JP2008121687A - Artificial heart pump - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an artificial heart pump adapted so that a part of a fixed body can be independently disassembled. <P>SOLUTION: A sleeve 5 and a fixed body 8 include permanent magnets 5b and 8b which generate magnetic repelling force in the axial direction, respectively, and a journal bearing for retaining the sleeve 5 in the radial direction is provided between the sleeve 5 and a fixed shaft 4 to thereby support the sleeve 5 without axial and radial contact by the repelling magnetic force by the permanent magnets and the dynamic pressure by the dynamic pressure bearing. Further, the fixed body 8 is connected by inserting a projection part 8b provided in the central position of a rear end surface 8x of the fixed body 8 to a hole 4a provided in the central position of an end surface 4x closer to the fixed body 8 of the fixed shaft 4 connected to a fixed body 3. Accordingly, the sleeve 5 can be removed only by removing the fixed body 3. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an artificial heart pump, and more particularly, to an artificial heart pump using an axial flow pump that pumps blood.

  Conventionally, an artificial heart pump that pumps blood by using the rotation of an impeller has been used as a medical alternative or auxiliary heart. As this artificial heart pump, those using a roller pump or a centrifugal pump and those using an axial pump are provided. Of these types of artificial heart pumps, those using an axial flow pump can be smaller in size than those used for a roller pump or a centrifugal pump.

  In a conventional artificial heart pump using this axial flow pump, a motor stator is included in a housing, and a rotor having an impeller around it includes a permanent magnet that performs a magnetic reaction with the motor stator. As such an artificial heart pump, as shown in FIG. 24, a rotor 104 having an impeller 105 on its outer peripheral surface is installed between fixed bodies 102 and 103 fixed to a housing 101. There are provided pivot bearings 106a and 106b installed on the surface facing the rotor 104. That is, the pivot bearings 106a and 106b are formed by projecting the center of the surface of the rotor 104 facing the fixed bodies 102 and 103.

  However, when supported by the pivot bearings 106a and 106b as shown in FIG. 24, wear powder may be generated in the pivot bearings 106a and 106b. In addition, since the gap between the fixed bodies 102 and 103 and the rotor 104 is narrowed, there is a possibility that a thrombus is easily formed or that red blood cells are destroyed (hemolysis).

  On the other hand, as shown in FIG. 25, a fixed rotor 102 and 103 are connected by a fixed shaft 121, and a cylindrical rotor 122 that rotates along the outer periphery of the fixed shaft 121 is provided. There is provided a configuration in which a dynamic pressure bearing is configured by providing a groove on each surface where the fixed bodies 102 and 103 face each other. That is, when the rotor 122 rotates, the contact between the rotor 122 and the fixed bodies 102 and 103 is prevented by the dynamic pressure generated by the grooves provided on the surfaces of the fixed bodies 102 and 103 facing the rotor 122, and the thrust is increased. Operates as a bearing. However, when the hydrodynamic bearing is configured in this way, a narrow gap for generating the dynamic pressure is required, and this gap may easily cause a thrombus or hemolysis.

In order to avoid such a problem, the present applicant not only constitutes a hydrodynamic bearing, but also uses a passive repulsive magnetic bearing that utilizes a magnetic repulsive force that balances the hydrothrust load applied to the impeller, so that the rotor and the fixed body An artificial heart pump that prevents contact with the body is proposed (see Patent Document 1). As shown in FIG. 26, the artificial heart pump provided with this passive repulsive magnetic bearing has a configuration as shown in FIG. 25, and by installing permanent magnets 131 and 132 on the rotor 122 and the fixed body 103 respectively, A passive repulsive magnetic bearing with a magnetic repulsive force commensurate with the load is constructed.
JP 2004-346930 A

  However, according to the artificial heart pumps configured as shown in FIGS. 25 and 26 described above, the fixed bodies 102 and 103 connected by the fixed shaft 121 are fixed to the housing 101 via the current plate and the diffuser. Therefore, when only the rotor 122 is removed for internal inspection or the like, it is necessary to disassemble all the fixed parts by the fixed bodies 102 and 103 and the fixed shaft 121. Moreover, not only the assembly performance is bad, but also the distance between the bearing surfaces by the axial fixed bodies 102 and 103 and the rotor 122 when the repulsive magnetic bearing is provided as shown in FIG. 26 is adjusted. Have difficulty.

  25 and 26, in addition to rotating the rotor 122 by the motor stator included in the housing 101 and the permanent magnet included in the rotor 122, the rotor 122 and the fixed shaft are also provided. It serves as a journal bearing that prevents radial contact with 121. However, since the permanent magnet is provided on the inner diameter side of the rotor 122, the outer diameter of the rotor 122 provided with the impeller is increased. In addition, when a high pressure is required, it is necessary to increase the rotational speed of the rotor 122. However, when the rotational speed is increased, the hemolysis characteristics are deteriorated. Therefore, since the size of the artificial heart pump is limited, the upper limit of the pressure is limited.

  Furthermore, when the hydrodynamic bearing is configured as shown in FIG. 25, a narrow gap for generating the dynamic pressure is required, and this gap may easily form a thrombus or cause hemolysis. In contrast, in the case of an artificial heart pump provided with a passive repulsive magnetic bearing as shown in FIG. 26, the gap can be made wider than in the case of using only a dynamic pressure bearing as shown in FIG. 25, thereby reducing the occurrence of thrombus and hemolysis. However, contact is generated between the rotor part and the fixed body at the rear part of the rotor due to the magnetic repulsion force under the operating conditions with a small hydrothrust load and at the time of start / stop. Further, depending on the operating conditions, contact may occur between the rotor and the fixed body before and after the rotor. In the configuration shown in FIG. 25, only the convex portion of the hydrodynamic bearing groove is contacted. However, since the contact is made in a relatively large area, there is a problem in durability. In addition, this may cause abrasion powder, thrombus, and hemolysis due to contact between the rotor and the fixed body.

  Further, in the conventional artificial heart pump, the motor stator included in the housing is constituted by a stator coil having a slot for winding a coil in order to obtain a large torque. However, in the case of a stator coil having a slot, the outer diameter of the housing is increased by the amount of the slot, which hinders downsizing of the artificial heart pump. Further, in each of the artificial heart pumps shown in FIGS. 25 and 26, since the rotor 122 includes a permanent magnet and is configured as a synchronous motor, the artificial heart pump is likely to step out due to load fluctuations and may stop. There is.

