CN115337534A - Magnetic suspension supercharging device for blood pump - Google Patents
Magnetic suspension supercharging device for blood pump Download PDFInfo
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- CN115337534A CN115337534A CN202211213987.6A CN202211213987A CN115337534A CN 115337534 A CN115337534 A CN 115337534A CN 202211213987 A CN202211213987 A CN 202211213987A CN 115337534 A CN115337534 A CN 115337534A
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- permanent magnet
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- volute
- blood pump
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- 239000008280 blood Substances 0.000 title claims abstract description 82
- 210000004369 blood Anatomy 0.000 title claims abstract description 82
- 239000000725 suspension Substances 0.000 title claims abstract description 51
- 239000012530 fluid Substances 0.000 claims abstract description 29
- 239000007788 liquid Substances 0.000 claims description 32
- 239000000919 ceramic Substances 0.000 claims description 27
- 229910052751 metal Inorganic materials 0.000 claims description 24
- 239000002184 metal Substances 0.000 claims description 24
- 238000005339 levitation Methods 0.000 claims description 4
- 230000002093 peripheral effect Effects 0.000 claims description 3
- 230000007704 transition Effects 0.000 claims description 3
- 238000010030 laminating Methods 0.000 claims description 2
- 230000000694 effects Effects 0.000 abstract description 35
- 238000009434 installation Methods 0.000 description 14
- 230000017531 blood circulation Effects 0.000 description 10
- 239000002473 artificial blood Substances 0.000 description 9
- 238000010586 diagram Methods 0.000 description 8
- 229910001069 Ti alloy Inorganic materials 0.000 description 4
- 230000005484 gravity Effects 0.000 description 4
- 230000009471 action Effects 0.000 description 2
- 230000003044 adaptive effect Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 230000020169 heat generation Effects 0.000 description 2
- 238000010438 heat treatment Methods 0.000 description 2
- 230000003068 static effect Effects 0.000 description 2
- 206010018910 Haemolysis Diseases 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- 238000005299 abrasion Methods 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000005265 energy consumption Methods 0.000 description 1
- 230000008588 hemolysis Effects 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 239000011664 nicotinic acid Substances 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 230000010349 pulsation Effects 0.000 description 1
- 230000004083 survival effect Effects 0.000 description 1
- 210000000115 thoracic cavity Anatomy 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/465—Details relating to driving for devices for mechanical circulatory actuation
- A61M60/489—Details relating to driving for devices for mechanical circulatory actuation the force acting on the actuation means being magnetic
- A61M60/495—Electromagnetic force
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/465—Details relating to driving for devices for mechanical circulatory actuation
- A61M60/489—Details relating to driving for devices for mechanical circulatory actuation the force acting on the actuation means being magnetic
- A61M60/492—Details relating to driving for devices for mechanical circulatory actuation the force acting on the actuation means being magnetic generated by permanent magnets
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- Health & Medical Sciences (AREA)
- Cardiology (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Mechanical Engineering (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Physics & Mathematics (AREA)
- Electromagnetism (AREA)
- Structures Of Non-Positive Displacement Pumps (AREA)
- External Artificial Organs (AREA)
Abstract
The invention discloses a magnetic suspension supercharging device for a blood pump, which comprises a volute and a rotor, wherein a fluid chamber is arranged in the volute, the rotor is positioned in the fluid chamber, the rotor structure comprises an impeller, the impeller comprises an impeller body and an impeller cover, the rotor structure further comprises a first permanent magnet assembly and a second permanent magnet assembly, the first permanent magnet assembly comprises a plurality of first permanent magnets, the first permanent magnets are sequentially arranged in a first groove in an axial fit mode, the second permanent magnet assembly comprises a plurality of second permanent magnets, the second permanent magnets are uniformly distributed along the circumferential direction of the impeller body, the impeller cover is arranged on one side, provided with the first groove and the second groove, of the impeller body, and the first permanent magnet assembly and the second permanent magnet assembly are respectively packaged in the first groove and the second groove by the impeller cover. The magnetic suspension supercharging device of the scheme can be matched with the permanent magnet assembly in the middle shaft and the coils in the two magnetic driving devices, so that the rotation and suspension effects of the rotor are achieved simultaneously.
Description
Technical Field
The invention relates to the technical field of heart auxiliary devices, in particular to a magnetic suspension supercharging device for a blood pump.
Background
The artificial blood pump has undergone three technological innovations from the pulsating blood pump which initially simulates the natural heart to the rotary blood pump which can provide continuous flow at present, and the technological innovations mainly solve the problems of the volume size, the bearing heating, the blood compatibility and the like of the artificial blood pump.
