JPH06237993A - Fluid supply device - Google Patents

Abstract

PURPOSE:To enable the execution of a heat exchange and gas exchange with one exchanger by having a vessel for storing liquid for executing the heat exchange, a temp. control means for regulating a liquid temp., a liquid feed means for feeding the liquid, a gas supply means for supplying the gas for executing the gas exchange and a confluent part where the liquid and the gas join. CONSTITUTION:This fluid supply device 1 has the vessel 2 in which the liquid for the heat exchange is stored. The liquid in the vessel 2 is kept at a desired temp. by the temp. control means. The liquid in the vessel 2 is supplied by the liquid feed means 5 to the confluent part 7 and the gas for the gas exchange is supplied by the gas supply means 6 to the confluent part 7. For example, air bubbles are incorporated into the liquid in the confluent part 7 and this liquid is supplied through a tubular body 71 to the inflow part 141 of an artificial lung 10. The heat exchange and the gas exchange are executed between the working fluid and the blood supplied from a blood inflow port 134 within the artificial lung 10. The working fluid discharged from an outflow part 151 is introduced through the tubular body 81 into a chamber 82 for sepn. of the gas from the solid where the air bubbles are removed. The liquid is recovered in the vessel 2.

Description

Detailed Description of the Invention

[0001]

FIELD OF THE INVENTION The present invention relates to a fluid supply device for supplying a working fluid to a heat and gas exchanger.

[0002]

2. Description of the Related Art For example, an extracorporeal blood circulation circuit for performing extracorporeal circulation of blood during heart surgery or the like includes an artificial lung (gas exchanger) for oxygenating and decarbonating blood and a temperature of blood. A heat exchanger for adjustment is installed. After cooling or heating the blood introduced to the outside of the body by the heat exchanger, oxygen is added and decarbonation is performed.

However, in such an extracorporeal blood circulation circuit, since the heat exchanger and the artificial lung are separately installed, the circuit configuration becomes complicated and the priming amount of blood in the circuit also increases. There's a problem.

As a solution to such a problem, the applicant of the present invention has filed a patent application for an invention of a heat and gas exchanger having both a heat exchange function and a gas exchange function on February 15, 1993. .

Further, for example, for an emergency patient, a simple device provided in an ambulance can be used, and as a high-priority treatment, blood having an artificial lung and not having a heat exchanger is used. The extracorporeal circulation circuit may only perform gas exchange with the patient's blood, but when performing gas exchange and heat exchange for open heart surgery in the hospital thereafter, a heat exchanger is used in the blood extracorporeal circulation circuit. Since it cannot be used additionally, it is necessary to replace it with a blood extracorporeal circulation circuit having both an artificial lung and a heat exchanger.

However, in this case, the extracorporeal blood circulation must be interrupted when exchanging the extracorporeal blood circulation circuit, and it takes time and labor to exchange the extracorporeal blood circulation circuit, and in particular, quick response is prioritized. Disadvantageous for urgent patients,
In addition, the new circuit must be primed again with the patient's blood, which increases the amount of priming.

Further, even during the open-heart surgery, changing the pattern of blood treatment, for example, gas exchange and heat exchange (cooling) are initially performed, but the heat exchange is interrupted midway and only gas exchange is performed. After that, it may be switched to perform heat exchange (heating) again.

As described above, conventionally, in the blood extracorporeal circulation circuit, gas exchange and heat exchange are selectively performed by a simple device, that is, either one or both of gas exchange and heat exchange is performed depending on the case. The development of a system that can be performed by

[0009]

SUMMARY OF THE INVENTION An object of the present invention is to provide a fluid supply device capable of supplying a working fluid to a heat and gas exchanger capable of performing heat exchange and gas exchange with one exchanger. To provide.

[0010]

Such an object is achieved by the present invention (1) described below. Also, (2)-
(8) is preferred.

(1) A fluid supply device for supplying a working fluid to a heat and gas exchanger having both a heat exchange function and a gas exchange function, the container storing a liquid for heat exchange, and the container for storing the liquid. It has a temperature adjusting means for adjusting the temperature, a liquid feeding means for feeding the liquid, a gas supply means for supplying a gas for gas exchange, and a confluence section for converging the liquid and the gas. A fluid supply device, wherein at least one of the liquid and the gas is supplied to the heat and gas exchanger.

