WO1993020860A1 - Pompe pourvue d'une roue a chambre fixe - Google Patents

Pompe pourvue d'une roue a chambre fixe Download PDF

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Publication number
WO1993020860A1
WO1993020860A1 PCT/US1993/002110 US9302110W WO9320860A1 WO 1993020860 A1 WO1993020860 A1 WO 1993020860A1 US 9302110 W US9302110 W US 9302110W WO 9320860 A1 WO9320860 A1 WO 9320860A1
Authority
WO
WIPO (PCT)
Prior art keywords
fluid
impeller
blood
fluid passages
outlet
Prior art date
Application number
PCT/US1993/002110
Other languages
English (en)
Inventor
George M. Johnson
Original Assignee
Medtronic, Inc.
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 Medtronic, Inc. filed Critical Medtronic, Inc.
Publication of WO1993020860A1 publication Critical patent/WO1993020860A1/fr

Links

Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D29/00—Details, component parts, or accessories
    • F04D29/18—Rotors
    • F04D29/22—Rotors specially for centrifugal pumps
    • F04D29/24—Vanes
    • F04D29/242—Geometry, shape
    • 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
    • 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A61M60/226—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly radial components
    • A61M60/232—Centrifugal pumps
    • 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/419—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being permanent magnetic, e.g. from a rotating magnetic coupling between driving and driven magnets
    • 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D1/00—Radial-flow pumps, e.g. centrifugal pumps; Helico-centrifugal pumps
    • F04D1/04—Helico-centrifugal pumps
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D13/00—Pumping installations or systems
    • F04D13/02—Units comprising pumps and their driving means
    • F04D13/021—Units comprising pumps and their driving means containing a coupling
    • F04D13/024—Units comprising pumps and their driving means containing a coupling a magnetic coupling
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D29/00—Details, component parts, or accessories
    • F04D29/18—Rotors
    • F04D29/22—Rotors specially for centrifugal pumps
    • F04D29/2261—Rotors specially for centrifugal pumps with special measures
    • F04D29/2272—Rotors specially for centrifugal pumps with special measures for influencing flow or boundary layer