The first generation of artificial blood pump is mainly designed in a bionic way, utilizes mechanical or electromagnetic drive to generate periodic volume change and simulates the pulsation of the heart, and most of the artificial blood pumps of the first generation are only used as extracorporeal auxiliary blood pumps due to the defects of large volume, complex structure, short service life and the like. The second generation of artificial blood pump generally adopts a high-speed rotating impeller (centrifugal or axial flow type) to drive blood to flow in a single direction, and the general characteristic of the first generation of artificial blood pump is to adopt a contact bearing immersed in the blood, and although the survival time of a patient is prolonged, in clinical application, the contact bearing can cause mechanical failure due to abrasion on one hand, and can cause heating due to long-time mechanical contact to induce blood compatibility problems such as hemolysis, thrombus and the like on the other hand. The third generation artificial blood pump is a suspension type rotary blood pump, and is characterized in that a non-contact bearing design is adopted, a rotor rotates in a suspension manner in the artificial blood pump, and the rotor is not in mechanical contact with other parts, so that the damage of the friction of the bearing to blood can be avoided, the blood compatibility is good, the volume is small, the artificial blood pump can be implanted into a thoracic cavity, and the blood pump is the blood pump with the best performance at present.
In order to realize the effects of rotation and suspension of a rotor, a magnetic suspension blood pump in the prior art is often provided with a suspension coil for realizing the suspension function and a rotation coil for realizing the rotation effect, so that the magnetic suspension blood pump in the prior art often has the problems of large volume and poor stability of the rotor.
In order to solve the technical problems, the inventor has invented a magnetic suspension axial end double-motor blood pump, which comprises a first magnetic driving device, a second magnetic driving device and a magnetic suspension supercharging device, wherein coils are arranged in the first magnetic driving device and the second magnetic driving device, an intermediate shaft is connected to the second magnetic driving device, a permanent magnet assembly is arranged in the intermediate shaft, the magnetic suspension supercharging device comprises a volute and a rotor, the rotor is arranged in the volute, the rotor realizes the rotating and suspending effects of the rotor through the action of the intermediate shaft and the first magnetic driving device and the second magnetic driving device, and the first magnetic driving device and the second magnetic driving device are both provided with only one coil.
Disclosure of Invention
Aiming at the defects in the prior art, the technical problems to be solved by the invention are as follows: how to provide a magnetic suspension supercharging device for a blood pump, which can be matched with a permanent magnet assembly in an intermediate shaft and coils in two magnetic driving devices so as to realize the rotation and suspension effects of a rotor at the same time.
In order to solve the technical problems, the invention adopts the following technical scheme:
a magnetic suspension supercharging device for a blood pump comprises a volute and a rotor, wherein a fluid chamber is arranged in the volute, an inflow port and an outflow port which are communicated with the fluid chamber are further arranged on the volute, the rotor is located in the fluid chamber, and gaps are formed between the peripheral wall surface of the rotor and the inner wall surface of the volute at the corresponding position;
rotor structure includes the impeller, the impeller includes impeller body and impeller lid annular first recess and a plurality of second recess have been seted up to one side of impeller body, and is a plurality of the second recess is followed the circumference equipartition of impeller body, rotor structure still includes first permanent magnet subassembly and second permanent magnet subassembly, first permanent magnet subassembly includes a plurality of first permanent magnets, and is a plurality of first permanent magnet is in proper order arranged along the axial laminating in the first recess, second permanent magnet subassembly includes a plurality of second permanent magnets, and is a plurality of the second permanent magnet is followed the circumference equipartition of impeller body, just the second permanent magnet with second recess one-to-one is installed in the second recess, the impeller lid is installed the impeller body is seted up first recess with one side of second recess, just the impeller lid respectively with first permanent magnet subassembly with second permanent magnet subassembly encapsulates in first recess with in the second recess.
In this aspect, the direction of the rotor rotation axis is an axial direction, and the direction perpendicular to the rotor axis is a radial direction.
The working principle of the invention is as follows: when the magnetic suspension pressurizing device is used, the rotor is wound on the middle shaft, the magnetic driving devices are arranged on two axial sides of the magnetic suspension pressurizing device, blood enters the liquid chamber from the inflow port, is pressurized by the rotation of the rotor and then flows out from the outflow port, and therefore the blood conveying effect is achieved.
