JPS6024849A - Treatment of single lumen catheter liquid - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to single lumen catheter fluid handling, and more particularly to a method and apparatus for controlling the opening and closing of venous and arterial lines in communication with and in communication with a single lumen catheter. .

[Background of the invention]

Various forms of methods and apparatus for single lumen catheter fluid processing, particularly blood processing, are disclosed in commonly assigned U.S. Patent No. 3,756,234, now Reissued Patent No.
It has been developed since issue 46. The most successful methods or devices employ the concept of controlling the opening or closing of a venous or arterial line in response to high or low pressure values occurring in a closed external circuit, and in which a single lumen circuit is used. an arterial line communicating with the catheter, a hemodialyzer, a hemofilter, a blood purification filter, a plasmapheresis device or an ascites device, and a venous line having a reservoir or drip chamber for an energized intravenous line and communicating with the single lumen catheter; Become.

The most common is a method that involves substantially simultaneously opening the venous line and closing the arterial line in response to a preset higher pressure value occurring within the venous line. These methods optionally also include substantially closing the venous line and simultaneously opening the arterial line in response to a pre-established lower pressure value occurring within the venous line. Generally, the pressure value within the intravenous line is
Detection is achieved by sensing the pressure within the gas cushion above the level of the fluid in the static 111i line reservoir, usually purified or processed blood. Also set in advance or l! Devices are also known in which a venous line is closed and an arterial line is opened substantially simultaneously in response to an increment of time. Similarly, devices are known in which an arterial line is closed and a venous line is opened substantially simultaneously in response to a set or adjustable time increment of i'+i+. These devices use pre-sensor 1-
means for opening the arterial line substantially simultaneously with the closure of the venous duct in response to a lower pressure value; or in response to a preset or adjustable time increment; including any means for simultaneously closing and simultaneously opening the arterial line. devices of the latter type, i.e. preconfigured or II,
No. 3, Applicant's U.S. Pat.
No. 756,234 and Reissue Patent No. 2!1,346, and indeed subsequent research has shown that the control of the single lumen catheter fluid treatment method by means of a timer mechanism is extremely important. It was not considered a subject of research because it was unable to achieve what was thought to be the goal. A device comprising means for closing an arterial or venous line in response to a pressure value developed in an extracorporeal blood circuit,
The arc is controlled according to the special conditions or conditions that exist within the extracorporeal blood circuit. In other words, a system comprising means for controlling the closure of arterial and/or venous lines in response to pressure values developed in an extracorporeal blood circuit can be self-regulating in nature. 1. In particular, by introducing a concept that allows an automatic adjustment system, a special combination of control means for closing venous and arterial lines in a single lumen catheter device has been achieved compared to systems used in the past. It has been found that substantially improved self-regulation can be achieved. In particular, it also does not include means to control the closure of the venous line according to the conditions within the arterial line.
It has been found that self-regulation in single lumen catheter devices is not perfect. Combining this knowledge with the method of controlling the closure of an arterial line according to conditions within the venous line, which were known in part from the devices described above, allows the arterial line to close and the venous line to close substantially simultaneously. A new and greatly improved method and apparatus have been developed that are useful for controlling the opening and opening of arterial lines substantially simultaneously as venous lines close.

This method and device are the subject of the invention. The present invention also provides a liquid line configuration that is particularly useful in this method and apparatus.

The present invention further takes into account that even if there is a sufficient amount of untreated liquid upstream of the liquid treatment device, it is less problematic to close the intravenous line. Similarly, or in other words, even if there is a sufficient amount of processing fluid downstream of the fluid processing device, it may be less problematic for the arterial line to close and the venous line to open substantially simultaneously. Become. Care must be taken to optimize the use of time in single lumen catheter fluid treatment methods.

Because the treatment time using a single lumen catheter is much longer than the treatment time required for a double lumen or twin needle treatment method, the known advantages of a single lumen catheter fluid treatment method are
This is because such a long liquid processing time makes it meaningless.