(2) The fluid supply device according to the above (1), wherein the confluence section is composed of a mixing means for mixing the liquid and the gas.

(3) The fluid supply device according to (2), wherein the mixing means mixes the gas in the liquid in the form of bubbles.

(4) The fluid supply device according to the above (1), wherein the confluence part is constituted by a flow path changing means capable of selectively supplying the liquid and the gas.

(5) The fluid supply device according to (4), wherein the flow path changing means is configured to alternately supply the liquid and the gas to the heat and gas exchanger.

(6) The fluid supply device according to any one of (1) to (5) above, wherein the ratio of liquid to gas supplied to the heat and gas exchanger can be set in the range of 1: 0 to 0: 1. .

(7) The above (1) to (1), which has a working fluid recovery line for recovering the working fluid from the heat and gas exchanger.
The fluid supply device according to any one of (6).

(8) The fluid supply device according to (7), wherein the working fluid recovery line is configured to return at least a liquid of the recovered working fluid to the container.

[0019]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The fluid supply device of the present invention will be described in detail below with reference to the preferred embodiments shown in the accompanying drawings.

FIG. 1 is a circuit configuration diagram schematically showing a configuration example of a fluid supply device of the present invention. The fluid supply apparatus 1 of the present invention shown in the same figure is an artificial lung with a heat exchanger (hereinafter simply referred to as “artificial lung”) 10 as a heat and gas exchanger having both a heat exchange function and a gas exchange function. Is a device for supplying a working fluid to the. The fluid supply device 1 includes a container 2 that stores a liquid for heat exchange in the artificial lung 10.
have. A liquid such as water or an aqueous solution is stored in the container 2.

Further, the container 2 is provided with temperature control means 3 for controlling the temperature of the liquid. The temperature adjusting means 3 includes a heating device (heater) 31 installed at the bottom of the container 2 and a cooling device (cooler) 32 installed at the side of the container 2.
It is composed of a temperature sensor 35 immersed in the liquid in the container 2 and a control means 36 composed of a microcomputer.

The heat transfer tube 33 of the heating device 31 penetrates through the bottom of the container 2 and is installed in the liquid in the container 2. By heat exchange with the heating medium flowing in the heat transfer tube 33, the container Two
The liquid inside is heated. In addition, the heat transfer tube 3 of the cooling device 32
4 is installed in the liquid in the container 2 by penetrating the side wall of the container 2, and the liquid in the container 2 is cooled by heat exchange with the cooling medium flowing in the heat transfer tube 34.

The temperature sensor 35 can detect the temperature of the liquid in the container 2, and the liquid temperature detected by the temperature sensor 35 is input to the control means 36 at appropriate times.
The control means 36 controls the operation of the heating device 31 or the cooling device 32 based on the inputted liquid temperature information so that the temperature of the liquid in the container 2 becomes a desired temperature (set temperature). . The set temperature of the liquid is higher or lower than the temperature of blood flowing into the artificial lung 10.

The fluid supply device 1 also has a working fluid supply line 4 for supplying a working fluid to the artificial lung 10.
The working fluid supply line 4 joins the liquid supply means 5 for supplying the liquid in the container 2, the gas supply means 6 for supplying the gas for gas exchange in the artificial lung 10, and the liquid and the gas. It is composed of a section 7 and a tube 71 that connects the confluence section 7 and the working fluid inlet 142 of the artificial lung 10.

The liquid feeding means 5 is composed of a pipe body 51, one end of which communicates with the vicinity of the bottom of the container 2 and the other end of which is located at the confluence portion 7, and a pump 52 installed in the middle of the pipe body 51. Has been done. When the pump 52 is operated, the liquid in the container 2 whose temperature has been adjusted to a desired temperature is supplied through the pipe body 51 to the merging portion 7 described later.

The pump 52 may be any type of pump such as a centrifugal pump, a roller pump, a bellows pump, or the like.

The gas supply means 6 is, for example, a gas supply source 61 composed of a cylinder or a compressor filled with a gas, and one end connected to the gas supply source 61 and the other end located at the confluence section 7. It is composed of a trachea 62 and a valve 63 that is installed in the middle of the air supply pipe 62 and opens and closes the flow path of the air supply pipe 62. With the valve 63 opened, the gas sent from the gas supply source 61 is supplied to the merging unit 7 described later via the air supply pipe 62.