When the radial suspension of the rotor is realized, the selection of the polarity of the first permanent magnet assembly in the first groove of the rotor needs to be in a mutually exclusive state with the permanent magnet assembly in the intermediate shaft due to the fact that like magnetic poles are opposite, and meanwhile the repulsive force between the first permanent magnet assembly in the first groove of the rotor and the permanent magnet assembly in the intermediate shaft needs to be far greater than the gravity of the rotor when the selection is performed, so that the gravity of the rotor can be ignored, at the moment, the repulsive force between the first permanent magnet assembly in the first groove of the rotor and the permanent magnet assembly in the intermediate shaft can enable the rotor to be in a static state in the radial direction, and the repulsive force also enables a radial gap to be formed between the intermediate shaft and the rotor, and therefore the radial suspension effect of the rotor is realized. Meanwhile, the permanent magnet assembly of the intermediate shaft is similar to the inner ring part of a traditional motor bearing, and the first permanent magnet assembly is similar to the outer ring part of the bearing, so that the inner ring part and the outer ring part of the bearing are completely separated, and the rotor can reach higher rotating speed.
When the effect of axial suspension and rotation of the rotor is realized, three-phase alternating current is introduced into coils in the magnetic driving devices on two axial sides to generate a rotating magnetic field, so that a second permanent magnetic component in the rotor interacts with the rotating magnetic field, and further the magnetic driving devices on the two axial sides of the rotor generate electromagnetic force to the second permanent magnetic component in the rotor, and meanwhile, a certain included angle is formed between the direction of the electromagnetic force generated by the magnetic driving devices to the second permanent magnetic component in the rotor and the rotating direction of the rotor, and the included angle is larger than 0 degrees, so that the electromagnetic force of the magnetic driving devices to the rotor can be decomposed into acting force in the tangential direction of the rotation of the rotor and acting force in the axial direction of the rotor, at the moment, the acting force of the electromagnetic force of the two magnetic driving devices in the tangential direction of the rotation of the rotor can push the rotor to rotate together, and simultaneously the acting force of the electromagnetic force of the two magnetic driving devices in the axial direction can realize the effect of pushing to the middle or pulling the rotor to two sides simultaneously, and the two acting forces in the axial direction are designed to be the same, so that the rotor can suspend the axial direction at a stable position under the action of the two axial forces.
To sum up, the magnetic suspension supercharging device of this scheme is when using, first permanent magnetic component in the rotor can with the permanent magnetic component interact in the jackshaft, in order to realize the radial suspension of rotor, second permanent magnetic component in the rotor can with the rotating magnetic field interact that magnetic drive device produced, make magnetic drive device produce the electromagnetic force rather than direction of rotation certain angle to the rotor, thereby utilize this electromagnetic force to realize the effect of the rotation and the axial suspension of rotor, consequently, the magnetic suspension supercharging device of this scheme can with the permanent magnetic component in the jackshaft, and the coil among two magnetic drive devices cooperates, in order to realize the rotor simultaneously rotatory and the suspension effect. Meanwhile, the blood pump formed by the structure of one rotor structure and two magnetic driving devices in the scheme can realize the effects of suspension and rotation at the same time only by one coil in the magnetic driving devices, thereby realizing the purposes of reducing the volume of the blood pump and reducing the use cost. Meanwhile, the rotor adopts a structural mode of two magnetic driving devices in the axial direction, so that the two magnetic driving devices apply acting force to the rotor at the same time, and the rotation stability of the rotor during suspension is better.
Preferably, the volute includes a first volute and a second volute, a first fluid channel is opened on the first volute, a second fluid channel is opened on the second volute, the first fluid channel and the second fluid channel together form a fluid chamber, and the first volute and the second volute are fixedly connected by a plurality of fasteners.
In this way, the rotor is installed in the volute, and then the first volute and the second volute are fixedly connected, so that the installation of the whole magnetic suspension supercharging device is realized.
Preferably, a central axis of the inflow port is perpendicular to a central axis of the outflow port, and the outflow port is provided along a tangential direction of an inner sidewall of the volute.
Thus, the flowing effect of the blood after the pressurization treatment of the rotor is ensured.
Preferably, the first volute comprises a first metal shell and a first ceramic piece, and the first ceramic piece corresponds to the second permanent magnet assembly in position, so that magnetic lines of force can pass through the first ceramic piece to reach the second permanent magnet assembly;
the second volute comprises a second metal shell and a second ceramic piece, and the second ceramic piece corresponds to the second permanent magnet assembly in position, so that magnetic lines of force can penetrate through the second ceramic piece to reach the second permanent magnet assembly.
Therefore, the first metal shell and the second metal shell are in direct contact with blood of a human body, so that the metal shell is made of titanium alloy when in specific use, the first ceramic piece and the second ceramic piece are respectively arranged at positions corresponding to the second permanent magnet assembly, and the arrangement of the ceramic pieces can ensure that magnetic lines of force of the magnetic driving device can smoothly pass through the ceramic pieces, so that the magnetic lines of force of the magnetic driving device can smoothly reach the rotor to drive the rotor to rotate.
