• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    The invention relates to a control device and method for hemodialysis and hemofiltration therapy, mainly for the treatment of chronic kidney failure. The aim of the invention is to enhance the functionality by providing an individual regimen of therapy or hemodialysis, or hemofiltration or sequential ultrafiltration. The outlet of the pump 1 is connected to the inlet of the dialyzer 26 through the vessel 7, which is connected through the pipe 10 to the inlet of the flow meter 11, and the adjustable hydroresistance 12 is installed on the line connecting the vessel 7 and the dialyzer dial 26, the measuring output of the flow meter 11 is connected to the input of the central unit 13 controls, the outputs of which are connected to control inputs of adjustable hydraulic resistance 12 and switchable valves 15, 16, 17. In this case, the input of the dialyzer 26 can be connected to the output of the pump 19, and the output of the dialyzer 26 - to in resistance house 20, the degree of ultrafiltration is defined as the difference between the flow through the flow meter 11 and the performance of the pump 1, which is determined by the control signal at the output of the central control unit 13, while to determine the compliance of the pump I with the control signal, the dialysate flow is directed through the bypass. 1 il. i W w od: 05 00
    公开号:SU1316681A1
    申请号:SU817771875
    申请日:1981-06-24
    公开日:1987-06-15
    发明作者:Зимон Вольфганг；Бруннер Юрген
    申请人:Феб Месгеретеверк Цвенитц (Инопредприятие)；
    IPC主号:
    专利说明:

    The invention relates to a device and for hemodialysis and hemofiltration therapy, a method of controlling it and can be used advantageously for the treatment of chronic kidney failure.
    A device for treating blood outside the body is known, comprising a pump and a device for circulating the patient’s blood outside the body, including a membrane filter (German Federal Pro- cedure No. 2754810, class A 61 M 1/03, 1979).
    However, the known device provides only hemofiltration.
    A device for treating blood outside the body is known, comprising a pump and a device for circulating blood outside the body (German Application No. 2832870, class A 61 M 1/03, 1980)
    A disadvantage of this device is that it does not maintain the balance of the fluid content in the blood.
    It is also known a device for treating blood outside the body, containing a dialyzer, two pumps, a dialysate source, a device for removing gas from the solution and its heating system, a bypass and adjustable hydraulic resistance installed on the input line of the dialyzer (Germany Application No. 2506039, A 61 M 1/03, 1972.
    However, the lack of functionality of this device does not allow for an individual regimen of hemodialysis or hemofiltration or sequential ultrafiltration.
    The purpose of the invention is to expand the functional capabilities of the device for treating the cancer outside the body by providing an individual regimen of hemodialysis, or hemofiltration, or sequential ultrafiltration.
    The goal is achieved by the fact that the outlet of pump 1 is connected by the input of dialyzer 26 through vessel 7, which through pipe 10 is connected to the input of flow meter 11, and adjustable hydraulic resistance 12 is installed on the line connecting vessel 7 and dialyzer 26, measuring output The flow meter 11 is connected to the input of the central control unit 13, the outputs of which are connected to the control inputs of the adjustable hydraulic resistance 12 and switchable valves 15, 6 and 17. In addition, the dialysate input. Section 26 is connected to the output of pump 19, and the output of the dialyzer 26 is connected to an input of adjustable hydraulic resistance 20. The degree of ultrafiltration is defined as the difference between the flow through the flow meter 11 and the performance of pump 1, and the capacity of pump I is controlled by the output signal of the central unit 13 controls, in order to determine compliance with performance
    five
    five
    0
    0
    five
    pump 1 to the control signal. At its input, the dialysate flow is directed through the bypass.
    The drawing schematically shows the proposed device.
    The first pump 1 draws clean water from the water tank 2. Between this pump 1 and the water tank 2 there are heating units 3 for heating the water to body temperature and the gas removal device 4. At the same time, this pump 1 sucks the dialysis concentrate from reservoir 5. The corresponding suction pipe is shut off by means of a magnetic valve 6. In pump 1, the dialysate is mixed from water and concentrate approximately in a ratio of 34: 1 or in ratios required for bicarbonate dialysis. Pump 1, which is the metering unit, delivers the preheated and degassing mixture to vessel 7. From vessel 7, second pump 8 delivers dialysate through dialyzer 26, then dialysate is usually discharged. Pump 8 is also metering. Pumps 1 and 8, forming a single structural structure, are powered by a common drive 9. Pump 1, compared to pump 8, has a higher feed rate for an exactly constant factor (for example, 5%). This excess flows from vessel 7 through line 10 to the discharge.
    Through the pipe 10, the vessel 7 is purged, as a result of which the liquid in the vessel 7 is always under a pressure equal to the atmospheric pressure. This can be achieved by using a hole in the vessel 7 with overflow and a vent hole in the Shily pipeline (which is preferable) by making sections and the required level of flow of the pipeline 10. On the pipeline 10 there is a flow meter 11, which produces an electrical signal proportional to the flow rate, for example turbine flow meter with an accuracy of up to the maximum flow rate of 5 l / h.