[Summary of the invention]

The method of the present invention includes providing an arterial line storage tank upstream of a liquid processing device to receive untreated liquid from a liquid source, providing arterial line opening/closing means upstream of the arterial line storage tank, and providing the liquid processing device with an arterial line opening/closing means. In order to receive the treated liquid from the venous line, a venous line storage tank should be provided downstream of the liquid processing device, a venous line opening/closing means should be provided downstream of the venous line storage tank, and untreated liquid should be introduced from the liquid source into the arterial line storage tank. , flowing this untreated fluid from the arterial line reservoir through the fluid treatment device into the venous line reservoir, and in response to the upper limit amount of treated fluid available in the venous line reservoir, closing the arterial line and substantially simultaneously opening the venous line, thereby returning the treated fluid to the fluid source, and closing the venous line and substantially simultaneously opening the arterial line in response to a lower limit amount of untreated fluid available in the arterial line reservoir; It consists of a process called .

Arterial and venous line opening and closing means are provided by those currently in common use, such as solenoid-operated clamps or stopping and starting fluid pumps, conveniently emotional roller pumps. However, in the present invention, untreated fluid flows continuously from the arterial line reservoir through the fluid treatment device, so that the treated fluid continuously accumulates in the venous line reservoir. Therefore, the clamping means for controlling the opening and closing of the arterial line is
It is generally located upstream of the arterial line fluid pump and upstream of the arterial line reservoir. Similarly, the intravenous line opening/closing clamp member j-2 is generally provided downstream of the intravenous line reservoir.

In one simplified embodiment of the invention, only one pumping means is provided to flow unprocessed fluid from the arterial line reservoir through the fluid treatment device and to collect treated fluid in the venous line reservoir. In this embodiment, the pressure varies not only within the intravenous line reservoir, but also within the fluid handling device. This is not necessarily preferred in hemodialysis methods or hemofiltration, blood purification or plasmapheresis operations using so-called high-flux membrane fluid treatment devices. In such operations, it is generally advantageous for the fluid pressure within the fluid treatment device to be substantially constant.

As described in detail below with reference to the accompanying drawings, a method for maintaining pressure values is obtained by increasing the volume ratio of the gas cushion in the intravenous line reservoir to the volume of the reservoir. . However, taking the above into consideration, a first liquid pump is provided on the upstream side of the liquid processing device, a second liquid pump is provided on the downstream side of the liquid processing device, and means for controlling the pump speed by the pressure between the two pumps is provided. With the dual pump system, the hydraulic pressure between the pump and the liquid processing device can be controlled more reliably.

The method and apparatus described above and variations of or according to the invention will now be described with reference to the accompanying drawings. The description with respect to the accompanying drawings also describes the single lumen catheter method and apparatus according to the present invention for use in the novel plasmapherese method. Shigashiko's plasmapherase method is
Methods other than single lumen catheterization can also be used. A device according to the invention, including a plasmapheresis method and a single lumen catheterization method, will be described below with reference to the accompanying drawings.

In addition, Fig. 1 is a schematic diagram of a device and a liquid line that operate using a single type liquid pump, Fig. 2 is a schematic diagram of a device and a liquid line that operate using two liquid pumps, and Fig. 3 is a schematic diagram of a device that operates using a single type liquid pump and a liquid line. 1 is a schematic diagram of a device and a liquid line operating with a double-head liquid pump and a pump for introducing a substituent liquid; FIG.

[Detailed description of the embodiments of the drawings]

In FIG. 1, reference numeral 10 denotes an arterial line storage tank, which is placed upstream of the liquid processing device I2. The liquid treatment device used in the device according to the invention is generally a conventional hemodialyzer, which can also be of high fluidity, provided that sufficient means are provided to control ultrafiltration. arterial line 14
leads into the arterial line reservoir 10 from the first arm 16 of the single lumen catheter device, indicated at 18 .

The arterial line opening/closing means, indicated generally at 20, and the venous line opening/closing means are shown as a combination or a single unit in the schematic diagram of FIG. 1 and also in FIGS. 2 and 3. Thus, the arterial line opening/closing means consists of a central member 22, which is located on the left and right sides of the drawing, i.e., the arterial line 14
is movable between a left-most position a111 where the arterial line is occluded by the central member 22 and the first contact element 24, and a right-most position where the arterial line is open. Opening and closing of the arterial line occurs upstream of the arterial line reservoir 10, with arrow 30 indicating the direction of fluid flow.