Preferably, a plurality of installation blind holes have been seted up along its circumferential direction on the first metal casing, on the second metal casing with connect the through-hole has been seted up to the position that the installation blind hole corresponds, and every connect through-hole department all to be equipped with the counter sink, every connect through-hole department all to be equipped with the fastener, just the fastener passes connect the through-hole and with the installation blind hole is connected, just the head of fastener is located in the counter sink.
Like this, when carrying out the connection between first metal casing and the second metal casing, stretch into the installation blind hole after passing connecting through hole with the fastener in, set up the screw thread in the installation blind hole to realize and be connected between the fastener, the fastener installation is accomplished the back, and the head of fastener is located the counter sink, thereby improves the pleasing to the eye degree of whole appearance.
Preferably, the impeller body includes impeller main part and follows a plurality of blades of impeller main part circumference equipartition, the whole arc structure that is of blade, every all be equipped with a second recess on the blade, adjacent two the blade with form the flow channel between the impeller main part, just the contained angle between flow channel's bottom surface and the horizontal plane is the angle of repose of flow channel's bottom surface.
Therefore, when blood flows to the rotor and the rotor rotates, the blood is mainly dispersed from the liquid flow channel between the two blades, and because the included angle between the bottom surface of the liquid flow channel and the horizontal plane is the angle of repose (angle of repose, which is the minimum angle formed by the horizontal plane and the surface when an object placed on the inclined plane is in a critical state of sliding down along the inclined plane) of the bottom surface of the liquid flow channel, when the blood flows on the liquid flow channel, the blood flows through the liquid flow channel very stably, the blood does not collide with the liquid flow channel violently, cells in the blood are not damaged greatly, and finally the blood flows out from the liquid flow channel very stably, so that the blood finally flowing out from the blood pump is very stable, the damage of the rotation of the rotor to the cells in the blood is reduced, and the requirement of a human body on the blood pump is better adapted.
Preferably, the end surface of the vane facing away from the impeller cover is inclined gradually outwards in the direction of the outer side surface thereof, and the inclination angle is 1.5-3.5 °.
Therefore, the end face of the blade, which is far away from the impeller cover, is gradually inclined outwards along the direction of the outer side face of the blade, so that the blade can generate a gyroscopic effect when rotating in blood, and the blade has inertia for keeping the rotation direction of the blade.
Preferably, the impeller cover and the liquid flow channel are provided with liquid flow grooves corresponding to the liquid flow channel, the inner end surface of the impeller cover abuts against the first permanent magnet assembly and the second permanent magnet assembly respectively, the outer end surface of the impeller cover is gradually inclined outwards along the direction of the outer side surface of the impeller cover, and the outer end surface of the impeller cover and the corresponding end surface of the impeller body are in smooth transition.
Therefore, the liquid flow groove on the impeller is adaptive to the liquid flow channel, the stable flow effect of blood is ensured, the outer end face of the impeller cover is also outwards inclined along the direction of the outer side face of the impeller cover, and the inclined angle on the impeller cover can be matched with the inclined angle on the impeller body to better realize the gyroscopic effect.
Preferably, the outer end surface of the impeller cover is inclined outwardly in the direction of the outer side surface thereof at an angle of 1.5 ° to 3.5 °.
Thus, the inclination angle on the impeller cover can better realize the gyroscopic effect.
Preferably, one side of the impeller body facing the impeller cover is provided with a first step portion, a second step portion and a third step portion in sequence along the radial direction, a first groove is formed between the first step portion and the second step portion, a second groove is formed between the second step portion and the third step portion, the end surface of the first step portion facing the impeller cover and the end surface of the second step portion facing the impeller cover are flush, and the end surface of the second step portion facing the impeller cover is lower than the end surface of the third step portion facing the impeller cover.
Drawings
FIG. 1 is a schematic structural diagram of a magnetic levitation supercharging device for a blood pump of the invention;
FIG. 2 is a schematic structural diagram of the other side of the magnetic suspension supercharging device for the blood pump;
FIG. 3 is a cross-sectional view of a magnetically levitated pressurizing device for a blood pump of the present invention;
FIG. 4 is a schematic structural diagram of a first volute used in a magnetically levitated booster device for a blood pump according to the present invention;
FIG. 5 is a schematic structural diagram of a second volute used in the magnetic levitation booster device for the blood pump according to the present invention;
FIG. 6 is a schematic structural diagram of an impeller in the magnetic levitation booster device for the blood pump according to the present invention;
FIG. 7 is a schematic structural diagram of the other side of an impeller in the magnetic suspension supercharging device for the blood pump;
FIG. 8 is a cross-sectional view of an impeller in a magnetically levitated booster device for a blood pump according to the present invention;
FIG. 9 is a schematic structural view of an impeller of the magnetically levitated pressurizing apparatus for a blood pump of the present invention with an impeller cover removed;
FIG. 10 is a schematic structural diagram of a impeller body in the magnetic suspension pressurizing device for the blood pump according to the present invention;
fig. 11 is a schematic structural diagram of the magnetic suspension pressurizing device for the blood pump, which is matched with a magnetic driving device and an intermediate shaft for use.