In the present embodiment, the gas supplied from the gas supply source 61 is a gas having a higher oxygen partial pressure and a lower carbon dioxide partial pressure than the blood flowing into the artificial lung 10.
Examples thereof include air, pure oxygen, and oxygen-rich gas. As a result, oxygen is added to the blood and decarboxylation gas is performed in the artificial lung 10.

The merging portion 7 is a working fluid (liquid and gas).
There are various configurations depending on the supply pattern. 2 to 5 are cross-sectional views each showing a configuration example of the confluence portion 7. These will be sequentially described below.

FIG. 2 shows a structural example in which the confluence section 7 is composed of a mixing means for mixing a liquid and a gas. The mixing means shown in the figure has a chamber (diameter expanded portion) 72 formed between the pipes 51 and 71, and a nozzle 73 that penetrates a wall portion of the chamber 72 and has a tip communicating with the chamber 72.
It consists of and. The base end of the nozzle 73 is the air supply pipe 62.
It is connected to the.

In such a mixing means, the tubular body 51
The liquid sent through the inside flows into the chamber 72, while the gas sent through the air supply pipe 62 is ejected from the tip of the nozzle 73 into the chamber 72 to form fine bubbles. Become. The bubbles are mixed in the liquid in the chamber 72, and the liquid containing the bubbles is supplied to the artificial lung 10 via the tube 71.

FIG. 3 shows another structural example in which the confluence part 7 is composed of a mixing means for mixing a liquid and a gas. The mixing means shown in the figure is located in the vicinity of the bottom of the chamber 74, a chamber (expanded portion) 74 formed between the pipes 51 and 71, an air supply pipe 62 penetrating the wall of the chamber 74, It is composed of a porous body (bubble generating member) 75 attached to the tip of the air supply pipe 62.

As the porous body 75, various sintered bodies and foams can be used, and examples thereof include foamed polyurethane, foamed polyethylene, microporous polypropylene, glass, ceramics such as unglazed ceramics, and the like.

In such a mixing means, the tubular body 51
The liquid sent through the inside flows into the chamber 72, while the gas sent through the air supply pipe 62 is supplied into the porous body 75 and is formed in the porous body 75. Fine bubbles are formed after passing through numerous pores. The bubbles are mixed in the liquid in the chamber 74, and the liquid containing the bubbles is supplied to the artificial lung 10 via the tube 71.

4 and 5 show another structural example of the confluence section 7. The merging section 7 shown in these figures is constituted by a flow path changing means capable of supplying liquid and gas alternatively or alternately. This flow path changing means includes a cylindrical main body 76, three branch pipes 77a, 77b and 77c projectingly formed on the outer periphery of the main body 76 at an angle of 90 °, and the main body 7
6 and a cylindrical cock 78 that is airtightly and rotatably fitted in the inner cavity of the cylinder 6.

The branch pipes 77a, 77b and 77c include
The ends of the pipe body 51, the air supply pipe 62, and the pipe body 71 are connected to each other. Further, inside the cock 78, a T-shaped flow path 7 that can communicate with the inner cavities of the branch pipes 77a to 77c.
9 is formed.

In such a flow path changing means, the main body 7
If the cock 78 in 6 is in the state shown in FIG.
7a and 77c communicate with each other through the flow path 79, and the branch pipe 7
7b is shut off. Thereby, only the liquid sent through the inside of the tubular body 51 is sequentially supplied to the artificial lung 10 through the branch pipe 77a, the flow channel 79, the branch pipe 77c, and the tubular body 71.

If the cock 78 in the main body 76 is rotated clockwise by 90 ° from the state shown in FIG. 4 to the state shown in FIG. 5, the branch pipes 77b and 77c communicate with each other through the flow passage 79. The branch pipe 77a is shut off. As a result, only the gas sent through the inside of the air supply pipe 62 is separated from the branch pipe 7
7b, the flow path 79, the branch pipe 77c, and the tubular body 71 in this order and are supplied to the artificial lung 10.

Selecting either liquid or gas as the working fluid to be supplied to the artificial lung 10 by fixing the posture of the cock 78 to either the state shown in FIG. 4 or the state shown in FIG. That is, in the artificial lung 10, it is possible to select whether to perform heat exchange or gas exchange.