32 is a storage tank for an intravenous line located downstream of the liquid processing device 12; The intravenous line 34 is connected from the intravenous line reservoir 32 to the second arm 36 of the single lumen catheter device 18.
is familiar with As already mentioned, the intravenous line opening/closing means generally consists of an assembly or fii-unit indicated at 20. The intravenous line opening/closing means is arranged from left to right in the drawing, between the extreme right position where the intravenous line 34 is occluded by the central member 22 and the second contact element 38 and the extreme left position where the intravenous line is opened. , is movable.

Opening and closing of the intravenous line 34 occurs downstream of the intravenous line reservoir 32.

The apparatus of FIG. 1 includes a single liquid pump 40, preferably a
It has a roller type pump to pass the untreated liquid from the arterial line storage tank 10 to the venous line storage tank 32 through the liquid processing device 12.
Used to pass inside.

The upper limit sensor for detecting the upper limit amount of treatment liquid in the intravenous line storage tank 32 has a high pressure value sensor 42 that detects when the pressure sensor 42 reaches a preset or predetermined high pressure value. , transmits the first signal to the arterial and venous line opening/closing unit 20 by the conductive wire 45 . This high pressure value is applied to the pressure transmission line 44 which transmits the pressure generated within the gas cushion 46 within the intravenous line storage tank 32.
It is transmitted to the pressure sensor 42 via. When the inside of the intravenous line storage tank 42 reaches a preset or set high pressure value and accordingly the inside of the pressure sensor 42 reaches a high pressure value, the first signal transmitted via the conductive wire 45 causes the moving member 22 to move to the leftmost position. , and the arterial line 14 is occluded between the moving member 22 and the first contact element 24 .

The liquid pump 40 pumps the untreated liquid from the arterial line storage tank 10 through the liquid processing device 12 to the venous line storage tank 32 until the untreated liquid in the arterial line storage tank 1o reaches the lower limit.
Continuously flow inside.

A lower limit sensor for detecting the lower limit amount of untreated liquid in the arterial line storage tank 10 opens and closes the arterial and venous lines when the pressure sensor 48 reaches a preset or set low pressure value. preferably includes a low pressure value sensor 48 for transmitting a second signal via the same electrically conductive wire 45. This low pressure value corresponds to the arterial line reservoir 1
The pressure generated in the gas cushion 52 in the air is transmitted to the pressure sensor 48 via the pressure transmission pipe 5o.

When a preset or predetermined low pressure value is reached in the arterial line reservoir and therefore in the pressure sensor 48, the transmitted second signal causes the moving member 22 to move to the rightmost position, and in this moving position. , the intravenous line 34 is connected to the moving part 22
and the second contact point 1 to 38 are closed.

As stated above, during operation of the device, arterial line 1
Closing 4 essentially opens the intravenous line 34 at the same time. Similarly, closing venous line 34 essentially opens arterial line 14 at the same time.

The above is the pressure that fluctuates within the intravenous line storage tank 32. In most cases, it is desirable that the pressure within the intravenous line reservoir 32 be significantly lower than a preset or established upper pressure limit. This is because, in the device configuration of the present invention, high pressure (i.e., higher than the fluid pressure in the fluid source) is required to return fluid to the fluid source through the intravenous line 34 and catheter device 18 while the intravenous line is open. This is because it becomes a driving force.

The amount of process liquid that returns to the source per unit time is an important factor, and the same amount is, of course, greatest when the pressure value is at or near the upper limit pressure. Furthermore, a storage tank 32 for intravenous line
The stability of the pressure, and thus the stability of the pressure within the liquid processing device, is effective for improving the control of the ultrafiltration amount, for example, in a device that controls the ultrafiltration amount by the permeation membrane pressure. It has been found that in order to better maintain high pressure values, the volume ratio of the air cushion 46 in the intravenous line reservoir 32 to the liquid volume in the same 32 can be increased.

