EP0390161B1 - Elektromagnetisch steuerbare Membranpumpe sowie deren Anwendung - Google Patents

Elektromagnetisch steuerbare Membranpumpe sowie deren Anwendung Download PDF

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Publication number
EP0390161B1
EP0390161B1 EP90106054A EP90106054A EP0390161B1 EP 0390161 B1 EP0390161 B1 EP 0390161B1 EP 90106054 A EP90106054 A EP 90106054A EP 90106054 A EP90106054 A EP 90106054A EP 0390161 B1 EP0390161 B1 EP 0390161B1
Authority
EP
European Patent Office
Prior art keywords
piston
membrane
medium
hollow cylinder
cover plate
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
EP90106054A
Other languages
German (de)
English (en)
French (fr)
Other versions
EP0390161A3 (de
EP0390161A2 (de
Inventor
Anton Harant
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
INFUS Hospitalbedarf GmbH and Co Vertriebs KG
Original Assignee
INFUS Hospitalbedarf GmbH and Co Vertriebs KG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by INFUS Hospitalbedarf GmbH and Co Vertriebs KG filed Critical INFUS Hospitalbedarf GmbH and Co Vertriebs KG
Priority to AT90106054T priority Critical patent/ATE90776T1/de
Publication of EP0390161A2 publication Critical patent/EP0390161A2/de
Publication of EP0390161A3 publication Critical patent/EP0390161A3/de
Application granted granted Critical
Publication of EP0390161B1 publication Critical patent/EP0390161B1/de
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
    • F04B43/04—Pumps having electric drive

