JP4759261B2 - Centrifugal blood pump device - Google Patents

Description

  The present invention relates to a centrifugal blood pump device for feeding blood.

Recently, an example of using a centrifugal blood pump for extracorporeal blood circulation in an oxygenator is increasing. Centrifugal pumps use a system that transmits driving torque from an external motor using magnetic coupling by completely eliminating physical communication between the outside and the blood chamber in the pump and preventing invasion of bacteria. Is used.
And as such a centrifugal blood pump, the present applicant has proposed what is shown in Unexamined-Japanese-Patent No. 2004-209240 (patent document 1).
The centrifugal blood pump device disclosed in this publication includes a housing having a blood inflow port and a blood outflow port, and a centrifugal blood pump having an impeller that rotates in the housing and feeds blood by centrifugal force during rotation. And a non-controllable magnetic bearing component (impeller rotational torque generator) for the impeller. Further, the housing has two dynamic pressure grooves facing the upper and lower surfaces of the impeller. Since this dynamic pressure groove is provided, it is attracted to the impeller rotational torque generating part side when the impeller position control part is not operated (in other words, when the electromagnet operation is stopped), but is formed between the dynamic pressure groove and the inner surface of the housing. Due to the hydrodynamic bearing effect, it is slightly separated from the inner surface of the housing and rotates in a non-contact state.
Further, there is a turbo pump disclosed in Japanese Patent Laid-Open No. 4-91396 (Patent Document 2). In FIG. 8 and FIG. 9 of Patent Document 2, a magnetic coupling is formed by a first permanent magnet provided on one surface of an impeller and a second permanent magnet opposed via a housing. The impeller is rotationally driven by rotating the rotor to which the second permanent magnet is attached. Further, the bearing is supported by a dynamic pressure groove provided on one surface of the impeller. The impeller is provided with another permanent magnet on the other surface, and the housing is provided with a magnetic body that provides an attractive force with the permanent magnet. A dynamic pressure groove is also formed on the other surface of the impeller.
Furthermore, there is a clean pump disclosed in Japanese Utility Model Publication No. 6-53790 (Patent Document 3). In this pump, a magnetic coupling is formed by a first permanent magnet provided on one surface of an impeller and a second permanent magnet provided on a rotor opposite to the first permanent magnet, and rotational force is applied to the impeller by rotating the rotor. In addition, a dynamic pressure groove is formed on one side of the impeller, and a control type magnetic bearing is arranged on the other side of the impeller. The number is to stop the magnetic bearing control.

JP 2004-209240 A JP-A-4-91396 Japanese Utility Model Publication No. 6-53790

In any of Patent Documents 1 to 3, a dynamic pressure groove is arranged between the end surface of the impeller and the housing-facing portion to support the impeller in the rotational axis direction, and the radial impeller support includes a permanent magnet in the impeller. This is common in that it uses passive rigidity such as using the attractive force with a permanent magnet or stator arranged outside the housing. In the case of a hydrodynamic bearing, the support rigidity is proportional to the rotation speed of the impeller. Therefore, in order for the impeller to rotate stably without contacting the housing even when a disturbance is applied to the pump, the normal rotation of the pump I want to increase the axial direction rigidity of the impeller by raising several areas, but with this configuration, since the radial direction is supported using the attractive force of the permanent magnet, the support rigidity is low and the impeller cannot be rotated at high speed. .
In order to increase the rigidity in the radial direction, there is a method of increasing the attractive force between the permanent magnet in the impeller and the permanent magnet or the stator arranged outside the housing. By increasing this, the negative impeller impinges on the axial. The rigidity value of the impeller (which means that if the impeller moves in the axial direction increases its suction force), the impeller support performance due to dynamic pressure may be hindered.
In the thing of patent document 2, the impeller is a system which floats in balance with the attraction force between the 1st permanent magnet and the 2nd permanent magnet, and the dynamic pressure of the impeller one side. Therefore, when the impeller is not rotating, the impeller is pressed against the housing by the attractive force between the first permanent magnet and the second permanent magnet. When the impeller starts rotating, the impeller and the housing The frictional resistance between them is large and it is difficult to start the rotation smoothly. In addition, the dynamic pressure is proportional to the rotation speed and the force is small in the region where the impeller rotation speed is low. Therefore, the impeller and the housing may come into contact with each other when the impeller rotates at low speed due to the fluid force acting on the impeller. . In particular, when the pump is used as a blood pump, blood damage such as hemolysis and thrombus may occur at the contacted portion due to friction between the impeller and the housing.
Moreover, the thing of patent document 3 requires an impeller position sensor and an electromagnet, and those controls are also required.
Therefore, an object of the present invention is not a magnetic levitation type centrifugal blood pump, but a centrifugal blood pump device that substantially rotates the impeller in a non-contact state using a so-called dynamic pressure groove. It is possible to reduce the size and prevent blood hemolysis and thrombus generation due to contact between the impeller and the housing due to the swing of the impeller in the housing when the impeller rotates. An object of the present invention is to provide a centrifugal blood pump device that can reduce the damage of the impeller or the housing due to the friction between the impeller and the housing facing the impeller, and can prevent blood hemolysis and thrombus generation.

What achieves the above object is as follows.
(1) A housing having a blood inflow port and a blood outflow port, and a first magnetic body or a first magnetic body and a second magnetic body in the housing, and rotating in the housing, and centrifugal force during rotation A centrifugal pump unit having an impeller for feeding blood by:
An impeller rotational torque generating unit for attracting the first magnetic body of the impeller of the centrifugal pump unit and rotating the impeller;
A centrifugal unit having a third magnetic body that attracts the impeller in a direction opposite to a direction attracted by a magnetic force generation source of the impeller rotational torque generation unit in cooperation with the first magnetic body or the second magnetic body of the impeller. Blood pump device,
In the centrifugal blood pump device, the attraction force by the magnetic force generation source of the impeller rotational torque generation unit and the attraction force by the third magnetic body with respect to the impeller in the centrifugal pump unit are within a movable range of the impeller in the housing. A first dynamic pressure groove provided on the inner surface of the housing on the impeller rotational torque generating portion side or on the surface of the impeller on the impeller rotational torque generating portion side, and the first 3 is provided with a second dynamic pressure groove provided on the inner surface of the housing on the magnetic body side or the surface on the third magnetic body side of the impeller,
And the attraction force by the magnetic force generation source of the impeller rotational torque generation unit with respect to the impeller in the centrifugal pump unit and the attraction force by the first magnetic body or the second magnetic body and the third magnetic body of the impeller The absolute value ka of the negative support rigidity value in the axial direction of the impeller constituted by the above and the absolute value kr of the positive rigidity value in the radial direction are two in the normal rotation speed region where the impeller rotates. The absolute value Kg of the positive stiffness value obtained in the dynamic pressure groove satisfies the relationship kg> ka + kr,
The centrifugal blood pump device is configured such that the impeller is supported to have a higher support rigidity in the axial direction of the impeller than a support rigidity in the radial direction of the impeller .
(2) The centrifugal blood pump device is configured such that the rotational speed ω (rad / s) of the impeller with respect to the radial rigidity value kr (N / m) of the impeller and the mass m (kg) of the impeller is ω < (Kr / m) The centrifugal blood pump device according to (1), which satisfies the relationship of ^0.5 .
(3) The centrifugal blood pump device according to (1) or (2), wherein the dynamic pressure generated by the first dynamic pressure groove and the dynamic pressure generated by the second dynamic pressure groove are different.
(4) The centrifugal blood pump device according to any one of (1) to (3), wherein the first dynamic pressure groove and / or the second dynamic pressure groove is an inward spiral groove.
(5) The centrifugal blood pump device according to any one of (1) to (4), wherein the third magnetic body is a permanent magnet.
(6) The impeller includes the first magnetic body and the second magnetic body, the third magnetic body is a permanent magnet, and the second magnetic body is a third magnet made of a permanent magnet. The surface area of the second magnetic body on the third magnetic body side is different from the surface area of the third magnetic body on the second magnetic body side. The centrifugal blood pump device according to any one of (1) to (5) above.

(7) The centrifugal blood pump device according to any one of (1) to (6), wherein the impeller floats and rotates near a central position of the housing at a predetermined impeller rotational speed. Blood pump device.
( 8 ) The third magnetic body is a permanent magnet, and the centrifugal blood pump device is operated immediately before or at the start of rotation of the impeller to change the magnetic force of the third magnetic body. The centrifugal blood pump device according to any one of (1) to ( 7 ), comprising a magnetic force adjusting coil.
( 9 ) The centrifugal blood pump device according to any one of (1) to ( 8 ), wherein the centrifugal blood pump device includes an electromagnet for biasing the impeller in a predetermined direction.
(10) The centrifugal blood pump device according to claim 9, wherein the electromagnet is operated immediately before the impeller rotation is started or at the time of rotation start-up.
(11) The impeller includes a conductive member, and the centrifugal blood pump device includes an eddy current generating coil capable of generating an eddy current in the conductive member of the impeller when current is supplied. The centrifugal blood pump device according to any one of (1) to ( 9 ), which is provided.
(12) The centrifuge according to any one of (8) to (11), wherein the electromagnet, the magnetic force adjusting coil, or the eddy current generating coil is operated immediately before or when the impeller starts rotating. Blood pump device.
(13) The centrifugal blood pump device according to any one of (8) to (12), wherein a current is passed through the electromagnet or the magnetic force adjusting coil when the impeller is in a certain rotation speed range. The centrifugal blood pump device described in 1.
(14) The centrifugal blood pump device according to any one of (1) to (13), wherein the centrifugal blood pump device includes a vibration unit for applying vibration to the impeller at rest.
(15) The centrifugal blood pump device according to (14), wherein the vibration unit is operated immediately before or after the impeller rotation is started.