That is, the total volume of the intravenous line storage tank 32 is increased compared to the conventional device (the liquid volume in the storage tank accounts for about three quarters of the total volume of the tank), and the liquid volume in the tank is increased, for example. ,
If it occupies less than one-third of the total volume of the storage tank, the high pressure value in the tank can be better maintained and - not drop below the high pressure value throughout.

Similarly, in the configuration of FIG. 1 of the drawings, it is desirable that the arterial line reservoir 10 maintain a low pressure value.

This is because such low pressure (as compared to the pressure of the liquid source) provides the driving force for removing liquid from the liquid source.

The maintenance of low pressure values in the arterial line reservoir 10 can be modified by increasing the volume ratio of the air cushion 52 to the liquid volume by suitably adapting the volume of the arterial line reservoir.

As described with reference to FIG. 1, in the liquid processing method, it is desirable to maintain the liquid in the liquid processing device 12 at a substantially constant pressure. In the configuration of FIG. 1, pressure fluctuations must occur within the venous line reservoir 32 and thus within the fluid treatment device 12 in order for the pressure to reach a high level value and occlude the arterial line. This pressure fluctuation is undesirable in liquid processing methods such as so-called high-flux membrane dialysis, blood purification, hemofiltration, etc.
Alternatively, in hemodialysis using the plasmapherese method, the amount of liquid passing from the liquid being processed across the membrane cage included in the liquid processing device 12 cannot be sufficiently controlled.

Therefore, it is necessary to separate the pressure generated within the intravenous line reservoir 32 from the liquid passing through the liquid treatment device 12. Is this the second liquid pump or liquid processing device? This can be conveniently achieved by providing it downstream of ¥12 and upstream of the intravenous line storage Off 32. Such a configuration is the second
In the figure, components common to those in FIG. 1 are designated by the same reference numerals.

In FIG. 2, the functions of the arterial line 10, the venous line chamber 32, the high and low pressure values, as well as the arterial line 111 and the venous line opening/closing means 20 will not be described again here. However, these functions are necessarily the same as the ``double'' with respect to Figure 1. The second liquid pump 54 is provided downstream of the liquid processing device 12 and upstream of the intravenous line storage tank 32 in FIG. a second pump 5 including the pump 4o of the arterial line 14 and the fluid treatment device 12;
4 is independent of the pressure generated in the intravenous line reservoir 32, unlike the arrangement of FIG. In both the configurations of FIGS. 1 and 2, the pump 40 is calculated from the pressure value generated in the arterial line reservoir 10
Let the hydraulic pressure of the flow be independent.

Pumps 40 and 54 in FIG. 2 operate in a variety of ways. However, as previously discussed with respect to FIG. 1, the pump 40 of the arterial line 14 is preferably operated continuously, and this is also the case in the configuration of FIG. In the apparatus shown in FIG. 2, with pump 40 operating continuously, it is preferred that second pump 54 also operate continuously. This mode of operation is novel in dual pump single lumen catheter construction. More specifically, as shown in FIG. 2, the relative pump speed, the speed of pump 40 as a function of the speed of pump 54, is controlled by the hydraulic pressure between two continuously operating pumps. The dual pump design is novel, and such a design has advantages over known dual pumps currently in use. In this manner, a desired fluid pressure value can be selected for a particular dialysate pressure for a particular lil treatment device 12, for example, according to the desired amount of ultrafiltration seen in a hemodialysis operation. Conveniently, liquid pumps 40 and 50
The speed of one of the pumps can be adjusted to a manually adjustable constant speed, and the speed of the other liquid pump can be varied in response to the hydraulic pressure between the pumps. In actual operation, it is preferred that liquid pump 40 be a constant speed pump and liquid pump 54 be a variable speed pump.

In the configuration shown in FIG. 2, the liquid pressure between the two liquid pumps 40 and 54 can be detected between the two pumps, that is, at any position on the upstream or downstream side of the liquid processing device 12. If there is a defective device, it can also be detected in the liquid processing device itself. However, in reality, it is convenient to provide the pressure tank 56 downstream of the liquid processing device 12, as shown in FIG.