Definitions

  • the present invention relates generally to centrifugal pumps used in pumping delicate fluids. More particularly, it relates to centrifugal pumps used for extracorporeal pumping of blood.
  • Blood is a complex and delicate fluid. It is essentially made up of plasma, a pale yellow liquid containing microscopic materials including the red corpuscles (erythrocytes), white corpuscles (leukocytes), and platelets (thrombocytes).
  • red corpuscles erythrocytes
  • white corpuscles leukocytes
  • platelets thrombocytes
  • Centrifugal pumps have been utilized in the prior art for the pumping of blood and other delicate biological and non-biological fluids.
  • One of the problems which has been encountered in utilizing this type of pump is that because of the relatively delicate nature and structure of blood, physical deterioration of the blood and at least some of its components invariably results.
  • the fluid as it moves from the vanes to the ring shaped volute space beyond the tips of the vanes, is reduced in velocity, and as the velocity decreases, the pressure increases according to Bernoulli's theorem. Handling of many delicate fluids, such as blood, in this fashion would destroy them for use.
  • centrifugal blood pump capable of operating efficiently at reduced speeds of rotation like conventional vaned pumps while retaining the gentle blood handling characteristics of vaneless pumps would be desirable.
  • the present invention accomplishes the objectives of reducing the speed of pump operation and increasing pump efficiency while maintaining the beneficial blood handling capabilities associated with vaneless pumps. These objectives are accomplished by providing an improved pumping apparatus and method of pumping blood and other delicate fluids.
  • the improved pump includes a housing for defining a chamber having a generally circular base.
  • a rotor is disposed for rotation about an axis within the chamber and includes an impeller having a peripheral edge.
  • the impeller includes an upper section having a central opening and a lower section.
  • the upper and lower sections have oppositely disposed surfaces. Separation means are included between the upper and lower sections of the impeller for defining a plurality of fluid passages between the oppositely disposed surfaces.
  • the separation means includes a leading edge and a trailing edge.
  • the leading edge is disposed such that it commences generally at the central opening and the trailing edge is disposed generally at the peripheral edge of the impeller such that the separation means commences at a point at or near the central opening and terminates at a point at or near the peripheral edge.
  • the fluid passages extend radially from a position at or near the central opening outwardly to a position at or near the peripheral edge of the impeller.
  • Inlet means are positioned within the housing for introducing fluid through the central opening into the fluid passages.
  • the pump includes outlet means positioned peripherally within the housing and generally tangential to the circular base. Means are provided for rotating the rotor at a speed such that fluid introduced in to the fluid passages is caused to rotate spirally outward between the inlet and the outlet. As the fluid flows outwardly toward the outlet it is collected in an annular unobstructed chamber about the impeller and then discharged through the outlet.
  • Various alternative designs of the impeller are included.
  • the fluid passages radiate straight out linearly in a direction from the axis of rotation to the peripheral edge.
  • the fluid passages radiate spirally in the direction of the flow of blood through the outlet.
  • the fluid passages radiate spirally in the opposite direction of the flow of fluid through the outlet.
  • the improved pump design provides significant advantages over conventional blood pumps. It has the pumping efficiency of conventional vaned blood pumps while reducing low pressure turbulence regions and related adverse blood handling characteristics associated with these pumps.
  • the improved pump of this invention is able to handle blood gently in the manner of vaneless blood pumps but is able to operate more efficiently at a slower speed of rotation, thus reducing the risks of hemolysis associated with friction and heat generated by higher speeds of rotation.
  • the improved pump achieves these benefits without the problems associated with prior blood pumps which have utilized a channeled blood flow construction. As discussed above, these prior pumps do not have desirable air entrapment capacity or gentle blood handling characteristics.
  • the construction of the improved pump of this invention eliminates those problems by providing channeled blood flow passages extending generally from the central opening of the upper section of the impeller to the peripheral edge. This minimizes blood turbulence at the central opening while providing sufficient air entrapment capacity necessary to safe blood handling.
  • the improved pump of the present invention is described as it would be used as a blood pump, it could also be utilized to pump other delicate biological or non-biological fluids which are capable of damage from turbulence, pressure changes or sheer stresses.
  • FIG. 1 is a top view of a pump according to the present invention.
  • FIG. 2 is a sectional view of the pump of FIG. 1 taken along line 2-2.
  • FIG. 3 is a perspective view of the lower section and separating surfaces of the impeller of FIGS. 1 and 2.
  • FIGS. 4 and 5 are perspective views of alternative impellers configurations.
  • FIG. 1 is a top view of a pump 10. Although pump 10 will be described with respect to the pumping of blood it is equally effective for pumping other delicate fluids.
  • FIG. 2 is a cross-sectional view of pump 10 taken along line 2-2 of FIG. 1 through the axis of rotation of the pump rotor 12.
  • Rotor 12 rotates in the direction of arrow 13.
  • pump 10 includes pumping chamber 14 which may, as in this embodiment, be constructed of a transparent material, and base 16 which is essentially circular.