  In view of such a problem, an object of the present invention is to provide an artificial heart pump having a structure in which a part of the fixed body can be independently disassembled. Another object of the present invention is to provide an artificial heart pump that can be downsized in the axial direction or radial direction. Another object of the present invention is to provide an artificial heart pump that increases the discharge pressure without increasing the rotational speed. Furthermore, another object of the present invention is to provide an artificial heart pump capable of making it difficult to cause a step-out due to load fluctuations.

  The artificial heart pump of the present invention includes a housing, a first and a second fixed body connected to the housing and fixed in front and rear in the axial direction of the housing, and a space between the first and second fixed bodies. A plurality of impellers protruding from an outer wall surface of the first rotating body, a motor stator included in a position surrounding the first rotating body in the housing and generating a rotating magnetic field, In the artificial heart pump that flows blood in the axial direction by rotating the first rotating body by the rotating magnetic field of the motor stator, each of the first rotating body and the first fixed body is the first The first and second permanent magnets that generate magnetic repulsive force that acts on the opposite side to the thrust load applied from the rear side to the front side with respect to the axial direction of the impeller that acts when the rotating body rotates, are provided inside, Above Between the first and second fixed body and said first rotary member, characterized in that it comprises a journal bearing which holds the first rotating member in the radial direction.

  The artificial heart pump includes first and second main shafts extending in the axial direction with respect to the front and rear of the first rotating body, and the first and second fixed bodies penetrate in the axial direction, respectively. And a first and second through hole into which the second main shaft is inserted, and the first and second permanent magnets constitute a thrust bearing for holding the first rotating body in the axial direction thereof, and the journal bearing is The first main shaft may be inserted into the first through hole and the second main shaft may be inserted into the second through hole.

  When configured in this manner, a second rotating body different from the first rotating body provided with an impeller protruding from the outer wall surface may be installed at the front end in the axial direction of the first main shaft. Absent. Further, a third permanent magnet that generates a magnetic repulsive force with the second permanent magnet in the first stationary body may be provided inside the second rotating body.

  In these configurations, the first and second fixed bodies include a plurality of stationary blades whose inner edges are connected to the outer wall surface and project toward the inner wall surface of the housing, and the outer edges of the stationary blades are the housing. The first and second fixed bodies may be fixed to the housing by being connected to each other.

  According to the present invention, by providing the journal bearing that holds the first rotating body in the radial direction between the first and second fixed bodies and the first rotating body, the first rotating body has a ring shape. It is not necessary to install a fixed shaft at the center position of the first rotating body, and the first rotating body can be formed into a cylindrical shape. Therefore, the installation position of the anisotropic permanent magnet and the rotor can be shifted in the radial direction toward the center position. Therefore, the size of the rotating body in the radial direction can be reduced and the size can be reduced.

  Also, by installing a second rotating body different from the first rotating body provided with the impeller, it is possible to provide a plurality of stages of impellers and increase the discharge pressure without increasing the rotation speed of the artificial heart pump. can do. Thereby, the hemolysis characteristic of the artificial heart pump can be improved.

<First Embodiment>
A first embodiment of the present invention will be described with reference to the drawings. FIG. 1 is a cross-sectional view showing a configuration of an artificial heart pump in the present embodiment. In addition, below, it demonstrates as front (upstream side) and back (downstream side) according to the flow of blood. Further, the artificial heart pump shown in FIG. 1 will be described by taking as an example the one provided with both a dynamic pressure bearing and a passive repulsive magnetic bearing as in FIG.

  The artificial heart pump of FIG. 1 has a cylindrical housing 1, a plurality of diffusers 2 joined to the inner wall surface of the housing 1, and a plurality of diffusers 2 projecting from the outer wall surface, thereby being supported by the housing 1. From the fixed body 3, the fixed shaft 4 installed in front of the fixed body 3, the sleeve 5 installed so as to be wrapped around the fixed shaft 4 and rotating on the outer periphery of the fixed shaft 4, and the outer wall surface of the sleeve 5 A plurality of projecting impellers 6, a plurality of rectifying plates 7 provided in front of the impeller 6, a fixed body 8 connected to and supported by the fixed shaft 4 and the rectifying plates 7 projecting from the outer wall surface, Is provided. The outer edge of the rectifying plate 7 and the inner wall surface of the housing 1 are not joined, and a gap is provided between them.

  This artificial heart pump is provided with a polar anisotropic permanent magnet 5 a inside the sleeve 5 and a motor stator 1 a made of an electromagnetic coil whose magnetic pole faces the outer wall surface of the sleeve 5 inside the housing 1. In addition, a plurality of polar anisotropic permanent magnets 5 a are provided radially about the central axis X of the artificial heart pump, and the direction of the magnetic flux is set to a direction perpendicular to the inner wall surface of the housing 1. Further, the magnetic poles facing the inner wall surface of the housing 1 of the adjacent polar anisotropic permanent magnets 5a are reversed in polarity. Therefore, by causing currents having different phases, such as three-phase currents, to flow through the magnetic coils constituting the motor stator 1a, the rotating power acts on the polar anisotropic permanent magnet 5a, and the sleeve 5 and the impeller 6 rotate as a motor rotor.

  A ring-shaped permanent magnet 5b is included in the front tip portion of the sleeve 5, and a permanent magnet 8a having a rear surface facing the front surface of the permanent magnet 5b is included in the fixed body 8. Is done. At this time, since the magnetic pole on the front surface of the permanent magnet 5b and the magnetic pole on the rear surface of the permanent magnet 8a have the same polarity, the magnetic repulsive force of the permanent magnets 5b and 8a acts. The permanent magnets 5b and 8a function as a thrust bearing with respect to the axial direction of the central axis X, and the magnetic repulsion force by the permanent magnets 5b and 8a increases the pressure behind the impeller 6 when the artificial heart pump is driven. The sleeve 5 is adjusted so as to be balanced with the hydrothrust load, which is a force for moving the sleeve 5 forward.

  A plurality of spiral thrust dynamic pressure generating grooves 100 as shown in FIG. 2 are formed on the front end surface 3x of the fixed body 3 and the rear end surface 8x of the fixed body 8, respectively. That is, dynamic pressure is generated in the blood flowing in the thrust dynamic pressure generating groove 100, and the thrust load applied to the sleeve 5 is supported together with the magnetic repulsive force by the permanent magnets 5b and 8a. By the above-described dynamic pressure bearing by the thrust dynamic pressure generating groove 100 and the passive repulsive magnetic bearing by the permanent magnets 5b and 8a, when the sleeve 5 is rotated, the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3 are Contact and contact between the front end surface 5y of the sleeve 5 and the rear end surface 8x of the fixed body 8 can be prevented.