(16) The centrifugal blood pump device according to any one of (1) to (15), wherein the centrifugal blood pump device includes a position sensor for detecting a position of the impeller.
(17) The centrifugal blood pump device operates the electromagnet or the magnetic force adjusting coil when the sensor detects that the impeller is not located within a predetermined range. The centrifugal blood pump device described in 1.
(18) The centrifugal blood pump device measures a relationship between the rotation speed of the impeller and the floating position of the impeller under the electromagnet or the magnetic force adjustment coil non-operating condition, and the impeller is at a predetermined rotation speed. The centrifugal blood pump device according to (16), wherein the electromagnet or the magnetic force adjusting coil is operated when the sensor detects that the position has deviated from the previously measured floating position.
(19) The centrifugal blood pump device includes a control unit that controls the operation of the electromagnet or the magnetic force adjusting coil, and the control unit turns on the current supplied to the electromagnet or the magnetic force adjusting coil. The centrifugal blood pump device according to any one of the above (8) to (18), which is OFF-controlled.
(20) The said impeller rotational torque generation part is provided with the rotor provided with the magnet for attracting | sucking the 1st magnetic body of the said impeller, and the motor which rotates this rotor (1) thru | or (19). The centrifugal blood pump device according to any one of the above.
(21) The impeller rotational torque generator includes a plurality of stator coils arranged on the circumference for attracting the first magnetic body of the impeller and rotating the impeller. Thru | or the centrifugal blood pump apparatus in any one of (19).

A centrifugal blood pump device according to the present invention includes a housing having a blood inflow port and a blood outflow port, and a first magnetic body or a first magnetic body and a second magnetic body therein, and is rotated within the housing. And a centrifugal pump unit having an impeller for feeding blood by centrifugal force during rotation, and an impeller rotational torque generating unit for sucking the first magnetic body of the impeller of the centrifugal pump unit and rotating the impeller And a third magnetic body that attracts the impeller in a direction opposite to the attraction direction by the magnetic force generation source of the impeller rotational torque generation unit in cooperation with the first magnetic body or the second magnetic body of the impeller. A centrifugal blood pump device having a magnetic force generation source of the impeller rotational torque generating unit with respect to the impeller in the centrifugal pump unit The attraction force by the third magnetic body is balanced near the center of the movable range of the impeller in the housing, and the inner surface of the housing on the impeller rotational torque generating portion side or the impeller A first dynamic pressure groove provided on the surface of the impeller rotational torque generating portion side and a second inner surface of the housing on the third magnetic body side or a surface of the impeller on the third magnetic body side. It has a dynamic pressure groove.
For this reason, it is a centrifugal blood pump device that rotates the impeller in a non-contact state substantially in the housing by utilizing a so-called dynamic pressure groove, which enables downsizing and smooth rotation startup, The distance between the housings can be secured and the occurrence of hemolysis can be reduced.

Furthermore, the attraction force by the magnetic force generation source of the impeller rotational torque generation unit with respect to the impeller in the centrifugal pump unit and the attraction force by the first magnetic body or the second magnetic body and the third magnetic body of the impeller For the absolute value ka of the negative support stiffness value in the axial direction of the impeller constituted by and the absolute value kr of the positive stiffness value in the radial direction, two motions in the normal rotational speed region where the impeller rotates The absolute value Kg of the positive stiffness value obtained in the pressure groove satisfies the relationship of the formula 1, and kg> ka + kr (the formula 1)
Further, with respect to the radial stiffness value of the impeller as kr (N / m) and the mass of the impeller as m (kg), the rotational speed ω (rad / s) of the impeller satisfies the relationship of the following two formulas. Ω <(kr / m) ^0.5 (2 formulas)
When a disturbance force acts on the impeller, the impeller can be prevented from moving in the axial direction from the radial direction, and mechanical contact between the impeller and the housing at the formation portion of the dynamic pressure groove can be avoided.

Also, if the dynamic pressure generated by the first dynamic pressure groove and the dynamic pressure generated by the second dynamic pressure groove are different, a disturbance such as a fluid force always acts on the impeller in a certain direction during pumping. In this case, the impeller can be lifted and rotated at the center position of the housing by increasing the performance of the dynamic pressure groove in the direction of the disturbance relative to the impeller more than the performance of the other dynamic pressure groove. The mechanical contact between them can be reduced, and a stable impeller flying performance can be obtained.
The impeller includes the first magnetic body and the second magnetic body, the third magnetic body is a permanent magnet, and the second magnetic body is a third magnetic body made of a permanent magnet. The surface area of the second magnetic body on the third magnetic body side is different from the surface area of the third magnetic body on the second magnetic body side. If so, the negative axial rigidity generated between the second magnetic body and the third magnetic body can be kept small.
In addition, if the centrifugal blood pump device includes an electromagnet for urging the impeller in a predetermined direction, the impeller can be started more smoothly by being activated when the impeller starts rotating. By operating during the rotation of the impeller, stable rotation of the impeller can be continued.

In addition, if the centrifugal blood pump device is provided with a magnetic force adjusting coil for changing the magnetic force of the permanent magnet, the impeller can be started more smoothly by being activated when the impeller starts rotating. Thus, by operating the impeller during rotation, it is possible to continue the stable rotation of the impeller.
The impeller includes a conductive material disposed at a position corresponding to the coil, and the centrifugal blood pump device generates an eddy current in the conductive material of the impeller when current is supplied. If an eddy current generating coil is provided, the impeller can be started more smoothly by being activated when the impeller starts rotating.
Further, if the centrifugal blood pump device is provided with a vibration means for applying vibration to the impeller at rest, the impeller can be started more smoothly by being activated when the impeller starts rotating. .

FIG. 1 is a front view of an example of the centrifugal blood pump device of the present invention. FIG. 2 is a plan view of the centrifugal blood pump apparatus shown in FIG. 3 is a cross-sectional view of the centrifugal blood pump device of FIG. 2 taken along line AA. 4 is a cross-sectional view of the centrifugal blood pump device of FIG. 3 taken along line BB. 5 is a cross-sectional view showing a state where the impeller is removed from the cross-sectional view taken along the line BB of the centrifugal blood pump device of FIG. 6 is a cross-sectional view showing a state in which the impeller is removed from the cross-sectional view taken along the line CC of the centrifugal blood pump device of FIG.
The centrifugal blood pump device 1 of the present invention includes a housing 20 having a blood inflow port 22 and a blood outflow port 23, and a first magnetic body 25 or a first magnetic body 25 and a second magnetic body 28 therein. A centrifugal pump unit 2 having an impeller 21 that rotates in the housing 20 and feeds blood by centrifugal force at the time of rotation, and the first magnetic body 25 of the impeller 21 of the centrifugal pump unit 2 and the impeller 21 The impeller rotational torque generating unit 3 for rotating the impeller 21 and the first magnetic body 25 or the second magnetic body 28 of the impeller 21 are attracted in a direction opposite to the attracting direction by the magnetic force generating source of the impeller rotational torque generating unit 3. 3 magnetic bodies 41. In the centrifugal blood pump device 1, the impeller 21 in the housing 20 is configured such that the attraction force generated by the magnetic force generation source of the impeller rotational torque generating unit 3 and the attraction force generated by the third magnetic body 41 with respect to the impeller 21 in the centrifugal pump unit 2. A first dynamic pressure groove 38 provided on the inner surface of the housing on the side of the impeller rotational torque generating part or on the surface of the impeller 21 on the side of the impeller rotational torque generating part, A second dynamic pressure groove 71 is provided on the inner surface of the housing on the third magnetic body side or on the surface on the third magnetic body side of the impeller.
When the impeller 21 does not rotate, the attraction force by the magnetic force generation source of the impeller rotation torque generation unit 3 and the attraction force by the third magnetic body 41 (specifically, a permanent magnet) act on the impeller 21. For this reason, the contact pressure between the impeller 21 and the housing when the impeller 21 is not rotated is smaller than that in which the suction force is applied to the impeller 21 only in one direction. For this reason, the frictional resistance between the impeller 21 and the housing generated when the impeller 21 starts to rotate is reduced, and the impeller 21 can be smoothly rotated and started.

Embodiments shown in the drawings will be described.
In the centrifugal blood pump device 1 of this embodiment, the impeller rotational torque generator 3 includes a rotor 31 including a magnet 33 for attracting the first magnetic body 25 of the impeller 21 and a motor 34 that rotates the rotor 31. I have. Further, in the centrifugal pump unit, the resultant force of the attraction force by the magnetic force generation source of the impeller rotational torque generation unit 3 with respect to the impeller 21 and the attraction force by the third magnetic body 41 (specifically, a permanent magnet) is Since it is balanced near the center of the movable range of the impeller 21, a first dynamic pressure groove 38 provided on the inner surface of the housing on the impeller rotational torque generating portion side or on the impeller rotational torque generating portion side of the impeller 21, Each of the second magnetic pressure grooves 71 provided on the inner surface of the housing on the third magnetic body side or the surface on the third magnetic body side of the impeller 21 is provided.
As shown in FIGS. 1 to 5, the centrifugal blood pump apparatus 1 of this embodiment includes a housing 20 having a blood inflow port 22 and a blood outflow port 23, a rotation within the housing 20, and a centrifugal force during rotation. Centrifugal blood pump unit 2 having an impeller 21 for feeding blood, an impeller rotational torque generating unit 3 for the impeller 21, and an auxiliary suction unit 4 for auxiliary suction of the impeller 21 in the opposite direction to the impeller rotational torque generating unit 3 Is provided. The auxiliary suction 4 includes a third magnetic body 41 (specifically, a permanent magnet).
As shown in FIG. 3, the impeller 21 rotates without contacting the inner surface of the housing due to the pressure generated by the dynamic pressure groove 38 during rotation. In particular, in this pump device 1, since the impeller is attracted in the direction opposite to the rotor by the third magnetic body (permanent magnet), it is in a state further separated from the distance between the impeller and the housing obtained by a normal dynamic pressure groove. Rotate.

