow fiber membrane 2 into uniform contact with blood in a blood vessel, the hollow fiber membrane 2 may be subjected to a process of imparting elasticity. Examples of such processing include crimping and curling.

The inner diameter of such a hollow fiber membrane 2 is 10 to 2
It is preferably 50 μm, more preferably 50 to 230 μm, even more preferably 70 to 210 μm. If the inner diameter is too small, the pressure applied to the inner wall when the processing liquid flows through the lumen may be excessive. On the other hand, if the inner diameter is too large, the apparatus 1 becomes large, and can be safely inserted into a blood vessel.
It becomes difficult to detain.

The thickness of the hollow fiber membrane 2 is preferably 1 to 60 μm, more preferably 5 to 50 μm, and
0 to 45 μm is more preferable. If the film thickness is too small, the strength of the hollow fiber membrane may be reduced, and if the film thickness is too large, the blood purification device becomes large, making it difficult to safely insert and detain in a blood vessel.

Further, the ultrafiltration rate of the hollow fiber membrane 2 is 5 to 3
It is preferably about 00 ml / hr / m ² / mmHg. If the ultrafiltration rate is too small, the blood purification efficiency may decrease. On the other hand, if the ultrafiltration rate is too large, the amount of water removed from the blood may increase, and the burden on the body may increase.

The total membrane area (membrane area on the outer surface) of the hollow fiber membrane 2 (hollow fiber membrane bundle 3) is determined by the thickness of the blood vessel to be placed,
Although it is appropriately set by the sites and the like, 0.05cm ² ~3m ²
It is preferred that For example, in the case of the inferior vena cava,
0.05 to ³ m ² is preferable, 0.1 to ² m ² is more preferable, and 0.1 to ¹ m ² is further preferable. Further, it is preferable that a 0.05～100Cm ² in the case of using inserted directly into solid organs such as brain blood vessel or ventricle or liver, kidney, more preferably 0.1~50cm ^2, 1~
20 cm ² is more preferred.

Further, the total length of the hollow fiber membrane 2 (hollow fiber membrane bundle 3) is preferably 10 to 100 cm. Especially when applied to the inferior vena cava, it is preferably about 10 to 80 cm,
７０70 cm is more preferred, and 30-60 cm is even more preferred. When it is used by being directly inserted into a cerebral blood vessel or ventricle or a real organ such as liver or kidney, it is preferably about 30 to 100 cm, more preferably 50 to 80 cm. If the hollow fiber membrane bundle 3 is too short, it becomes difficult to secure a membrane area for obtaining a sufficient blood purification action,
If it is too long, it will be difficult to safely insert and place it in a blood vessel.

The hollow fiber membrane 2 is fixed and held by at least one fixing member 8 and, if necessary, a plurality of hollow fiber membranes 2.
Are bundled to form a hollow fiber membrane bundle 3.

The fixing member 8 is formed by curing a resin material near both ends of the hollow fiber membrane 2. Each hollow fiber membrane 2 penetrates the fixing member 8 and communicates with a supply port 51 and a discharge port 91 described later.

The material of the fixing member 8 is not particularly limited, but is preferably made of a non-denatured resin material such as polyurethane or polyester.

A supply port 51 for supplying a treatment liquid to the inner cavity 21 is liquid-tightly joined to the fixing member 8 at one end of the hollow fiber membrane 2. A supply port 5 having a certain volume is formed in the supply port 51. This supply port 5
It functions as a communication means for connecting the supply port 51 and the open end of the hollow fiber membrane 2. Further, it also functions as a distributing means for evenly distributing the processing liquid supplied from the supply port 51 to each hollow fiber membrane 2.

The shape of the supply port 5 is preferably such that the outer diameter gradually changes from the supply port 51 to the end face of the fixing member 8. Thus, the device 1 of the present invention can be safely inserted into and removed from a blood vessel.

The constituent material of the supply port 5 is not particularly limited. For example, a resin material such as polyvinyl chloride, polyethylene, polypropylene, polyurethane, and silicone can be used. Is preferred.

The method of joining the supply port 5 to the fixing member 8 is not particularly limited, and may be formed integrally with the fixing member 8 or a separate member. In the case of a separate member, the bonding method with the fixing member 8 includes bonding with an adhesive, heat fusion, and the like.

Here, the specific substance that passes through the hollow fiber membrane 2 means a substance serving as a disease factor, and examples thereof include urea, ammonia, β ₂ -microglobulin, myoglobin, and creatinine. Further, the treatment liquid means a liquid in which the balance of physiological saline, electrolyte, and the like used for blood purification is adjusted, and examples thereof include a dialysate, an electrolyte, and a replenisher.

On the other hand, a discharge port 91 for discharging the processing liquid having passed through the inner cavity is liquid-tightly joined to the fixing member 8 on the other end side. The discharge port 91 is formed with a discharge port 9 similarly to the supply port 51. The discharge port 9 functions as a communication unit that connects the discharge port 91 and the open end of the hollow fiber membrane 2.

As described above, by providing the supply port 51 at one end of the hollow fiber membrane 2 and providing the discharge port 4 at the other end, the processing liquid passes through the inner cavity 21 in one direction. The pressure loss of the liquid can be suppressed. In addition, the treatment liquid that has come into contact with the blood via the hollow fiber membrane 2 and the blood that has not come into contact with the blood do not mix, so that efficient blood purification can be performed.