The pressure tank 56 shown in FIG. 2 is substantially the same as the arterial line storage tank 10 and the venous line storage tank 32, and includes a gas cushion 5B, a pressure transmission pipe 60, and a pressure sensor fi2. However, it is contemplated that other types of devices may be used to sense the fluid pressure between the two fluid pumps 40.54 and work just as well, or better. For example, a pressure sensing device having a visible membrane (not shown) in contact with the liquid between both pumps on one side and a pressure transmitting liquid on the other side would be more effective than the illustrated device with a compressible gas cushion. Generates a large impulse in response to pressure changes. In this way, it is possible to improve the control (l'Iu) of the variable speed pump in response to pressure changes between the two pumps.

In any event, as opposed to maintaining pressure in the arterial line reservoir 10 and the venous line reservoir 32, the pressure sensing device is used to accurately control the speed of the variable speed pump in response to pressure. For this purpose, it is necessary to generate impulses that respond to even the smallest pressure changes. The pressure sensor 62 shown in FIG.
4 to control the current supplied to the variable speed pump 54 via f.
This causes the variable speed pump 54 to be driven at a speed that maintains the pressure value selected by the pressure sensor 62. The speed of the pump 40 can be set to an arbitrary speed, for example, about 200 m.
By setting the speed to send blood of β/min to the liquid processing device 12 and setting the pressure sensor 62 to an arbitrary pressure, the variable speed pump 54 can be set at a speed that maintains the pressure set by the pressure sensor 62. Adjust automatically. Extinction,
Overdosage can be improved by improving the control of fluid pressure between pumps 4 (1+54). If dialysate pressure is accurately controlled and regulated in hemodialysis operations, the permeate membrane pressure It is connected to a dialyzer ('/I1. processing device 12) and controlled so that a desired excess amount can be obtained.

The configuration shown in FIG.
! It can be used with most types of extracorporeal treatment methods, such as hyperthermia and plasmapheresis. The arterial line and venous line pumps are a single unisort, and a pump insert for sending liquid from the arterial line storage tank to the liquid processing device 12 and a pump for sending the venous line storage tank-1 liquid from the liquid processing device 12. Practical experience with so-called double-head blood pumps connecting both inserts has shown that such a device is particularly suitable for carrying out a new type of plasmapheresis operation.

FIG. 3 shows a configuration including the double head blood pump described above. In the above-mentioned double-head blood pump, in actual operation, the amount of fluid extracted from the patient and the normal Uft are the same, and the saliva processing device 12 is connected between the two pumps.
It is used to ensure that the drug is returned to the patient, regardless of its characteristics. For example, in conventional hemodialysis treatment that exceeds 3 to 4 hours, the dialysate in the liquid processing device 12 is 1100 mm and 11 g.
Since the pressure is maintained at a negative pressure lower than atmospheric pressure, no excess growth or weight loss of the patient occurs. This is associated with sufficient or reliable occlusion of the arterial and venous line pump inserts within the double head blood pump.

To explain in more detail with reference to Figure 3, Figures 1 and 2
Components common to the figures are indicated by the same reference numerals. However, the configuration of FIG. 3 includes the double-head blood pump described above, and in view of the similarity (but not identity) in function to the pump 40.54 of FIG. 2, the same reference numeral 40.
I'm asking about -54.

The double-head blood pump 40-54 discharges the same amount of liquid to the patient as is returned to the patient, but the liquid processing device 12 (plasmaferase device 12 in FIG. 3) contains the liquid. The amount of fluid entering the stream, eg, downstream or upstream of a double-head blood pump, is passed through the M membrane material formed in the plasmapheresis device 12 to provide exactly the same amount of fluid.