The housing 20 includes a blood inflow port 22 and a blood outflow port 23, and is formed of a nonmagnetic material. A blood chamber 24 communicating with the blood inflow port 22 and the blood outflow port 23 is formed in the housing 20. An impeller 21 is accommodated in the housing 20. The blood inflow port 22 is provided so as to protrude substantially vertically from the vicinity of the center of the upper surface of the housing 20. As shown in FIGS. 2 and 4, the blood outflow port 23 is provided so as to protrude in a tangential direction from the side surface of the housing 20 formed in a substantially cylindrical shape.
As shown in FIG. 4, a disc-like impeller 21 having a through-hole at the center is housed in a blood chamber 24 formed in the housing 20. As shown in FIG. 3, the impeller 21 includes a lower shroud 27 formed on a donut plate-shaped member that forms a lower surface, an upper shroud 28 formed on a donut plate-shaped member that is open at the center that forms an upper surface, It has a plurality of (for example, seven) vanes 18 formed therebetween. A plurality (seven) blood passages 26 partitioned by the adjacent vanes 18 are formed between the lower shroud and the upper shroud. As shown in FIG. 4, the blood passage 26 communicates with the central opening of the impeller 21, starts from the central opening of the impeller 21, and extends so that the width gradually increases to the outer peripheral edge. In other words, the vane 18 is formed between the adjacent blood passages 26. In this embodiment, each blood passage 26 and each vane 18 are provided at equal angular intervals and in substantially the same shape.

As shown in FIG. 3, a plurality (for example, 14 to 24) of first magnetic bodies 25 (permanent magnets, driven magnets) are embedded in the impeller 21. In this embodiment, the first magnetic body 25 is embedded in the lower shroud 27. The embedded magnetic body 25 (permanent magnet) attracts the impeller 21 to the side opposite to the blood inflow port 22 by a permanent magnet 33 provided on the rotor 31 of the impeller rotational torque generating unit 3 described later, and is coupled to the rotor. And the rotational torque is provided to transmit from the impeller rotational torque generating section.
Further, by embedding a certain number of magnetic bodies 25 as in this embodiment, sufficient magnetic coupling with the rotor 31 described later can be ensured. The shape of the magnetic body 25 (permanent magnet) is preferably circular. Alternatively, a ring-shaped magnet may be polarized into multiple poles (for example, 24 poles), in other words, a plurality of small magnets may be arranged in a ring shape so that the magnetic poles are alternately or the same.
Further, the impeller 21 includes a second magnetic body 28 provided in the upper shroud itself or in the upper shroud. In this embodiment, the entire upper shroud is formed of the magnetic body 28. The second magnetic body 28 attracts (in other words, biases) the impeller 21 to the side opposite to the rotor 31, in other words, the blood inflow port 22 side, by the third magnetic body 41 (specifically, a permanent magnet). It is provided for. As the magnetic body 28, magnetic stainless steel or the like is used.

As shown in FIG. 3, the impeller rotational torque generating unit 3 includes a rotor 31 housed in the housing 20 and a motor 34 for rotating the rotor 31. The rotor 31 includes a plurality of permanent magnets 33 provided on the surface on the blood pump unit 2 side. The center of the rotor 31 is fixed to the rotating shaft of the motor 34. The permanent magnets 33 are provided in plural and at equal angles so as to correspond to the arrangement form (number and arrangement position) of the permanent magnets 25 of the impeller 21.
As shown in FIGS. 2 and 3, the impeller auxiliary suction unit 4 includes at least one third magnetic body 41 (specifically, a permanent magnet) fixed to attract the magnetic body 28 of the impeller. ing. Specifically, it has a plurality of third magnetic bodies 41 (specifically, permanent magnets) housed in the housing 20. The plurality of third magnetic bodies 41 (specifically, permanent magnets) are provided at equal angular intervals. In the present embodiment, three third magnetic bodies 41 (specifically, permanent magnets) are provided. As the magnetic body 41, one or a plurality of ring-shaped members may be provided concentrically, and two or more magnetic bodies 41 may be arranged at substantially equal angles as illustrated. In this case, the number of magnetic materials is preferably 2 to 8, and more preferably 3 to 6.

Further, in the centrifugal blood pump device 1 of this embodiment, the housing 20 includes an inner surface of the housing that houses the impeller 21 and forms the blood chamber 24 as shown in FIGS. A dynamic pressure groove 38 is provided on the inner surface 20a. The impeller 21 rotates in a non-contact state due to a dynamic pressure bearing effect formed between the dynamic pressure groove 38 and the impeller 21 generated by rotating at a predetermined number of rotations or more.
As shown in FIG. 5, the dynamic pressure groove 38 is formed in a size corresponding to the bottom surface (rotor side surface) of the impeller 21. In the pump device 1 of this embodiment, one end is provided on the peripheral edge (circumference) of the circular portion slightly spaced from the center of the housing inner surface 20a, and in a spiral shape (in other words, curved) to the vicinity of the outer edge of the housing inner surface 20a. , Extending so that the width gradually widens. Further, a plurality of dynamic pressure grooves 38 are provided, and each of the dynamic pressure grooves 38 has substantially the same shape and is arranged at substantially the same interval. The dynamic pressure groove 38 is a recess, and the depth is preferably about 0.005 to 0.4 mm. About 6 to 36 dynamic pressure grooves are preferably provided. In this embodiment, twelve dynamic pressure grooves are arranged at an equal angle with respect to the central axis of the impeller. Dynamic pressure groove 38 in the pump apparatus of this embodiment is a so-called inward spiral groove shape, by the impeller is rotated in the counterclockwise direction, the pumping of fluid by the action of the dynamic pressure grooves, the outer diameter of the groove Since the pressure is increased from the inner diameter toward the inner diameter, a repulsive force is obtained between the impeller 21 and the housing 20 forming the dynamic pressure groove, which becomes the dynamic pressure.
The dynamic pressure groove may be provided not on the housing side but on the rotor side surface of the impeller 21. Also in this case, it is preferable to have the same configuration as the above-described dynamic pressure groove.

Since it has such a dynamic pressure groove, it is attracted to the impeller rotational torque generating portion 3 side, but is formed between the dynamic pressure groove 38 of the housing and the bottom surface of the impeller 21 (or between the dynamic pressure groove of the impeller and the inner surface of the housing). Due to the effect of the hydrodynamic bearing, it is slightly separated from the inner surface of the housing and rotates in a non-contact state to secure a blood flow path between the lower surface of the impeller and the inner surface of the housing. Prevent the occurrence of thrombus. Furthermore, in the normal state, the dynamic pressure groove exhibits a stirring action between the lower surface of the impeller and the inner surface of the housing, thereby preventing partial blood retention between the two.
Furthermore, the dynamic pressure groove 38 is preferably rounded so that the corner portion has an R of at least 0.05 mm. By doing so, the generation of hemolysis can be reduced.
Then, the centrifugal blood pump device 1 has a housing inner surface on the third magnetic body 41 (specifically, permanent magnet) side or a third magnetic body 41 (specifically, permanent magnet) side of the impeller 21. A second dynamic pressure groove 71 is provided on the surface.

Specifically, as shown in FIGS. 3 to 6, the housing 20 includes a housing inner surface that houses the impeller 21 and forms a blood chamber 24, and is provided on a housing inner surface 20 a on the rotor 31 side. And a second dynamic pressure groove 71 provided on the housing inner surface 20b on the third magnetic body 41 (specifically, permanent magnet) side.
For this reason, the impeller 21 rotates in a non-contact state due to a dynamic pressure bearing effect formed between the first dynamic pressure groove 38 and the impeller 21 that is generated by rotating at a rotation speed greater than or equal to a predetermined number. When a dynamic impact is received and when the dynamic pressure by the first dynamic pressure groove 38 becomes excessive, the impeller is prevented from sticking to the housing inner surface 20b side. The dynamic pressure generated by the first dynamic pressure groove and the dynamic pressure generated by the second dynamic pressure groove may be different.
It is desirable for the impeller 21 to rotate with the gap between the upper shroud 28 of the impeller 21 and the housing inner surface 20b being substantially the same as the gap between the lower shroud 27 of the impeller 21 and the housing inner surface 20a. When disturbance such as fluid force acting on the impeller 21 is large and one gap becomes narrow, the dynamic pressure by one dynamic pressure groove arranged on the narrowing side is made larger than the dynamic pressure by the other dynamic pressure groove. In order to make both gaps substantially the same, it is desirable to make the groove shapes different from each other. When the disturbance such as the fluid force acting on the impeller 21 is small, it is desirable that both dynamic pressure groove shapes are the same.

