US3508656A - Portable dialysate supply system - Google Patents

Portable dialysate supply system Download PDF

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Publication number
US3508656A
US3508656A US3508656DA US3508656A US 3508656 A US3508656 A US 3508656A US 3508656D A US3508656D A US 3508656DA US 3508656 A US3508656 A US 3508656A
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United States
Prior art keywords
dialysate
pump
dialysate fluid
water
concentrate
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Expired - Lifetime
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English (en)
Inventor
Earl J Serfass
Vernon H Troutner
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Milton Roy LLC
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Milton Roy LLC
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1654—Dialysates therefor
    • A61M1/1656—Apparatus for preparing dialysates
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1654—Dialysates therefor
    • A61M1/1656—Apparatus for preparing dialysates
    • A61M1/166—Heating
    • A61M1/1664—Heating with temperature control
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/168—Sterilisation or cleaning before or after use
    • A61M1/1686—Sterilisation or cleaning before or after use by heat
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00—Fluid handling
    • Y10T137/0318—Processes
    • Y10T137/0324—With control of flow by a condition or characteristic of a fluid
    • Y10T137/0329—Mixing of plural fluids of diverse characteristics or conditions
    • Y10T137/034—Controlled by conductivity of mixture
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00—Fluid handling
    • Y10T137/2496—Self-proportioning or correlating systems
    • Y10T137/2499—Mixture condition maintaining or sensing
    • Y10T137/2509—By optical or chemical property