Arrow 30 again indicates the direction of liquid flow. Therefore,
Once the incoming liquid (1) is monitored, the amount of liquid (plasma) forced through the thin film material is automatically monitored again. FIG. 3 shows a container 66 containing a replacement or replacement fluid and a pressure chamber 70 provided downstream of the plasmapheresis device 12 and upstream of the double-sol' blood pumps 40-54 for replacement. A liquid pump 68 is shown for inflowing liquid. A pressure transmission pipe 72 is provided to transmit the pressure of the gas cushion 74 within the pressure chamber 70 to the pressure sensor 78. Pressure sensor 78, for example 0-200 am
It is easily adjustable to any set pressure value between 11 g. The liquid pump 68 can be a variable speed pump and can vary its speed to maintain the pressure value set by the pressure sensor 78. A conductive wire communicating from the pressure sensor 78 to the liquid pump 68 provides a pressure responsive feed hack to the pump 68. However, pump 68 could also be a manually adjustable displacement variable speed pump through which the desired amount of displacement liquid is delivered per unit time.

In such a device, it is preferable to provide a pressure sensor 78 and a feedbank to the pump 68, which, for example, ensure that the hydraulic pressure in the plasmapheresis device 12 does not exceed a maximum limit. In this latter device, the pressure sensor 78 and the feedhack to the pump 68 operate to ensure that: For example, plasma is extracted from whole blood at a maximum safe pressure value that can be set at the pressure sensor 78 in excess of the capacity of the plasmapheresis device 12 at the maximum safe pressure value that can be set at the pressure sensor 78.
Ensure that the pump speed of pump 68 is not manually set to Fllt.

The method and apparatus according to the invention also include particular considerations regarding ease of use and safety. Regarding ease of use, for example in the device of FIG. 1, the high pressure sensor 42 can be set to a 1rjt pressure value of, for example, 250IIIrA11 g, and the low pressure sensor 48 can be set to a low pressure value of, for example, -120 mm11 g. For a standard blood tubing set with a standard pump insert, the speed of the pump 40 can also be set to deliver 200 mβ/min of blood to the fluid processing device 12. Other than standard injection operations, no person i is actually required. Most preferably, however, the pump 40a;+- is manually adjustable so that the pump can be adjusted such that its maximum stroke volume, and hence its maximum usage, consists of the effective blood flow from the patient's tubes or vessels. . Also, the pump speed is too high (resulting in a pressure lower than the low pressure value)
In some cases, an alarm (not shown) condition may occur, indicating that not enough blood is available from the patient's tubes or vessels. In this case it is necessary to reduce the pump speed.

Similarly to the above, the pressure sensor 4 in the devices shown in FIGS.
High and low pressure values can also be set within 2 and 48.

Further, the pump 40 in FIG. 2 or the double head blood pump 40-54 in FIG. 3 can be set to deliver a fixed amount of blood to the liquid processing device 12 per unit time. but,
For the same reasons discussed in FIG. 1, pump 40 of FIG. 2 and double head blood pumps 40-54 of FIG. 3 are most preferably variable speed pumps whose speeds are manually adjustable.

Due to the self-adjustability of the device of the invention, the stroke volume for each selected pump speed is automatically maximized. There is no need to count cycles or calculate stroke volume. For example, the speed of the pump 40 is
1i control can be read directly from the pump speed adjustment knob. Two limit situations can be described: first, when a virtually unlimited amount of fluid can be obtained from the patient, such as when a large catheter is placed in a large central canal; This is the case when the volume is limited, for example in small tubes.

With particular reference to FIG. 2, the pressure adjustment automatically adjusts pump 54 to follow the speed of pump 40, thereby maintaining the pressure value set at pressure sensor 62.