  And the baffle plate 7 which protruded from the outer wall surface of the fixed body 8 is arrange | positioned at equal intervals in the circumferential direction centering | focusing on the central axis X, and also both edges are on the outer wall surface of the fixed body 3, and the inner wall surface of the housing 1. The joined diffusers 2 are arranged at equal intervals in the circumferential direction around the central axis X. And each of the front end of the fixed body 8 and the rear end of the fixed body 3 has a structure in which the central portion is raised. Therefore, the blood taken in by the bulge at the front end of the fixed body 8 is branched without resistance and guided to the rectifying plate 7, and the blood rectified by the diffuser 2 by the bulge at the rear end of the fixed body 3 is guided without resistance. . Further, the impellers 6 protruding from the outer wall surface of the sleeve 5 are also arranged at equal intervals in the circumferential direction around the central axis X.

  Further, a protrusion 8b provided at the center position of the rear end face 8x of the fixed body 8 is inserted into the hole 4a provided at the center position of the end face 4x on the fixed body 8 side of the fixed shaft 4 joined to the fixed body 3. Is connected. Each of the hole 4a and the protruding portion 8b has a threaded shape, and the protruding portion 8b is rotated and inserted into the hole 4a, whereby the fixed body 8 is fixed to the fixed shaft 4 around which the sleeve 5 is mounted. .

  In such an artificial heart pump, first, the fixed body 3 having the fixed shaft 4 bonded thereto is inserted into the housing 1, and then the outer edge of the diffuser 2 projected from the fixed body 3 is bonded to the housing. 3 and the fixed shaft 4 are fixed in the housing 1. Then, after the sleeve 5 having the impeller 6 on the outer peripheral surface is mounted on the fixed shaft 4, the fixed body 8 is rotated while inserting the protruding portion 8 b of the fixed body 8 into the hole 4 a of the fixed shaft 4. A fixed body 8 is fixed to the fixed shaft 4, and a sleeve 5 is installed between the fixed bodies 3 and 8.

  Therefore, since the rectifying plate 7 connected to the fixed body 8 is not fixed to the housing 1 and the fixed body 8 and the fixed shaft 4 are connected by screws, the fixed body 8 is compared with the conventional case. Can be easily fixed, and its assemblability can be improved. Further, when removing the sleeve 5 provided with the impeller 6 for internal inspection or the like, it is only necessary to remove the fixed body 8 and take it out from the housing 1, and the fixed shaft 4 around which the sleeve 5 is wrapped is connected as in the conventional case. It is not necessary to remove both the fixed bodies 3 and 8 from the housing 1.

  In this embodiment, the fixed body 8 provided with the rectifying plate 7 is inserted and fixed to the fixed shaft 4, but the outer edge of the rectifying plate 7 is attached to the inner wall surface of the housing 1 as shown in FIG. 3. The fixing body 8 may be fixed by bonding, and a gap may be provided between the diffuser 2 and the inner wall surface of the housing 1. At this time, the protrusion 3b provided at the center position of the front end surface 3x of the fixed body 3 is formed in the hole 4b provided at the center position of the end surface 4y on the fixed body 3 side of the fixed shaft 4 joined to the fixed body 8. It is connected by being inserted. Each of the hole 4b and the protrusion 3b has a threaded shape, and the protrusion 3b is rotated and inserted into the hole 4b, whereby the fixed body 3 is fixed to the fixed shaft 4 around which the sleeve 5 is mounted. .

  Further, the inner edge of the rectifying plate 7 is joined to the fixed body 8 and the outer edge of the rectifying plate 7 is separated from the housing 1. However, as shown in FIG. It may be fixed to the inner wall surface of the housing 1 and protruded from the inner wall surface of the housing 1 to separate the inner edge of the rectifying plate 7 from the fixed body 8. Similarly, as in the artificial heart pump of FIG. 3, as shown in FIG. 4B, even when the outer edge of the rectifying plate 7 is joined to the inner wall surface of the housing 1 to fix the fixed body 8, the outer edge of the diffuser 2. May be joined to the inner wall surface of the housing 1 and fixed in a shape protruding from the inner wall surface of the housing 1 to separate the inner edge of the diffuser 2 from the fixed body 3.

  Furthermore, in the artificial heart pump shown in FIGS. 1 and 4A, the protrusion 8b is provided on the fixed body 8 and is inserted into the hole 4a of the fixed shaft 4 to be fixed. As shown in FIG. Further, a protrusion 4c is provided at the center position of the end face 4x of the fixed shaft 4 on the fixed body 8 side, and a hole 8c into which the protrusion 4c is inserted is provided at the center position of the rear end face 8x of the fixed body 8. I do not care. Similarly, as shown in FIG. 5 (b), as in the artificial heart pump of FIG. 3, the outer edge of the rectifying plate 7 is joined to the inner wall surface of the housing 1 to fix the fixed body 8 in FIGS. 3 and 4 (b). Also in the artificial heart pump, the protrusion 4d is provided at the center position of the end face 4y on the fixed body 3 side of the fixed shaft 4, and the hole 3c into which the protrusion 4d is inserted is provided at the center position of the front end face 3x of the fixed body 3. It does not matter even if it is provided.

<Second Embodiment>
A second embodiment of the present invention will be described with reference to the drawings. FIG. 6 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 6, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 6 is similar to the artificial heart pump of FIG. 1 in that the front end surface 5y of the sleeve 5 and the rear of the fixed body 8 are disposed between the rear end surface 8x of the fixed body 8 and the front end surface 4x of the fixed shaft 4. One or more adjustment rings 9 for adjusting the gap with the end face 8x are installed. At this time, the adjustment ring 9 is mounted on the protrusions 8 b of the fixed body 8, and the fixed body 8 provided with the adjustment ring 9 is inserted into the hole 4 a of the fixed shaft 4. , 8 and the sleeve 5 are adjusted. That is, a test operation is performed at the time of manufacture, and the contact between the fixed bodies 3 and 8 and the sleeve 5 is measured, whereby the gap between the fixed bodies 3 and 8 and the sleeve 5 is confirmed. Thereafter, the distance between the fixed bodies 3 and 8 is adjusted by the number of adjusting rings 9 installed between the fixed shaft 4 and the fixed body 8, and the gap between the fixed bodies 3 and 8 and the sleeve 5 is adjusted.

