WO2022185961A1 - Dispositif de pompe - Google Patents

Dispositif de pompe Download PDF

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Publication number
WO2022185961A1
WO2022185961A1 PCT/JP2022/006803 JP2022006803W WO2022185961A1 WO 2022185961 A1 WO2022185961 A1 WO 2022185961A1 JP 2022006803 W JP2022006803 W JP 2022006803W WO 2022185961 A1 WO2022185961 A1 WO 2022185961A1
Authority
WO
WIPO (PCT)
Prior art keywords
impeller
pump device
housing
magnet
blood
Prior art date
Application number
PCT/JP2022/006803
Other languages
English (en)
Japanese (ja)
Inventor
古川新平
森武寿
Original Assignee
テルモ株式会社
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 テルモ株式会社 filed Critical テルモ株式会社
Priority to JP2023503715A priority Critical patent/JPWO2022185961A1/ja
Publication of WO2022185961A1 publication Critical patent/WO2022185961A1/fr

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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
    • 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
    • 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
    • A61M60/818—Bearings
    • A61M60/82—Magnetic bearings

Definitions

  • the present invention relates to a pump device having a housing containing an impeller.
  • a pump device is used as a blood circulation device that circulates blood (fluid) in a heart-lung machine.
  • this type of pump device one having an impeller that rotates within a housing is widely known.
  • a support shaft is provided in the housing, and an impeller is rotatably supported by the support shaft. That is, the impeller has a supported portion at its center of rotation.
  • a bearing portion for receiving the support shaft is provided on the bottom surface of the supported portion.
  • the hollow interior of the impeller and the interior space of the housing communicate with each other through washout holes formed in the impeller.
  • new blood is drawn into the internal space of the housing from the blood inflow port by the centrifugal force generated by this rotation.
  • Blood enters the hollow interior of the impeller through the clearance between the housing and the impeller.
  • the blood further reaches the interior space of the housing through the washout hole, and is then discharged out of the housing through the blood outflow port. That is, blood flow occurs.
  • a main object of the present invention is to provide a pump device capable of suppressing stagnation of fluid such as blood in the impeller.
  • a pump device having an impeller holding a permanent magnet and a housing containing the impeller
  • the impeller is formed with a plurality of communication holes that allow the hollow interior of the impeller to communicate with the internal space of the housing, and is provided in the housing at a position surrounded by the plurality of communication holes.
  • a pump device is provided in which a bearing portion for receiving the tip end of the support shaft and communication passages for individually communicating the communication holes and the bearing portions are formed on the bottom surface of the supported portion.
  • a communicating path is formed that communicates the bearing portion and the communicating hole. Therefore, when fluid such as blood enters the bearing portion during rotation of the impeller, the fluid subjected to centrifugal force is guided to the communicating hole through the communicating passage. That is, the fluid is rapidly discharged from the bearing. Therefore, it becomes difficult for the fluid to remain at the contact portion between the bearing portion and the support shaft.
  • FIG. 1 is a schematic perspective view of a main part of a heart-lung machine constructed by incorporating a pump device according to an embodiment of the present invention
  • FIG. It is a principal part longitudinal cross-sectional view of a pump apparatus.
  • 3 is a schematic longitudinal sectional view of an impeller that constitutes the pump device of FIG. 2;
  • FIG. 4 is a schematic vertical cross-sectional view of a magnet holder holding a permanent magnet; 3 is an exploded perspective view of a magnet holder;
  • FIG. It is an upper perspective view which shows the external appearance of an impeller. It is the bottom view which visually recognized the vane support part which comprises an impeller from the hollow inside side of an impeller.
  • FIG. 4 is a vertical cross-sectional view of essential parts showing the flow of fluid (blood) within the pump device when the impeller rotates.
  • the pump device may be one that causes fluids other than blood to flow.
  • FIG. 1 is a schematic perspective view of a main part of a heart-lung machine 12 configured by incorporating a pump device 10 according to this embodiment.
  • the heart-lung machine 12 functions as a power source for removing the patient's blood from the body and feeding new blood into the body, thereby assisting the patient's cardiopulmonary function (or replacing the cardiopulmonary function). do) play a role.
  • the heart-lung machine 12 connects a blood removal tube 18 and a blood transfer tube 20 to the pump device 10 to form a circulation circuit for circulating blood between the patient and the patient.
  • the blood removal tube 18 has a blood removal lumen 18a inside, and its tip opening is left in a desired living organ (for example, the left ventricle of the heart) to suck the patient's blood through the blood removal lumen 18a.