Definitions

  • the invention relates to an electromagnetically controllable diaphragm pump according to the preamble of claim 1 and an application of the diaphragm pump.
  • Diaphragm pumps of this type are commercially available per se and are known, for example, from DE-A-37 19 939. They are used to convey small, very precise volume units of a liquid, with a separation between the pumped liquid and moving devices of the pump.
  • diaphragm pumps an elastic and tight diaphragm is clamped in place at the edges and the central section is subjected to a lifting movement.
  • the central section of the membrane is connected to a core or piston designed as a moving coil, which is surrounded by an excitation coil. When excited, the piston is attracted in the area of the excitation coil against the restoring force of the membrane or another device that applies spring tension. In the event of de-excitation, the reset takes place through the action of the spring preload.
  • the medium to be conveyed is sucked through an inlet opening into the displacement space formed on the side of the membrane facing away from the piston between the membrane and a cover plate causing the clamping.
  • a valve that opens only in the suction direction in the simplest case a flap that is spring-loaded, is expediently provided in the suction opening in the cover plate.
  • the aspirated volume is expelled again through another opening, which contains a valve that opens only in the direction of expulsion, in the simplest case again a spring-loaded flap. This ensures that one stroke can only be sucked in and the other stroke can only be expelled.
  • a disadvantage of commercially available metering pumps of this type is that relatively stiff membranes must be used so that they do not bend during the discharge stroke, in which they have to convey against pressure. The consequence of this is that high adjustment forces have to be applied in order to overcome the high restoring force or spring preload specified by such membranes.
  • Another disadvantage is that the membranes age and become softer over time. However, this changes the volume delivered per stroke, which is extremely undesirable. This is particularly undesirable when it comes to highly precise delivery quantities, for example in the delivery of very small quantities in the medical field.
  • a particular example is the promotion of dialysate to a dialyzer in hemodialysis.
  • the membrane pump according to the invention can be used in hemodialysis.
  • the invention is based on the finding that a very soft membrane can be used if it remains supported against an incompressible liquid over the entire stroke movement. This is achieved by moving the piston in a constant volume of this incompressible liquid with the membrane being carried along. Because of the design as a double diaphragm pump, extremely constant delivery rates are possible in that a suction stroke is carried out in parallel with one membrane and an ejection stroke is carried out in the other membrane.
  • hemodialysis allows a system in which no valves have to be controlled, but continuous delivery can be actively ensured with a simple structure.
  • the delivery rate can be changed by changing the stroke speed, which in turn can be controlled very precisely by changing the excitation current or the clock frequency.
  • an accurate accounting system can be achieved in this way with an extremely simple construction and a high degree of maintenance friendliness.
  • the diaphragm pump has a hollow cylinder 1, in the interior of which a cylindrical piston 2 is arranged to be axially displaceable.
  • the piston 2 is guided in the interior of the hollow cylinder 1 via slide rings 3, which bear against the inner wall of the hollow cylinder 1.
  • An air gap between the piston 2 and the inner wall of the hollow cylinder 1 is also ensured by means of the slide rings 3. This air gap is particularly necessary when the hollow cylinder 1 consists of a magnetizable material such as soft iron. If the hollow cylinder 1 consists of a dielectric such as a plastic, the guidance of the piston 2 can be ensured in another way.
  • a membrane 6 is firmly clamped between the hollow cylinder 1 and a respective cover plate 9 at the edge.
  • each membrane 6 is firmly and tightly connected to the piston 2.
  • the piston 2 itself has at least one through bore 4 in the axial direction, such that the spaces 5 between the end faces of the piston 2 and the respectively associated membrane 6 are connected to one another via the through bore 4.
  • the through hole 4 and the spaces 5 are filled with an incompressible liquid.
  • the hollow cylinder 1 has two excitation coils 7 and 8 on its outside, each of which is assigned to one of the membranes 6. Connection lines 17 and 18 lead to the outside and are connected to an electrical control, not shown.
  • the two excitation coils 7 and 8 are separated from one another by axially centrally arranged separating elements 14.
  • a first displacement 12 is formed between a membrane, in FIG. 1 of the left-hand membrane 6 and the associated cover plate 9, while a second displacement 13 is formed between the other membrane, in FIG. 1 of the right-hand membrane 6 and the associated cover plate 9.
  • At least one feed opening 10 and one discharge opening 11 are provided in the cover plates 9.
  • Each feed opening 10 is assigned an inlet valve which can only be opened in the inlet direction, but is closed in the opposite direction.
  • Each outlet opening 11 is also assigned a valve which, however, can only be opened in the outlet direction, but is always closed in the other direction. In the simplest case, these are spring-loaded flap valves, as are common in hydraulic and pneumatic systems.
  • FIGS. 2 and 3 Other valve designs are shown in FIGS. 2 and 3.
  • Fig. 2 shows an outlet valve 20 which can be screwed into the outlet opening 11 of the cover 9 or fastened in another way.
  • the outlet valve 20 consists of a sleeve part 21 which can be fastened in this opening 11 and onto which a nozzle part 22 can be screwed with the interposition of a seal 23 and the nozzle end of which is designed such that lines, for example hose lines, can be fastened thereon.
  • a valve seat 24 is formed near the end facing the outlet opening 11.
  • valve body 25 On the side of the valve seat facing away from this outlet opening 11 there is a valve body 25 which is pressed against the valve seat 24 by a spring 26, the spring 26 being supported at the other end on the screwed-on connecting piece 22, which is also essentially hollow cylindrical. At a pressure in the direction of the arrow, the valve body 25 lifts off the valve seat 24 against the force of the spring 26 and allows a medium to flow past until the delivery pressure ceases.
  • Fig. 3 shows an inlet valve 30, which is constructed in a similar manner and has a screw-in part 31 and a nozzle part 32, which are also essentially hollow cylindrical and which can be connected to one another tightly via a seal 33.
  • a valve seat 34 is formed at the end facing the screw-in part 31, against which a valve body 35 abuts, with the aid of a spring 36 supported in the screw-in part 31.
  • valves 20 and 30 shown in FIGS. 2 and 3, as mentioned, can be screwed into the openings 10 and 11 of the cover plate 9 in such a way that the displacements 12 and 13 are not affected in their contours.