The dynamic pressure groove 71 is formed in a size corresponding to the upper surface (side surface of the permanent magnet) of the impeller 21, similarly to the dynamic pressure groove 38 described above. 3 and FIG. 6, the housing inner surface 20b has one end on the periphery (circumference) of a circular portion slightly spaced from the center of the housing inner surface 20b, and has a spiral shape (in other words, curved). The width gradually extends to the vicinity of the outer edge of the. In particular, in this embodiment, the dynamic pressure groove has a so-called herringbone shape bent halfway. In addition, a plurality of dynamic pressure grooves 71 are provided, and each of the dynamic pressure grooves 71 has substantially the same shape and is disposed at substantially the same interval. The dynamic pressure groove 71 is a recess, and the depth is preferably about 0.005 to 0.4 mm. About 6 to 36 dynamic pressure grooves are preferably provided. In this embodiment, twelve dynamic pressure grooves are arranged at an equal angle with respect to the central axis of the impeller.
The second dynamic pressure groove may be provided not on the housing side but on the surface of the impeller 21 on the permanent magnet side. Also in this case, it is preferable to have the same configuration as the second dynamic pressure groove described above. Furthermore, the dynamic pressure groove 71 is preferably rounded so that the corner portion has an R of at least 0.05 mm. By doing so, the generation of hemolysis can be reduced.

In the centrifugal blood pump device 1 of the present invention, the attractive force (the downward acting force in FIG. 3) between the first magnetic body 25 and the magnet 33 (impeller rotational torque generating unit 3), and the second magnetic The resultant force of the attractive force (upward acting force in FIG. 3 ) between the body 28 and the third magnetic body 41 is set to be zero at the substantially central position of the housing 20 that is the movable range of the impeller 21. Yes. For this reason, in any movable range of the impeller 21, the acting force due to the suction force to the impeller 21 is very small. As a result, since the frictional resistance at the time of relative sliding between the impeller 21 and the housing 20 generated when the impeller 21 starts rotating can be reduced, there is almost no damage (surface irregularities) on the surfaces of both members at the time of relative sliding, and the speed is further reduced. Even when the dynamic pressure at the time of rotation is small, the impeller 21 easily floats from the housing 20 without contact. Further, hemolysis / thrombus may occur due to relative sliding between the impeller 21 and the housing 20, and thrombus due to slight surface damage (unevenness) generated during the relative sliding may occur. Thus, a method of reducing the contact pressure between the impeller 21 and the housing 20 by applying suction forces from both sides of the impeller, balancing the suction forces, and reducing the resultant force to the limit is effective.

Moreover, although the impeller auxiliary | assistant attracting | sucking part 4 is comprised by the magnetic body 28 provided in the impeller, and the 3rd magnetic body 41 (specifically permanent magnet) provided in the housing, it is restricted to this. Instead, the impeller may be provided with a permanent magnet, and the housing may be provided with a magnetic body that exerts an attractive force with the permanent magnet.
In order to prevent impeller rigidity from being reduced due to the attractive force of the magnetic body 28 and the permanent magnet 41 in the impeller auxiliary suction portion 4, it is preferable that the opposing magnetic body and the permanent magnet have different sizes of the facing surfaces. 3, the third magnetic body 41 (specifically, a permanent magnet) is smaller than the magnetic body 28, and the sizes of the opposing surfaces are different. Accordingly, the amount of change in the suction force that changes depending on the distance between the two, that is, the negative rigidity is suppressed to a small value, thereby preventing the impeller support rigidity from being lowered.

FIG. 7 includes the structure shown in FIGS. 1 to 4 and acts on the impeller 21 between the first magnetic body 25 and the permanent magnet 33, and the second magnetic body 28 and the third magnetism. Force acting on the impeller 21 at a predetermined rotational speed when the magnitude of the resultant force with the suction force between the bodies 41 is adjusted to be zero at a place other than the center position within the movable range of the impeller 21 in the housing 20 Show the relationship.
That is, the attractive force with respect to the impeller 21 due to the attractive force between the first magnetic body 25 and the permanent magnet 33 is made larger than the attractive force between the second magnetic body 28 and the third magnetic body 41, and the resultant force becomes zero. It is assumed that the impeller is lifted at the lower part of the impeller movable range. The two dynamic pressure groove shapes arranged on both sides of the impeller are the same. In FIG. 7, the horizontal axis represents the impeller position (the left side in the figure is the motor side), and the vertical axis represents each acting force on the impeller 21 (refer to FIG. 3, the direction of the acting force on the impeller 21 acts on the motor side. In other words, the acting force is negative), that is, the attraction force, dynamic pressure, and resultant force of the first magnetic body 25 acting on the impeller 21 and the permanent magnet 33, and the net force acting on the impeller. "showed that. As can be seen from the figure, the floating position of the impeller is a position where the net force acting on the impeller is zero, and the floating position of the impeller 21 is greatly deviated from the center position of the movable range of the impeller 21. As a result, the distance between the impeller 21 during rotation of the impeller and the motor-side housing is reduced, and the impeller 21 contacts the housing 20 even if a small disturbance force acts on the impeller 21.

On the other hand, the magnitude of the resultant force of the attractive force between the first magnetic body 25 and the permanent magnet 33 acting on the impeller 21 and the attractive force between the second magnetic body 28 and the third magnetic body 41 is determined by the impeller 21. FIG. 8 shows a force relationship acting on the impeller 21 at a predetermined rotational speed in the pump device of the present invention adjusted to be zero at a substantially central position within the movable range of the housing 20.
That is, the attraction performance for the impeller 21 by the attraction force between the first magnetic body 25 and the permanent magnet 33 and the attraction performance for the impeller 21 by the attraction force between the second magnetic body 28 and the third magnetic body 41 are substantially the same. Furthermore, the shape of the dynamic pressure grooves arranged on both sides of the impeller is the same. In FIG. 8, the horizontal axis indicates the impeller position (the left side in the figure is the motor side), and the vertical axis indicates each acting force on the impeller 21 (refer to FIG. 3 when the direction of the acting force on the impeller 21 acts on the motor side. The acting force is negative), that is, the attractive force between the first permanent magnet and the second permanent magnet acting on the impeller 21, the attractive force between the first ferromagnetic material and the second ferromagnetic material, The dynamic pressure and the resultant force “net force acting on the impeller” are shown. In the figure, the dynamic pressure 1 indicates the acting force by the dynamic pressure groove 38 disposed on the motor side with respect to the impeller 21, and the dynamic pressure 2 indicates the acting force by the dynamic pressure groove 71 disposed on the counter motor side with respect to the impeller.

In the case of FIG. 8 where the resultant force of the two suction forces is zero at the central position compared to that of FIG. 7 where the impeller 21 is not zero at the central position within the movable range within the housing 20, the impeller Since the support rigidity with respect to the floating position of 21 is increased and the net force acting on the impeller 21 is zero at the center of the housing, the impeller 21 is at the center position when no disturbance force acts on the impeller 21. You can see that it surfaced.
Thus, the impeller 21 rotates the impeller 21 by the action of the attractive force of the first magnetic body 25 and the permanent magnet 33, the attractive force of the second magnetic body 28 and the third magnetic body 41, and the dynamic pressure groove. The floating position is determined by the balance with the dynamic pressure generated at times. The attraction force between the first magnetic body 25 and the permanent magnet 33 acting on the impeller and the attraction force between the third magnetic body 41 and the second magnetic body 28 are made substantially the same, and the dynamic pressure arranged on both sides of the impeller By making the shape of the groove 38 and the dynamic pressure groove 71 substantially the same, the impeller 21 can float substantially at the center of the housing 20 when the impeller 21 rotates. As shown in FIGS. 3 and 4, since the impeller 21 has a configuration in which blades are formed between two disks, the two surfaces facing the housing 20 have substantially the same surface shape and almost the same area. It is possible to provide dynamic pressure grooves having substantially the same dynamic pressure performance on both sides of the impeller 21.
Since the impeller 21 is levitated at the center position of the housing 20, the impeller 21 can keep the distance farthest from the housing 20. As a result, a disturbance force is applied to the impeller 21 when the impeller 21 is lifted, and the risk of contact with the housing 20 is reduced even if the floating position of the impeller 21 is changed. A thrombus due to the contact between the impeller 21 and the housing 20 is reduced. Occurrence and the possibility of hemolysis are also reduced.

7 and 8, the two dynamic pressure grooves have the same shape. However, as shown in FIGS. 5 and 6, the shape of each dynamic pressure groove may be changed to change each dynamic pressure performance. . For example, when a disturbance is always applied in one direction to the impeller 21 such as a fluid force during pumping, the performance of the dynamic pressure groove 38 in the direction of the disturbance is improved from the performance of the other dynamic pressure groove 71. As a result, the impeller 21 can be floated and rotated at the center position of the housing 20. As a result, the probability of contact between the impeller 21 and the housing 20 can be kept low, and stable impeller flying performance can be obtained.
Further, in the centrifugal blood pump device 1 of this embodiment, the attraction force generated by the magnetic force generation source of the impeller rotational torque generating portion with respect to the impeller in the centrifugal pump portion, the first magnetic body or the second magnetic body of the impeller, and the third The normal rotation speed region in which the impeller rotates with respect to the absolute value ka of the negative support stiffness value in the axial direction of the impeller constituted by the attractive force with the magnetic body and the absolute value kr of the positive stiffness value in the radial direction It is preferable that the absolute value Kg of the positive stiffness value obtained by the two dynamic pressure grooves satisfies the relationship kg> ka + kr (1 formula) .