The shape of the discharge port 9 is preferably such that the outer diameter gradually changes from the outer diameter at the discharge port 91 to the outer diameter of the end face of the hollow fiber membrane bundle 3 similarly to the supply port 5 described above. . Thus, the device 1 of the present invention can be safely inserted into and removed from a blood vessel.

As the constituent material of the discharge port 9, the same material as that of the supply port 5 can be used, and the discharge port 9 may be made of a material different from that of the supply port.

The joining method with the fixing member 8 is as follows.
The same as the supply port 51 can be used.

Although the case of blood purification has been described above, the present invention is not limited to this.
It can also be used when purifying body fluids such as tissue fluid by inserting a hollow fiber membrane directly into a solid organ such as the liver.

Next, the operation of the device 1 of the present embodiment will be described. When used for hemodialysis or hemodiafiltration, the processing liquid flows into the supply port 5 from the supply port 51. When the supply port 5 is filled with the processing liquid, the processing liquid is supplied to the lumen 21 of the hollow fiber membrane 2 by pressure. The treatment liquid contacts the pores formed in the hollow fiber membrane 2 while passing through the lumen 21 to separate and remove specific substances such as unnecessary substances in blood. Then, it is discharged outside the body through a discharge port 91 formed on the other end side of the hollow fiber membrane 2.

When used for hemofiltration, the treatment liquid is supplied to the outlet 9
After filling the inner cavity 21 with the treatment liquid from at least one of the supply port 1 and the supply port 51, blood filtration is performed. The specific substance that has moved into the lumen 21 of the hollow fiber membrane 2 due to the transmembrane pressure is discharged together with the treatment liquid from at least one of the discharge port 91 and the supply port 51.

Alternatively, the filtrate can be suctioned and discharged from at least one of the discharge port 91 and the supply port 51 by applying a negative pressure to the hollow fiber membrane 2 without using the processing liquid.

FIG. 2 is a longitudinal sectional view, a sectional view taken along line AA and a sectional view taken along line BB showing a second embodiment of the in-vivo purifying apparatus according to the present invention.
It is a line sectional view.

As shown in the figure, in the apparatus 1 of this embodiment, the supply port 51 and the discharge port 91 are joined to one end of the hollow fiber membrane 2 in a liquid-tight manner, and the storage section 7 is joined to the other end. I have.

Further, there is provided a connecting pipe 12 consisting of a hollow pipe for communicating the supply port 51 with the storage section 7.

Hereinafter, only differences from the above-described first embodiment will be described, and description of the same items will be omitted.

One end of the connection pipe 12 is connected to the supply port 51,
The other end is connected to the storage unit 7. Further, it is located near the center of the hollow fiber membrane bundle 3, and near both ends of the connection pipe 12 penetrates the fixing members 8 and 8 and extends substantially parallel to the hollow fiber membrane 2. Thus, the treatment liquid supplied from the supply port 51 can be quickly introduced into the storage unit 7 without passing through the lumen 21 of the hollow fiber membrane 2. In addition, the shear rate of blood on the membrane surface is the largest on the outer peripheral surface of the hollow fiber bundle,
High mass transfer efficiency. Therefore, since the connecting pipe 12 is located near the center of the hollow fiber membrane bundle 3, there is no adverse effect on the blood purification processing efficiency.

The size of the connecting pipe 12 is not particularly limited, but the outer diameter is preferably about 0.5 to 15 mm. If the outer diameter is too small, the supply efficiency of the processing liquid is reduced. If the outer diameter is too large, the size of the device 1 becomes large due to the size of the hollow fiber membrane bundle 3, making it difficult to insert and detain safely in a blood vessel. Become.

As a constituent material of the connecting pipe 12, for example,
The same constituent material as the hollow fiber membrane 2 can be used.

The connecting pipe 12 may be fixedly adhered to the fixing member 8 with an adhesive or the like, or may be formed integrally with the fixing member 8.

The storage section 7 also functions as a distributing means for evenly distributing the processing liquid supplied from the supply port 51 through the connecting pipe 12 to each hollow fiber membrane 2. The shape of the storage section 7 is not particularly limited, but the top 71 on the outer surface is preferably rounded. Thereby, the device 1 can be safely inserted and placed in the blood vessel.

As the constituent material of the storage section 7, the same material as the supply port 51 and the discharge port 91 can be used.

In this embodiment, a supply port 51 and a discharge port 91 are provided at one end of the hollow fiber membrane 2. With such a configuration, it is not necessary to provide an opening for supplying the processing liquid to the apparatus 1 and an opening for discharging the processing liquid to the outside of the apparatus 1, and thus the puncture is performed. The number of holes can be reduced to one, so that tissue damage can be suppressed and the burden and pain on the patient can be reduced.

When the apparatus 1 of the present embodiment is used for hemodialysis and hemodiafiltration, as shown in FIG. 8, a treatment liquid is supplied from the supply port 51 to the storage section 7 through the connection pipe 12. After the storage section 7 is filled with the processing liquid, the processing liquid flows into the lumen 21 of the hollow fiber membrane 2 due to the pressure as shown by the arrow in the figure.

The treatment liquid separates and removes a specific substance from blood through the pores formed in the hollow fiber membrane 2 while passing through the lumen 21. Then, it is removed from the outside of the body through the outlet 9.