  In the present embodiment, the adjustment ring 9 is added to the configuration of the artificial heart pump shown in FIG. 1. However, the adjustment ring 9 may be added to the configuration of the artificial heart pump shown in FIG. . Also at this time, as in FIG. 6, the adjustment ring 9 is mounted on the protrusion 8 b of the fixed body 8 and is inserted into the hole 4 a of the fixed shaft 4. Further, an adjustment ring is added to the configuration of the artificial heart pump shown in FIGS. 3 and 4B, and the adjustment ring 9 is mounted on the protrusion 3 b of the fixed body 3 and inserted into the hole 4 b of the fixed shaft 4. It doesn't matter if it is done. Further, as in the artificial heart pump of FIGS. 5 (a) and 5 (b), the fixed shaft 4 is provided with projections 4c and 4d, and the adjustment ring 9 is mounted on the projections 4c and 4d to fix the fixed body. It may be inserted into the 8 holes 8 c and the holes 3 c of the fixed body 3.

<Third Embodiment>
A third embodiment of the present invention will be described with reference to the drawings. FIG. 7 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 7, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 7 differs from the artificial heart pump of FIG. 1 in that the outer edge of the rectifying plate 7 is joined to the inner wall surface of the housing to fix the fixed body 8 and the fixed shaft 4 is fixed to the fixed bodies 3 and 8. The fixed shafts 41 and 42 connected to each are divided into two parts. In this artificial heart pump, first, the outer edge of the diffuser 2 is fixed to the inner wall surface of the housing 1 to fix the fixed body 3 provided with the diffuser 2 in the housing 1, and then the fixed body 3 is connected to the fixed body 3. A sleeve 5 having an impeller 6 is mounted on the shaft 41. Then, the fixed body 8 is installed in the housing 1 so that the fixed shaft 42 connected to the fixed body 8 is inserted into the hole of the sleeve 5.

  When the fixed bodies 3 and 8 and the sleeve 5 are respectively installed in the housing 1 in this way, a trial run is performed to measure the contact between the fixed bodies 3 and 8 and the sleeve 5, whereby the fixed bodies 3 and 8 and the sleeve 5 are measured. 5 is confirmed. Thereafter, when the installation position of the fixed body 8 is moved and changed in the X-axis direction so as to adjust the gap between the confirmed fixed bodies 3 and 8 and the sleeve 5, the outer edge of the rectifying plate 7 is moved to the housing 1. The fixed body 8 is fixed in the housing 1 by being fixed to the inner wall surface. Thus, by moving the fixed body 8 in the X-axis direction, the distance between the fixed bodies 3 and 8 is easily adjusted, and the gap between the fixed bodies 3 and 8 and the sleeve 5 is adjusted to an appropriate distance. be able to. In this embodiment, the fixed body 3 is fixed and the fixed body 8 is moved and adjusted. However, the fixed body 8 may be fixed and the fixed body 3 may be moved and adjusted.

  Further, when removing the sleeve 5 provided with the impeller 6 for internal inspection or the like, it is only necessary to remove one of the fixed bodies 3 and 8 and take it out from the housing 1. It is not necessary to take out both the fixed bodies 3 and 8 to which the shaft 4 is connected from the housing 1.

<Fourth Embodiment>
A fourth embodiment of the present invention will be described with reference to the drawings. FIG. 8 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 8, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 8 differs from the artificial heart pump of FIG. 1 in that the fixed shaft 4 is connected only to the fixed body 3 and the sleeve 5 is sandwiched between the fixed shaft 4 and the fixed body 8. A bottom 51 is provided at the position. A ring-shaped permanent magnet 5 b is included in the bottom 51 of the sleeve 5. The permanent magnet 5b is installed so as to be located inside the polar anisotropic permanent magnet 5a. That is, the outer peripheral diameter of the permanent magnet 5b is smaller than the inner peripheral diameter of the polar anisotropic permanent magnet 5a, and overlaps at the position of the front end of the polar anisotropic permanent magnet 5a in the X-axis direction. The permanent magnet 5b is installed.

  Further, a columnar permanent magnet 8 a is installed at a position facing the permanent magnet 5 b inside the fixed body 8. At this time, since the magnetic pole on the front surface of the permanent magnet 5b and the magnetic pole on the rear surface of the permanent magnet 8a have the same polarity, the magnetic repulsive force of the permanent magnets 5b and 8a acts. Further, a through hole 52 is provided at the center position of the bottom 51 of the sleeve 5, and the blood flowing into the gap between the inner peripheral wall of the sleeve 5 and the outer peripheral wall of the fixed shaft 4 is discharged by this through hole 52, Blood clotting can be prevented.

  Thus, according to the configuration of the present embodiment, the permanent magnet 5b used as a part of the passive repulsive magnetic bearing can be installed at a position overlapping the polar anisotropic permanent magnet 5a in the axial direction. The length in the axial direction of 5 can be a length depending only on the polar anisotropic permanent magnet 5a. Further, as shown in FIG. 9, a permanent magnet 43 that generates a magnetic force that repels and repels the magnetic force generated on the rear side of the permanent magnet 5 b may be included in the front end of the fixed shaft 4. With this configuration, it is possible to prevent contact between the front end of the fixed shaft 4 and the inner wall surface of the bottom 51 of the sleeve 5, and also prevent contact between the fixed body 3 and the sleeve 5.

<Fifth Embodiment>
A fifth embodiment of the present invention will be described with reference to the drawings. FIG. 10 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. 10, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 10 differs from the artificial heart pump of FIG. 1 in that it penetrates in the center of the fixed bodies 3 and 8 in the X-axis direction instead of the fixed shaft 4 and the sleeve 5 that functioned as journal bearings. The holes 31 and 81 are provided, and the main shafts 53 and 54 inserted into the through holes 31 and 81 of the fixed bodies 3 and 8 are provided with an impeller 50 connected to both ends in the X-axis direction. That is, by inserting the main shafts 53 and 54 into the through holes 31 and 81, the through holes 31 and 81 and the main shafts 53 and 54 function as journal bearings, and the impeller 6 protrudes from the outer peripheral wall of the impeller 50 at equal intervals. The impeller 50 includes a polar anisotropic permanent magnet 5a and a permanent magnet 5b similar to the sleeve 5.