Description of reference numerals: the impeller comprises an impeller body 1, a first step part 101, a second step part 102, a third step part 103, a first groove 104, a second groove 105, an impeller cover 2, blades 3, an impeller main body 4, a liquid flow channel 5, a first permanent magnet assembly 6, a second permanent magnet assembly 7, a first volute 8, a first metal shell 801, a first ceramic piece 802, a mounting blind hole 803, a second volute 9, a second metal shell 901, a second ceramic piece 902, a connecting through hole 903, a magnetic driving device 10 and an intermediate shaft 11.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the drawings of the embodiments of the present invention. It is to be understood that the embodiments described are only a few embodiments of the present invention, and not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the described embodiments of the invention without any inventive step, are within the scope of protection of the invention. Unless defined otherwise, technical or scientific terms used herein shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention belongs.
The use of "first," "second," and similar terms in the description and in the claims of the present application does not denote any order, quantity, or importance, but rather the terms are used to distinguish one element from another. Similarly, the singular forms "a," "an," and "the" do not denote a limitation of quantity, but rather denote the presence of at least one, unless the context clearly dictates otherwise. The terms "comprises," "comprising," or the like, mean that the elements or items listed before "comprises" or "comprising" encompass the features, integers, steps, operations, elements, and/or components listed after "comprising" or "comprising," and do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. "upper", "lower", "left", "right", and the like are used only to indicate relative positional relationships, and when the absolute position of the object to be described is changed, the relative positional relationships may also be changed accordingly.
As shown in fig. 1 to 10, a magnetic suspension pressurizing device for a blood pump includes a volute and a rotor, wherein a fluid chamber is arranged in the volute, an inflow port and an outflow port communicated with the fluid chamber are further arranged on the volute, the rotor is located in the fluid chamber, and gaps are respectively arranged between peripheral wall surfaces of the rotor and inner wall surfaces of the corresponding volute;
the rotor structure comprises an impeller, the impeller comprises an impeller body 1 and an impeller cover 2, an annular first groove 104 and a plurality of second grooves 105 are formed in one side of the impeller body 1, the plurality of second grooves 105 are uniformly distributed in the circumferential direction of the impeller body 1, the rotor structure further comprises a first permanent magnet assembly 6 and a second permanent magnet assembly 7, the first permanent magnet assembly 6 comprises a plurality of first permanent magnets, the plurality of first permanent magnets are sequentially arranged in the first groove 104 in an axial fit mode, the second permanent magnet assembly 7 comprises a plurality of second permanent magnets, the plurality of second permanent magnets are uniformly distributed in the circumferential direction of the impeller body 1, the second permanent magnets correspond to the second grooves 105 one by one and are arranged in the second grooves 105, the impeller cover 2 is arranged on one side, formed in the impeller body 1, of the first groove 104 and the second groove 105, and the first permanent magnet assembly 6 and the second permanent magnet assembly 7 are respectively packaged in the first groove 104 and the second groove 105 by the impeller cover 2.
In this aspect, the direction of the rotor rotation axis is an axial direction, and the direction perpendicular to the rotor axis is a radial direction.
The working principle of the invention is as follows: when the magnetic suspension pressurizing device is used, the rotor is wound on the intermediate shaft 11, the magnetic driving devices 10 are arranged on two axial sides of the magnetic suspension pressurizing device, as shown in the attached drawing 11, blood enters the liquid chamber from the inflow port, then is pressurized by the rotation of the rotor and flows out from the outflow port, and therefore the blood conveying effect is achieved.