Further, for example, the state shown in FIG. 4 and the state shown in FIG. 5 are cyclically changed by, for example, continuously rotating the cock 78 in the same direction, or repeating the forward / reverse rotation of the cock 78. If they are generated alternately, the liquid and the gas can be alternately supplied to the artificial lung 10, and heat exchange and gas exchange can be performed. In this case, the cycle of the state change of the cock 78 (the time from the state shown in FIG. 4 to the state shown in FIG. 5 and again to the state shown in FIG. 4) is not particularly limited and may be, for example, 0.1 to 5 It may be a relatively short time of about seconds or a relatively long time of about 60 to 120 minutes.

Next, the structure of the artificial lung will be described. FIG. 6 is a vertical cross-sectional view showing a structural example of an artificial lung that supplies a working fluid by the fluid supply device of the present invention. As shown in the figure, the artificial lung 10 includes a tubular body 13 and the tubular body 13
Cover member (housing) liquid-tightly joined to both ends of
It has a housing 12 composed of 14 and 15.

The tubular main body 13, which is a main member of the housing 12, has a taper shape in which the inner diameter is minimized at the central portion 130 in the axial direction, and the inner diameter gradually increases from the central portion 130 to both end portions. . This tubular body 1
A bundle of a large number of hollow fiber membranes 16 which are gas permeable membranes is housed in 3, and both ends of the bundle of hollow fiber membranes 16 are
It is embedded in the partition walls 17 and 18 and fixed near both ends of the cylindrical main body 13, respectively.

The partition walls 17 and 18 are formed by injecting and curing a polymer potting material such as polyurethane, silicone, or epoxy in the vicinity of both ends of the cylindrical body 13, and the partition wall 17 will be described later. The part 131 and the outflow part 151 are liquid-tightly shielded, and the partition wall 18 is liquid-tightly shielded from an outflow part 132 and an inflow part 141 described later.

As described above, since the tubular main body 13 has a tapered shape in which the inner diameter increases from the central portion 130 toward both ends, the bundle of hollow fiber membranes 16 accommodated in the central portion 130. Since the hollow fiber membrane 16 is placed in the vicinity and is narrowed down, the contact rate between the hollow fiber membrane 16 and the blood flowing outside the hollow fiber membrane 16 is increased, and the efficiency of gas exchange and heat exchange is enhanced.

The inflow part 131 and the outflow part 132 of the blood are respectively provided in the upper part and the lower part of the cylindrical main body 13 in FIG.
Are formed. The inflow part 131 and the outflow part 13
2 has an inner diameter larger than that of the tapered portion of the cylindrical main body 13. Further, a tubular blood inflow port 134 and a blood outflow port 135, which communicate with the internal spaces of the inflow part 131 and the outflow part 132, are formed in a protruding manner, respectively.

In such a housing 12, the cover member 14 joined to the lower end of the cylindrical main body 13 in FIG. 6 forms an inflow portion 141 for the working fluid, and the cover member 15 joined to the upper end of FIG. Due to the working fluid outflow portion 15
1 is formed.

On the side of the cover member 14, the cover member 1
4, a tubular working fluid inlet 142 communicating with the inside of the cover member 4 is formed to project, and a tubular working fluid outlet 152 communicating with the inside of the cover member 15 is formed to project at a side portion of the cover member 15. .

The space formed by the gaps between the hollow fiber membranes 16 and the gap between the hollow fiber membranes 16 and the inner surface of the tubular body 13 is a blood flow path from the blood inflow portion 131 to the blood outflow portion 132. 133 is formed.

Further, both ends of each hollow fiber membrane 16 are opened so as to communicate with the inside of the cover members 14 and 15, respectively, and the inner cavity of each hollow fiber membrane 16 has an inlet 14 for the working fluid.
A flow path from 1 to the outflow portion 151 is formed.

In the artificial lung 10 as described above, the hollow fiber membrane 16 is a medium for exchanging gas between blood and working fluid, and also a medium for exchanging heat. The hollow fiber membrane 16 that can be used may be either a porous membrane or a dense membrane. As the porous film, for example, a porous polyolefin-based material such as polypropylene or polyethylene,
Examples thereof include those made of cellulose-based materials such as cellulose-di-acetate, and examples of the dense membrane include those made of silicone rubber.