    YQ with max 5
    five
    0
    With the help of an installation valve, which is driven by a magnetic or electromagnetic actuator, a negative pressure can be created in the hydraulic system, which, when the blood circulation is closed, leads to ultrafiltration of fluid from the blood into the dialysate. This amount of fluid is connected to the flow created by pumps 1 and 8, so that fluid can flow through a single opening of the system, pipe 10. The difference between the flows through pipe 10 when the dialyzer 26 is connected and when dialysate flow is taken off bypass pipe 18 is a direct ultrafiltration measure . The value of the main flow through the pipe 10 without dialyzer is automatically subtracted by the central control unit 13 from the signal of the actual value of the flow meter (zero point shift), so that the actual
    the value of the degree of ultrafiltration. In order to avoid an error in the constant dispensing of the pump 8 as a result of the gases released in the dialyzer, a separator 14 is located in front of the pump 8. It can be made in the form of a float chamber.
    The need to achieve high accuracy is identical to proportional dosing of pumps 1 and 8 (the accuracy of measuring the degree of ultrafiltration should be 50 ml / h with dialysate flow up to 50 l / h, and each fluctuation of the main flow can lead to a direct indication error.) with each change of the adjustment parameters and at set intervals, preferably 30 minutes, with the help of the central control unit 13, to ensure the automatic closing of the valves 15 and 16 and the short-term opening (up to ation stream in line 10) the valve 17 in the conduit 18. baypas- nom Then through conduit 10 flows only the base stream. The central control unit 13 automatically shifts the zero point in accordance with these measurements, therefore, the accuracy of the ultrafiltration measurement becomes independent of drift phenomena, tolerances and dosing dependencies on the system variable parameters. The bypass line 18 is located parallel to the dialyzer 26 and has approximately the same hydraulic resistance with it in order to avoid errors as a result of different pressure drops. The central control unit 13 contains control systems which, upon entering a predetermined value of the degree of ultrafiltration or the total amount of ultrafiltration and a predetermined dialysis time, allow to achieve the desired degree of ultrafiltration. The control loop is closed by a signal of the actual value of the flow meter 11. In order to quickly reach the predetermined degree of ultrafiltration, the average ultrafiltration degree for this type of dialyzer is additionally entered into the central control unit 13, which defines the corresponding transmembrane pressure as the initial value using the adjusting valve 12. Significant deviations between the transmembrane pressure practically necessary for a certain degree of ultrafiltration and In theory expected transmembrane pressure for a particular dialyzer indicate a system malfunction or dialyzer 26 and the central control unit are outputted as an alarm. The central control unit is preferably made with mathematically oriented logic with microprocessor control, with all measurement functions being digitized before processing.
    The proposed device also contains an additional pump 19 and a second installation valve 20, which serve to create a positive pressure on the membrane of the dialyzer 26, as a result of which a transmembrane pressure equal to zero or a negative transmembrane pressure arises. The pump 19 serves only to increase the pressure and should not have any metering properties (centrifugal pump). If the required degree of ultrafiltration is less than the degree that is achieved with the fully open setting valve 12, then the pressure boosting system is automatically activated by means of the central control unit 13.
    Thus, the device performs hemodialysis with ultrafiltration measurement and maintaining balance. By closing valve 16 and opening valve 17, this device works as a clean filtration system, since
    0 in the membrane of the dialyzer 26, through the open conduit 21, a vacuum created in the system is applied and, in accordance with the resulting transmembrane pressure through conduit 21, a certain amount of liquid is exhausted. The remaining functions of the instrument remain unaffected. Ultrafiltration is measured again through the flow meter 11, and to determine the main flow, only valve 15 is closed. To save dialysis concentrate and energy, the heater 3 is automatically switched off in filtering mode and the concentrate is supplied by means of the valve 6. Drive 9 of pumps 1 and 8 minimizes flow through bypass line 18.
    For the transition from ultrafiltration to dialysis, approximately 10 minutes before the programmed start of dialysis, the heater 3 is turned on and the concentrate is supplied through the central control unit 13, so that by the beginning of dialysis there is a stable mixture.
    0 The device is additionally equipped with a system for hemofiltration, which produces an elimination of 20 liters of liquid, which is compensated by simultaneously replacing the liquid in the blood circulation circuit. The degree of substitution is calculated from the difference between
    5 by the measured degree of ultrafiltration and the medically necessary degree of dehydration by means of the central control unit 13. This value is decisive for controlling the operation of the unit 13 by the operation of a conventional infusion pump 22, which
     delivers the required amount of fluid from the supply vessel 23 to the circulation circuit. When shown, the additive can be made before the dialyzer 26 (predilution) or after the dialyzer 26 (post5 dilution). For this purpose, valves 24 and 25 are provided which allow the selection of a method or a programmed shift controlled in time. As with hemo
    Filtrations can take place to a degree of ultrafiltration up to 10 l / h, the measurement range of the flow meter 11, which is automatically produced by the central control unit 13, is necessary.