In the apparatus 1 of this embodiment, the supply and discharge directions of the processing liquid may be reversed. That is, the treatment liquid can be used so as to enter the storage unit 7 via the lumen 21 of the hollow fiber membrane 2 and then be discharged via the connection pipe 12.

On the other hand, when used for blood filtration, the treatment liquid is filled into the lumen 21 through at least one of the discharge port 91 and the supply port 51, and then blood filtration is performed. The specific substance that has moved into the lumen 21 of the hollow fiber membrane 2 due to the transmembrane pressure is discharged together with the treatment liquid from at least one of the discharge port 91 and the supply port 51.

Alternatively, a negative pressure may be applied to the hollow fiber membrane 2 without using a treatment liquid, and the filtrate may be suctioned and discharged from at least one of the discharge port 91 and the supply port 51.

Next, an embodiment in which a plurality of the hollow fiber membranes 2 are provided and a part of the hollow fiber membrane and the remaining hollow fiber membrane have different flow directions of the treatment liquid in the lumen will be described.

FIG. 3 is a side sectional view, AA line sectional view and BB showing a third embodiment of the in-vivo purifying apparatus according to the present invention.
It is a line sectional view.

In the apparatus 1 of this embodiment, the supply port 51 and the discharge port 91 are liquid-tightly joined to one end of the hollow fiber membrane 2, and the storage section 7 is liquid-tightly joined to the other end.

Hereinafter, only the differences from the above-described first and second embodiments will be described, and description of the same items will be omitted.

As shown in FIG. 3, the supply port 51 communicates with the inner cavity 21 of a part of the hollow fiber membrane 2 in the fixing member 8. This part of the hollow fiber membrane 2 is located near the core of the hollow fiber membrane bundle 3.

When the apparatus 1 of this embodiment is used for hemodialysis or hemodiafiltration, the treatment liquid is first supplied only to the supply port 51 and the inner cavity 21 of a part of the hollow fiber membrane 2 communicating therewith. The supplied treatment liquid comes into contact with blood through the pores formed in the hollow fiber membrane 2 while passing through the inner cavity 21 to separate and remove a specific substance from the blood. And it flows into the storage part 7 joined to the other end side. Then, the treatment liquid flows from the other end side joined to the storage unit 7 into the remaining hollow fiber membrane 2 ′, that is, into the lumen 21 ′ of the hollow fiber membrane 2 ′ which does not communicate with the supply port 51, and again flows into the hollow fiber membrane 2 ′. The specific substance is separated / removed from the blood through the pores indicated by 'and discharged from the discharge port 91.

As in the present embodiment, the treatment liquid is supplied to a part of the hollow fiber membranes 2 from the supply port 51 and flows into the storage section 7 while purifying the blood. Inflow and blood purification. Thereby, the core portion and the outer peripheral portion of the hollow fiber membrane bundle 3 can be used evenly, which is particularly effective for hemodiafiltration.

Further, since the supply port 51 and the discharge port 91 are provided at one end (the same side) of the hollow fiber membrane 2,
As in the embodiment, the burden on the patient can be reduced.

In this embodiment, the supply and discharge directions of the processing liquid may be reversed. That is, it is also possible to use the treatment liquid such that it enters the storage section 7 via the lumen 21 ′ of the hollow fiber membrane 2 ′ and then is discharged via the lumen 2.

On the other hand, when used for blood filtration, the treatment liquid is filled into the lumen 21 through at least one of the discharge port 91 and the supply port 51, and then the blood filtration is performed. The specific substance that has moved into the lumen 21 of the hollow fiber membrane 2 due to the transmembrane pressure is discharged together with the treatment liquid from at least one of the discharge port 91 and the supply port 51.

Alternatively, a negative pressure may be applied to the hollow fiber membrane 2 without using the treatment liquid, and the filtrate may be sucked and discharged from at least one of the discharge port 91 and the supply port 51.

FIG. 4 shows a fourth embodiment of the in-vivo purifying apparatus according to the present invention.
It is a side sectional view, an AA line sectional view, and a BB line sectional view showing an example.

Hereinafter, only differences from the above-described first to third embodiments will be described, and description of the same items will be omitted.

As shown in FIG. 4, in the apparatus 1 of this embodiment, the supply port 51 and the discharge port 91 are liquid-tightly joined to one end of the hollow fiber membrane bundle 3. The supply port 51 and the discharge port 91 are each in communication with the lumen 21 of the hollow fiber membrane 2 in the fixing member 8. The supply port 51 and the discharge port 91 are separated by the partition wall 4. Therefore, the supply port 51 and the discharge port 91 divide the hollow fiber membrane bundle 3 into two. Thereby, the supply port 5
A part of the hollow fiber membrane 2 communicating with 1 and the remaining hollow fiber membrane 2 ′ communicating with the outlet 91 have opposite flow directions of the treatment liquid. A reservoir 7 is liquid-tightly joined to the other end of the hollow fiber membrane bundle 3.

As a constituent material of the partition wall 4, the supply port 5
The same material as that of 1 and the like can be used.

Further, a part of the hollow fiber membrane 2 and the remaining hollow fiber membrane 2 ′ may be equally divided as in this embodiment, or may be unevenly divided.