Specifically, when the absolute value ka of the negative stiffness value in the axial direction is 20000 N / m and the positive stiffness value in the radial direction is 10000 N / m, the two dynamic pressures in the rotational speed region where the impeller 21 normally rotates. The absolute value Kg of the positive stiffness value obtained by the grooves 38 and 71 is set to a value exceeding 30000 N / m.
Since the axial support rigidity of the impeller 21 is a value obtained by subtracting the negative rigidity due to the magnetic coupling or the like from the rigidity caused by the dynamic pressure generated in the dynamic pressure groove 38, the relationship of (Expression 1) described above is obtained. The support of the impeller 21 can increase the support rigidity in the axial direction more than the support rigidity in the radial direction. By setting in this way, when a disturbance force acts on the impeller 21, the impeller 21 can suppress movement in the axial direction from the radial direction, and the impeller 21 and the housing 20 in the formation portion of the dynamic pressure groove 38 can be suppressed. It is possible to avoid mechanical contact.
In particular, as shown in FIGS. 3 and 5, the dynamic pressure groove 38 is partially grooved in a plane, so that the mechanical contact between the housing 20 and the impeller 21 is performed at this portion during the rotation of the impeller 21. If there is, scratches (unevenness on the surface) are generated on one or both surfaces of the impeller 21 or the housing 20, and when blood passes through this portion, there is a possibility that thrombus may be generated. In order to prevent mechanical contact at the dynamic pressure groove and suppress thrombus generation, the effect of increasing the axial rigidity is high compared to the radial rigidity.

Although FIG. 5 shows a dynamic pressure groove having an inward spiral groove shape, this dynamic pressure groove shape may be any shape.
As shown in FIG. 6, the second dynamic pressure groove 71 in this embodiment has a so-called herringbone shape. The impeller 21 is disposed so as to face the dynamic pressure groove, and the impeller 21 rotates clockwise with respect to the groove, so that the pumping of the fluid by the action of the dynamic pressure groove causes the outer diameter side and the inner diameter of the impeller 21 to be pumped. It acts to create a flow of pumping fluid from the side towards its center. As a result, a repulsive force is obtained between the impeller 21 and the housing 20 forming the dynamic pressure groove, which becomes a dynamic pressure. There are various dynamic pressure groove shapes, but in order to use as a blood pump, an inward spiral groove shape in which the flow of the pumping fluid is smooth is preferable.
If the impeller 21 is unbalanced, the impeller 21 swings during rotation. This swing is when the natural frequency determined by the mass of the impeller 21 and the support rigidity value of the impeller 21 matches the rotational speed of the impeller 21. To the maximum.

In the pump device of this embodiment, since the support rigidity of the impeller 21 is smaller in the radial direction than in the axial direction, the maximum rotation speed of the impeller 21 is set to be equal to or lower than the natural frequency in the radial direction where the support rigidity is weak. Is desirable. Therefore, in order to prevent mechanical contact between the impeller 21 and the housing 20, the attractive force between the first permanent magnet and the permanent magnet 33 disposed opposite to the first permanent magnet via the housing 20, the second magnetic body 28, The radial stiffness value of the impeller 21 configured by the attraction force with the third magnetic body 41 facing and disposed via the housing 20 is kr (N / m), the impeller mass is m (kg), and the impeller When the rotational speed is ω (rad / s), it is desirable that the relationship of ω <(kr / m) ^0.5 is satisfied.
Specifically, when the impeller mass is 0.03 kg and the radial stiffness value is 2000 N / m, the maximum speed of the impeller is set to 258 rad / s (2465 rpm) or less, and conversely the maximum speed of the impeller. Is set to 366 rad / s (3500 rpm), the radial rigidity is set to 4018 N / m or more.
Furthermore, it is desirable to set the maximum rotational speed of the impeller 21 to 80% or less of this ω. Specifically, when the impeller mass is 0.03 kg and the radial rigidity value is 2000 N / m, the maximum rotational speed is set to 206.4 rad / s (1971 rpm) or less, and conversely When the maximum rotational speed is desired to be 366 rad / s (3500 rpm), the radial rigidity value is set to 6279 N / m or more. By setting the maximum rotation speed of the impeller 21 in this way, contact between the impeller 21 and the housing 20 during the rotation of the impeller 21 can be suppressed.

In FIGS. 1 to 6, the second magnetic body 28 is made of a soft magnetic material and the third magnetic body 41 is made of a permanent magnet. Basically, the second magnetic body 28 and the third magnetic body 28 are made of permanent magnets. The body 41 may be configured to generate an attractive force with each other. The ferromagnetic body includes a soft magnetic material, a hard magnetic material, and a permanent magnet, and may be configured by a combination thereof.
In addition, this pump has an attractive force between the first magnetic body 25 and the permanent magnet 33 opposed thereto, and an attractive force between the second magnetic body 28 and the third magnetic body 41 disposed opposite thereto. The impeller 21 and the housing 20 are not in contact with each other when the rigidity due to the dynamic pressure becomes larger than the negative rigidity value in the axial direction of the impeller 21 configured by the above. Therefore, it is desirable to make the negative rigidity value as small as possible. Therefore, in order to suppress the negative rigidity value to a small value, it is preferable that the opposing second magnetic body 28 and the third magnetic body 41 have different sizes of the facing surfaces. 1 to 6, the size of the third magnetic body 41 is made smaller than that of the second magnetic body 28, and the sizes of the opposing surfaces are made different, so that the attractive force that varies depending on the distance between the two is obtained. By suppressing the amount of change, that is, negative rigidity, the impeller support rigidity is prevented from being lowered.

Further, the centrifugal blood pump device of the present invention changes the magnetic force of the third magnetic body 41 (specifically, a permanent magnet) like the pump device 30 of the embodiment shown in FIGS. 9 and 10. The magnetic force adjusting coil 42 may be provided. The difference between the pump device 30 of this embodiment and the pump device 1 of the above-described embodiment is only the presence or absence of the magnetic force adjusting coil 42.
In this embodiment, a magnetic force adjusting coil 42 is wound around the side surface of the third magnetic body 41 (specifically, a permanent magnet). In this pump device 30, a plurality of permanent magnet units configured as described above are arranged at a plurality of equal angles. Specifically, six permanent magnet units are arranged at an equal angle. Then, by supplying current to the coil, the attractive force of the permanent magnet can be increased or decreased. The permanent magnet is preferably provided with a yoke 43. In this unit, when a current is passed through the coil, the yoke functions as an electromagnet, and the magnetic force of the entire unit is increased. Instead of the magnetic force adjusting coil, an electromagnet for biasing the impeller toward the third magnetic body (permanent magnet) may be provided.
In addition, the permanent magnet unit includes an annular third magnetic body (specifically, a permanent magnet), a yoke having a tip inserted into the opening of the permanent magnet, and a coil wound around the outside of the yoke. It may be provided. In this type unit, by passing a current through the coil, the yoke functions as an electromagnet, and the magnetic force of the entire unit increases.

The forms of the permanent magnet and the coil are not limited to those of the pump device 30 shown in FIGS. 9 and 10, and may be those shown in FIGS. 11 and 12, for example. In this pump device 40, as shown in FIGS. 11 to 13, a ring-shaped third magnetic body 41 (specifically, a permanent magnet) is used. An inner coil 47 wound around the outer surface of the core 48 is accommodated, and an outer coil 46 is wound around the outer periphery of the ring-shaped permanent magnet 41. The inner coil 47 and the outer coil 46 are continuous by a wire 49 and have the same winding direction, and current flows in the same direction in both.
Also in the pump devices 30 and 40 of these embodiments, when the impeller is not rotated, the attraction force between the rotor permanent magnet 33 and the impeller permanent magnet 25 acting on the impeller 21, the impeller magnetic body 28, and the third The direction of the resultant force with the attractive force between the magnetic bodies 41 (specifically, permanent magnets) is balanced in the center of the movable range within the housing of the impeller. For this reason, it is unclear at which position in the housing the impeller 21 is located when the impeller is not rotating.

Then, at the time of starting the rotation or just before the rotation, the magnetic flux density exerted on the magnetic body 28 of the impeller 21 from the third magnetic body 41 (specifically, permanent magnet) to the coil 42 (or the coils 46 and 47) is increased. By passing an electric current, the attractive force between the magnetic body 28 of the impeller 21 and the third magnetic body 41 (specifically, a permanent magnet) can be increased, and the impeller 21 is disposed on the third magnetic body 41 side . Contact the inner surface of the housing. Thereafter, when the impeller starts to rotate or immediately before it, a current is passed through the coil 42 in a direction that weakens the magnetic flux density exerted on the magnetic body 28 of the impeller 21 from the third magnetic body 41, and the magnetic body 28 and the third magnetic body 41. When the impeller 21 is brought into a mechanical non-contact state with the housing 20 by slightly moving the impeller 21 to the motor side by weakening the suction force between them, the impeller 21 is rotated to be provided on the housing 20. Due to the dynamic pressure groove, a dynamic pressure acts on the impeller 21, and the impeller 21 rotates in a non-contact state with the housing.
Conversely, before the impeller rotates, a current is passed through the coil 42 in the direction of decreasing the magnetic flux density exerted on the magnetic body 28 of the impeller 21 from the magnetic body 41 to weaken the attractive force between the magnetic body 28 and the third magnetic body 41. Thus, the impeller 21 contacts the inner surface of the housing 20 on the motor side. Thereafter, at the time of starting the rotation or just before the rotation, a current is supplied to the coil 42 in the direction of increasing the magnetic flux density exerted on the magnetic body 28 of the impeller 21 from the magnetic body 41, thereby increasing the attractive force toward the magnetic body 41 with respect to the impeller 21. Thus, a method may be adopted in which the impeller 21 is rotated in a state in which the impeller 21 is mechanically in non-contact with the housing by slightly moving the impeller 21 toward the third magnetic body 41.
By forming a non-contact state with the housing 20 at the start of rotation of the impeller 21 in this way, relative slip between the impeller 21 and the housing 20 can be avoided, and therefore the impeller 21 and the housing 20 from the relative slip are caused by this relative slip. There is no generation of abrasion powder and it is effective for applications that require cleanliness. Furthermore, even when this pump is used as a blood pump, it is possible to avoid damage to blood such as hemolysis and thrombus generated due to relative sliding between the impeller and the housing.