In the artificial lung 10, the blood inflow portion (inlet) and the blood outflow portion (outlet) are provided upside down in FIG. 6, and blood flows in the flow path 133 upward in FIG. Such a configuration may be adopted.

Next, the operation of the artificial lung 10 will be described. The liquid containing bubbles, which is the working fluid sent through the working fluid supply line 4, flows into the cover member 14 from the working fluid inlet 142, and when the pressure becomes equal to or higher than a predetermined value, one end of each hollow fiber membrane 16 is reached. From the other end of the hollow fiber membrane 16 into the outflow portion 151, and from the working fluid outlet 152 to the working fluid recovery line 8
Sent to.

The liquid and gas may flow in any of the inner cavities of the hollow fiber membranes 16. For example, when the hollow fiber membranes 16 are held vertically, a bubble flow, a slug flow, or an annular flow. Any of the annular spray flows (see “Gas-Liquid Two-Phase Flow”, pages 7-9, published by Yokendo, 1981) is preferable, but it is particularly preferable to form a slag flow.

On the other hand, from the blood inflow port 134, the inflow part 13
Blood flows into the hollow fiber membranes 1 and
The gap between them and the gap between the hollow fiber membrane 16 and the inner surface of the tubular body 13, that is, the flow path 133, flows downward in FIG. 6 along the longitudinal direction of the hollow fiber membrane 16 and reaches the outflow portion 132. Further, the blood is discharged from the blood outlet 135 to the outside of the casing 12.

While the blood flows in the flow path 133, the blood passes through a large number of pores formed in the hollow fiber membrane 16 and the hollow fiber membrane 1
The gas is exchanged by contacting with the gas flowing through the lumen of No. 6.
As a result, the blood is oxygenated and decarbonated.
At the same time, the blood exchanges heat with the liquid flowing through the hollow fiber membrane 16 through the hollow fiber membrane 16 while flowing through the flow path 133. Thereby, the blood is cooled or heated to a desired temperature.

As shown in FIG. 1, the outflow portion 1 of the artificial lung 10
The working fluid discharged from 51 is the working fluid recovery line 8
Will be collected by. The working fluid recovery line 8 has a gas-liquid separation tank 82 and a working fluid outlet 15 of the artificial lung 10 at one end.
2, a pipe body 81 connected to No. 2 and having the other end penetrating the sidewall of the gas-liquid separation tank 82 and communicating with the gas-liquid separation tank 82, and one end penetrating the bottom of the gas-liquid separation tank 82. Communicating with 82,
The other end is configured by a pipe body 85 penetrating the side wall of the container 2 and communicating with the inside of the container 2.

The upper part of the gas-liquid separation tank 82 is covered with a lid 83. A degassing port 84 is formed in the lid 83.

The liquid containing bubbles that has flowed out from the working fluid outlet 152 of the artificial lung 10 flows into the gas-liquid separation tank 82 through the pipe 81, and the bubbles therein float and rise to the gas-liquid separation tank 82. Accumulated in the upper space of the chamber and then ruptured to degas
Exhausted from 4. Near the bottom of the gas-liquid separation tank 82,
The liquid from which the bubbles have been separated and removed is stored, and the liquid is separated from the gas-liquid separation tank 82 and the container 2 by the drop of the pipe 85.
It is collected in the container 2 via.

It is also possible to provide a pump (not shown) in the middle of the tubular body 85 and operate it to send the liquid from which bubbles have been separated and removed to the container 2.

The working fluid recovery line 8 does not have the gas-liquid separation tank 82, and directly recovers the liquid containing bubbles in the container 2 and floats the bubbles in the container 2 to remove them from the liquid. May be

The working fluid recovery line may be configured to collect or discard the working fluid in a container other than the container 2. Further, the present invention may not have such a working fluid recovery line.

In the fluid supply device 1, the ratio of liquid to gas supplied to the heat and gas exchanger such as the artificial lung 10 can be set continuously or stepwise in the range of 1: 0 to 0: 1. It is preferably possible. The setting method will be described below in relation to the configuration of the merging unit 7.