  • the incompressible liquid is moved from one space 5 through the through hole 4 to the other space 5 such that this incompressible liquid always exerts the same supporting force on both membranes 6 , the membranes 6 cannot bend.
  • the displacements 12 and 13 and the two stroke volumes are mutually also the same.
  • a simple continuous delivery can be achieved with such a double diaphragm pump according to FIG. 1, as will be explained with reference to FIG. 5.
  • This double diaphragm pump P in which the one excitation state and thus the lifting state is shown schematically by a broad black line and an excitation of the excitation coil 7 and an excitation of the excitation coil 8 and a corresponding movement of the piston 2 to the left corresponds to the illustration in FIG. 1 ,
  • All inlet openings 10 are connected via correspondingly assigned valves 30 to a container R via conventional lines and without a valve at branch point 28.
  • the outlet openings 11 with associated outlet valves 20 are led directly to a consumer U via a union point 29 without additional valves with a discharge line.
  • the two displacements 12 and 13 of the pump P can also be supplied from different containers, for example in order to supply different media to the same consumer in a predetermined volume ratio to one another.
  • two consumers can be supplied alternately from a common supply.
  • the double diaphragm pump according to FIG. 1 corresponding to the application according to FIG. 5 allows a delivery rate that is twice as high as in a diaphragm pump with only one diaphragm.
  • the excitation coils 7 and 8 can be excited by alternating current, then the piston 2 consists at least partially, for example in the form of an annular sleeve part, of a permanent magnetic material. If DC excitation occurs, the piston 2 is, in the same way at least partially, made of a soft magnetic material, such as soft iron or the like. It turns out that the hollow cylinder 1 can also consist of soft iron, it then acts as a yoke and must then have an air gap possess against the piston 2, unless the outside of the piston 2 consists of a dielectric. Exists on the other hand the hollow cylinder 11 made of a dielectric material, the piston 2 can be guided without an air gap. In any case, the incompressible liquid must not have any magnetic properties.
  • the double diaphragm pump according to the invention is particularly suitable for balancing systems. This is explained in more detail using a special application, namely hemodialysis, using the schematic illustration according to FIG. 4.
  • FIG. 4 shows two double diaphragm pumps P1 and P2, which are actuated in a push-pull manner with respect to one another.
  • the left-hand inlet openings 10 of both pumps P1 and P2 are connected via appropriate inlet valves 30 but without additional valves at a branching point 38 to a container T for fresh dialysate.
  • the left-hand outlet openings 11 are connected to the dialysate inlet 41 of a dialyzer D via corresponding outlet valves 20 and via a union point 39 without additional valves and via a flow regulator 40.
  • the dialyser D is supplied with blood to be purified from an unillustrated patient via an inlet 43.
  • the contaminated blood is cleaned with the help of the dialysate in the usual way according to the osmotic principle.
  • the purified blood leaves the dialyzer D via an outlet 44, the contaminated dialysate leaves the dialyzer via an outlet 42.
  • the contaminated dialysate is fed via a branch point 45 without additional valves and via corresponding inlet valves 30 to the right-hand inlet openings 10 of the two pumps P1 and P2 .
  • the right-hand outlet openings of both pumps P1 and P2 are connected to a drain W via associated outlet valves 20 and a union point 46 without additional valves.
  • Fresh dialysate is thus always available for delivery to the dialyser D, which is delivered to the dialyser D in a volume quantity per time unit which is dependent on the stroke speed of the piston 2 but is constant. Due to the design as a double diaphragm pump of the pumps P1 and P2, however, the exact same amount, namely the same volume per unit of time, is also discharged from the outlet 42 and sucked into the pump, which is just releasing fresh dialysate to the dialyzer D. In this way, a so-called zero balance is achieved, ie no weight (so-called ultrafiltrate) is removed from the patient. By using two double diaphragm pumps P1 and P2, a completely continuous operation is also achieved.
  • limit switches 15 and 16 are provided, which trigger a change of excitation when the respective membrane 6 abuts the respective cover plate 9 by signaling.
  • the fastening element 19 can bridge contacts for central fastening of the membrane 6 on the piston 2 when it is in contact with the respective end position detector 15, 16.
  • a non-contact proximity switch or other limit switches of a known type can also be used.
  • the incompressible liquid supports the membrane 6, which is why a comparatively soft membrane can be used, which in turn allows a longer stroke. Since the piston 2 moves by displacing this incompressible liquid through the through hole 4 to the other side of the piston 2, it is advantageous if the incompressible liquid has lubricating properties, that is to say that it promotes the displacement movement of the piston 2. In particular for applications in which the incompressible liquid could trigger undesirable reactions when it comes into contact with the conveyed medium, for example poisoning of the dialysate in the described use case, an incompressible liquid which is compatible with the conveyed medium must also be selected.
  • incompressible liquid Since entry of incompressible liquid into the conveyed medium is a signal for a leak, in particular a crack or a porosity of the membrane 6, it is also expedient to choose the incompressible liquid so that in such a case an externally immediately apparent reaction is triggered , such as a clearly recognizable color change or the like. Since, moreover, the pressure conditions change suddenly in such cases, alarms which respond to this can be used to indicate such a case.
  • Double-diaphragm pumps depend on the fact that different volume quantities per unit of time are conveyed from the two displacements 12 and 13, so this can be achieved in that the diaphragms 6 each have different elasticities and / or the excitation coils 7 and 8 are excited with current of different heights . This results in different lifting speeds. Structurally more complex, but also conceivable, is a different size of the two displacements 11 and 13, whereby it should be noted that the lifting height remains the same due to the design.
  • inlet openings 10 and outlet openings 11 can be provided per lifting chamber 12 or 13, which are supplied or disposed of in parallel.
  • a diaphragm pump is therefore specified which has a simple structure and can therefore be easily and easily maintained, with individual elements being easily replaceable.
  • the diaphragm pump can also be used if sterilization is required at least with regard to the flow path of a medium.
  • the diaphragm pump is therefore also suitable for medical applications.