When the apparatus 1 of this embodiment is used for hemodialysis and hemodiafiltration, the treatment liquid flows into the lumen 21 of the hollow fiber membrane 2 from the supply port 51. While separating / removing a specific substance from the blood through the pores formed in the hollow fiber membrane 2, the specific substance flows into the reservoir 7 joined to the other end. Then, the treatment liquid flows into the lumen 21 ′ of the remaining hollow fiber membrane 2 ′ communicating with the storage part 7, and again separates and removes a specific substance from blood through the pores of the hollow fiber membrane 2 ′. Are discharged from the discharge port 91.

When used for hemofiltration, the treatment liquid is supplied to the outlet 9
After filling the lumens 21 and 21 ′ from at least one of the inlet port 1 and the supply port 51, the treated liquid and the filtrate filtered from the blood through the hollow fiber membranes 2 and 2 ′ are supplied to the discharge port 91 and the supply port 91. It is discharged from at least one of the ports 51.

Alternatively, a negative pressure is applied to at least one of the hollow fiber membranes 2 and 2 ′ without using a treatment liquid.
The filtrate can be sucked and discharged from at least one of the discharge port 91 and the supply port 51.

Next, an embodiment used only for hemofiltration will be described. FIG. 5 is a side sectional view, a sectional view taken along the line AA and a sectional view showing a fifth embodiment of the in-vivo purifying apparatus according to the present invention.
It is a B sectional view.

The device 1 of the present embodiment is to be placed in a blood vessel and selectively separates and removes a specific substance in blood in the blood vessel. It is characterized by having a hollow fiber membrane 2 and an outlet 91 for communicating with the inner cavity 21 of the hollow fiber membrane 2 and discharging a specific substance that has passed through the hollow fiber membrane 2.

The discharge port 91 is joined to one end of the hollow fiber membrane 2 in a liquid-tight manner, and a closing portion 75 is provided at the other end. The other end of the hollow fiber membrane 2 is closed at the closing portion 75. Instead of the closing portion 75, a storage portion 7 communicating with the open end of the hollow fiber membrane 2 may be joined.

When performing blood filtration, the hollow fiber membrane 2 is inserted into a predetermined blood vessel, and is sucked through the outlet 91. Since the other end side of the hollow fiber membrane 2 is closed by the storage part 7 or the fixing member 8, the lumen 21 is in a negative pressure state. As a result, a pressure difference is generated between the inside and the outside of the hollow fiber membrane 2, blood filtration is performed, and plasma containing a specific substance passes through the hollow fiber membrane 2. The specific substance is removed by sucking and discharging the same through the opening 56 to purify the blood.

Alternatively, the processing solution is filled into the inner cavity 21 of the hollow fiber membrane 2 through the discharge port 91 and subjected to blood filtration. Suction and discharge.

As described above, in the case of hemofiltration, there is no need to circulate the treatment liquid, so that even if the discharge port 91 also serves as the supply port 51, sufficient blood purification efficiency can be obtained.

FIG. 6 shows a sixth embodiment of the in-vivo purifying apparatus according to the present invention.
It is a sectional side view showing an example.

The apparatus 1 has one hollow fiber membrane 2, a discharge port 91 communicating with an opening at one end of the hollow fiber membrane 2, and a closed end 75 for closing the hollow fiber membrane 2 at the other end. And

When performing hemofiltration, first, the hollow fiber membrane 2
Is inserted into a predetermined blood vessel, and is sucked through the outlet 91. Since the other end of the hollow fiber membrane 2 is closed by the closed end 75, the lumen is in a negative pressure state. As a result, a pressure difference is generated between the inside and the outside of the hollow fiber membrane 2, blood filtration is performed, and plasma containing a specific substance passes through the hollow fiber membrane 2. This is connected to the outlet 91
The specific substance is removed by suctioning and discharging the blood, thereby purifying the blood.

Alternatively, the processing solution is filled into the inner cavity 21 of the hollow fiber membrane 2 from the discharge port 91, and after the blood filtration is performed, the processing liquid containing the specific substance that has passed through the hollow fiber membrane 2 is discharged to the discharge port 91. Suction and discharge from.

As described above, in the case of hemofiltration, it is not necessary to circulate the treatment liquid, so that even if the discharge port 91 also serves as the supply port 51, sufficient blood purification efficiency can be obtained.

Next, an embodiment used only for hemodialysis will be described. FIG. 7 is a side sectional view showing a seventh embodiment of the in-vivo purifying apparatus according to the present invention.

The apparatus 1 has one hollow fiber membrane 2, an opening of a supply port 51 and an outlet 91 at one end of the hollow fiber membrane 2, and a hollow fiber membrane 2 at the other end. And a closing end 75 that closes the end.

A tube 35 is provided in the lumen 21 of the hollow fiber membrane 2 to form a double tube structure.

One of the hollow fiber membrane 2 and the inner tube 35 is connected to the supply port 51 of the treatment liquid, and the other end is connected to the discharge port 91. Thereby, hemodialysis can be performed efficiently without the treatment liquids before and after the treatment being mixed with each other.

In this embodiment, one end of the tube 35 is connected to a supply port 51 for supplying a processing liquid, and the hollow fiber membrane 2 is connected to a discharge port 91.

The opening end 351 at the other end of the tube 35 is
Preferably, it is located near the closed end 75. Thus, the supply of the processing liquid from the opening end 351 is not hindered.