Definitions

  • dialysate fluid concentrate Water and dialysate fluid concentrate are mixed to form dialysate fluid which is supplied to the dialyzer.
  • concentration of the dialysate fluid is continuously monitored by a conductivity cell.
  • the output of the conductivity cell is applied to control a pump which supplies the concentrate.
  • This pump also has a secondary speed control loop.
  • a tachometer in the secondary loop corrects speed variations caused by changes other than the conductivity cell output signal.
  • hemodialysis One of the most successful means for treating chronic kidney failure is by hemodialysis using an artificial kidney system.
  • hemodialysis the patients blood is circulated from an artery through an artificial kidney, or dialyzer, where excess water and waste materials are removed. The blood is returned to the patients veins.
  • a central station dialysate supply system for supplying dialysate fluid to a number of patients in a hospital is described in Transactions of the American Society of Artificial Organs, vol. X, 1964, page 107, Grimsrud, Cole, Lehman, Babb and Scribner.
  • All of the blood dialysis supply systems described above use a two-stroke pump to mix dialysate concentrate with water to produce a supply of dialysate fluid.
  • These pumps have very accurate controlled strokes so that the water and the concentrate are mixed in precise Volumetric proportions.
  • the pumps are relatively expensive and bulky. Further, extensive movement of the pump will affect the calibration so they are not suitable for a truly portable system.
  • dialysate fluid does not necessarily have a controlled concentration.
  • concentration of the dialysate fluid changes. What is required in dialysate supply systems is the production of a dialysate fluid having controlled sodium and chloride concentration at a prescribed temperature.
  • the variation of the concentration of the dialysate fluid with change in temperature is a particular problem in a system having extensive monitor controls such as the systems described in the above-mentioned Serrez reference and Serrez et al. patent application. These systems have a concentration monitor which sounds an alarm when the concentration of the dialysate fluid varies outside of preset limits. When dialysis treatment is performed during the night, as it is frequently, the patient will often be awakened by the alarm when the concentration of the dialysate fluid changes because of a change in the ambient temperature of the top water.
  • This invention relates to blood dialysis supply systems and more particularly to a portable blood dialysis system.
  • the dialysate fluid and tap water are mixed in a system which includes a servo controlled pump.
  • the servo controlled pump supplies concentrate to a mixer.
  • the water and concentrate are mixed to form dialysate fluid having a controlled concentration.
  • a conductivity cell monitors the concentration of the dialysate fluid and the resultant signal controls the pump. This permits the use of a relatively simple, compact, inexpensive pump in the system rather than more costly and bulky volumetric measuring devices.
  • a secondary control loop is provided for the pump by a tachometer control.
  • the tachometer senses these changes in the pump speed and quickly restores the pump to its normal operating speed.
  • FIG. 1 shows a diagram of the portable dialysate supply system
  • FIG. 2 shows a schematic diagram of the control loops for the concentrate pump.
  • FIG. 1 the block diagram shows the circulation of dialysate fluid and the electrical control functions performed by the system.
  • the hydraulic conections are shown with heavy lines while the electrical connections are shown with lighter lines.
  • the dialysate fluid to be circulated in the dialyzer is a mixture of tap Water from the source 34 and concentrate from the concentrate reservoir 15.
  • the composition of the dialysate fluid may be changed in accordance with the therapy required for a particular patient. In general, the composition of the dialysate fluid is described in Hemodialysis for Chronic Renal Failure, Freeman, M'aher and Schreiner, Annals of Internal Medicine, volume 62, No. 3, March 1965.
  • the concentrate and tap water are mixed in the proper proportions in the mixer 11. Water from the source 34 passes through the pressure reducing valve 2 to the air trap and vent 3. Overflow from the air trap and vent 3 goes to drain 35.
  • a flow control valve 4 provides the desired flow and flow meter 5 monitors the flow of water.
  • the water passes through the normally open solenoid valve 6.
  • the norm-ally open valve 6 is closed and the manually operated by-pass valve 7 is preset to provide about one-fourth the flow of water which is heated to a much higher temperature. Automatic reduction of water flow during sterilization is an important feature resulting in reduction of heater size, cost, and power requirements.
  • the water is supplied to an electric heater 8 which produces water at the desired temperature, approximately 37 C. for normal dialysis and approximately 95 C. for sterilization.
  • Thermistor sensing circuitry 9 is provided for controlling the heater 8, that is, varying the electric current to obtain the desired heating.
  • Thermistor circuitry 10 monitors the water temperature and actuates an alarm relay when the water temperature is outside of normal limits.
  • a controllable volume pump 13 supplies dialysate concentrate from the reservoir 15 through the check valve 12 to the mixer 11.
  • the mixed water and concentrate passes through the concentration control element 18 on its way to the dialyzer.
  • the concentration control element 18 is a conductivity cell which produces an electrical signal representing the concentration of the dialysate fluid supplied from the mixer 11.
  • the electrical signal produced by the conductivity cell is applied to the pump 13 to control the volume of concentrate supplied to the mixer 11 so that the concentration of the dialysate fluid remains constant.
  • the control circuitry for this control loop is shown in block form in FIG. 2.
  • a secondary speed control loop is provided for the pump 13.
  • This control loop includes a tachometer 33 driven at the same speed as the pump 13.
  • the tachometer 33 produces an electrical signal representing the speed of the pump and this is applied to maintain the speed of the pump constant regardless of variations other than conductivity changes.
  • Another conductivity cell 19 is provided for monitoring the conductivity of the dialysate fluid.