Landscapes

  • Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • General Engineering & Computer Science (AREA)
  • Reciprocating Pumps (AREA)
  • External Artificial Organs (AREA)
EP90106054A 1989-03-30 1990-03-29 Elektromagnetisch steuerbare Membranpumpe sowie deren Anwendung Expired - Lifetime EP0390161B1 (de)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT90106054T ATE90776T1 (de) 1989-03-30 1990-03-29 Elektromagnetisch steuerbare membranpumpe sowie deren anwendung.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3910331A DE3910331A1 (de) 1989-03-30 1989-03-30 Elektromagnetisch steuerbare membranpumpe sowie deren anwendung
DE3910331 1989-03-30

Publications (3)

Publication Number Publication Date
EP0390161A2 EP0390161A2 (de) 1990-10-03
EP0390161A3 EP0390161A3 (de) 1991-02-13
EP0390161B1 true EP0390161B1 (de) 1993-06-16

Family

ID=6377490

Family Applications (1)

Application Number Title Priority Date Filing Date
EP90106054A Expired - Lifetime EP0390161B1 (de) 1989-03-30 1990-03-29 Elektromagnetisch steuerbare Membranpumpe sowie deren Anwendung

Country Status (8)

Country Link
US (1) US5152671A (es)
EP (1) EP0390161B1 (es)
JP (1) JPH0331588A (es)
AT (1) ATE90776T1 (es)
CA (1) CA2013561A1 (es)
DD (1) DD297860A5 (es)
DE (2) DE3910331A1 (es)
ES (1) ES2047184T3 (es)