FIG. 14 shows a change in the distance between the impeller 21 and the housing at the time of the rotation start of the impeller and the increase in the rotation speed, and at the rated rotation of the pump device 30 of the embodiment shown and described in FIGS. 9 and 10. . As shown in FIG. 14, when the current is passed through the coil 42 for a moment, the impeller is momentarily moved to the third magnetic body 41 (specifically, the permanent magnet) side (coil side). The distance increases. Immediately thereafter, the current is turned off, and the impeller 21 is rotationally driven before the impeller 21 contacts the housing 20, whereby the dynamic pressure is increased and the distance between the impeller and the housing is further increased. This dynamic pressure is approximately proportional to the rotation speed of the impeller, and keeps floating at a constant distance between the impeller and the housing during rated rotation.
Further, the current flowing through the coil 42 at the time of activation may be maintained at a constant current for a certain period. FIG. 15 shows a case where a constant current is supplied to the coil 42 for a predetermined period before the impeller rotation is started, the impeller is rotated within the period in which this current is supplied, and then the current to the coil 42 is stopped. The change of the distance between the impeller 21 and the housing 20 is shown. In this case, the distance between the impeller and the housing increases as a current starts to flow through the coil 42, and the action of dynamic pressure is added immediately after the impeller rotates, so that the speed at which the distance between the impeller and the housing increases becomes faster. When the current is stopped, the speed at which the distance between the impeller and the housing increases is reduced.

Further, in order not to change the flying position according to the rotational speed of the impeller, the direction and magnitude of the current of the coil 42 is changed so as to assist the dynamic pressure by the rotational speed, and the acting force on the impeller 21 is changed. Good. Considering that the dynamic pressure increases substantially in proportion to the rotation speed of the impeller, the acting force should be changed in an inversely proportional relationship with the rotation speed. In general, the value of the current flowing through the coil 42 is rotated. The number may be given in an inversely proportional relationship. In this case, a rotation speed detector for directly measuring the rotation speed may be provided, but it is preferable not to provide a new member in order to reduce the size of the apparatus. For example, the rotational speed may be calculated from the motor current value, or the coil current may be controlled using the motor current value.
In the case of the centrifugal pump devices 30 and 40 described above, the blood pump device includes a control mechanism 6 as shown in FIG.
The control mechanism 6 of the centrifugal blood pump device 30 of the embodiment shown in FIG. 16 is for the power amplifier 52 for the motor 34 of the impeller rotational torque generating unit 3, the motor control circuit 53, the motor current monitoring unit 55, and the coil 42. Power amplifier 54, coil control circuit 56, and control unit 51. The motor current monitoring function may be provided in the control unit 51. The control mechanism 6 controls the impeller rotational torque generation unit (specifically, the motor) and the coil 42. And the control mechanism 6 is provided with the function to control the electric current sent through the coil 42 at the time of pump starting as mentioned above. Furthermore, the control mechanism 6 has a function of changing the attraction force of the impeller by the coil 42 in accordance with the rotation speed of the impeller rotation torque generation unit (in other words, the rotation speed generated by the impeller rotation torque generation unit). Is preferred. Further, the control mechanism 6 changes the attraction force of the impeller 21 by the coil 42 according to the rotation speed of the impeller rotation torque generation unit (in other words, the rotation speed generated by the impeller rotation torque generation unit). It is preferable to have a function of keeping the distance between the housings substantially constant, and this distance is preferably 50 to 150 μm.

Further, the blood pump device of the present invention may include an impeller position sensor 45. In the pump device 50 of the embodiment shown in FIGS. 17 and 18, a plurality (preferably 3 to 6, specifically three) of the sensors 45 are arranged at an equal angle. Similarly, the third magnetic bodies 41 are also arranged at a plurality of (preferably 3 to 6, specifically three) equiangular angles. The third magnetic body 41 includes a magnetic force adjusting coil 42 and a yoke 43 as in the above-described embodiment. Further, the plurality of magnetic bodies and the plurality of sensors are arranged alternately and at an equal angle. Two sensors may be provided at opposite positions, or one ring-shaped sensor 45 as in the pump device 60 of the embodiment shown in FIG. When using such a ring-shaped sensor, it is preferable to arrange so as to surround the proximal end portion of the inflow port.
By providing such a sensor, it is possible to measure the movement of the impeller in real time, and to finely manage the pump system. The sensor may be provided not on the permanent magnet side but on the impeller rotational torque generating unit side. And the electric current sent through a coil may be adjusted using the output of the sensor which monitors the behavior of this impeller. For example, if the direction of the current flowing through the coil is changed, the acting force on the impeller 21 can be reduced. That is, if an electric current is applied by the coil so as to increase the magnetic flux from the permanent magnet, the impeller is strongly attracted to the coil side, and if an electric current is applied to weaken the magnetic flux from the permanent magnet, the impeller The attractive force to the coil side becomes weak. Therefore, the position of the impeller can be finely controlled by changing the magnitude of the coil current and the direction of the current based on the output of the sensor.
Thus, when providing a sensor, a blood pump apparatus is provided with the control mechanism 7 as shown in FIG.

The control mechanism 7 of the centrifugal blood pump device 50 of the embodiment shown in FIG. 20 is for the power amplifier 52 for the motor 34 of the impeller rotational torque generating unit 3, the motor control circuit 53, the motor current monitoring unit 55, and the coil 42. Power amplifier 54, coil control circuit 56, control unit 51, and sensor unit 57. The motor current monitoring function may be provided in the control unit 51. In addition, when the impeller is in a certain rotation speed range, it is preferable that an electric current is passed through the electromagnet or the magnetic force adjusting coil. Moreover, it is preferable to operate an electromagnet or a magnetic force adjusting coil when a dynamic disturbance is applied to the impeller during the impeller rotation.
For the purpose of power saving, a current may be passed through the coil only in a certain rotation speed range. FIG. 21 shows a block diagram in this case. The sensor 45 generates a sensor output 102 through the sensor amplifier 101. The sensor output 102 drives the coil 42 via the controller 103 and the power amplifier 104. Here, the output of the rotation speed detector 106 of the impeller provided separately is input to the setting device 107 that sets the operating rotation range of the coil 42. With this setting device 107, the relay coil 108 is turned ON in the determined rotational speed range, the power amplifier 104 and the first coil 42 are connected by the relay contact 109, and the first coil 42 operates. In the example shown in FIG. 21, the operation of the coil is controlled by the relay on / off. However, in order to make the coil inactive, the output of the controller 103 is forcibly set to zero and the power amplifier 104 is not operated. Any method such as a method may be used. Here, the rotation speed of the impeller is detected by a separately provided impeller rotation speed detector 106, but this is a signal from a motor controller (a signal from a motor current monitoring section) that drives the impeller (not shown) to rotate. May be used.

FIG. 22 shows the impeller floating state when the coil is operated in the low speed range of the impeller. During low-speed rotation, the coil is operated by the sensor output. Therefore, at low speed, there is almost no change in the flying position depending on the number of rotations. Furthermore, it is preferable to operate the coil when the impeller deviates from a preset flying range. FIG. 23 shows a block diagram of a system relating to a configuration in which the coil is operated when the impeller receives disturbance when the impeller rotates at a constant rotation and the flying position is out of the set range. The sensor 45 generates a sensor output 102 through the sensor amplifier 101. The sensor output 102 is configured to drive the coil 42 via the controller 103 and the power amplifier 104. Here, a sensor arithmetic circuit 110 is provided between the sensor amplifier 101 and the controller 103.
There are various algorithms for the sensor arithmetic circuit 110. For example, as shown in FIG. 24, the output is proportional to the input of the circuit, and the output is set to zero in the levitation setting range. As shown in FIG. 25, there is a method of outputting a signal proportional to the amount of deviation from the levitation setting range. FIG. 26 shows an example of a change in the impeller flying position in a state where the impeller is subjected to a disturbance when the method shown in FIG. 24 is adopted. It can be seen that the impeller has stably floated within the set floating range set as shown in the figure. In this method, the coil operates only when the impeller receives a disturbance and the flying position changes greatly. Therefore, the coil does not consume power during normal pump operation without a disturbance, and is suitable for power saving of the pump system. ing.
Also, the relationship between the rotational speed of the impeller and the impeller floating position under the non-operating condition of the electromagnet or the magnetic force adjusting coil is measured, and the sensor detects that the impeller has deviated from the floating position measured in advance at each rotational speed. In such a case, it is preferable to operate an electromagnet or a magnetic force adjusting coil.