  Each of the rear end surface of the main shaft 53 and the front end surface of the main shaft 54 has a structure in which the central portion thereof is raised. Then, the end portions of the rear side of the fixed body 3 and the front side of the fixed body 8 are configured by curved surfaces that are continuous with the curved surfaces of the rear end surface of the main shaft 53 and the front end surface of the main shaft 54, respectively. Therefore, blood taken in by the raised surface of the main shaft 54 and the curved surface on the front side of the fixed body 8 is branched without resistance and guided to the current plate 7, and is rectified by the diffuser 2 by the curved surface on the rear side of the fixed body 3 and the raised surface of the main shaft 53. Guide the blood to flow together without resistance.

  Thus, in this embodiment, unlike the other embodiments in which the sleeve 5 from which the impeller 6 protrudes is a rotating body, the impeller 50 having the main shafts 53 and 54 and from which the impeller 6 protrudes is used as a rotating body. Unlike the other embodiments, the rotary shaft 4 is not required. Therefore, since the installation positions of the polar anisotropic permanent magnet 5a and the permanent magnet 5b can be moved to the inner diameter side as compared with the artificial heart pump of the other embodiments, the impeller 50 in the artificial heart pump of the present embodiment. Can be made smaller than the outer diameter of the sleeve 5 in the artificial heart pump of the other embodiments, and the radial shape of the artificial heart pump can be reduced.

<Sixth Embodiment>
A sixth embodiment of the present invention will be described with reference to the drawings. FIG. 11 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 11, the same parts as those in FIG. 10 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump shown in FIG. 11 is similar to the artificial heart pump shown in FIG. 10 except that the impeller 55 installed at the front end of the main shaft 54, the impeller 61 protruding from the outer wall surface of the impeller 55, and the inside of the impeller 55 And a ring-shaped permanent magnet 5d installed in the. Further, the length of the fixed body 8 in the axial direction is substantially equal to the length of the rectifying plate 7, and unlike the artificial heart pump of FIG. 10, the front side of the fixed body 8 is formed by a flat surface parallel to the rear side. The Furthermore, instead of the front end surface of the main shaft 54 of the artificial heart pump of FIG. 10, the front end surface of the impeller 55 has a structure in which the central portion thereof is raised.

  The permanent magnet 5d is included on the rear side of the impeller 55 so as to oppose the permanent magnet 8a, and the generated magnetic force is made to repel the magnetic force generated on the front side of the permanent magnet 8a. . By configuring in this way, contact between the front end face of the fixed body 8 and the rear end face of the impeller 55 is prevented, and the rear end face of the impeller 50 connected to the impeller 55 and the main shaft 54 and the fixed body. 3 can also be prevented from contacting the front end face.

  Similarly to the impeller 6, the impellers 61 are arranged at equal intervals in the circumferential direction around the central axis X. The impellers 6 and 61 constitute a two-stage axial flow pump in which the rectifying plate 7 is sandwiched between the impellers 6 and 61 as a stationary blade. Thus, by setting it as 2 steps | paragraphs, compared with the case where it is set as a single | single-stage structure like the artificial heart pump of other embodiment, a high discharge pressure is obtained with low rotation speed. Therefore, it can operate | move by a low rotation speed and can improve a hemolysis characteristic.

<Seventh Embodiment>
A seventh embodiment of the present invention will be described with reference to the drawings. FIG. 12 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 12, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 12 differs from the configuration of the artificial heart pump of FIG. 1 in that impellers 62 and 63 are sleeved toward the inner wall surface of the housing 1 on the front side and the rear side of the sleeve 5 instead of the impeller 6. 5 so as to protrude from the outer wall surface. The impellers 62 and 63 are arranged at equal intervals in the circumferential direction around the central axis X. A stationary blade 64 is installed between the impellers 62 and 63 so as to protrude from the inner wall surface of the housing 1 to the outer wall surface of the sleeve 5. Similar to the impellers 62 and 63, the stationary blades 64 are also arranged at equal intervals in the circumferential direction around the central axis X.

  As described above, the artificial heart pump shown in FIG. 12 is configured as an axial flow pump having a two-stage configuration with the impellers 62 and 63 installed with the stationary blade 64 interposed therebetween. By adopting a two-stage configuration in this way, as in the sixth embodiment, a higher discharge pressure can be obtained at a lower rotational speed than when a single-stage configuration is used as in the artificial heart pump of the other embodiments. . Therefore, it can operate | move by a low rotation speed and can improve a hemolysis characteristic.

  Although the present embodiment has been described based on the configuration of FIG. 1 of the first embodiment, as shown in FIGS. 3, 4 (a), (b), and FIGS. 5 (a), (b). Similarly, the configuration including the impellers 62 and 63 and the stationary blade 64 may be used instead of the impeller 6. Further, as in the conventional case, the configuration may include the impellers 62 and 63 and the stationary blade 64 instead of the impeller 6 in a state where the diffuser 2 and the rectifying plate 7 are connected to both the fixed bodies 3 and 8 and the housing 1. .

  Further, in contrast to the configurations of the second to fourth embodiments described above, impellers 62 and 63 are installed on the outer wall surface of the sleeve 5 instead of the impeller 6, and the stationary blades 64 are disposed on the inner wall surface of the housing 1. It may be installed between the impellers 62 and 63. Further, in contrast to the configurations of the fifth and sixth embodiments described above, impellers 62 and 63 are installed on the outer wall surface of the impeller 50 instead of the impeller 6, and the stationary blade 64 is disposed on the inner wall surface of the housing 1. May be installed between the impellers 62 and 63.

  In the first to seventh embodiments described above, the passive repulsive magnetic bearing is configured by the permanent magnets 5b and 8a included in the sleeve 5 and the fixed body 8, but as shown in FIG. In addition to the passive repulsive magnetic bearing by the permanent magnets 5b and 8a, a ring-shaped permanent magnet 5c is included in the rear tip portion of the sleeve 5, and the front surface is a permanent magnet inside the fixed body 3. The permanent magnet 3a facing the rear surface of 5c may be included. That is, the magnetic poles on the rear surface of the permanent magnet 5c and the magnetic poles on the front surface of the permanent magnet 3a have the same polarity, so that a passive repulsive magnetic bearing by the magnetic repulsive force of the permanent magnets 5c and 3a can be configured. I do not care. FIG. 13 shows a configuration in which a passive repulsive magnetic bearing using permanent magnets 5c and 3a is added to the configuration of FIG.