When the radial suspension of the rotor is realized, the selection of the polarity of the first permanent magnet assembly 6 in the first groove 104 of the rotor needs to be in a mutually repulsive state with the permanent magnet assembly in the intermediate shaft 11 due to the opposite like magnetic poles, and meanwhile, the repulsive force between the first permanent magnet assembly 6 in the first groove 104 of the rotor and the permanent magnet assembly in the intermediate shaft 11 needs to be far greater than the gravity of the rotor when in selection, so that the gravity of the rotor can be ignored, at the moment, the rotor can be in a static state in the radial direction by utilizing the repulsive force between the first permanent magnet assembly 6 in the first groove 104 of the rotor and the permanent magnet assembly in the intermediate shaft 11, and the repulsive force also enables a radial gap to be formed between the intermediate shaft 11 and the rotor, thereby realizing the radial suspension effect of the rotor. Meanwhile, the permanent magnet assembly of the intermediate shaft 11 is similar to the inner ring part of a traditional motor bearing, and the first permanent magnet assembly 6 is similar to the outer ring part of the bearing, so that the inner ring part and the outer ring part of the bearing are completely separated, and the rotor can reach higher rotating speed.
When the effect of axial suspension and rotation of the rotor is realized, three-phase alternating current is introduced into coils in the magnetic driving devices 10 at two axial sides to generate a rotating magnetic field, so that the second permanent magnetic component 7 in the rotor interacts with the rotating magnetic field, and further the magnetic driving devices 10 at two axial sides of the rotor generate electromagnetic force to the second permanent magnetic component 7 in the rotor, and meanwhile, a certain included angle is formed between the direction of the electromagnetic force generated by the magnetic driving devices 10 to the second permanent magnetic component 7 in the rotor and the rotating direction of the rotor, and the included angle is greater than 0 °, so that the electromagnetic force of the magnetic driving devices 10 to the rotor can be decomposed into an acting force in the tangential direction of the rotation of the rotor and an acting force in the axial direction of the rotor, at the moment, the acting forces of the electromagnetic force of the two magnetic driving devices 10 in the tangential direction of the rotation of the rotor push the rotor together, and the acting force of the electromagnetic force of the two magnetic driving devices 10 in the axial direction simultaneously realize the effect of pushing towards the middle or pulling towards two sides of the rotor, and the two forces in the axial direction are designed to be the same, so that the rotor is suspended at a stable position under the effect of the two axial forces.
To sum up, the magnetic suspension supercharging device of this scheme is when using, first permanent magnetic component 6 in the rotor can interact with the permanent magnetic component in the jackshaft 11, in order to realize the radial suspension of rotor, second permanent magnetic component 7 in the rotor can interact with the rotating magnetic field that magnetic drive device 10 produced, make magnetic drive device 10 produce the rotor and become the electromagnetic force of certain angle rather than direction of rotation, thereby utilize this electromagnetic force to realize the effect of the rotation and the axial suspension of rotor, consequently, the magnetic suspension supercharging device of this scheme can cooperate with the permanent magnetic component in the jackshaft 11, and the coil in two magnetic drive device 10, in order to realize the rotor rotation simultaneously and the effect of suspending. Meanwhile, the blood pump formed by the structure of one rotor and two magnetic driving devices 10 in the scheme can realize the suspension and rotation effects at the same time only by one coil in the magnetic driving device 10, thereby realizing the purposes of reducing the volume and the use cost of the blood pump. Meanwhile, the rotor of the invention adopts a structural mode of two magnetic driving devices 10 in the axial direction, so that the two magnetic driving devices 10 apply acting force to the rotor at the same time, and the stability of rotation is better when the rotor is suspended.
In this embodiment, the volute includes a first volute 8 and a second volute 9, a first fluid channel is opened on the first volute 8, a second fluid channel is opened on the second volute 9, the first fluid channel and the second fluid channel jointly form a fluid chamber, and the first volute 8 and the second volute 9 are fixedly connected by a plurality of fasteners.
In this way, the rotor is installed in the volute, and then the first volute 8 and the second volute 9 are fixedly connected, thereby realizing the installation of the whole magnetic suspension supercharging device.
In the present embodiment, the central axis of the inflow port is perpendicular to the central axis of the outflow port, and the outflow port is disposed in the tangential direction of the inner sidewall of the volute.
Thus, the flowing effect of the blood after the pressurization treatment of the rotor is ensured.
In this embodiment, the first volute 8 includes a first metal casing 801 and a first ceramic sheet 802, and the first ceramic sheet 802 corresponds to the second permanent magnet assembly 7 in position, so that magnetic lines of force can pass through the first ceramic sheet 802 to reach the second permanent magnet assembly 7;
the second volute 9 comprises a second metal casing 901 and a second ceramic piece 902, and the position of the second ceramic piece 902 corresponds to the position of the second permanent magnet assembly 7, so that magnetic lines of force can pass through the second ceramic piece 902 to reach the second permanent magnet assembly 7.