  • the blood supply tube 20 has a blood supply lumen 20a inside, and its tip opening is left in a desired living organ (for example, subclavian artery), and the blood of the pump device 10 is supplied through the blood supply lumen 20a. .
  • the heart-lung machine 12 may have a configuration in which a reservoir, an oxygenator, etc. are further provided in the middle of the circulation circuit (blood removal tube 18 and blood transfer tube 20). According to this configuration, the heart-lung machine 12 can return the blood that has been removed from the body and has been subjected to oxygenation, etc., into the patient's body.
  • the pump device 10 includes an impeller 30 housed within the housing 28 . Centrifugal force generated as the impeller 30 rotates causes the blood to flow as described above. That is, the pump device 10 is a so-called centrifugal pump.
  • the pump device 10 includes a driving device 32 that rotates the impeller 30 , a pump main body 34 that houses the impeller 30 , and a control section 36 that controls driving of the driving device 32 .
  • the housing 28 has a drive-side housing 38 forming the drive device 32 and a body-side housing 40 forming the pump body 34 .
  • a central projection 42 is formed in the drive-side housing 38 , and an insertion hole 44 is formed in the main-body-side housing 40 .
  • the body-side housing 40 is positioned and fixed to the drive-side housing 38 by inserting (engaging) the central protrusion 42 into the insertion hole 44 . Further, the body-side housing 40 and the driving-side housing 38 are separated from each other by disengaging (disengaging from) the central protrusion 42 from the insertion hole 44 .
  • the housing 28 is composed of the body side housing 40 and the driving side housing 38 that are detachable and assembled together when used, so that the driving force of the driving device 32 can be transmitted to the impeller 30 .
  • the pump body 34 is removed from the drive device 32 and discarded.
  • the pump body 34 is configured as a disposable type that is replaced after each use and is disposable or sterilized.
  • the driving device 32 is configured as a reuse type, and a new pump body 34 is attached to operate the impeller 30 of this pump body 34 at the next occasion of use.
  • the drive device 32 includes a motor 50 housed within the drive-side housing 38 .
  • the central convex portion 42 is a hollow body, and the rotating shaft 52 of the motor 50 is accommodated in the hollow interior.
  • a ring-shaped fixed-side repelling magnet 53 is attached to the lower end of the rotating shaft 52 .
  • the fixed-side repulsion magnet 53 is magnetized so that the inner peripheral side is the S pole and the outer peripheral side is the N pole, but conversely, the inner peripheral side is the N pole and the outer peripheral side is the S pole. It may be magnetized as follows. As will be described later, the fixed-side repulsion magnet 53 and the movable-side repulsion magnet 54 provided on the impeller 30 repel each other.
  • a drive-side coupling magnet 56 is held at the upper end of the rotating shaft 52 .
  • the drive-side coupling magnet 56 has an annular shape, and forms a magnetic coupling mechanism with a movable-side coupling magnet 58 (permanent magnet) provided on the impeller 30 .
  • a movable-side coupling magnet 58 permanent magnet
  • the driving side coupling magnet 56 is magnetized so that the polarity alternates along the circumferential direction. That is, in the drive-side coupling magnet 56, the arrangement of N poles, S poles, N poles, and S poles is repeated along the circumferential direction.
  • the control unit 36 is composed of a well-known computer having an input/output interface (not shown), a memory and a processor, and controls driving of the motor 50 .
  • a monitor, a speaker, operation buttons, etc. are provided on the outer surface of the control unit 36, and a user such as a doctor or a nurse sets the driving contents of the pump device 10 by operating the operation buttons.
  • the control unit 36 controls the supply of electric power from the battery based on the user's setting information, and rotates the rotation shaft 52, for example, in the range of 0 to 80000 rpm.
  • the body-side housing 40 of the pump body 34 includes a cylindrical lower housing portion 60 attached to the driving device 32 and a substantially conical upper housing portion 62 connected to the upper portion of the lower housing portion 60 .
  • the lower housing portion 60 and the upper housing portion 62 are configured to be separable from each other so that the impeller 30 can be taken out.
  • An internal space 64 is formed from the lower housing portion 60 to the upper housing portion 62 inside the body-side housing 40 .
  • the impeller 30 is rotatably accommodated in this internal space 64, and blood flows in and out.
  • a shaft tube portion 66 that pivotally supports the impeller 30 is provided on the center side of the lower housing portion 60 .
  • the hollow interior of the shaft tube portion 66 serves as an insertion hole 44 into which the central convex portion 42 is inserted.
  • a fitting hole 67 is formed in the center of the upper end of the shaft tube portion 66, and a pivot 68 (support shaft) is fitted into the fitting hole 67.