    The proposed device provides a freely programmable change of dialysis, ultrafiltration and ultrafiltration with substitution (hemofiltration) for dialysis with ultrafiltration and substitution (hemorrhoids 26 through the vessel 7, which is connected to the inlet of the flow meter 11 through conduit 10, and adjustable hydraulic resistance 12 is installed on the line connecting the vessel 7 and the dialyzer input 26. The measuring output of the flow meter 11 is connected to the input of the central control unit 13, the outputs of which are connected to the control inputs of the regulated The hydraulic resistance 12 and switch
    diafiltration) to achieve optimal 10 valves 15, 16 and 17.
    individual individual therapy regimen.2. The device according to claim 1, wherein
    that the inlet of the dialyzer 26 is connected to the outlet of the pump 19, and the outlet of the dialyzer 26 is connected to the inlet of adjustable hydraulic resistance 20.
    3. A method of controlling an out-of-body blood treatment device, characterized in that the degree of ultrafiltration is defined as the difference between
    权利要求:
    Claims (1)
    [1]
    Claims 1. Outside blood treatment device
    containing a dialyzer, two pumps, a dialysate source, a device for removing gas from the solution and its heating system, a bypass and adjustable flow resistance established
    15
    flow through the flow meter 11 and the output of the dialysator input line, the difference between the pump 1 and the output
    pump 1 is determined by the value of the control signal at the output of the central control unit 13, and to determine whether the pump I performance corresponds to the control signal at its input, the dialysate flow is directed through the bypass.
    In order to expand functionality by providing an individual regimen of hemodialysis or hemofiltration, or sequential ultrafiltration, the output of pump 1 is connected to the inlet of dialyzer 26 through vessel 7, which is connected through pipe 10 to input of flow meter 11, and adjustable hydraulic resistance 12 installed on the line connecting the vessel 7 and the dialyzer input 26. The measuring output of the flow meter 11 is connected to the input of the central control unit 13, the outputs of which are connected with the control inputs of the adjustable flow resistance 12 and switch
     valves 15, 16 and 17.
    flow through the flow meter 11 and the performance of the pump 1, and the performance
     pump 1, and performance
    pump 1 is determined by the value of the control signal at the output of the central control unit 13, and to determine whether the pump I performance corresponds to the control signal at its input, the dialysate flow is directed through the bypass.
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    同族专利:
    公开号 | 公开日
    BG39335A1|1986-06-16|
    DE3122756A1|1982-06-09|
    DD157952A3|1982-12-22|
    CS485581A1|1984-06-18|
    YU190881A|1983-12-31|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    EP0121085B1|1983-03-01|1986-09-10|Sartorius GmbH.|Apparatus for the preparation of medical infusion solutions|
    DE3439661C2|1984-10-30|1988-04-14|Fresenius Ag, 6380 Bad Homburg, De|
    US4828543A|1986-04-03|1989-05-09|Weiss Paul I|Extracorporeal circulation apparatus|
    IT1320024B1|2000-04-07|2003-11-12|Gambro Dasco Spa|METHOD FOR ADJUSTING THE INFUSION IN A DIALYSIS MACHINE AND DIALYSIS MACHINE FOR THE APPLICATION OF THE MENTIONED METHOD.|
    US7241272B2|2001-11-13|2007-07-10|Baxter International Inc.|Method and composition for removing uremic toxins in dialysis processes|
    AU2003249296A1|2002-07-19|2004-02-09|Baxter Healthcare S.A.|Systems and methods for performing peritoneal dialysis|
    US8029454B2|2003-11-05|2011-10-04|Baxter International Inc.|High convection home hemodialysis/hemofiltration and sorbent system|
    US8038639B2|2004-11-04|2011-10-18|Baxter International Inc.|Medical fluid system with flexible sheeting disposable unit|
    US8057423B2|2007-07-05|2011-11-15|Baxter International Inc.|Dialysis system having disposable cassette|
    US8114276B2|2007-10-24|2012-02-14|Baxter International Inc.|Personal hemodialysis system|
    US9415150B2|2007-11-09|2016-08-16|Baxter Healthcare S.A.|Balanced flow dialysis machine|
    US8057679B2|2008-07-09|2011-11-15|Baxter International Inc.|Dialysis system having trending and alert generation|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    DD80223288A|DD157952A3|1980-08-13|1980-08-13|DEVICE FOR EXTRACORPORAL TREATMENT OF BLOOD|
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