In this way, since the first metal shell 801 and the second metal shell 901 are in direct contact with blood of a human body, the metal shell is made of titanium alloy in specific use, and the first ceramic plate 802 and the second ceramic plate 902 are respectively disposed at positions corresponding to the second permanent magnet assembly 7, the arrangement of the ceramic plates can ensure that magnetic lines of force of the magnetic driving device 10 can smoothly pass through, so that the magnetic lines of force of the magnetic driving device 10 can smoothly reach the rotor to drive the rotor to rotate.
In this embodiment, a plurality of installation blind holes 803 have been seted up along its circumferential direction on first metal casing 801, and connect the through-hole 903 has been seted up with the position that installation blind hole 803 corresponds on second metal casing 901, and all is equipped with the counter sink in every connect the through-hole 903 department, and every connect the through-hole 903 department all is equipped with the fastener, and the fastener passes connect the through-hole 903 and is connected with installation blind hole 803, and the head of fastener is located the counter sink.
Like this, when carrying out the connection between first metal casing 801 and second metal casing 901, pass behind connect through 903 with the fastener and stretch into installation blind hole 803, set up the screw thread in the installation blind hole 803 to realize with being connected between the fastener, after the fastener installation, the head of fastener is located the countersunk head, thereby improves the pleasing to the eye degree of whole appearance.
In this embodiment, the impeller body 1 includes an impeller main body 4 and a plurality of blades 3 uniformly distributed along a circumferential direction of the impeller main body 4, the blades 3 are integrally arc-shaped, each blade 3 is provided with a second groove 105, a liquid flow channel 5 is formed between two adjacent blades 3 and the impeller main body 4, and an included angle between a bottom surface of the liquid flow channel 5 and a horizontal plane is a repose angle of the bottom surface of the liquid flow channel 5.
Thus, when blood flows to the rotor and the rotor rotates, the blood is mainly dispersed from the liquid flow channel 5 between the two blades 3, and because the included angle between the bottom surface of the liquid flow channel 5 and the horizontal plane is the angle of repose (angle of repose, which is the minimum angle between the inclined surface and the horizontal surface when an object placed on the inclined surface is in a critical state of sliding down along the inclined surface) of the bottom surface of the liquid flow channel 5, when the blood flows on the liquid flow channel 5, the blood flows through the liquid flow channel 5 very stably, the blood does not collide with the liquid flow channel 5 violently, cells in the blood are not damaged greatly, and finally the blood flows out from the liquid flow channel 5 very stably, so that the blood flowing out from the blood pump finally is also very stable, damage to the cells in the blood caused by the rotation of the rotor is reduced, and the requirement of a human body on the blood pump is better adapted.
In the present embodiment, the bottom surface of the flow channel 5 is curved in the rotational direction of the impeller.
Thus, the bottom surface of the liquid flow channel 5 is bent along the rotation direction of the impeller, and the drainage effect on blood can be better realized, so that the collision of blood is further reduced.
In this embodiment, both side surfaces of the flow channel 5 are curved in the rotation direction of the impeller.
Thus, the two side surfaces of the flow channel 5 are also bent in the rotation direction of the impeller, and the effect of draining blood can be further achieved by the two side surfaces of the flow channel 5, thereby further reducing the collision of blood.
In this embodiment, the end surface of the vane 3 facing away from the impeller cover 2 is inclined gradually outward in the direction of the outer side surface thereof at an angle of 1.5 ° to 3.5, and specifically, the end surface of the vane 3 facing away from the impeller cover 2 is inclined outward in the direction of the outer side surface thereof at an angle of 2 °, as shown in Ɵ in fig. 8.
Therefore, the end face of the blade 3 departing from the impeller cover 2 is gradually inclined outwards along the direction of the outer side face of the blade 3, so that when the blade 3 rotates in blood, the blade 3 can generate a gyroscopic effect, and the blade 3 has inertia for keeping the rotation direction of the blade 3, so that once the blade 3 rotates, the magnetic driving device 10 can keep the continuous rotation of the rotor only by providing a small electromagnetic force for the rotor due to the gyroscopic effect generated by the blade, and therefore, on one hand, the energy consumed for keeping the rotor rotating can be reduced, on the other hand, the heat generation of the magnetic driving device 10 can also be reduced, the energy consumption and the heat generation phenomenon of the blood pump in the use process are greatly reduced, and the performance requirement of a human body on the blood pump is better met.
In this embodiment, the impeller cover 2 is provided with a flow channel corresponding to the flow channel 5 at a position corresponding to the flow channel 5, the inner end surface of the impeller cover 2 abuts against the first permanent magnet assembly 6 and the second permanent magnet assembly 7, the outer end surface of the impeller cover 2 is gradually inclined outwards along the direction of the outer side surface thereof, and the outer end surface of the impeller cover 2 is in smooth transition with the corresponding end surface of the impeller body 1.