The outer diameter of the tube 35 is not particularly limited, but is preferably about 30 to 80% of the inner diameter of the hollow fiber membrane 2. If the outer diameter of the tube 35 is too large, the space between the tube 35 and the hollow fiber membrane 2 becomes narrow, and the amount of treatment liquid that can pass therethrough decreases, making it difficult to perform sufficient hemodialysis. On the other hand, if the outer diameter is too small, the inner diameter of the tube 35 must be small, and it becomes difficult to efficiently supply the processing liquid.

As a constituent material of such a tube 35, the same material as that of the hollow fiber membrane 2 can be used. Further, the tube 35 may be formed simultaneously with the production of the hollow fiber membrane 2, or may be produced separately from the hollow fiber membrane 2 and inserted into the lumen 21 of the hollow fiber membrane 2.

In the case of performing hemodialysis, the processing solution is supplied to the supply port 5
1 through the tube 35, and the processing liquid is supplied to the lumen 21 of the hollow fiber membrane 2 from the open end 351.

Then, the treatment liquid comes into contact with blood through the hollow fiber membrane 2 and is discharged outside the body through the outlet 91 while passing between the inside of the hollow fiber membrane 2 and the outside of the tube 35 while performing dialysis. You.

In the present embodiment, the tube 35 is connected to the supply port 51, but may be connected to the discharge port 91. Further, a side hole may be provided near the opening end 351 of the tube 35.

Although the in-vivo purifying apparatus according to the present invention has been described with reference to the illustrated embodiments, the present invention is not limited to these embodiments. For example, in each of the above-described embodiments, the supply port and the discharge port may be used. May be interchanged with each other.

[0114]

Next, specific examples of the present invention will be described.

1. Production of in-vivo purification device (Production Example 1)

An in-vivo in-vivo purifying apparatus (in-vivo in-vivo purifying apparatus) having the structure shown in FIG. 1 was produced. The following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 26 μm Total length: 50 cm Ultrafiltration rate: 12 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium, membrane area: 0.19 m ²

Both ends of the hollow fiber membrane 2 were fixed with polyurethane fixing members 4 to form a hollow fiber membrane bundle 3. Next, a supply port 51 made of polyurethane was joined to one end of the hollow fiber membrane 2 (hollow fiber membrane bundle 3) in a liquid-tight manner, and a discharge port 91 was joined to the other end.

(Preparation Example 2) An in-dwelling blood purification apparatus was prepared in the same manner as in Preparation Example 1, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 45 μm Total length: 60 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 0.15 m ²

(Preparation Example 3) An in-dwelling blood purification apparatus having a configuration shown in FIG. 2 was prepared. The following was used as the hollow fiber membrane 2.

Inner diameter: 100 μm Thickness: 15 μm Overall length: 30 cm Ultrafiltration rate: 8 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 0.13 m ²

Both ends of the hollow fiber membrane 2 were fixed with polyurethane fixing members 4 to form a hollow fiber membrane bundle 3. Next, a supply port 51 and a discharge port 91 made of polyurethane were joined to one end of the hollow fiber membrane bundle 3, and the storage section 7 was joined to the other end.

The connecting pipe 12 made of polyurethane is connected to the supply port 5
1 and is arranged near the center axis of the hollow fiber membrane bundle 3 in parallel with the hollow fiber membrane 2, and penetrates the fixing member 4.

(Preparation Example 4) An in-dwelling blood purification device was prepared in the same manner as in Preparation Example 3, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 250 μm Film thickness: 40 μm Total length: 80 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 0.26 m ²

(Preparation Example 5) An in-dwelling blood purification apparatus having a configuration shown in FIG. 3 was prepared. The following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Thickness: 26 μm Total length: 50 cm Ultrafiltration rate: 12 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 0.19 m ²

Both ends of the hollow fiber membrane 2 were fixed with polyurethane fixing members 4 to form a hollow fiber membrane bundle 3. Next, a supply port 51 and a discharge port 91 made of polyurethane were joined to one end of the hollow fiber membrane bundle 3, and a storage section 7 was joined to the other end.

In this example, the supply port 51 is configured to communicate with the hollow fiber membrane 2 near the center of the hollow fiber membrane 3.

(Preparation Example 6) An in-dwelling blood purification device was prepared in the same manner as in Preparation Example 5, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 20 μm Total length: 50 cm Ultrafiltration rate: 54 ml / hr / m ² / mmHg Material: polymethyl methacrylate Membrane area: 0.16 m ²

(Production Example 7) An in-dwelling blood purification apparatus having a configuration shown in FIG. 4 was produced. The following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Thickness: 26 μm Total length: 40 cm Ultrafiltration rate: 12 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 0.16 m ²

Both ends of the hollow fiber membrane 2 were fixed by polyurethane fixing members 4 to form a hollow fiber membrane bundle 3. Next, a supply port 51 and a discharge port 91 made of polyurethane were joined to one end of the hollow fiber membrane bundle 3 in a liquid-tight manner, and the storage section 7 was joined to the other end.

In this example, the supply port 51 and the discharge port 9 were used.
1 is constituted by dividing one port joined to one end side of the hollow fiber membrane bundle 3 into two by a partition wall 4 projecting from the fixing member.

(Preparation Example 8) An in-dwelling blood purification device was prepared in the same manner as in Preparation Example 7, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 45 μm Total length: 50 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 0.15 m ²

(Manufacturing Example 9) An in-dwelling blood purification apparatus having the structure shown in FIG. 5 was manufactured. The following was used as the hollow fiber membrane 2.