  • a tip of the pivot 68 is provided with a shaft-like support portion 70 as a curved portion that is curved into a spherical segment shape.
  • the shaft-like support portion 70 rotatably supports the impeller 30 from the inside.
  • the upper housing part 62 has a blood inflow port 74 connected to the blood removal tube 18 and a blood outflow port 78 connected to the blood transfer tube 20 .
  • the blood inflow port 74 is provided in the ceiling and center of the upper housing portion 62 and protrudes upward.
  • the blood outflow port 78 protrudes tangentially from the side of the internal space 64 and has an outflow channel 78a communicating with the internal space 64 therein.
  • the impeller 30 is housed in the body-side housing 40 so as to cover the shaft tube portion 66 .
  • a slight clearance is generated between the outer peripheral wall of the impeller 30 and the inner peripheral wall of the lower housing portion 60 and between the inner peripheral wall of the impeller 30 and the outer peripheral wall of the shaft tube portion 66 .
  • this clearance interval depends on the size of the pump main body 34, it is set in the range of, for example, about 0.1 mm to 1 mm.
  • the impeller 30 holds a magnet holder 80 .
  • the magnet holder 80 holds the movable side repulsion magnet 54 and the movable side coupling magnet 58 .
  • the magnet holder 80 includes a small-diameter cylindrical portion 84 having a small inner diameter and an outer diameter and a thin wall, and a small-diameter cylindrical portion 84 having a large inner diameter and an outer diameter. and a thick, large-diameter cylindrical portion 86 .
  • the axial dimension of the small-diameter cylindrical portion 84 is smaller than that of the large-diameter cylindrical portion 86 .
  • An outer stepped portion 88 is formed on the outer peripheral wall of the magnet holder 80 based on the difference in outer diameter between the small-diameter cylindrical portion 84 and the large-diameter cylindrical portion 86 . Further, the magnet holder 80 is formed with a stepped insertion hole 90 extending along its height direction (axial direction). An inner stepped portion 92 is formed in the stepped insertion hole 90 based on the inner diameter difference between the small-diameter cylindrical portion 84 that is the lower portion of the magnet holder 80 and the large-diameter cylindrical portion 86 that is the upper portion of the magnet holder 80 .
  • the movable-side repulsion magnet 54 is held on the outer peripheral wall of the small-diameter cylindrical portion 84 .
  • the outer stepped portion 88 serves as a stopper wall that blocks the movable-side repulsion magnet 54 .
  • the inner peripheral side of the movable-side repulsive magnet 54 is magnetized so as to have a polarity opposite to the polarity of the outer peripheral side of the fixed-side repulsive magnet 53 .
  • the inner stepped portion 92 abuts the lower end surface of the movable coupling magnet 58 .
  • the movable-side coupling magnet 58 is magnetized so that the polarity alternates along the circumferential direction. That is, the movable-side coupling magnet 58 repeats the arrangement of N pole, S pole, N pole, and S pole.
  • the material of the magnet holder 80 configured as described above is not particularly limited, in the present embodiment, as the material of the impeller 30 is polyethylene, as will be described later, polyethylene is selected similarly. preferably.
  • the impeller 30 has a cylindrical cover 100.
  • the cylindrical cover 100 encloses the magnet holder 80 together with the movable-side repulsion magnet 54 and the movable-side coupling magnet 58 .
  • the shaft tube portion 66 enters into the hollow interior of the cylindrical cover portion 100 .
  • the outer peripheral wall of the shaft tube portion 66 and the inner peripheral wall of the cylindrical cover portion 100 are separated by a predetermined distance.
  • the vane support portion 102 has a shape as if it were notched in the middle of convergence.
  • washout holes 104a to 104a are provided at the top of the vane support portion 102 as communication holes for communicating the hollow interior of the impeller 30 and the interior space 64 of the body-side housing 40.
  • 104d is formed.
  • the washout holes 104a to 104d are partitioned into adjacent ones by a bridge portion 106, which will be described later. When the bridge portion 106 is removed, the washout holes 104a to 104d are connected to form a substantially perfect circle.
  • a plurality of (eg, eight) vanes 108 are erected on the tapered surface of the vane support portion 102 so as to extend from the cylindrical cover portion 100 side toward the washout holes 104a to 104d.
  • Each vane 108 gently curves toward the center of the cylindrical cover 100 on the way from the cylindrical cover 100 to the washout holes 104a-104d. Vanes 108 apply centrifugal force to the blood as impeller 30 rotates.
  • a space between adjacent vanes 108 serves as a flow path through which blood flows.
  • a bridge portion 106 extending toward the rotation center of the impeller 30 is individually provided on the outer peripheral edge of the washout holes 104a to 104d. In this embodiment, four bridge portions 106 are provided. At the center of rotation of the impeller 30 , a supported portion 120 having a lower cylindrical portion 114 and an upper tapered reduced diameter portion 116 is provided. As a result, the supported portion 120 is integrally connected to the vane supporting portion 102 .