<Eighth Embodiment>
An eighth embodiment of the present invention will be described with reference to the drawings. FIG. 14 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. 14, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 14 has a configuration in which a plurality of cone-shaped protrusions 32 are installed on the outer peripheral side of the fixed shaft 4 on the front end surface 3x of the fixed body 3 in the configuration of the artificial heart pump of FIG. That is, as shown in FIG. 15, the protrusions 32 are arranged on the front end surface 3 x of the fixed body 3 so as to be equally spaced in the circumferential direction with the same radius around the central axis X. The protrusion 32 has a conical shape with a vertex formed on the front side, and the vertex contacts the rear end surface 5x of the sleeve 5 when rotating at a low rotational speed such as when starting and stopping.

  Similarly to the first embodiment, the artificial heart pump configured as described above is a hydrodynamic fluid that is a force that moves the sleeve 5 forward when the pressure behind the impeller 6 is higher than when the impeller 6 is operated. Thrust load is generated. Then, by acting so that the magnetic repulsion force by the permanent magnets 5b and 8a is balanced with the hydrothrust load, the contact between the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3, and the sleeve 5 Contact between the front end face 5y and the rear end face 8x of the fixed body 8 can be prevented. At this time, blood flows into the gap formed between the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3. However, since the protrusions 32 are arranged at intervals, the flow of the blood flowing in is obstructed. There is no.

  In addition, since the hydrothrust load is small at the time of starting / stopping, the sleeve 5 moves backward due to the magnetic repulsive force of the permanent magnets 5b, 8a. Therefore, the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3 try to contact each other, and the rear end surface 5x of the sleeve 5 contacts the apex of the protrusion 32. By doing in this way, when the sleeve 5 moves backward and comes into contact with the fixed body 3 at the time of start / stop, the contact is only the apex of the protrusion 32, and the contact area can be reduced. . Therefore, it is possible to suppress the generation of wear during contact and to suppress the degradation of hemolysis performance.

  Although the present embodiment has been described based on the configuration of FIG. 1 of the first embodiment, as shown in FIGS. 3, 4 (a), (b), and FIGS. 5 (a), (b). Similarly, the protrusion 32 may be provided on the front end surface 3x of the fixed body 3 for the various configurations. Similarly, the protrusions 32 may be provided on the front end face 3x of the fixed body 3 in the configurations of the second to seventh embodiments described above.

<Ninth Embodiment>
A ninth embodiment of the present invention will be described with reference to the drawings. FIG. 16 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 16, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 16 differs from the artificial heart pump of FIG. 1 in that the fixed shaft 4 is connected only to the fixed body 8 and the sleeve 5 is sandwiched between the fixed shaft 4 and the fixed body 3. A bottom 55 is provided at the position. A conical projection 56 whose apex is on the rear side is formed at the center position of the rear end surface facing the front end surface 3x of the fixed body 3 at the bottom 55 of the sleeve 5, and the front end surface of the fixed body 3 At the center position of 3x, a groove 33 excavated in a cone shape is formed. A pivot bearing is formed by the protrusion 56 provided on the bottom 55 of the sleeve 5 and the groove 33 provided on the front end surface 3x of the fixed body 3. The apex angle of the groove 33 is set to an angle equal to or greater than the apex angle of the protrusion 56.

  Further, the bottom portion 55 of the sleeve 5 is formed with a plurality of through-holes 57 penetrating in the axial direction on the outer peripheral side of the protruding portion 56. As shown in FIG. 17, the through holes 57 are arranged at equal intervals in the circumferential direction with the same radius around the central axis X. Then, by forming a plurality of through holes 57 in the bottom 55 of the sleeve 5, blood that flows into the gap formed between the rear end surface 5 x of the sleeve 5 and the front end surface 3 x of the fixed body 3 and the inner wall surface of the sleeve 5. It can flow through the gap between the fixed shaft 4 and the outer wall surface, and blood stagnation can be avoided.

  Similarly to the first embodiment, the artificial heart pump configured as described above is a hydrodynamic fluid that is a force that moves the sleeve 5 forward when the pressure behind the impeller 6 is higher than when the impeller 6 is operated. Thrust load is generated. Then, by acting so that the magnetic repulsion force by the permanent magnets 5b and 8a is balanced with the hydrothrust load, the contact between the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3, and the sleeve 5 Contact between the front end face 5y and the rear end face 8x of the fixed body 8 can be prevented.

  In addition, since the hydrothrust load is small at the time of starting / stopping, the sleeve 5 moves backward due to the magnetic repulsive force of the permanent magnets 5b, 8a. Therefore, the rear end surface 5x of the sleeve 5 and the front end surface 3x of the fixed body 3 try to contact each other, and the apex of the protrusion 56 of the bottom portion 55 of the sleeve 5 contacts the groove 33 provided on the front end surface 3x of the fixed body 3. To do. By doing in this way, when the sleeve 5 moves backward and comes into contact with the fixed body 3 at the time of starting and stopping, the contact becomes only the apex of the protrusion 56, and the contact area can be reduced. . Therefore, it is possible to suppress the generation of wear during contact and to suppress the degradation of hemolysis performance.

  In the present embodiment, the description has been made based on the configuration of FIG. 1 of the first embodiment. However, the configuration shown in FIGS. 3, 4A, and 5A is also applicable. Similarly, the fixed shaft 4 may be separated from the fixed body 3, and the groove 33 may be provided on the front end surface 3 x of the fixed body 3, and the sleeve 5 may be provided with a bottom portion 55 having a protrusion 56 and a through hole 57. Absent. Similarly, in the configurations of the second and seventh embodiments described above, the fixed shaft 4 is separated from the fixed body 3, a groove 33 is provided on the front end surface 3 x of the fixed body 3, and the sleeve 5 is protruded. You may make it provide the bottom part 55 provided with the part 56 and the through-hole 57. FIG.