Regarding operational safety, the following can be understood from the above. However, any change in resistance to flow automatically responds as a change in the time at which the clamping device 20 switches from the one-field position to the other limit position. This feature of automatic εI+, ] clauses provides a significant advantage as it can eliminate the need for various monitoring functions. This novel feature also allows for simple alarm condition control. If the time interval is too long, for example, 5 seconds or more, then immediately the pressure is lower than the lower limit pressure value in the arterial line 10 for more than 5 seconds, or for more than 5 seconds. 2, e.g. by a timer or delay timer (not shown) that stops the pump or both pumps when the pressure is higher than the upper pressure limit in the intravenous line reservoir 32;
An alarm condition can be generated. Arterial line reservoir 1o0) If the low pressure value is greater than or equal to the operating time, the blood pump 4o indicates that the velocity is too high for the amount of fluid passing from the fluid source to the arterial line reservoir 1o, or that the single lumen catheter is Displays that there is a failure. Similarly, if the pressure inside the intravenous line storage tank 32 is higher than the operating time, a failure is displayed. Another most preferred alarm condition indicating that the pump has stopped is when a low pressure value of about atmospheric pressure occurs within the venous line reservoir 32. That is,
This indicates that the intravenous line 3o is disconnected or the single lumen catheter is not in place. The alarm condition that will cause the pump to stop is when a high pressure value of approximately atmospheric pressure develops in the arterial line reservoir 10, which means that the arterial line 14 is disconnected or the catheter is in place. Show that there is no.

The device of the present invention, as shown, allows for a very flexible user interface.

First, for example, the pressure value is sent to the pressure sensor 42. /18, (also pressure sensor 62 for certain special liquid treatment devices 12) In the configuration shown in FIGS. , the pump 40 may be operated. The opening and closing of the pulse line and the venous line are performed automatically.
4 automatically follows the speed of the pump 4o to maintain the pressure value set by the pressure sensor 62.

[Brief explanation of the drawing]

FIG. 1 is a schematic diagram of an apparatus and liquid lines operating using a single liquid pump. FIG. 2 is a schematic diagram of an apparatus and liquid line operating -ζ using a lltl heavy body of 2+[1,i. FIG. 3 shows a device operating using a so-called double-head blood pump and a pump for introducing substituent fluid. FIG. In the diagram, 41 for IO arterial line? b) ■ 12 Liquid processing device 14 Arterial line 16 First arm 18 Single lumen catheter device 20 Arterial and venous opening/closing means 22 Central member 24 First contact membrane 1-: 30 Arrow 32 Reservoir for venous line 36 Second arm 38 21 Concubine iQJ! Niremen 1 to 40 Single type lix body pump 42 High pressure value sensor 44 Pressure transmission pipe 45 Conductive wire 46 Gas cushion 48 Low pressure value sensor 50 Pressure transmission pipe 52 Gas cushion 111th Lieutenant Figure 2 348-

Claims (1)