When the merging portion 7 is a liquid and gas mixing means as shown in FIGS. 2 and 3, the ratio of the liquid supply amount and the gas supply amount to the merging portion 7, that is, the mixing ratio is appropriately adjusted. To do. Specifically, by adjusting the discharge amount of the pump 52 and the opening degree of a flow rate control valve (not shown) provided in the middle of the pipe body 51, the liquid supply amount to the merging portion 7 is adjusted. By adjusting the opening of the valve 63, the amount of gas supplied to the merging portion 7 is adjusted.

In this case, if the pump 52 is stopped and the supply of the liquid is cut off, only gas is supplied as the working fluid to the artificial lung 10, so that only gas exchange is performed. On the contrary, if the valve 63 is closed and the gas supply is cut off, only the liquid is supplied to the artificial lung 10 as the working fluid, so only the heat exchange is performed.

When the merging portion 7 is the flow path changing means as shown in FIGS. 4 and 5, if the cock 78 is in the state shown in FIG. 4, only the liquid is supplied to the artificial lung 10 as the working fluid. Therefore, only heat exchange is performed, and if the posture of the cock 78 is set to the state shown in FIG. 5, only gas is supplied as the working fluid to the artificial lung 10, so only gas exchange is performed.

If the state shown in FIG. 4 and the state shown in FIG. 5 are periodically alternated by rotating the cock 78, liquid and gas are alternately supplied to the artificial lung 10,
Heat exchange and gas exchange take place. In this case, the artificial lung 1
The ratio of the liquid and the gas supplied to 0 is adjusted by adjusting the ratio of the liquid supply amount and the gas supply amount to the merging portion 7 as described above, and the time for which the cock 78 maintains the state shown in FIG.
It can be set as appropriate by adjusting the ratio of the time for holding the state shown in (4) or by combining these.

Further, it is preferable that the fluid supply apparatus 1 be constructed so that the ratio of the liquid to the gas supplied to the artificial lung 10 can be changed appropriately by the adjusting method described above. This allows
In the artificial lung 10, only gas exchange or only heat exchange can be performed, and switching can be performed, for example, in the following patterns. Also, when performing gas exchange and heat exchange in the following items, the artificial lung 10
It is preferable to adopt a configuration in which the ratio of the liquid and the gas supplied to the can be changed. This makes it possible to finely adjust the balance between heat exchange and gas exchange in the artificial lung 10.

Gas exchange → heat exchange heat exchange → gas exchange gas exchange → gas exchange and heat exchange heat exchange → gas exchange and heat exchange gas exchange and heat exchange → gas exchange gas exchange and heat exchange → heat exchange any of the above ~ A combination of two or more

In these cases, for example, for an emergency patient, oxygenation and decarbonation are performed on the patient's blood as the minimum necessary treatment possible in an ambulance, and then in a hospital. During open heart surgery and the like, cooling of blood, addition of oxygen, and decarbonation can be performed.

Further, even during the open-heart surgery, the pattern can be changed once or twice or more in the middle, as described in the above items 1 to 4, depending on the case and the condition of the patient.

The artificial lung connected to the fluid supply device 1 of the present invention is usually an artificial lung having both the heat exchange function and the gas exchange function described above, but the present invention is not limited to this and has a heat exchange function. You may connect an artificial lung that does not. Moreover, you may connect the heat exchanger which does not have a gas exchange function. When connecting an artificial lung that does not have a heat exchange function, by the adjustment method described above, when the working fluid supplied to the artificial lung is only gas, and when a heat exchanger that does not have a gas exchange function is connected, By the adjustment method described above, the working fluid supplied to the artificial lung is only liquid.

Next, the fluid supply apparatus of the present invention will be described in more detail with reference to specific examples.

Example 1 A fluid supply device having the structure shown in FIG. 1 was manufactured. In this fluid supply device, the volume of the container was 10,000 ml, about 5000 ml of water was put in this container, and the temperature of the water in the container was kept at 20 ° C. by the temperature control means.

A centrifugal pump was used as a pump in the liquid feeding means. As a gas supply source, a cylinder filled with pure oxygen was used. The structure of the merging section was a mixing means having the structure shown in FIG. In this mixing means, the volume of the chamber was 2 ml, and the diameter of the tip of the gas ejection nozzle was 1.5 mm.

The volume of the gas-liquid separation tank in the working fluid recovery line was 1000 ml. The artificial lung with a heat exchanger connected to the fluid supply device has an effective length of 100 mm in the casing,
A large number of porous hollow fiber membranes made of polypropylene having an inner diameter of about 220 μm were arranged and the effective membrane area was 1.8 m ² .