  • the dialysate fluid is supplied to the constant head vessel 20.
  • the head vessel 20 has an overflow outlet 21 coupled through a drain cup 24 to the gravity drain 35.
  • the head vessel 20 provides a supply of dialysate fluid at a constant pressure to the dialyzer.
  • the dialysate fluid is supplied through pressure control valve 25 to the inlet dialysate port of the dialyzer which may be of the Kiil type, for example.
  • blood ports are provided for passage of blood on one side of a membrane and dialysate ports are provided for passage of dialysate fluid on the other side of the membrane.
  • the dialysate fluid passes through the dialyzer on one side of the membrane and out through the outlet dialysate port.
  • a pressure gauge 27 is provided to monitor the negative pressure at the outlet of the dialyzer.
  • Flow meter 28 is provided to monitor the flow rate through the dialyzer and blood leak detector 29 is provided to sense the presence of blood in the dialysate fluid.
  • a vacuum breaker 30 is provided so that if the system becomes clogged, a large negative pressure which might break the membrane will not be applied to the dialyzer.
  • the eflluent pump 32 applies the negative pressure through check valve 31, and regulates dialysate flow through the dialyzer.
  • the temperature monitor thermistor circuit 10 the conductivity monitor 19, over-temperature sensor 23, pressure gauge 27, and blood leak detector 29 are all monitoring circuits of the type in which a set of relay contacts are activated when the monitored condition exceeds its adjustable preset limits. All of these relay contacts are connected in a circuit to control the volt power for the eflluent pump 32. When any monitored condition exceeds its limits the relay contacts will be activated and power will be cut off to the pump 32.
  • a level monitoring probe, 22, of the conductivity type located in the head vessel is also included in this control circuit. If dialysate make-up rate becomes less than the flow rate to the dialyzer, the level drop in the head vessel is sensed and the efiluent pump 32 turned ofi.
  • an Ag, AgCl detector may be provided. Such a detector would similarly be connected to monitor the chloride content of the dialysate fluid and turn oil the pump 32 when the concentration is outside the desired limits.
  • the silver, silver chloride detector could also be used in place of concentration control element 18 to control the pump 13.
  • the system is electrically programmed to automatically proceed through the following steps; rinse, pre-sterilize, normalize, monitor test, alarm test, system test, dialyze, after-sterilize.
  • the control system and monitors are interlocked to prevent the flow of anything other than normal dialysate to the dialyzer.
  • the system for controlling the pump 13 in accordance with the control signal from the concentration monitor can be of well known type.
  • One suitable system is shown in block form in FIG. 2.
  • the conductivity cell includes a sensor 36 for determining conductivity.
  • Another sensor 37 which is temperature sensitive, provides temperature compensation for the conductivity cell 36.
  • the sensors 36 and 37 are connected in a bridge circuit 38. Variations in the conductivity from a given setpoint produce an error signal which is amplified in amplifier 39.
  • the phase detector 40 senses the phase of the error signal which is an indication of whether the conductivity is above or below the setpoint.
  • the error signal is compared with an adjustable setpoint in the setpoint control 41.
  • the error signal from the setpoint control 41 is compared with the signal from tachometer 33 in the error comparator 42.
  • the resultant signal is amplified in error amplifier 43 and power amplifier 44 and is used to drive the servo motor 45.
  • the servo motor 45 drives the concentrate pump 13 to provide the desired volume of concentrate to the mixing chamber 11.
  • a blood dialysis system comprising:
  • dialyzer having a membrane, blood ports for passage of blood through said dialyzer on one side of said membrane and dialysate ports for passage of dialysate fluid through said dialyzer on the other side of said membrane,
  • a mixer for mixing said water and said dialysate concentrate to produce dialysate fluid, said dialysate fluid being supplied from said mixer to said dialysate ports,
  • a controllable volume electrically driven pump connected to continuously supply dialysate concentrate from said source of concentrate to said mixer
  • a tachometer driven at the same speed as said pump, said tachometer producing a tachometer signal representing the speed of said pump, and
  • an eflluent pump for supplying said dialysate fluid from said mixer to said dialysate ports
  • monitoring means includes:
  • a blood leak detector each having a set of relay contacts which are activated when the monitored condition exceeds preset limits, said relay contacts being connected in a circuit to control the application of power to said eflluent pump.
  • a blood dialysis system comprising:
  • dialyzer having a membrane, blood ports for passage of blood through said dialyzer on one side of said membrane and dialysate ports for passage of dialysate fluid through said dialyzer on the other side of said membrane,
  • a mixer for mixing said water and said dialysate concentrate to produce dialysate fluid, said dialysate fluid being supplied from said mixer to said dialysate ports,
  • a controllable volume, constant speed, electrically driven pump connected to continuously supply dialysate concentrate from said source of concentrate to said mixer
  • a normally open solenoid valve connected between said source of water and said heater from supplying a normal flow of Water to said heater during dialysis, said normally open valve being closed during sterilization of said system
  • bypass valve in said bypass, said bypass valve being preset to provide about one-fourth said normal flow of water to said heater during sterilization so that said water is heated to a much higher temperature during sterilization.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Urology & Nephrology (AREA)
  • Anesthesiology (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Emergency Medicine (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
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  • Veterinary Medicine (AREA)
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US3508656D 1968-04-10 1968-04-10 Portable dialysate supply system Expired - Lifetime US3508656A (en)