  • Rotor 12 includes a shaft (not shown), and an impeller 18 having a lower section 20 and an upper section 22 which, in this embodiment, is made of a transparent material to allow the blood to be viewed as it passes through the pump.
  • Upper section 22 is provided with a central opening 24.
  • Upper section 22 and lower section 20 have oppositely disposed surfaces 26 and 28, respectively, which are separated by a plurality of separating surfaces 30.
  • separating surfaces 30 are integrally formed as a portion of lower section 22 although it should be realized that they could be formed as separate pieces or as an integral portion of upper section 22.
  • impeller 18 could be formed of integral construction in any conventional manner.
  • Separating surfaces 30 divide the space between oppositely disposed surfaces 26 and 28 a plurality of fixed chambers or blood flow passages 32 which extend radially from central opening 24 to the peripheral edge 34 of impeller 18. Blood enters pump 10 through an axial inlet 36 and is discharged through a tangential outlet 38. Although inlet 36 and outlet 38 maybe located elsewhere, the locations shown in this embodiment are preferred for optimum pump efficiency and blood handling characteristics.
  • the pump rotor 12 may be driven in any conventional manner such as by the magnetic coupling of rotating drive magnets located in a controller console and driven magnets embedded in rotor 12.
  • Such a drive system is well known and utilized commercially, for example in the BioMedicus, Inc., BP-80 blood pump and is not shown in the figure.
  • blood enters the pump through inlet 36.
  • Drive means coupled to rotor 12 causes impeller 18 to rotate.
  • Blood enters central opening 24 and is caused to move downwardly and outwardly through blood flow passages 32 by the centrifugal action of the pump and the forces exerted upon the blood by oppositely disposed surfaces 26 and 28 and separating surfaces 30.
  • the blood is collected in an unobstructed annular chamber 40 located between impeller 18 and housing 14. Some of the blood is then discharged through outlet
  • a portion of the blood collected in annular chamber 40 is not discharged through outlet 38 but flows back towards inlet 36 in the space 42 between the upper section 22 of impeller 18 and housing 14.
  • This backflow of blood is significant since air bubbles which have been inadvertently introduced into the blood or which have formed in the blood are carried along with the back flowing blood towards inlet 36. These air bubbles collect in an air entrapment pocket 44 located near inlet 36.
  • the precise location at which air is entrapped is dependant upon the position of the pump during use and upon the pressure differential between the inlet and outlet of the pump.
  • the pressure differential is large with the pressure at the outlet being greater than at the inlet.
  • Blood flow passages 32 are constructed to maximize the inlet to outlet pressure differential and thus increase the air entrapment capabilities of the pump. This is done by extending the leading edge 45 and trailing edge 47 of separating surfaces 30 generally the entire distance from central opening 24 to peripheral edge 34. This maximizes the length of the fixed chambers or blood flow passages 32. Since the pressure differential between inlet and outlet increases as the length of the blood flow passages 32 increases, this construction maximizes the pressure differential thus enhancing the air entrapment capabilities of the pump.
  • the pressure differential can be changed in order to tune the pump to any desired blood flow dynamics. This may be done by shortening the length of separating surfaces 30 such that trailing edge 47 is moved closer to the leading edge 45 and central opening 24. This tuning procedure may be used for all of the impeller variations shown herein and is not illustrated in the drawings. It is important to note that the pump should not be tuned by altering the position of leading edges 45. Leading edges 45 are positioned generally at central opening 24 in order to reduce the velocity of the edges with respect to the blood entering the pump from inlet 36. If separating surfaces 30 are shortened by moving leading edges 45 away from central opening 24 the velocity of the leading edges 45 with respect to the entering blood will be increased. This increased velocity creates turbulence that will result in increased hemolysis and damage to the formed elements of the blood.
  • FIG. 3 is a perspective view of lower section 20 of impeller 18. Separating surfaces 30 radiate straight out in a linear fashion in a direction from the axis of rotation to peripheral edge 34 to form blood flow passages 32 between lower section 20 and upper section 22 (not shown in this figure).
  • FIGS. 4 and 5 show alternative designs for lower section 20 of impeller 18.
  • separating surfaces 30 radiate spirally in a direction opposite to that of the flow of blood through tangential outlet 38.
  • separating surfaces 30 of lower section 20 radiate spirally in the direction of the flow of blood through tangential outlet 28.
  • the blood flowing through blood flow passages 32 is urged by partitioning surfaces 30 to flow in the direction of the blood being discharged through tangential outlet 38 thus further improving pump efficiency.
  • the pump of the present invention is able to pump blood in a gentle yet efficient manner.
  • Separating surfaces 30, which extend generally from the central opening 24 of upper section 22 to peripheral edge 34 impart an impelling force on the blood with an efficiency exceeding conventional vaned pumps.
  • the shape, number and arrangement of separating surfaces 30 may be varied.
  • the cross-sectional configuration of blood flow passages 32 could be formed in a variety of shapes including rectangular, circular or oval.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Mechanical Engineering (AREA)
  • Animal Behavior & Ethology (AREA)
  • Cardiology (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • General Engineering & Computer Science (AREA)
  • Geometry (AREA)
  • Physics & Mathematics (AREA)
  • External Artificial Organs (AREA)