(Example 2) A fluid supply device similar to that of Example 1 was manufactured except that the structure of the merging portion was the mixing means having the structure shown in FIG. In this mixing means, the volume of the chamber was set to 60 ml, and as the porous body for bubble generation installed in the chamber, a foamed polyethylene having an average pore diameter of 500 μm was molded into a tubular shape with a closed tip. .

(Embodiment 3) A fluid supply apparatus similar to that of Embodiment 1 was manufactured except that the structure of the merging portion was changed to the flow passage changing means having the structure shown in FIGS. 4 and 5. When supplying the working fluid,
The cock was rotated, and water and oxygen were alternately supplied for 0.5 seconds each.

[Experiment 1] 5000 ml of cold water (20 ° C.) in the container was used using each of the fluid supply devices of Examples 1, 2 and 3.
3800 ml of oxygen from the cylinder while supplying at a rate of / min
cold water containing oxygen bubbles was flown into the lumen of each hollow fiber membrane of the artificial lung. At the same time, cow blood at 37 ° C was supplied at 3800 ml / min to the blood inlet of the artificial lung, and cow blood was allowed to flow in the gaps between the hollow fiber membranes to cool, oxygenate and deoxidize the cow blood. Carbon dioxide was continued for about 10 minutes.

The temperature and the amount of dissolved oxygen of bovine blood collected from the blood outlet of the artificial lung were measured, and the heat exchange capacity (heat exchange coefficient) and oxygen addition capacity of the artificial lung were determined from the measured data. The results are shown in Table 1 below.

[Experiment 2] After completion of Experiment 1, cold water (20 ° C.) in the container was supplied at 5000 ml / min to each of the fluid supply devices of Examples 1, 2 and 3 while oxygen from the cylinder was supplied. Was stopped, and only cold water was allowed to flow into the lumen of each hollow fiber membrane of the artificial lung. In the fluid supply device of Example 3, the cock was fixed in the state shown in FIG. At the same time, bovine blood was supplied to the blood inlet of the artificial lung under the same conditions as in Experiment 1, and the bovine blood was continuously cooled for about 10 minutes.

The temperature of bovine blood collected from the blood outlet of the artificial lung was measured, and the heat exchange capacity (heat exchange coefficient) of the artificial lung was determined from the measured data. The results are shown in Table 1 below.

[Experiment 3] After the completion of Experiment 2, the supply of cold water in the container to each of the fluid supply devices of Examples 1, 2 and 3 was stopped, and oxygen was supplied from the cylinder at 3800.
It was supplied at ml / min, and only oxygen was flown into the lumen of each hollow fiber membrane of the artificial lung. In the fluid supply device of Example 3, the cock was fixed in the state shown in FIG. At the same time, bovine blood was supplied to the blood inlet of the artificial lung under the same conditions as in Experiment 1, and the bovine blood was continuously oxygenated and decarbonated for about 10 minutes.

The dissolved oxygen content of bovine blood collected from the blood outlet of the artificial lung was measured, and the oxygen addition capacity of the artificial lung was determined from this measurement data. The results are shown in Table 1 below.

[0084]

[Table 1]

The oxygen adding ability in Table 1 shows the difference in the amount of dissolved oxygen in blood before and after passing through the artificial lung per minute. Further, the heat exchange coefficient K in Table 1 is expressed by the following equation (1).

[0086]

[Equation 1]

As is clear from the results shown in Table 1, it was confirmed that when the fluid supply devices of Examples 1 to 3 were used, excellent heat exchange ability and oxygen addition ability were obtained. It was confirmed that even when the supply pattern of cold water and oxygen was changed, the heat exchange capacity and the oxygen addition capacity were within a range in which practical problems did not occur.

[Experiment 4] Bovine blood (23 ° C.) was used in the same manner as in Experiments 1 to 3 except that the fluid supply devices of Examples 1 to 3 were used and hot water held at 40 ° C. in the container was used. Was heated, oxygenated, and decarbonated.

As a result, all of the fluid supply devices of Examples 1 to 3 exhibited the same heat exchange capacity and oxygen addition capacity as in Table 1 above.