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DE (1) DE1918063A1 (enrdf_load_stackoverflow)
FR (1) FR2005982A1 (enrdf_load_stackoverflow)
GB (1) GB1264833A (enrdf_load_stackoverflow)

Cited By (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3809243A (en) * 1972-01-26 1974-05-07 Sarns Inc Turbidity monitor for dialysis machines
US3844940A (en) * 1973-04-26 1974-10-29 Kopf D Systems System for measuring ultrafiltration rate
US3847809A (en) * 1972-07-03 1974-11-12 David Kopf Syst Proportioning system
FR2230379A1 (enrdf_load_stackoverflow) * 1973-05-25 1974-12-20 Bellco Spa
JPS5156785A (enrdf_load_stackoverflow) * 1974-11-13 1976-05-18 Yuno Rabo Kk
US4060485A (en) * 1975-06-09 1977-11-29 I T L Technology, Inc. Dialysis apparatus
US4079007A (en) * 1976-09-07 1978-03-14 Union Carbide Corporation Hemodialysis system with modular dialysate manifold assembly
US4119113A (en) * 1975-02-06 1978-10-10 Extracorporeal Medical Systems, Inc. Double-action proportioning pump
US4122010A (en) * 1976-02-26 1978-10-24 Gambro Ab Apparatus for treating blood
US4153554A (en) * 1977-02-22 1979-05-08 American Micro-Bionics Corp. Apparatus for use in artificial kidney system
US4191646A (en) * 1976-10-14 1980-03-04 Gambro Ab Apparatus for conducting fluids in a dialysis system
DE3930181A1 (de) * 1989-09-09 1991-03-21 Fresenius Ag Druckausgleichsgefaess fuer ein haemodialysekonzentrat
US5183760A (en) * 1989-05-19 1993-02-02 Sweetana Stephanie A Apparatus for in vitro determination of substances across membranes, biological tissues, or cell cultures
DE3744840C2 (enrdf_load_stackoverflow) * 1986-10-30 1993-08-05 Cobe Laboratories, Inc., Lakewood, Col., Us
US5591636A (en) * 1993-10-18 1997-01-07 Precision Instrument Design Membrane holder
US5599688A (en) * 1993-10-18 1997-02-04 Precision Instrument Design Device and method for circulating fluid over a membrane
US6146883A (en) * 1998-09-14 2000-11-14 Navicyte, Inc. Packing device for transporting confluent cell monolayers
US20080208111A1 (en) * 2007-02-27 2008-08-28 Deka Products Limited Partnership Peritoneal Dialysis Sensor Apparatus Systems, Devices and Methods
US20080216898A1 (en) * 2007-02-27 2008-09-11 Deka Products Limited Partnership Cassette System Integrated Apparatus
US20090008331A1 (en) * 2007-02-27 2009-01-08 Deka Products Limited Partnership Hemodialysis systems and methods
US20100051529A1 (en) * 2008-08-27 2010-03-04 Deka Products Limited Partnership Dialyzer cartridge mounting arrangement for a hemodialysis system
US20100192686A1 (en) * 2007-02-27 2010-08-05 Deka Products Limited Partnership Blood treatment systems and methods
US20100327849A1 (en) * 2006-04-14 2010-12-30 Deka Products Limited Partnership Sensor apparatus systems, devices and methods
US20110071465A1 (en) * 2008-01-23 2011-03-24 Deka Research & Development Fluid volume determination for medical treatment system
US8292594B2 (en) 2006-04-14 2012-10-23 Deka Products Limited Partnership Fluid pumping systems, devices and methods
WO2012122018A3 (en) * 2011-03-08 2012-11-15 Baxter International Inc. Non- invasive medical fluid level detection system and method applying radio waves
US8357298B2 (en) 2007-02-27 2013-01-22 Deka Products Limited Partnership Hemodialysis systems and methods
US8393690B2 (en) 2007-02-27 2013-03-12 Deka Products Limited Partnership Enclosure for a portable hemodialysis system
US8425471B2 (en) 2007-02-27 2013-04-23 Deka Products Limited Partnership Reagent supply for a hemodialysis system
US8491184B2 (en) 2007-02-27 2013-07-23 Deka Products Limited Partnership Sensor apparatus systems, devices and methods
US8562834B2 (en) 2007-02-27 2013-10-22 Deka Products Limited Partnership Modular assembly for a portable hemodialysis system
US8708950B2 (en) 2010-07-07 2014-04-29 Deka Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
US9028691B2 (en) 2007-02-27 2015-05-12 Deka Products Limited Partnership Blood circuit assembly for a hemodialysis system
US9078971B2 (en) 2008-01-23 2015-07-14 Deka Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
US9115709B2 (en) 1999-07-20 2015-08-25 Deka Products Limited Partnership Fluid pumping apparatus for use with a removable fluid pumping cartridge
CN105521527A (zh) * 2014-10-15 2016-04-27 克里斯托夫·杜姆沙特 透析浓缩物制备设备
US9517295B2 (en) 2007-02-27 2016-12-13 Deka Products Limited Partnership Blood treatment systems and methods
US9597442B2 (en) 2007-02-27 2017-03-21 Deka Products Limited Partnership Air trap for a medical infusion device
US9724458B2 (en) 2011-05-24 2017-08-08 Deka Products Limited Partnership Hemodialysis system
US9861732B2 (en) 2011-11-04 2018-01-09 Deka Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
US10201650B2 (en) 2009-10-30 2019-02-12 Deka Products Limited Partnership Apparatus and method for detecting disconnection of an intravascular access device
US10537671B2 (en) 2006-04-14 2020-01-21 Deka Products Limited Partnership Automated control mechanisms in a hemodialysis apparatus
WO2020141160A1 (de) * 2018-12-31 2020-07-09 Fresenius Medical Care Deutschland Gmbh Vorrichtung und verfahren zur herstellung einer dialyselösung
AU2020202330B2 (en) * 2007-02-27 2021-05-27 Deka Products Limited Partnership Sensor apparatus systems, devices and methods
CN114618036A (zh) * 2022-03-02 2022-06-14 佛山复星禅诚医院有限公司 一种血液透析a液质量监测系统
CN118178762A (zh) * 2024-03-15 2024-06-14 山东乐齐医疗科技有限公司 一种透析水中央供液控制调节系统