  In the first to ninth embodiments described above, the passive repulsive magnetic bearing is configured by the permanent magnets 5b and 8a included in the sleeve 5 and the fixed body 8, but as shown in FIG. Instead of providing the permanent magnets 5b and 8a, a ring-shaped ring-shaped magnetic body 34 is included on the front end face side inside the fixed body 3, and the front end face of the magnetic body 34 is extremely anisotropic. The permanent permanent magnet 5a may be opposed to the rear end surface. With this configuration, the magnetic body 34 and the polar anisotropic permanent magnet 5a are generated by generating an attractive force in the direction opposite to the thrust repulsion force during rotation. A magnetic bearing with the magnet 5a can be configured. FIG. 18 shows a configuration in which the configuration shown in FIG. 1 is provided with a magnetic bearing including the magnetic body 34 and the polar anisotropic permanent magnet 5a.

<Tenth Embodiment>
A tenth embodiment of the present invention will be described with reference to the drawings. FIG. 19 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. 19, the same parts as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  Unlike the artificial heart pump shown in FIG. 1, the artificial heart pump shown in FIG. 19 includes an impeller 58 in which both end faces in the X-axis direction are conical (conical) convex surfaces instead of the fixed shaft 4 and the sleeve 5. The front end surface 3x of the fixed body 3 is a conical concave surface similar to the rear end surface 58x of the impeller 58, and the rear end surface 8x of the fixed body 8 is a conical concave surface similar to the front end surface 58y of the impeller 58. The A plurality of spiral thrust dynamic pressure generating grooves 100 (see FIG. 2) are formed on each of the front end surface 3x of the fixed body 3 and the rear end surface 8x of the fixed body 8 to function as a dynamic pressure bearing. Further, the impeller 58 is installed so that the impeller 6 protrudes on the outer wall surface thereof, like the fixed body 50 of FIG. 10, and the polar anisotropic permanent magnet 5a is included therein.

  The impeller 58 includes permanent magnets 5b and 5c each having a ring shape and a conical taper shape on the front end face side and the rear end face side. The permanent magnet 5b is formed so that its front end face is substantially parallel to the front end face of the impeller 58, and the permanent magnet 5c is formed so that its rear end face is substantially parallel to the rear end face of the impeller 58. Is done. The fixed body 3 includes a ring-shaped and conical taper-shaped permanent magnet 3a having a front end surface substantially parallel to the rear end surface of the permanent magnet 5c, and the fixed body 8 includes a front of the permanent magnet 5b. A permanent magnet 8a having a ring-like and conical taper shape having a rear end face substantially parallel to the end face is included.

  Therefore, the repulsive magnetic force by the permanent magnets 3a and 5c acts between the fixed body 3 and the impeller 58, and the repulsive magnetic force by the permanent magnets 8a and 5b acts between the fixed body 8 and the impeller 58, Further, the impeller 58 is supported in a non-contact manner in the axial direction and the radial direction by the dynamic pressure by the dynamic pressure bearing. That is, as shown in FIG. 20, the impeller 58 has a repulsive magnetic force F1 by the permanent magnets 3a and 5c and a repulsive magnetic force F2 by the permanent magnets 8a and 5b, respectively, with respect to the rear end surface and the front end surface of the impeller 58. Takes vertically.

  Since each of the repulsive magnetic forces F1 and F2 has an angle with respect to the X-axis direction and the radial direction perpendicular to the X-axis, it can be decomposed into forces F1x and F2x in the X-axis direction and forces F1y and F2y in the radial direction. Therefore, since each of the radial forces F1y and F2y circulates around the rear end surface and the front end surface of the impeller 58, it acts as a journal bearing, and both the X-axis direction forces F1x and F2x are in the opposite directions. Therefore, it acts as a thrust bearing.

  As described above, in the present embodiment, since the permanent magnets 3a, 8a, 5b, and 5c can form journal bearings and thrust bearings, the rotating shaft 4 is required as in the first to fourth embodiments. Not configured. Therefore, since the installation positions of the polar anisotropic permanent magnet 5a and the permanent magnets 5b and 5c can be moved to the inner diameter side, the outer diameter of the impeller 50 in the artificial heart pump of the present embodiment can be set as in the other embodiments. The outer diameter of the sleeve 5 in the artificial heart pump can be made smaller, and the radial shape of the artificial heart pump can be made smaller.

  In the present embodiment, both end faces 58x and 58y in the X-axis direction of the impeller 58 are conical, but as shown in FIG. 21, both end faces 58x and 58y in the X-axis direction of the impeller 58 are spherical. In addition, the spherical shape of each of the front end surface 3x of the fixed body 3 and the rear end surface 8x of the fixed body 8 may be used. At this time, each of the front end face of the permanent magnet 5b, the rear end face of the permanent magnet 5c, the front end face of the permanent magnet 3a, and the rear end face of the permanent magnet 8a may be conical tapered or spherical. I do not care.

  In the present embodiment, as in the seventh embodiment, a plurality of impellers are installed in the impeller 8 and a stationary blade protruding from the housing 1 is installed at a position between the stages. It doesn't matter.

<Eleventh embodiment>
An eleventh embodiment of the present invention will be described below with an example of an artificial heart pump configured as shown in FIG.

  The artificial heart pump of the present embodiment includes a stator coil configured by arranging a plurality of slots, which are part of the core of the magnetic coil, in the circumferential direction of the housing 1 and winding the magnetic coil around each slot. Instead of (slotted stator coil), it is constituted by a slotless stator coil without a slot. Therefore, in the case of a stator coil with a slot as shown in FIG. 22A, the size in the radial direction of the housing 1 is affected by the size of the slot 150, whereas as shown in FIG. By using a slotless stator coil, the influence of the size of the slot 150 can be eliminated. Thereby, the magnitude | size of the radial direction of the housing 1 can be made small, and size reduction of an artificial heart pump can be achieved.

  In the present embodiment, the artificial heart pump having the configuration shown in FIG. 1 has been described as an example. However, the configuration is not limited to the artificial heart pump according to the present configuration, and each configuration in the first to tenth embodiments or a conventional configuration is used. In this case, the configuration of this embodiment may be applied by using the motor stator 1a as a slotless stator coil.

<Twelfth Embodiment>
A twelfth embodiment of the present invention will be described with reference to the drawings. FIG. 23 is a cross-sectional view showing the configuration of the artificial heart pump in the present embodiment. In FIG. 23, the same portions as those in FIG. 1 are denoted by the same reference numerals, and detailed description thereof is omitted.