  • a recessed receiving portion 122 as a recessed bearing portion is formed on the lower surface of the columnar portion 114, which is the bottom surface of the supported portion 120.
  • the inner wall surface of the concave receiving portion 122 is curved corresponding to the curved shape of the shaft-like support portion 70 .
  • the impeller 30 is rotatably supported by the pivot 68 by contacting the outer wall surface of the shaft-shaped support portion 70 with the inner wall surface of the concave receiving portion 122 .
  • communication passages 124 a to 124 d are formed on the lower surface of the columnar portion 114 so as to be recessed from the columnar portion 114 toward the tapered reduced diameter portion 116 side.
  • the groove-shaped communicating paths 124a-124d extend linearly from each of the washout holes 104a-104d to the recessed receiving portion 122, respectively. Therefore, the washout holes 104a-104d individually communicate with the recessed receiving portions 122 via the communication paths 124a-124d.
  • the washout hole 104a communicates with the recessed receiving portion 122 via the communicating path 124a, and furthermore, communicates with the washout holes 104b-104d via the communicating paths 124b-124d. communicate. The same applies to the washout holes 104b-104d.
  • the communicating passages 124a to 124d are formed at positions slightly offset with respect to the radius of the cylindrical portion 114. As shown in FIG. In other words, the imaginary extension line L that virtually extends the communication paths 124a to 124d into the recessed receiving portion 122 does not pass through the center O of the recessed receiving portion 122 (or the cylindrical portion 114). Therefore, the communicating paths 124a and 124c do not face each other, and similarly, the communicating paths 124b and 124d do not face each other. It should be noted that the offset arrangement of the communication paths 124a to 124d is not essential. That is, the communication paths 124a to 124d may be formed so as to extend along the radius of the cylindrical portion 114. As shown in FIG.
  • the impeller 30 configured as described above is an integrally molded product. That is, the impeller 30 is a single member that integrally includes the cylindrical cover portion 100, the vane support portion 102, the vanes 108, the bridge portion 106, and the supported portion 120. As shown in FIG. For this reason, the impeller 30 does not have a seam, which is a trace of connecting the members.
  • the material of the impeller 30 is polyethylene. The positions of the movable-side coupling magnet 58 and the movable-side repulsion magnet 54 held by the magnet holder 80 substantially match the design positions.
  • the impeller 30 can be produced by injection molding. That is, for example, after the magnet holder 80 holding the movable-side repelling magnet 54 on the outer peripheral wall of the small-diameter cylindrical portion 84 and holding the movable-side coupling magnet 58 on the inner stepped portion 92 is accommodated in the mold cavity, Molten polyethylene resin is injected into the cavity.
  • the molten resin is filled while deforming into the shape of the impeller 30 following the shape of the cavity. After that, the molten resin filled in the cavity is cooled and hardened, so that the impeller 30 having the magnet holder 80 enclosed in the cylindrical covering portion 100 is obtained. Also, the upper end of the magnet holder 80 is covered with the vane support portion 102 . It should be noted that there is no particular problem even if the fusion between the molten resin and the magnet holder 80 occurs during the process from injection to cooling and hardening.
  • polyethylene has relatively large sink marks during cooling and hardening. Therefore, it is difficult to manufacture an impeller in which the movable-side repulsion magnet 54 and the movable-side coupling magnet 58 are enclosed in the cylindrical cover 100 from polyethylene. That is, in this case, the molten resin shrinks during cooling and hardening. Along with this, the magnet surrounded by the molten resin moves with the molten resin. This is because, as a result, the magnets are misaligned. Thus, when polyethylene is selected as the impeller material, it is not easy to obtain an impeller in which the magnets are arranged at the designed positions.
  • the magnet holder 80 is used in the present embodiment.
  • the magnet holder 80 that holds the movable-side repulsion magnet 54 and the movable-side coupling magnet 58 is relatively heavy due to its own weight. For this reason, the magnet holder 80 is difficult to move even when it is pressed by the molten resin that tends to contract inward in the diametrical direction. Therefore, the molten resin that forms the cylindrical cover 100 is inhibited from significantly shrinking. For this reason, it is possible to obtain the impeller 30 in which the magnet holder 80 is arranged at a predetermined designed position, in other words, at a desired position.