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FR2307550A1 (fr) * 1975-04-14 1976-11-12 Gensollen Yves Procede de controle permanent de la concentration dans une centrale de distribution de liquide de dialyse et de separation des gaz en solution
US4202760A (en) * 1978-07-24 1980-05-13 Cordis Dow Corp. Apparatus and method for preparation of a hemodialysis solution optionally containing bicarbonate
DE2838414C2 (de) * 1978-09-02 1984-10-31 Fresenius AG, 6380 Bad Homburg Vorrichtung zur Hämodialyse und zum Entziehen von Ultrafiltrat
JPS55129067A (en) 1979-03-28 1980-10-06 Terumo Corp Device for moving hollow thread type substance
DE3416057A1 (de) * 1984-04-30 1985-10-31 Fresenius AG, 6380 Bad Homburg Haemodialysevorrichtung
JPS63164959A (ja) * 1986-10-30 1988-07-08 コーブ・ラボラトリーズ・インコーポレーテッド 透析液製造装置
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US3416664A (en) * 1964-11-16 1968-12-17 Herman L. Kumme Artificial kidney
US3352779A (en) * 1965-10-23 1967-11-14 Sweden Freezer Mfg Co Hemodialysis system
US3406826A (en) * 1965-11-17 1968-10-22 Charles B. Willock Artificial kidney liquid metering and dispensing device

Cited By (112)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3809243A (en) * 1972-01-26 1974-05-07 Sarns Inc Turbidity monitor for dialysis machines
US3847809A (en) * 1972-07-03 1974-11-12 David Kopf Syst Proportioning system
US3844940A (en) * 1973-04-26 1974-10-29 Kopf D Systems System for measuring ultrafiltration rate
FR2230379A1 (enrdf_load_stackoverflow) * 1973-05-25 1974-12-20 Bellco Spa
US3882020A (en) * 1973-05-25 1975-05-06 Bellco Spa Concentrate diluter for preparing dialysis liquid in artificial kidneys
JPS5156785A (enrdf_load_stackoverflow) * 1974-11-13 1976-05-18 Yuno Rabo Kk
US4119113A (en) * 1975-02-06 1978-10-10 Extracorporeal Medical Systems, Inc. Double-action proportioning pump
US4060485A (en) * 1975-06-09 1977-11-29 I T L Technology, Inc. Dialysis apparatus
US4122010A (en) * 1976-02-26 1978-10-24 Gambro Ab Apparatus for treating blood
US4079007A (en) * 1976-09-07 1978-03-14 Union Carbide Corporation Hemodialysis system with modular dialysate manifold assembly
US4191646A (en) * 1976-10-14 1980-03-04 Gambro Ab Apparatus for conducting fluids in a dialysis system
US4153554A (en) * 1977-02-22 1979-05-08 American Micro-Bionics Corp. Apparatus for use in artificial kidney system
DE3744840C2 (enrdf_load_stackoverflow) * 1986-10-30 1993-08-05 Cobe Laboratories, Inc., Lakewood, Col., Us
US5183760A (en) * 1989-05-19 1993-02-02 Sweetana Stephanie A Apparatus for in vitro determination of substances across membranes, biological tissues, or cell cultures
DE3930181A1 (de) * 1989-09-09 1991-03-21 Fresenius Ag Druckausgleichsgefaess fuer ein haemodialysekonzentrat
US5591636A (en) * 1993-10-18 1997-01-07 Precision Instrument Design Membrane holder
US5599688A (en) * 1993-10-18 1997-02-04 Precision Instrument Design Device and method for circulating fluid over a membrane
US6146883A (en) * 1998-09-14 2000-11-14 Navicyte, Inc. Packing device for transporting confluent cell monolayers
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FR2005982A1 (enrdf_load_stackoverflow) 1969-12-19

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