Inner diameter: 80 μm Thickness: 20 μm Total length: 60 cm Ultrafiltration rate: 18 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 0.45 m ²

Both ends of the hollow fiber membrane 2 were fixed with polyurethane fixing members 4 to form a hollow fiber membrane bundle 3. Next, a polyurethane outlet 91 was joined to one end of the hollow fiber membrane bundle 3 in a liquid-tight manner, and a reservoir 7 was joined to the other end. In this example, the other end of the hollow fiber membrane 2 is closed by the fixing member 8.

(Preparation Example 10) An in-dwelling blood purification device was prepared in the same manner as in Preparation Example 9, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 45 μm Overall length: 60 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 0.22 m ²

(Preparation Example 11) An in-dwelling blood purification apparatus having a configuration shown in FIG. 6 was prepared. The following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Thickness: 26 μm Total length: 100 cm Ultrafiltration rate: 12 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 7.6 cm ²

A discharge port 91 is connected to one end of the hollow fiber membrane 2. A closed end 75 made of polyurethane was formed on the other end side, and the hollow fiber membrane 2 was closed.

(Preparation Example 12) An in-dwelling blood purification device was prepared in the same manner as in Preparation Example 11, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Film thickness: 45 μm Total length: 80 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 7.3 cm ²

(Production Example 13) An in-dwelling blood purifying apparatus having the structure shown in FIG. 7 was produced. The following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Thickness: 26 μm Total length: 100 cm Ultrafiltration rate: 12 ml / hr / m ² / mmHg Material: regenerated cellulose of copper ammonium Membrane area: 7.6 cm ² Tube outer diameter: 100 μm (with respect to hollow fiber membrane inner diameter) Ratio: 50
%) Tube material: polyurethane

A supply port 51 and a discharge port 91 made of polyurethane are joined to one end of the hollow fiber membrane 2. A closed end 75 made of polyurethane was formed on the other end, and the other end of the hollow fiber membrane 2 was closed.

One end of the polyurethane tube 35 was connected to the supply port 51, and was arranged near the central axis of the hollow fiber membrane 2 in parallel with the hollow fiber membrane 2. The open end 351 at the other end of the tube 35 is located near the closed end 75.

(Production Example 14) An in-dwelling blood purification device was produced in the same manner as in Production Example 13, except that the following was used as the hollow fiber membrane 2.

Inner diameter: 200 μm Thickness: 45 μm Total length: 100 cm Ultrafiltration rate: 480 ml / hr / m ² / mmHg Material: polysulfone Membrane area: 8.7 cm ² Tube outer diameter: 120 μm (to inner diameter ratio of hollow fiber membrane: 60)
%) Tube material: polyurethane

[0155] 2. Evaluation of blood purification performance (Experimental example 1)

The blood purification performance was examined by incorporating each of the intravascular infusion blood purification devices produced in the above Production Examples 1 to 8 into the experimental circuit shown in FIG.

First, bovine blood 20 whose urea nitrogen concentration was adjusted to 100 mg / dl was placed in bovine blood container 22, kept at 37 ° C., and continuously stirred.

[0158] The indwelling blood purification apparatus 1 prepared in each of the above-mentioned preparation examples is placed in a cylindrical container 15 having an inner diameter of 3 cm having a dialysate inlet 18, a dialysate outlet 19, a bovine blood inlet 16, and a bovine blood outlet 17. did.

The bovine blood container 22 and the bovine blood inlet 16 were connected by a bovine blood circuit 23, and the bovine blood outlet 17 and the bovine blood container 22 were connected by a bovine blood circuit 27 to form a circulation path. In addition, the supply port 51 of the in-dwelling blood purification device 1
The dialysate container 31 and the dialysate container 31 were connected by a dialysate circuit 33, and the outlet 91 and the dialysate collection container 39 were connected by a dialysate circuit 36. The following was used as the dialysate.

[0160]

The bovine blood circuit 23 is provided with a pump 25 for transmitting bovine blood, the dialysate circuit 33 is provided with a pump 34 for transmitting dialysate, and the dialysate circuit 36 is further provided with a pump 34. A pump 37 for collecting dialysate is provided.

After the intravascular blood purification apparatus 1 and the entire circuit were filled with the dialysate, the circulation of the dialysate was started.

Hemodialysis Experiments in the hemodialysis flow range were performed as follows.

The flow rate of bovine blood is set to 1000 by the pump 25.
ml / min. Further, the supply rate of the dialysate is 50 ml / min by the pump 34, and the discharge rate of the dialysate is 55 ml / min by the pump 37, that is, the filtration rate from the blood is 5 ml.
/ Min.

Ten minutes after the start of the circulation of the dialysate, the discharged dialysate was sampled, and the clearance was calculated from the urea nitrogen concentration. The clearance was calculated by the following equation (1).

Clearance = concentration in discharged dialysate / concentration in bovine blood before dialysis × dialysate outflow rate (1)

[0167]

[Table 1]

The sum of the dialysate volume in the dialysate container 31 and the dialysate collection container 39 and the dialysate container 3 before the start of circulation.
The amount of water removal was determined from the difference from the total amount of dialysate 30 in 1.

Hemodiafiltration Experiments in the flow area of hemodiafiltration were performed as follows.