  • the impeller 30 in which the movable-side coupling magnet 58 and the movable-side repulsion magnet 54 are arranged at predetermined positions is manufactured despite the fact that polyethylene, which has a large sink mark, is used as the material. It is possible. By using this impeller 30, it is possible to obtain the pump device 10 in which various characteristics such as output and efficiency meet design values.
  • the impeller 30 is obtained as an integrally molded product, it is sufficient to prepare one injection molding device. In other words, there is no need to separately prepare an injection molding apparatus for each member in order to individually obtain a plurality of members. In addition, the equipment and solvent for joining the members are not required, and the joining work is also unnecessary. Therefore, it is possible to simplify the production equipment for the impeller 30 and reduce the cost of equipment investment. Also, the work up to obtaining the impeller 30 is simplified.
  • a heart-lung machine 12 including a pump device 10 is constructed for a patient to assist cardiopulmonary function.
  • the user connects the blood removal tube 18 and the blood supply tube 20 to the prepared pump body 34 .
  • the pump device 10 is assembled by attaching the pump main body 34 to the driving device 32 .
  • the user inserts the center convex portion 42 of the driving side housing 38 into the insertion hole 44 of the main body side housing 40 to position and fix the pump main body 34 and the driving device 32 to each other.
  • the rotating shaft 52 rotates following the energization of the motor 50 of the driving device 32 .
  • the drive-side coupling magnet 56 provided on the rotary shaft 52 rotates.
  • the drive-side coupling magnet 56 and the movable-side coupling magnet 58 are magnetized so that N poles and S poles are alternately arranged along the winding direction. Therefore, when the drive-side coupling magnet 56 performs a revolving motion, the same poles of the drive-side coupling magnet 56 and the movable-side coupling magnet 58 repel each other, and the different poles attract each other. Based on this, the impeller 30 rotates.
  • the center of rotation is the supported portion 120 , more specifically, the abutting portion between the shaft-like support portion 70 and the concave receiving portion 122 .
  • the communication paths 124a to 124d are formed on the lower surface of the supported portion 120 as described above (see FIG. 7 in particular). Therefore, the centrifugal force generated by the rotation of the impeller 30 causes the blood to flow from the recessed receiving portion 122 toward the washout holes 104a-104d via the communicating passages 124a-124d. This flow is shown as arrow B in FIG. That is, when the impeller 30 rotates, the blood flow indicated by the arrow A and the blood flow indicated by the arrow B occur simultaneously inside the pump device 10 .
  • the blood that has entered the concave receiving portion 122 reaches the washout holes 104a to 104d via the communicating paths 124a to 124d. Then, it merges with the blood that has flowed through the hollow interior of the cylindrical cover 100 and reached the washout holes 104 a to 104 d, and advances into the internal space 64 . As described above, by forming the communication paths 124 a to 124 d on the lower surface of the supported portion 120 , the blood that has entered the concave receiving portion 122 is discharged from the concave receiving portion 122 . As a result, stagnation of blood in concave receiving portion 122 can be suppressed.
  • the impeller 30 is a seamless integrally molded product as described above. Therefore, the impeller 30 has excellent strength. Moreover, since the material of the impeller 30 is polyethylene, cracks are less likely to occur. Therefore, in the pump device 10, a decrease in pump efficiency or the like is suppressed.
  • the positions of the movable-side coupling magnet 58 and the movable-side repulsion magnet 54 accurately correspond to the designed positions. Therefore, various characteristics such as the output and pump efficiency of the pump device 10 can be obtained at values that match the design values.
  • the present invention is not particularly limited to the above-described embodiment, and various modifications are possible without departing from the gist of the present invention.
  • the number of washout holes is not limited to four. Also, the number of communicating paths may be set according to the number of washout holes.
  • the inner peripheral wall of the stepped insertion hole 90 of the magnet holder 80 may be exposed.
  • the shaft tube portion 66 is inserted into the stepped insertion hole 90 .
  • the impeller may be configured by joining a plurality of members.
  • two accommodation chambers are formed when the members are joined together, and the movable-side repulsion magnet 54 and the movable-side coupling magnet 58 may be individually accommodated in each of the accommodation chambers. That is, in this configuration, it is not particularly necessary to use the magnet holder 80 .
  • the material of the impeller is also not particularly limited to polyethylene, and other resins may be used. Specific examples of other resins include polycarbonate, polyacetal, polypropylene, styrenic resins (GPPS, HIPS, SAN, ABS), and acrylic resins (MBS, PMMA).