[Claims] 1. A single lumen catheter device that takes untreated fluid from a fluid source through a single lumen catheter and an arterial line, passes it through a fluid treatment device, and returns treated fluid to the fluid source through a venous line and a single lumen catheter. a method for controlling closing of an arterial line and substantially simultaneously opening an arterial line in a fluid source for receiving raw fluid from a fluid source; An arterial line storage tank is provided upstream of the processing device, an arterial line opening/closing means is provided upstream of the arterial line storage tank, and a venous line storage tank is provided downstream of the liquid processing device to receive the processing liquid from the liquid processing device. providing a venous line opening/closing means downstream of the venous line storage tank; introducing untreated liquid from the liquid source into the arterial line storage tank through the arterial line; and introducing the untreated liquid from the arterial line storage tank. flowing through the fluid treatment device into the venous line reservoir, closing the arterial line and substantially simultaneously opening the venous line in response to the -F limit amount of treatment fluid available in the venous line reservoir, thereby causing the treatment fluid to flow into the venous line reservoir; 2. A method comprising the steps of: returning the fluid to the fluid source; and closing the venous line and simultaneously opening the arterial line in response to a lower limit amount of untreated fluid obtained in the arterial line. The method according to claim 1, wherein the liquid is continuously passed through the liquid processing device from the arterial line storage tank, and the processing liquid is continuously accumulated in the venous line storage tank.3. The system detects the upper limit of the amount of processing liquid that can be obtained in the intravenous line storage tank by detecting the upper limit pressure value that occurs in the gas cushion in the intravenous line storage tank when the intravenous line is closed. 1. The method of claim 1. 4. Passing the untreated liquid from the arterial line reservoir through the processing device, while the arterial line is closed, to a gas cushion in the arterial line reservoir. The method according to claim 1, wherein the lower limit amount of untreated liquid obtained in the arterial line reservoir is detected by detecting the lower limit pressure value that occurs.5. a 27th body pump is provided downstream of the liquid treatment device and upstream of the intravenous line storage tank, and the pump speed of at least one pump is set to the first 3. The method of claim 2, wherein the method is variable in response to fluid pressure fluctuations between the liquid pump and the second liquid pump. 6. An injection point is provided on the downstream side of the liquid processing device and upstream of the second liquid pump, so that a replacement liquid can be introduced into the processing liquid to replace the liquid removed from the liquid processed by the liquid processing device. A method according to any one of claims 1 to 5. 7. The arterial line in a single lumel catheter device, which takes untreated fluid from the fluid source through the sysigluon catheter and the arterial line, passes through the fluid treatment device, and returns the treated fluid to the fluid source through the venous line and single lumel catheter. 2. An apparatus comprising: means for controlling a venous line to be closed and substantially simultaneously opened to the venous line; at least one liquid pump means for pumping from an arterial line reservoir disposed in the arterial line through the fluid handling device into a venous line reservoir disposed in the venous line downstream of the fluid handling device; , upper limit sensor means for detecting an upper limit amount of processing liquid available in the venous line storage tank; and in response to a first signal transmitted by the upper limit sensor means to the arterial line occlusion means, the arterial line is closed; an arterial line occlusion means for closing the venous line and substantially simultaneously opening the venous line; a lower limit sensor means for detecting a lower limit amount of untreated liquid to be immized in the arterial line storage tank; venous line occlusion means for closing the venous line in response to a second signal generated by the venous line and substantially simultaneously closing the venous line and opening the arterial line. 8. The pump means is continuously operable to continuously pump untreated fluid from the arterial line reservoir (111) through the fluid treatment device into the venous line reservoir.
Apparatus described in section. 9. Claim 7, wherein the first pump is operable between the arterial line reservoir and the treatment device, and the second pump is operable between the treatment device and the venous line reservoir. Apparatus described in section. 10. The device according to claim 9, wherein one of the two pumps is a variable speed pump. 11. The variable speed pump responds to pressure fluctuations in the liquid flowing between the two pumps. 11. The apparatus of claim 10, wherein the second pump is variable in response to pressure fluctuations in the liquid between the two pumps. 11. The device according to claim 9. 13. The device according to claim 9, wherein at least one of the two pumps is a constant speed pump. 14. The constant speed pump has a constant speed manually adjustable. 15. The device according to claim 13, wherein the first pump is a constant speed pump; 12. The apparatus of claim 11, further comprising a pressure sensor for controlling the variable speed pump and means for varying the variable speed pump in response to a signal transmitted to the variable speed pump by the pressure sensor. The sensor is the device according to claim 16, which includes a pressure (11) provided downstream of the liquid processing device and upstream of the second pump.18. 18. The apparatus of claim 17 including means for connecting to an infusion line for introducing replacement fluid to replace fluid removed from the venous line.19. Claim 7, wherein the first signal is transmittable to an arterial line occlusion means when occurring within a sac reservoir.
Apparatus described in section. 20. The lower limit sensor means is capable of transmitting said second signal to the venous line occlusion means when a preselected constant low pressure value occurs within the arterial line reservoir; equipment. 21. Of the two arms of the single lumen catheter, the first catheter protruding end for connecting two arms, the second catheter protruding end for connecting with the inlet of the liquid treatment device, and the first catheter protruding end for connecting the two arms of the single lumen catheter, and and a second freedom η') 1, and a first arterial line reservoir between the arterial line reservoir and the second freedom 111 for coupling with the arterial line peristaltic pump.
an arterial line having an oscillating tube portion, a first free end for coupling with the outlet of the fluid handling device, and a second free end of the sump for coupling with another of the two arms (7) of the single lumen catheter; a free catheter 1; a reservoir for the intravenous line between the first and second free ends of the intravenous line; 411 and said first free tube α1″ (1 and said second ff:i &
A liquid line device consisting of a pressure tank between dynamic tube sections.