FIG. 27 shows a block diagram in this case. The sensor 45 generates a sensor output 102 through the sensor amplifier 101. The sensor output 102 drives the coil 42 via the controller 103 and the power amplifier 104. Here, the output of the impeller rotational speed detector 106 provided separately is input to the floating position setting circuit 112, and the impeller floating reference position signal 114 at each rotational speed obtained is added to or subtracted from the sensor output 102 by the adder 113. As a result, the coil is operated so that the impeller is lifted to the position set by the impeller lift reference position signal 114. The flying position setting circuit 112 is set in advance to obtain the relationship between the rotational speed of the impeller and the flying position as shown in FIG. 28 and to output the impeller flying reference position signal 114 so as to maintain this relationship. For example, the current flows through the coil only when a disturbance is applied to the impeller and the actual impeller lift is deviated from the pre-measured flying position. Therefore, when no disturbance is applied to the impeller, no current flows through the coil, thus saving power. Can be planned.
Furthermore, it is also possible to control only the dynamic disturbance acting on the impeller during the impeller rotation. FIG. 29 shows a block diagram of this configuration. In this method, an output 116 obtained by passing the sensor output 102 through the low-pass filter 115 is used as a reference signal, and a current is passed through the coil based on a signal obtained as a difference between the reference signal and the sensor output 102. Since the output 116 of the low-pass filter 115 of the sensor output is regarded as a position where it can stably float in balance with static disturbance acting on the impeller, the acting force on the impeller due to the change in the first coil current is the movement acting on the impeller. It can act only on mechanical disturbances.

  Normally, in a magnetic bearing that operates an electromagnet according to the sensor output, the controller performs so-called PID control including all proportional elements, differential elements, and integral elements, which makes the construction of the controller complicated and increases the cost. End up. However, in the present invention, the first coil is used for auxiliary support of the impeller supported by the dynamic pressure. Therefore, the controller 103 that determines the current flowing through the first coil is ON / OFF control. Alternatively, either proportional control, differential control, or integral control may be used. As control of the impeller, when controlling to float at a certain position, it may be configured only by integral control, or may be configured only by differential control in applications where dynamic disturbance is applied to the impeller. . Further, in the case where a somewhat static displacement of the impeller flying position is allowed and fluctuations in the impeller flying position are to be suppressed to some extent even when a dynamic disturbance is applied to the impeller, it may be configured only by proportional control.

In all the embodiments described above, as in the centrifugal pump device 70 of the embodiment shown in FIGS. 30 to 33, the impeller 21 is provided with the conductive member 62, and the impeller 21 of the housing 20 is not rotated. A first eddy current generating coil that is disposed at a position corresponding to the conductive member 62 on the side where the impeller contacts and can generate eddy current in the conductive member 62 of the impeller 21 by supplying current. 61, and a second vortex arranged at a position corresponding to the peripheral edge of the magnetic body 28 constituting the upper shroud and capable of generating an eddy current in the magnetic body 28 of the impeller 21 by supplying a current. It may be provided with a current generating coil 63. In this case, the coil 42 described above may not be provided.
FIG. 30 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. 31 is a cross-sectional view taken along line GG of the centrifugal blood pump apparatus of FIG. 30, and FIG. 32 is a cross-sectional view taken along line HH of the centrifugal blood pump apparatus of FIG. 33 is a bottom view of the centrifugal blood pump device of FIG.
In the pump device 70 of this embodiment, as the conductive member 62, a ring-shaped member is used as shown in FIG. 31, which is a cross-sectional view taken along the line GG of FIG. The conductive member 62 is disposed near the outer periphery of the impeller. The first eddy current generating coil 61 uses a ring-shaped coil body formed in a shape corresponding to the conductive member 62 as shown in FIG. 33 which is a bottom view of the pump device of this embodiment. It has been. Then, by causing a steep current to flow through the coil 61 immediately before or after the impeller starts rotating, an eddy current is generated in the conductive member 62 disposed on the opposed portion of the impeller 21. Due to the repulsive force due to the interaction between the flowing current and the eddy current flowing in the conductive member 62, the impeller 21 is pushed toward the permanent magnet and is separated from the housing. This utilizes the so-called Lenz's law.

In the pump device 70 of this embodiment, the magnetic body 28 that is also a conductive member is a ring-shaped member. Further, the conductive member (magnetic body) 28 constitutes the upper surface including the upper outer peripheral portion of the impeller. As shown in FIG. 30, the second eddy current generating coil 63 uses a ring-shaped coil body formed in a shape corresponding to the outer edge portion of the conductive member 28. Then, by causing a steep current to flow through the coil 63 immediately before or after the impeller starts rotating, an eddy current is generated in the conductive member 28 disposed on the opposite portion of the impeller 21. Due to the repulsive force due to the interaction between the flowing current and the eddy current flowing in the conductive member 28, the impeller 21 is pushed to the motor side and separated from the housing. This utilizes the so-called Lenz's law.
In this embodiment, it is necessary to apply a steep current to the coils 61 and 63. FIG. 34 shows the relationship between the waveform of the current flowing through the eddy current generating coil and the acting force on the impeller. As can be seen from the figure, a repulsive force acts on the impeller by applying a steep current. Therefore, an appropriate acting force can be exerted on the impeller by adjusting the current application pattern.

When such an eddy current generating coil is provided, the blood pump apparatus includes a control mechanism 8 as shown in FIG.
As shown in FIG. 35, the control mechanism 8 of the centrifugal blood pump device 70 of this embodiment includes a power amplifier 52 for the motor 34 of the impeller rotational torque generating unit 3, a motor control circuit 53, a motor current monitoring unit 55, A power amplifier 58, a coil control circuit 59, and a control unit 51 for two eddy current generating coils 61 and 63 are provided. The motor current monitoring function may be provided in the control unit 51.
Further, in all the embodiments described above, as in the centrifugal pump device 80 of the embodiment shown in FIG. 36, the first vibration means (third magnetic body side vibration means for vibrating the housing surface facing the impeller 21 is used. ) 82 and second vibration means (motor-side vibration means) 81 may be provided. As the vibration means 81 and 82, any of those using a piezoelectric element, those using an electromagnetic force, and those using a high-frequency vibration element may be used. The impeller 21 is separated from the housing by the vibration when the vibration means 81 and 82 are operated at the time of the rotation start of the impeller or immediately before the start. Further, as the vibration means 81 and 82, a plurality of vibration means arranged at an equal angle, or a ring-shaped one is preferable.
When such a vibration means is provided, the blood pump device includes a control mechanism 9 as shown in FIG. The control mechanism 9 of the centrifugal blood pump device 80 of this embodiment includes a power amplifier 52 for the motor 34 of the impeller rotational torque generating unit 3, a motor control circuit 53, a motor current monitoring unit 55, and a first vibration unit 81. An oscillation circuit 91 for the second oscillation means 82, and a control unit 51. The motor current monitoring function may be provided in the control unit 51.

Further, in the pump device of the above-described embodiment, the impeller rotational torque generating unit includes a rotor and a motor, but is not limited to this. For example, as illustrated in FIGS. 38 to 41, A stator coil may be used.
FIG. 38 is a front view of another embodiment of the centrifugal blood pump device of the present invention. FIG. 39 is a longitudinal sectional view of the centrifugal blood pump device of the embodiment shown in FIG. 40 is a cross-sectional view taken along line II of the centrifugal blood pump device of FIG. 41 is a bottom view of the centrifugal blood pump device of FIG. The plan view of the centrifugal blood pump device of the embodiment shown in FIG. 38 is the same as FIG.
The difference between the pump device 90 of this embodiment and the pump device 1 described above is only the mechanism of the impeller rotational torque generator 3. In this pump device 90, an impeller rotational torque generating unit including a plurality of stator coils 91 arranged on the circumference for attracting the first magnetic body 25 of the impeller 21 of the centrifugal pump unit 2 and rotating the impeller 21. 3.
The substantial difference between the pump device 90 of this embodiment and the pump device 1 of the above-described embodiment is only the mechanism of the impeller rotational torque generator 3. The impeller rotational torque generator 3 in the pump device 90 of this embodiment is of a type that directly drives the impeller without providing a so-called rotor.

Further, as in this embodiment, a certain number of magnetic bodies 25 are embedded in the impeller, so that sufficient magnetic coupling with the stator coil 91 can be ensured. The shape of the magnetic body 25 (permanent magnet) is preferably substantially trapezoidal. The magnetic body 25 may be either a ring shape or a plate shape. Moreover, it is preferable that the number and arrangement | positioning form of the magnetic body 25 respond | correspond to the number and arrangement | positioning form of a stator coil. The plurality of magnetic bodies 25 are arranged on the circumference so that the magnetic poles are alternately different and at substantially the same angle with respect to the central axis of the impeller.
The impeller rotational torque generating unit 3 includes a plurality of stator coils 91 housed in the housing 20 as shown in FIGS. 39 and 41. A plurality of stator coils 91 are arranged on the circumference so as to be substantially equiangular with respect to the central axis of the circumference. Specifically, six stator coils are used. As the stator coil, a multi-layer stator coil is used. By switching the direction of the current flowing through each stator coil 91, a rotating magnetic field is generated, and the impeller is attracted and rotated by this rotating magnetic field.
The pump device of the type using such a stator coil is the same except for the pump device 1 and the impeller rotational drive system of the above-described embodiment.