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Mechanical Engineering (AREA)
  • Anesthesiology (AREA)
  • Cardiology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Structures Of Non-Positive Displacement Pumps (AREA)

Abstract

Dans une turbine (30) constituant un dispositif de pompe (10), une pluralité de trous de communication (104a-104d) sont formés, permettant une communication entre l'intérieur creux correspondant et l'espace intérieur (64) d'un logement (28). La turbine (30) comporte une partie supportée (120) supportée par un arbre de support (68) disposé dans le logement (28). Sur la surface inférieure de la partie supportée (120), une partie palier (122) qui reçoit l'extrémité avant (70) de l'arbre de support et des chemins de communication (124a-124d) qui permettent une communication individuelle entre chacun des trous de communication et la partie palier sont formés.
PCT/JP2022/006803 2021-03-04 2022-02-21 Dispositif de pompe WO2022185961A1 (fr)

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Application Number Priority Date Filing Date Title
JP2023503715A JPWO2022185961A1 (fr) 2021-03-04 2022-02-21

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Application Number Priority Date Filing Date Title
JP2021034498 2021-03-04
JP2021-034498 2021-03-04

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2008183229A (ja) * 2007-01-30 2008-08-14 Jms Co Ltd ターボ式血液ポンプ
WO2016042976A1 (fr) * 2014-09-19 2016-03-24 テルモ株式会社 Pompe centrifuge
WO2020017787A1 (fr) * 2018-07-17 2020-01-23 서강대학교산학협력단 Pompe à sang centrifuge
CN111249551A (zh) * 2020-01-21 2020-06-09 深圳汉诺医疗科技有限公司 一种用于人工心脏的蜗式泵头、人工心脏泵和ecmo设备
WO2020255499A1 (fr) * 2019-06-19 2020-12-24 テルモ株式会社 Dispositif de pompe

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2008183229A (ja) * 2007-01-30 2008-08-14 Jms Co Ltd ターボ式血液ポンプ
WO2016042976A1 (fr) * 2014-09-19 2016-03-24 テルモ株式会社 Pompe centrifuge
WO2020017787A1 (fr) * 2018-07-17 2020-01-23 서강대학교산학협력단 Pompe à sang centrifuge
WO2020255499A1 (fr) * 2019-06-19 2020-12-24 テルモ株式会社 Dispositif de pompe
CN111249551A (zh) * 2020-01-21 2020-06-09 深圳汉诺医疗科技有限公司 一种用于人工心脏的蜗式泵头、人工心脏泵和ecmo设备

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