Abstract

Appareil et procédé de pompage de sang et autres fluides délicats. L'appareil comprend un rotor (12) pourvu d'une roue (18) qui comporte une partie supérieure (22) et une partie inférieure (20) à sufaces opposées (26, 28), la partie supérieure (22) comprenant une ouverture centrale (24). Des surfaces de séparation (30), disposées entre les parties supérieure et inférieure (22, 20) définissent une multiplicité de passages (32) d'écoulement de fluide entre les surfaces opposées (26, 28). Les surfaces de séparation (30) comprennent un bord avant (45) et un bord arrière (47), le bord avant (45) étant placé au niveau de l'ouverture centrale (24), ou à proximité de celle-ci, et le bord arrière (47) etant placé au niveau du pourtour (34) de la roue (18), ou à proximité de celui-ci. Cette structure maximise le différentiel de pression du fluide de l'orifice d'entrée à l'orifice de sortie, et minimise la trubulence, de sorte que la pompe présente de bonnes aptitudes de piégeage d'air, ainsi que des caractéristiques de manipulation en douceur du sang.
PCT/US1993/002110 1992-04-10 1993-03-10 Pompe pourvue d'une roue a chambre fixe WO1993020860A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US86726492A 1992-04-10 1992-04-10
US07/867,264 1992-04-10

Publications (1)

Publication Number Publication Date
WO1993020860A1 true WO1993020860A1 (fr) 1993-10-28

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Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0657652A1 (fr) * 1993-12-09 1995-06-14 Senju Seiyaku Kabushiki Kaisha Pompe controlant de très faibles débits
WO1997021927A1 (fr) * 1995-12-14 1997-06-19 Warman International Limited Pompe centrifuge
EP0900572A1 (fr) * 1997-09-04 1999-03-10 Sulzer Electronics AG Pompe centrifuge
AU705250B2 (en) * 1995-12-14 1999-05-20 Weir Warman Ltd Centrifugal pump
US5919125A (en) * 1997-07-11 1999-07-06 Cobe Laboratories, Inc. Centrifuge bowl for autologous blood salvage
US5976388A (en) * 1997-05-20 1999-11-02 Cobe Cardiovascular Operating Co., Inc. Method and apparatus for autologous blood salvage
US6048363A (en) * 1997-05-13 2000-04-11 Nagyszalanczy; Lorant Centrifugal blood pump apparatus
EP1013294A1 (fr) * 1998-12-16 2000-06-28 Sulzer Electronics AG Pompe à flux diagonal
NL1028471C2 (nl) * 2005-03-07 2006-09-11 Hemodynamics Holding B V Pomp voor kwetsbaar fluïdum, gebruik van dergelijke pomp voor pompen van bloed.
IT201800009506A1 (it) * 2018-10-16 2020-04-16 Eurosets Srl Pompa centrifuga a levitazione magnetica
CN111699009A (zh) * 2017-12-08 2020-09-22 加维克之心有限责任公司 单流入双抽吸离心血泵
US11013838B2 (en) 2016-04-27 2021-05-25 Sarah Elizabeth Hagarty Closed loop system for direct harvest and transfer for high volume fat grafting
CN114198313A (zh) * 2021-12-07 2022-03-18 中国船舶重工集团公司第七一九研究所 一种集成式泵站
US11674517B2 (en) 2007-02-27 2023-06-13 Miracor Medical Sa Device to assist the performance of a heart

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CH277438A (de) * 1949-09-28 1951-08-31 Guebeli Vincent Zentrifugalpumpe.
FR2451480A1 (fr) * 1979-03-16 1980-10-10 Belenger Jacques Pompe centrifuge medicale
AT394136B (de) * 1989-05-02 1992-02-10 Schima Heinrich Rotor einer zentrifugalpumpe fuer blut oder andere scherempfindliche fluessigkeiten
EP0518050A1 (fr) * 1991-05-10 1992-12-16 Terumo Kabushiki Kaisha Pompe à liquide