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7241272B2 (en) 2001-11-13 2007-07-10 Baxter International Inc. Method and composition for removing uremic toxins in dialysis processes
DE10201027C1 (de) * 2002-01-11 2003-08-07 Eads Deutschland Gmbh Flüssigkeitspumpe
WO2004009158A2 (en) 2002-07-19 2004-01-29 Baxter International Inc. Systems and methods for performing peritoneal dialysis
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
DE102004042578A1 (de) * 2004-09-02 2006-03-23 Roche Diagnostics Gmbh Mikropumpe zur Förderung von Flüssigkeiten mit niedrigen Förderraten im Druck/Saug-Betrieb
JP4925898B2 (ja) * 2007-04-04 2012-05-09 ゼブラ株式会社 リフィールホルダ
US8114276B2 (en) 2007-10-24 2012-02-14 Baxter International Inc. Personal hemodialysis system
WO2017163274A1 (ja) * 2016-03-23 2017-09-28 ニチバン株式会社 スタンプ型塗膜転写具

Family Cites Families (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE1453610B2 (de) * 1964-03-07 1972-06-29 Philips Patentverwaltang GmbH, 2000 Hamburg Gegentakt-dosierpumpe zum dosieren von fluessigen oder gasfoermigen medien
US3433983A (en) * 1966-11-14 1969-03-18 United Aircraft Corp Electromagnetic actuator
US3625636A (en) * 1969-07-09 1971-12-07 Robert E Nelson Liquid level regulating system
GB1307825A (en) * 1970-01-18 1973-02-21 Hamilton Tool Gauge Ltd Diaphragm pump assembly with control circuit
FR2086970A5 (es) * 1970-04-15 1971-12-31 Jeumont Schneider
BE792314A (fr) * 1971-12-06 1973-06-05 Rhone Poulenc Sa Perfectionnement aux reins artificiels
US3979284A (en) * 1972-07-31 1976-09-07 Rhone-Poulenc S.A. Artificial haemodialysis kidneys
CH573550A5 (en) * 1973-01-26 1976-03-15 Klaue Hermann Magnetic push pull compressor - has diaphragms or pistons which reciprocate by electro magnets
JPS5272379A (en) * 1975-12-15 1977-06-16 Toray Ind Inc Separation of fluid
US4209391A (en) * 1978-11-06 1980-06-24 Cordis Dow Corp. Apparatus and method for automatically controlling hemodialysis at a pre-selected ultrafiltration rate
DE3016720A1 (de) * 1980-04-30 1981-11-05 Dr. Eduard Fresenius, Chemisch-pharmazeutische Industrie KG Apparatebau KG, 6380 Bad Homburg Haemodialysegeraet
DE3328744A1 (de) * 1983-08-09 1985-02-28 Fresenius AG, 6380 Bad Homburg Haemodialysevorrichtung
SU1252541A1 (ru) * 1985-03-20 1986-08-23 Краснодарское Отделение Всесоюзного Научно-Исследовательского Проектно-Конструкторского И Технологического Института Источников Тока Мембранный вакуум-насос
DE3719939A1 (de) * 1986-06-14 1987-12-17 Lohberg Hans Martin Elektromagnetische membranpumpe
DE8616123U1 (de) * 1986-06-14 1986-08-21 Lange, Detlef, 4796 Salzkotten Elektromagnetische Membranpumpe

Also Published As

Publication number Publication date
EP0390161A3 (de) 1991-02-13
DE3910331A1 (de) 1990-10-04
DE3910331C2 (es) 1991-07-18
DE59001750D1 (de) 1993-07-22
ES2047184T3 (es) 1994-02-16
CA2013561A1 (en) 1990-09-30
US5152671A (en) 1992-10-06
DD297860A5 (de) 1992-01-23
ATE90776T1 (de) 1993-07-15
EP0390161A2 (de) 1990-10-03
JPH0331588A (ja) 1991-02-12

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