The flow rate of the bovine blood was set to 1000 by the pump 25.
ml / min. Further, the supply rate of the dialysate is set to 50 ml / min by the pump 34, the discharge rate of the dialysate is set to 60 ml / min by the pump 37, and the filtration flow rate from the blood is set to 10 ml / min.
Set to min.

The dialysate discharged 10 minutes after the start of circulation of the dialysate was sampled, and the clearance was calculated from the urea nitrogen concentration. The clearance was calculated by the above equation (1).

The sum of the dialysate volume in the dialysate container 31 and the dialysate collection container 39 and the dialysate container 3 before the start of circulation.
The amount of water removal was determined from the difference from the total amount of dialysate 30 in 1.
The results are shown in Table 1.

Hemofiltration Experiments in the hemodiafiltration flow regime were performed as follows.

The flow rate of the bovine blood was set to 1000 by the pump 25.
ml / min. The pump 34 sets the dialysate supply rate to 0 ml / min, the pump 37 sets the filtrate discharge rate to 10 ml / min, and the filtration flow rate from the blood is 10 ml / min.
Set to.

The dialysate was supplied to the bovine blood container 22 at a rate of 5 ml / min for replenishment (the supply circuit was not shown).

The filtrate discharged 10 minutes after the start of circulation was sampled, and the urea nitrogen clearance was calculated. The clearance was calculated by the following equation (2).

Clearance = concentration of filtrate outlet ÷ concentration of bovine blood × filtrate flow rate (2)

Also, the sum of the dialysate volume in the dialysate container 31 and the dialysate collection container 39 and the dialysate container 3 before the start of circulation.
The amount of water removal was determined from the difference from the total amount of dialysate 30 in 1.
Table 1 shows the results.

(Experimental Example 2) Each of the in-vivo blood purification devices prepared in Preparation Examples 13 and 14 was incorporated in an experimental circuit shown in FIG. 9 to adjust the supply flow rate of the dialysate to 0.04 ml / d.
The blood purification (hemodialysis) performance was examined in the same manner as in Experimental Example 1 except that the min was set. Table 1 shows the results.

(Experimental Example 3) Each of the in-vivo blood purification devices produced in Production Examples 9 and 10 was incorporated in an experimental circuit shown in FIG. 10 to examine the blood filtration performance.

First, the bovine blood 20 prepared so that the concentration of urea nitrogen becomes 100 mg / dl is put into the bovine blood container 22 and
The mixture was kept at ℃ and continuously stirred.

The blood purification apparatus 1 for indwelling in a blood vessel prepared in each of the above-mentioned preparation examples was set in a cylindrical container 15 having an inner diameter of 3 cm and having a filtrate outlet 41, a bovine blood inlet 16, and a bovine blood outlet 17.

The bovine blood container 22 and the bovine blood inlet 16 were connected by a bovine blood circuit 23, and the bovine blood container 22 and the bovine blood outlet 17 were connected by a bovine blood circuit 27 to form a circulation path. In addition, the outlet 91 of the indwelling blood purifier 1 and the filtrate collecting container 49 are connected by the filtrate circuit 46. The bovine blood circuit 23 is provided with a pump 25 for sending bovine blood, and the filtrate circuit 46 is provided with a pump 40 for sending filtrate and treatment liquid.

After the inside of the blood purification apparatus 1 and the whole filtrate circuit 46 were filled with physiological saline, blood filtration was started.

The flow rate of bovine blood was set to 1000 by the pump 25.
ml / min. The flow rate of the filtrate was set to 30 ml / min by the pump 40. The dialysate was supplied to the bovine blood container 22 at 25 ml / min for replenishment (supply circuit not shown).

[0186] Ten minutes after the start of blood filtration, the filtrate was sampled from the filtrate outlet, and the urea nitrogen clearance was calculated. The clearance is calculated by the above equation (2). Table 1 shows the results.

(Experimental Example 4) The in-dwelling blood purification apparatus prepared in Preparation Example 11 was incorporated in the experimental circuit shown in FIG. 10, the flow rate of the filtrate was set to 0.04 ml / min, and 100 minutes from the start of circulation. Blood purification (hemofiltration) performance was examined in the same manner as in Experimental Example 3 except that the filtrate discharged after the elapse was sampled. Table 1 shows the results.

(Experimental Example 5) The in-blood vessel-purified blood purification apparatus produced in Production Example 12 was incorporated in an experimental circuit shown in FIG. 10, the flow rate of the filtrate was set to 0.4 ml / min, and 100 minutes from the start of circulation. Blood purification (hemofiltration) performance was examined in the same manner as in Experimental Example 3 except that the filtrate discharged after the elapse was sampled. Table 1 shows the results.

From these results, it was found that all of the intravascular indwelling blood purifying devices of the respective production examples exhibited sufficient blood purifying performance by a simple operation.

[0190]

As described above, according to the in-vivo purifying apparatus of the present invention, since the body fluid such as blood does not circulate outside the body, the burden on the patient can be greatly reduced. In addition, operability during blood purification is improved, and prompt and accurate treatment can be performed, so that effective treatment can be performed even for serious patients entering an ICU, CCU, or the like.

Further, since the device is small, it is possible to purify body fluids by directly inserting it into a cerebral blood vessel, a cerebral ventricle or a parenchymal organ such as the liver, so that the range of options as therapeutic means can be expanded. .

In addition, the bedside space is not occupied widely, and does not hinder other concurrent treatments.