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CH277438A (de) * 1949-09-28 1951-08-31 Guebeli Vincent Zentrifugalpumpe.
FR2451480A1 (fr) * 1979-03-16 1980-10-10 Belenger Jacques Pompe centrifuge medicale
AT394136B (de) * 1989-05-02 1992-02-10 Schima Heinrich Rotor einer zentrifugalpumpe fuer blut oder andere scherempfindliche fluessigkeiten
EP0518050A1 (fr) * 1991-05-10 1992-12-16 Terumo Kabushiki Kaisha Pompe à liquide

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
US,A,RE28742 (RAFFERTY ET AL.) 23 March 1976 *

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0657652A1 (fr) * 1993-12-09 1995-06-14 Senju Seiyaku Kabushiki Kaisha Pompe controlant de très faibles débits
US5599175A (en) * 1993-12-09 1997-02-04 Senju Seiyaku Kabushiki Kaisha Micro flow controlling pump
AU705250B2 (en) * 1995-12-14 1999-05-20 Weir Warman Ltd Centrifugal pump
WO1997021927A1 (fr) * 1995-12-14 1997-06-19 Warman International Limited Pompe centrifuge
US6048363A (en) * 1997-05-13 2000-04-11 Nagyszalanczy; Lorant Centrifugal blood pump apparatus
US5976388A (en) * 1997-05-20 1999-11-02 Cobe Cardiovascular Operating Co., Inc. Method and apparatus for autologous blood salvage
US5919125A (en) * 1997-07-11 1999-07-06 Cobe Laboratories, Inc. Centrifuge bowl for autologous blood salvage
EP0900572A1 (fr) * 1997-09-04 1999-03-10 Sulzer Electronics AG Pompe centrifuge
EP1013294A1 (fr) * 1998-12-16 2000-06-28 Sulzer Electronics AG Pompe à flux diagonal
NL1028471C2 (nl) * 2005-03-07 2006-09-11 Hemodynamics Holding B V Pomp voor kwetsbaar fluïdum, gebruik van dergelijke pomp voor pompen van bloed.
WO2006096049A1 (fr) * 2005-03-07 2006-09-14 Hemodynamics Holding B.V. Pompe pour fluide delicat, utilisation de la pompe pour pomper du sang
US12117007B1 (en) 2007-02-27 2024-10-15 Miracor Medical Sa Device to assist the performance of a heart
US11674517B2 (en) 2007-02-27 2023-06-13 Miracor Medical Sa Device to assist the performance of a heart
US12104600B2 (en) 2007-02-27 2024-10-01 Miracor Medical Sa Device to assist the performance of a heart
US11754077B1 (en) 2007-02-27 2023-09-12 Miracor Medical Sa Device to assist the performance of a heart
US11013838B2 (en) 2016-04-27 2021-05-25 Sarah Elizabeth Hagarty Closed loop system for direct harvest and transfer for high volume fat grafting
CN111699009A (zh) * 2017-12-08 2020-09-22 加维克之心有限责任公司 单流入双抽吸离心血泵
WO2020079602A1 (fr) * 2018-10-16 2020-04-23 Eurosets S.R.L. Pompe centrifuge à lévitation magnétique
US11644043B2 (en) 2018-10-16 2023-05-09 Eurosets S.R.L. Magnetic levitation centrifugal pump
US20220025897A1 (en) * 2018-10-16 2022-01-27 Eurosets S.R.L. Magnetic levitation centrifugal pump
CN112888862B (zh) * 2018-10-16 2023-08-22 欧赛特有限公司 磁悬浮离心泵
JP2022502606A (ja) * 2018-10-16 2022-01-11 ユーロセッツ エス．アール．エル． 磁気浮上式遠心ポンプ
CN112888862A (zh) * 2018-10-16 2021-06-01 欧赛特有限公司 磁悬浮离心泵
IT201800009506A1 (it) * 2018-10-16 2020-04-16 Eurosets Srl Pompa centrifuga a levitazione magnetica
CN114198313A (zh) * 2021-12-07 2022-03-18 中国船舶重工集团公司第七一九研究所 一种集成式泵站
CN114198313B (zh) * 2021-12-07 2024-04-16 中国船舶重工集团公司第七一九研究所 一种集成式泵站

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