In each of the above embodiments, the case where the working fluid is supplied to the hollow fiber membrane type artificial lung by the fluid supply device of the present invention has been described, but the present invention is not limited to this, and a flat membrane is used as a gas permeable membrane. It may be applied to the artificial lung used.

Further, the fluid supply device of the present invention is not limited to supplying the working fluid to the artificial lung, but may be any one that supplies the working fluid to the heat and gas exchanger having the heat exchange function and the gas exchange function. Any type may be used, and the use is not limited to medical use, and may be industrial use, for example.

Further, in the present invention, the fluid for exchanging heat and gas with the working fluid is not limited to blood, but may be any other body fluid such as plasma, liquid other than body fluid, gas or the like.

[0093]

As described above, according to the fluid supply device of the present invention, heat exchange and gas exchange can be performed by one exchanger, and the heat exchange ability and the gas exchange ability are excellent.
Therefore, when the fluid supply device of the present invention is used to supply the working fluid to the oxygenator with a heat exchanger, the circuit configuration of the blood extracorporeal circulation circuit including the oxygenator is simplified and the amount of priming of blood in the circuit is simplified. Can be reduced.

Further, in the fluid supply apparatus of the present invention, the ratio of heat exchange and gas exchange can be set to a desired value, and further, this ratio can be changed, so that optimum conditions can be obtained according to the situation. It is possible to expand the application.

Therefore, when the fluid supply device of the present invention is used to supply the working fluid to the artificial lung with a heat exchanger, the blood is supplied without exchanging the artificial lung from the whole blood extracorporeal circuit or the extracorporeal blood circuit. It is possible to change the processing pattern, for example, to change from one pattern of only gas exchange, only heat exchange, or a combination of heat exchange and gas exchange to another pattern. As a result, labor and time for replacing the extracorporeal blood circulation circuit and the artificial lung in the circuit can be saved, and a quicker response is possible, and the number of times of priming blood in the circuit can be minimized. , The amount of priming can be reduced.

The fluid supply device of the present invention has a simple structure and can efficiently supply gas and liquid.

[Brief description of drawings]

FIG. 1 is a circuit configuration diagram schematically showing a configuration example of a fluid supply device of the present invention.

FIG. 2 is a cross-sectional view showing a configuration example of a merging portion in the fluid supply device of the present invention.

FIG. 3 is a cross-sectional view showing another configuration example of the confluence section in the fluid supply device of the present invention.

FIG. 4 is a cross-sectional view showing another configuration example (during liquid supply) of the confluence portion in the fluid supply device of the present invention.

FIG. 5 is a cross-sectional view showing another configuration example (during gas supply) of the confluence portion in the fluid supply device of the present invention.

FIG. 6 is a vertical cross-sectional view showing a configuration example of an artificial lung.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Fluid supply device 2 Container 3 Temperature control means 31 Heating device 32 Cooling device 33, 34 Heat transfer tube 35 Temperature sensor 36 Control means 4 Working fluid supply line 5 Liquid feeding means 51 Pipe 52 Pump 6 Gas supply means 61 Gas supply source 62 pipe 63 valve 7 confluence part 71 pipe 72 chamber 73 nozzle 74 chamber 75 porous body 76 main body 77a, 77b, 77c branch pipe 78 cock 79 flow path 8 working fluid recovery line 81 pipe 82 gas-liquid separation tank 83 lid Body 84 Deaeration port 85 Tubular body 10 Oxygenator with heat exchanger 12 Housing 13 Cylindrical body 130 Central part 131 Inflow part 132 Outflow part 133 Flow path 134 Blood inflow port 135 Blood outflow port 14 Cover member 141 Inflow part 142 Working fluid Inlet port 15 Cover member 151 Outflow part 152 Working fluid outlet port 16 Medium Fiber membrane 17, 18 partition walls

Claims (1)

[Claims] 1. A fluid supply device for supplying a working fluid to a heat and gas exchanger having both a heat exchange function and a gas exchange function, the container storing a liquid for heat exchange, and the temperature of the liquid. A temperature adjusting means for adjusting, a liquid feeding means for feeding the liquid, a gas supply means for supplying a gas for gas exchange, and a confluence portion where the liquid and the gas merge. A fluid supply device, wherein at least one of the liquid and the gas is supplied to the heat and gas exchanger.