FIG. 1 is a front view of an embodiment of a centrifugal blood pump apparatus according to the present invention. FIG. 2 is a plan view of the centrifugal blood pump apparatus shown in FIG. 3 is a cross-sectional view of the centrifugal blood pump device of FIG. 2 taken along line AA. 4 is a cross-sectional view of the centrifugal blood pump device of FIG. 3 taken along line BB. 5 is a cross-sectional view showing a state where the impeller is removed from the cross-sectional view taken along the line BB of the centrifugal blood pump device of FIG. 6 is a cross-sectional view showing a state in which the impeller is removed from the cross-sectional view taken along the line CC of the centrifugal blood pump device of FIG. FIG. 7 is a diagram illustrating the relationship between the impeller floating position and each acting force when the dynamic pressure groove is provided only on one side with respect to the impeller. FIG. 8 is a diagram illustrating the relationship between the impeller floating position and each acting force when dynamic pressure grooves are provided on both sides of the impeller. FIG. 9 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. 10 is a cross-sectional view taken along line DD of the centrifugal blood pump device of FIG. FIG. 11 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. 12 is a cross-sectional view of the centrifugal blood pump device of FIG. 11 taken along the line EE. FIG. 13 is a cross-sectional view of a magnetic force adjusting coil used in the centrifugal blood pump apparatus of FIG. FIG. 14 is an explanatory diagram for explaining the relationship between an example of a method of applying a coil current to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention and the impeller floating state. FIG. 15 is an explanatory diagram for explaining the relationship between another example of the method of applying a coil current to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention and the impeller floating state. FIG. 16 is a block diagram of an embodiment including a control mechanism of the centrifugal blood pump apparatus of the present invention. FIG. 17 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. 18 is a cross-sectional view of the centrifugal blood pump device of FIG. 17 taken along line FF. FIG. 19 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. FIG. 20 is a block diagram of another embodiment including the control mechanism of the centrifugal blood pump apparatus of the present invention. FIG. 21 is a block diagram illustrating an example of a method for controlling the coil current supplied to the magnetic force adjustment coil of the centrifugal blood pump device of the present invention. FIG. 22 is an explanatory diagram for explaining a relationship between another example of a method of applying a coil current to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention, the impeller floating state, and the rotational speed. FIG. 23 is a block diagram illustrating another example of a method for controlling the coil current supplied to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention. It is a figure which shows an example of the algorithm of the sensor arithmetic circuit in the block diagram in FIG. It is a figure which shows the other example of the algorithm of the sensor arithmetic circuit in the block diagram in FIG. FIG. 26 is an explanatory diagram for explaining the relationship between another example of the method of applying a coil current to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention and the impeller floating state. FIG. 27 is a block diagram illustrating another example of a method for controlling the coil current supplied to the magnetic force adjustment coil of the centrifugal blood pump device of the present invention. FIG. 28 is an explanatory diagram for explaining the relationship between the rotational speed of the impeller and the floating position in the centrifugal blood pump device of the present invention. FIG. 29 is a block diagram illustrating another example of a method for controlling the coil current supplied to the magnetic force adjusting coil of the centrifugal blood pump device of the present invention. FIG. 30 is a plan view of another embodiment of the centrifugal blood pump device of the present invention. 31 is a cross-sectional view taken along line GG of the centrifugal blood pump device of FIG. 32 is a cross-sectional view of the centrifugal blood pump device of FIG. 31 taken along the line HH. 33 is a bottom view of the centrifugal blood pump device of FIG. FIG. 34 is an explanatory diagram for explaining the relationship between an example of a method of applying a coil current to the eddy current generating coil of the centrifugal blood pump device of the present invention and the acting force on the impeller. FIG. 35 is a block diagram of another embodiment including the control mechanism of the centrifugal blood pump apparatus of the present invention. FIG. 36 is a longitudinal sectional view of another embodiment of the centrifugal blood pump device of the present invention. FIG. 37 is a block diagram of another embodiment including the control mechanism of the centrifugal blood pump apparatus of the present invention. FIG. 38 is a front view of another embodiment of the centrifugal blood pump device of the present invention. FIG. 39 is a longitudinal sectional view of the centrifugal blood pump device of the embodiment shown in FIG. 40 is a cross-sectional view taken along line II of the centrifugal blood pump device of FIG. 41 is a bottom view of the centrifugal blood pump device of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Centrifugal blood pump apparatus 3 Impeller rotational torque generation part 20 Housing 21 Impeller 41 3rd magnetic body 38 1st dynamic pressure groove 71 2nd dynamic pressure groove

Claims (21)

A housing having a blood inflow port and a blood outflow port, and a first magnetic body or a first magnetic body and a second magnetic body are provided therein, and the blood rotates by centrifugal force during rotation in the housing. A centrifugal pump unit having an impeller for feeding, and
An impeller rotational torque generating unit for attracting the first magnetic body of the impeller of the centrifugal pump unit and rotating the impeller;
A centrifugal unit having a third magnetic body that attracts the impeller in a direction opposite to a direction attracted by a magnetic force generation source of the impeller rotational torque generation unit in cooperation with the first magnetic body or the second magnetic body of the impeller. Blood pump device,
In the centrifugal blood pump device, the attraction force by the magnetic force generation source of the impeller rotational torque generation unit and the attraction force by the third magnetic body with respect to the impeller in the centrifugal pump unit are within a movable range of the impeller in the housing. A first dynamic pressure groove provided on the inner surface of the housing on the impeller rotational torque generating portion side or on the surface of the impeller on the impeller rotational torque generating portion side, and the first 3 is provided with a second dynamic pressure groove provided on the inner surface of the housing on the magnetic body side or the surface on the third magnetic body side of the impeller,
And the attraction force by the magnetic force generation source of the impeller rotational torque generation unit with respect to the impeller in the centrifugal pump unit and the attraction force by the first magnetic body or the second magnetic body and the third magnetic body of the impeller The absolute value ka of the negative support rigidity value in the axial direction of the impeller constituted by the above and the absolute value kr of the positive rigidity value in the radial direction are two in the normal rotation speed region where the impeller rotates. The absolute value Kg of the positive stiffness value obtained in the dynamic pressure groove satisfies the relationship kg> ka + kr,
The centrifugal blood pump device according to claim 1, wherein the impeller is supported such that the support rigidity in the axial direction of the impeller is higher than the support rigidity in the radial direction of the impeller . The centrifugal blood pump device is configured such that the rotational speed ω (rad / s) of the impeller with respect to the radial rigidity value kr (N / m) of the impeller and the mass m (kg) of the impeller is ω <(kr / m) The centrifugal blood pump device according to claim 1, which satisfies a relationship of ^0.5 . The centrifugal blood pump device according to claim 1 or 2, wherein the dynamic pressure generated by the first dynamic pressure groove and the dynamic pressure generated by the second dynamic pressure groove are different. The centrifugal blood pump device according to any one of claims 1 to 3, wherein the first dynamic pressure groove and / or the second dynamic pressure groove is an inward spiral groove. The centrifugal blood pump device according to any one of claims 1 to 4, wherein the third magnetic body is a permanent magnet. The impeller includes the first magnetic body and the second magnetic body, the third magnetic body is a permanent magnet, and the second magnetic body is a third magnetic body made of a permanent magnet. 2. The surface area of the second magnetic body on the third magnetic body side and the surface area of the third magnetic body on the second magnetic body side are different from each other. Or a centrifugal blood pump device according to any one of 5 to 5; The centrifugal blood pump device according to any one of claims 1 to 6, wherein the centrifugal blood pump device is such that the impeller floats and rotates in the vicinity of the center position of the housing at a predetermined impeller rotational speed. The third magnetic body is a permanent magnet, and the centrifugal blood pump device is operated immediately before or when the impeller starts to rotate , and magnetic force adjustment for changing the magnetic force of the third magnetic body is performed. The centrifugal blood pump device according to any one of claims 1 to 7, further comprising a coil for operation. The centrifugal blood pump device according to any one of claims 1 to 8 , wherein the centrifugal blood pump device includes an electromagnet for biasing the impeller in a predetermined direction. The centrifugal blood pump device according to claim 9, wherein the electromagnet is operated immediately before the impeller is started to rotate or at the time of starting the rotation. The impeller includes a conductive member, and the centrifugal blood pump device includes an eddy current generating coil capable of generating an eddy current in the conductive member of the impeller when current is supplied. The centrifugal blood pump device according to any one of claims 1 to 9 . The centrifugal blood pump device according to claim 11, wherein the eddy current generating coil is operated immediately before the impeller rotation is started or when the impeller is started. The centrifugal blood pump according to any one of claims 8 to 12, wherein the centrifugal blood pump device causes a current to flow through the electromagnet or the magnetic force adjusting coil when the impeller is in a certain rotation speed range. Pump device. The centrifugal blood pump device according to any one of claims 1 to 13, wherein the centrifugal blood pump device includes vibration means for applying vibration to the impeller at rest. The centrifugal blood pump device according to claim 14, wherein the vibration means is operated immediately before the impeller rotation is started or at the time of rotation start-up. The centrifugal blood pump device according to any one of claims 1 to 15, wherein the centrifugal blood pump device includes a position sensor for detecting a position of the impeller. The centrifugal blood pump device according to claim 16, wherein the centrifugal magnet pump operates the electromagnet or the magnetic force adjusting coil when the sensor detects that the impeller is not located within a predetermined range. Blood pump device. The centrifugal blood pump device measures the relationship between the rotation speed of the impeller and the floating position of the impeller under the electromagnet or the magnetic force adjustment coil non-operating condition, and the impeller measures in advance at a predetermined rotation speed. The centrifugal blood pump device according to claim 16, wherein the electromagnet or the magnetic force adjusting coil is operated when the sensor detects a deviation from the floating position. The centrifugal blood pump device includes a control unit that controls the operation of the electromagnet or the magnetic force adjusting coil, and the control unit controls ON / OFF of the current supplied to the electromagnet or the magnetic force adjusting coil. The centrifugal blood pump device according to any one of claims 8 to 18, wherein the device is a centrifugal blood pump device. The said impeller rotational torque generation part is provided with the rotor provided with the magnet for attracting | sucking the 1st magnetic body of the said impeller, and the motor which rotates this rotor. Centrifugal blood pump device. 20. The impeller rotational torque generator includes a plurality of stator coils arranged on a circumference for attracting the first magnetic body of the impeller and rotating the impeller. A centrifugal blood pump device according to claim 1.

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