  The artificial heart pump of FIG. 23 differs from the artificial heart pump of FIG. 1 in that a cylindrical shape in which an induced current flows in the sleeve 5 based on the rotating magnetic field generated by the motor stator 1a, instead of the polar anisotropic permanent magnet 5a. It is the structure provided with the cage rotor 5e. That is, the artificial heart pump of this embodiment does not constitute a synchronous motor by the motor stator 1a and the polar anisotropic permanent magnet 5a unlike the artificial heart pump of the other embodiments, but the motor stator 1a and the cage. An induction motor is constituted by the rotor 5e. Therefore, since the sleeve 5 is rotated by the power of the induction motor, unlike the case of rotating by the power of the synchronous motor as in the other embodiments, it is possible to suppress the step-out that occurs when the load fluctuates.

  In the present embodiment, the artificial heart pump having the configuration of FIG. 1 has been described as an example. However, the configuration is not limited to the artificial heart pump according to the present configuration, and each configuration in the first to eleventh embodiments or a conventional configuration. In this case, the polar anisotropic permanent magnet 5a may be a squirrel-cage rotor 5e to apply the configuration of the present embodiment.

  Further, in the artificial heart pump configured in each of the above-described embodiments, the hardness of the material constituting the rotating member that is rotationally driven, such as the sleeve 5 and the impellers 50, 55, and 58, the fixed bodies 3 and 8, and the fixed shaft The hardness of the material constituting the fixing member fixed to the housing 1 such as 4, 41, 42 may be different. That is, for example, the material constituting the rotating member may be a carbonitrided titanium alloy, and the material constituting the fixing member may be an untreated titanium alloy. Conversely, the material constituting the rotating member may be untreated. The material constituting the fixing member may be carbonitrided titanium alloy. Carbonitriding refers to heating the treated product in a gas atmosphere in which ammonia (NH3) is added to a carburizing gas generated by dripping a modified carburizing gas or liquid such as natural gas, city gas, propane, or butane gas. Carburizing is performed.

  Thus, since the fixing member and the rotating member are made of materials having different hardnesses, seizure at the time of contact can be prevented, and the sliding characteristics can be kept good. In addition, by using titanium alloy as the material used for each part, not only compensates for its biocompatibility, but also produces titanium alloys with different hardness by processing by carbonitriding, so that the temperature atmosphere during processing The thermal deformation of the member to be processed can be suppressed.

These are sectional drawings which show the structure of the artificial heart pump of 1st Embodiment. These are figures which show the structure of the thrust dynamic pressure generation groove | channel in the artificial heart pump of FIG. These are sectional drawings which show another structure of the artificial heart pump of 1st Embodiment. These are sectional drawings which show another structure of the artificial heart pump of 1st Embodiment. These are some sectional drawings of the artificial heart pump for showing another structure of 1st Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 2nd Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 3rd Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 4th Embodiment. These are sectional drawings which show another structure of the artificial heart pump of 4th Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 5th Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 6th Embodiment. These are sectional drawings which show the structure of the artificial heart pump of 7th Embodiment. These are sectional drawings which show the structure of the artificial heart pump which has the passive type repulsive magnetic bearing installed in both two fixed bodies. These are sectional drawings which show the structure of the artificial heart pump of 8th Embodiment. These are figures which show the positional relationship of the projection part in the artificial heart pump of FIG. These are sectional drawings which show the structure of the artificial heart pump of 9th Embodiment. These are figures which show the positional relationship of the through-hole in the artificial heart pump of FIG. These are sectional drawings which show the structure of the artificial heart pump which has a magnetic bearing by a magnetic body. These are sectional drawings which show the structure of the artificial heart pump of 10th Embodiment. These are figures which show the relationship of the repulsive magnetic force by the permanent magnet in the artificial heart pump of FIG. These are sectional drawings which show another structure of the artificial heart pump of 10th Embodiment. FIG. 3 is a schematic view showing a configuration of a stator coil having slots and a slotless stator coil. These are sectional drawings which show another structure of the artificial heart pump of 12th Embodiment. These are sectional drawings which show the structure of the conventional artificial heart pump using a pivot bearing. These are sectional drawings which show the structure of the conventional artificial heart pump using a dynamic pressure bearing. These are sectional drawings which show the structure of the conventional artificial heart pump using a passive type repulsive magnetic bearing.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Housing 2 Diffuser 3 Fixed body 4 Fixed shaft 5 Sleeve 6 Impeller 7 Current plate 8 Fixed body 9 Adjustment ring

Claims (6)

A housing, first and second fixed bodies connected to the housing and fixed in front and rear in the axial direction of the housing, and a first rotating body installed between the first and second fixed bodies, A plurality of impellers projecting from the outer wall surface of the first rotating body, and a motor stator that is included in a position surrounding the first rotating body in the housing and generates a rotating magnetic field, and the rotating magnetic field of the motor stator In the artificial heart pump for flowing blood in the axial direction by rotating the first rotating body by
The first rotating body and the first fixed body act on the opposite side to the thrust load applied from the rear side to the front side with respect to the axial direction of the impeller that acts when the first rotating body rotates. First and second permanent magnets that generate a magnetic repulsive force are provided inside,
An artificial heart pump comprising a journal bearing that holds the first rotating body in a radial direction between the first and second fixed bodies and the first rotating body. Comprising first and second main shafts extending in the axial direction relative to the front and rear of the first rotating body;
The first and second fixed bodies respectively include first and second through holes through which the first and second main shafts are inserted through in the axial direction.
The first and second permanent magnets constitute a thrust bearing that holds the first rotating body in its axial direction,
2. The journal bearing according to claim 1, wherein the first main shaft is inserted into the first through hole and the second main shaft is inserted into the second through hole. Artificial heart pump.   The second rotating body different from the first rotating body provided with an impeller protruding from an outer wall surface thereof is installed at the front end in the axial direction of the first main shaft. Artificial heart pump.   4. The artificial heart pump according to claim 3, further comprising a third permanent magnet that generates a magnetic repulsive force with the second permanent magnet in the first stationary body inside the second rotating body. 5. The first and second fixed bodies include a plurality of stationary blades whose inner edges are connected to an outer wall surface and project toward the inner wall surface of the housing,
The artificial heart according to any one of claims 1 to 4, wherein an outer edge of the stationary blade is connected to the housing, whereby the first and second fixed bodies are fixed to the housing. pump. A plurality of vanes fixed to the inner wall surface of the housing and projecting from the inner wall surface of the housing to the outer wall surface of the rotating body;
The said rotary body WHEREIN: The said impeller is installed in multiple stages in the said axial direction, and the said stationary blade is installed between the said impellers of the stage adjacent to the said axial direction. The artificial heart pump according to crab.

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