[Brief description of the drawings]

FIG. 1 is a side sectional view and an AA line sectional view showing a first embodiment of an in-vivo purifying apparatus according to the present invention.

FIG. 2 is a side sectional view, an AA line sectional view and a BB line sectional view showing a second embodiment of the in-vivo purifying apparatus of the present invention.

FIG. 3 is a side sectional view, a sectional view taken along line AA and a sectional view taken along line BB of a third embodiment of the in-vivo purifying apparatus according to the present invention.

FIG. 4 is a side sectional view, an AA line sectional view, and a BB line sectional view showing a fourth embodiment of the in-vivo purifying apparatus according to the present invention.

FIG. 5 is a side sectional view, an AA sectional view, and a BB sectional view showing a fifth embodiment of the in-vivo purifying apparatus of the present invention.

FIG. 6 is a side sectional view showing a sixth embodiment of the in-vivo purifying apparatus according to the present invention.

FIG. 7 is a side sectional view showing a seventh embodiment of the in-vivo purifying apparatus according to the present invention.

FIG. 8 is a longitudinal sectional view showing a usage state of the in-vivo purifying apparatus shown in FIG.

FIG. 9 is a schematic diagram of an experimental circuit used in a test example in an example.

FIG. 10 is a schematic diagram of an experimental circuit used in a test example in an example.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 In-vivo purifying apparatus 2 Hollow fiber membrane 2 'Hollow fiber membrane 21 Inner cavity 21' Inner cavity 3 Hollow fiber membrane bundle 35 Tube 351 Open end 4 Partition wall 5 Supply port 51 Supply port 7 Storage section 71 Top section 75 Closure Part 8 fixing member 9 discharge port 91 discharge port 12 connecting pipe 15 cylindrical container 16 bovine blood inlet 17 bovine blood outlet 18 dialysate inlet 19 dialysate outlet 20 bovine blood 22 bovine blood container 23 bovine blood circuit 25 pump 27 bovine blood circuit 30 Dialysate 31 dialysate container 33 dialysate circuit 34 pump 36 dialysate circuit 37 pump 39 dialysate collection container 40 pump 41 filtrate outlet 46 filtrate circuit 49 filtrate collection container

Claims (14)

[Claims] 1. An in-vivo purifying apparatus for indwelling in a blood vessel and selectively separating and removing a specific substance in blood in the blood vessel, wherein at least one hollow body having an outer peripheral surface capable of contacting blood. A fiber membrane, a supply port for supplying a processing liquid to the inner cavity of the hollow fiber membrane, and an outlet for discharging the processing liquid that has passed through the inner cavity of the hollow fiber membrane. Type purification device. 2. The in-vivo purifying apparatus according to claim 1, wherein the supply port is provided at one end of the hollow fiber membrane, and the discharge port is provided at the other end of the hollow fiber membrane. 3. The in-vivo purifying apparatus according to claim 1, wherein the supply port and the discharge port are provided at one end of the hollow fiber membrane. 4. The in-vivo purifying apparatus according to claim 3, wherein a storage portion for storing the treatment liquid is provided at the other end of the hollow fiber membrane. 5. The in-vivo purifying apparatus according to claim 3, further comprising a connecting pipe that communicates the supply port or the discharge port with the storage section. 6. The hollow fiber membrane according to claim 3, further comprising a plurality of said hollow fiber membranes, wherein a part of said hollow fiber membrane and a remaining hollow fiber membrane have different flow directions of said treatment liquid in said lumen. The in-vivo purifying device according to any one of the above. 7. An in-vivo purifying apparatus for indwelling in a blood vessel and selectively separating and removing a specific substance in blood in the blood vessel, wherein at least one hollow body having an outer peripheral surface capable of contacting blood. An in-vivo purifying apparatus, comprising: a fiber membrane; and an outlet for discharging the specific substance that has passed through the hollow fiber membrane through the lumen of the hollow fiber membrane. 8. The hollow fiber membrane has an inner diameter of 10 to 250 μm.
The in-vivo purifying device according to any one of claims 1 to 7, wherein the purifying device is: 9. The in-vivo purifying apparatus according to claim 1, wherein the thickness of the hollow fiber membrane is 1 to 60 μm. 10. The ultrafiltration rate of the hollow fiber membrane is 5 to 30.
Claims 1 a 0ml / hr / m ² / mmHg body indwelling purifying apparatus according to any one of 9. 11. The hollow fiber membrane has a total length of 10 to 100 cm.
The in-vivo purifying device according to any one of claims 1 to 10, which is: 12. The hollow fiber membrane has a total membrane area of 0.05 cm.
^The in-vivo purifying device according to any one of claims 1 to 11, which has a size of ² to ³ m2. 13. An in-vivo purifying device for indwelling in a body and selectively separating / removing a specific substance in a body fluid in the body, wherein at least one hollow fiber membrane whose outer peripheral surface is in contact with the body fluid. And a supply port for supplying a treatment liquid to the inner cavity of the hollow fiber membrane; and an outlet for discharging the treatment liquid passing through the inner cavity of the hollow fiber membrane. apparatus. 14. An indwelling purifying device for indwelling in a body and selectively separating / removing a specific substance in a body fluid in the body, wherein at least one hollow fiber membrane whose outer peripheral surface is in contact with the body fluid. And a discharge port for discharging the specific substance that has passed through the hollow fiber membrane and communicated with the inner cavity of the hollow fiber membrane.