Therefore, the liquid flow groove on the impeller is adaptive to the liquid flow channel 5, the stable flow effect of blood is ensured, the outer end face of the impeller cover 2 is also outwards inclined along the direction of the outer side face of the impeller cover, and the inclined angle on the impeller cover 2 can be matched with the inclined angle on the impeller body 1 to better realize the gyroscopic effect.
In this embodiment, the outer end surface of the impeller cap 2 is inclined outwardly at an angle of 1.5 ° to 3.5 ° in the direction of the outer side surface thereof, and specifically, the outer end surface of the impeller cap 2 is inclined outwardly at an angle of 2 ° in the direction of the outer side surface thereof, as shown in Ɵ in fig. 8.
In this way, this angle of inclination on the impeller cover 2 allows a better gyroscopic effect to be achieved.
In the present embodiment, the side of the impeller body 1 facing the impeller cover 2 is provided with a first step 101, a second step 102 and a third step 103 in sequence in the radial direction, a first groove 104 is formed between the first step 101 and the second step 102, a second groove 105 is formed between the second step 102 and the third step 103, the end surface of the first step 101 facing the impeller cover 2 and the end surface of the second step 102 facing the impeller cover 2 are flush, and the end surface of the second step 102 facing the impeller cover 2 is lower than the end surface of the third step 103 facing the impeller cover 2.
In the present embodiment, the end of the blade 3 facing away from the impeller cover 2 protrudes from the impeller body 4, and the end of the blade 3 facing the impeller cover 2 is flush with the end surface of the impeller body 4.
Thus, when blood flows into the blades 3, the blades 3 protrude from the impeller main body 4, so that the blood can be basically concentrated at the blades 3 and flows out of the liquid flow channels 5 along with the rotation of the blades 3, and the blood conveying effect is ensured.
In this embodiment, the joint of the impeller body 4 and the blade 3 is provided with an arc chamfer, and the peripheries of the impeller body 4 and the blade 3 are provided with arc chamfers.
Thus, the rounded chamfer reduces the effect on blood flow.
In this embodiment, impeller cover 2 includes a first cover portion corresponding to the position of first groove 104, and a second cover portion corresponding to the position of second groove 105, the first cover portion protrudes outward toward one end of first permanent magnet assembly 6 and extends into first groove 104 to abut against first permanent magnet assembly 6, and the second cover portion abuts against second permanent magnet assembly 7 toward one end of second permanent magnet assembly 7.
In the embodiment, the impeller body 1 and the impeller cover 2 are made of titanium alloy.
Thus, since the impeller body 1 and the impeller cover 2 are in direct contact with blood of a human body, titanium alloys are used for both.
It should be noted that the above embodiments are only used for illustrating the technical solutions of the present invention and not for limiting the technical solutions, and those skilled in the art should understand that the technical solutions of the present invention can be modified or substituted with equivalent solutions without departing from the spirit and scope of the technical solutions, and all should be covered in the claims of the present invention.
Claims (10)
1. A magnetic suspension supercharging device for a blood pump is characterized by comprising a volute and a rotor, wherein a fluid chamber is arranged in the volute, an inflow port and an outflow port which are communicated with the fluid chamber are also arranged on the volute, the rotor is positioned in the fluid chamber, and gaps are formed between the peripheral wall surface of the rotor and the inner wall surface of the volute at the corresponding position;
rotor structure includes the impeller, the impeller includes impeller body and impeller lid annular first recess and a plurality of second recess have been seted up to one side of impeller body, and is a plurality of the second recess is followed the circumference equipartition of impeller body, rotor structure still includes first permanent magnet subassembly and second permanent magnet subassembly, first permanent magnet subassembly includes a plurality of first permanent magnets, and is a plurality of first permanent magnet is in proper order arranged along the axial laminating in the first recess, second permanent magnet subassembly includes a plurality of second permanent magnets, and is a plurality of the second permanent magnet is followed the circumference equipartition of impeller body, just the second permanent magnet with second recess one-to-one is installed in the second recess, the impeller lid is installed the impeller body is seted up first recess with one side of second recess, just the impeller lid respectively with first permanent magnet subassembly with second permanent magnet subassembly encapsulates in first recess with in the second recess.
2. The magnetically levitated pressurizing device for a blood pump according to claim 1, wherein the volute comprises a first volute and a second volute, a first fluid passage is formed on the first volute, a second fluid passage is formed on the second volute, the first fluid passage and the second fluid passage jointly form a fluid chamber, and the first volute and the second volute are fixedly connected through a plurality of fasteners.
3. The magnetically levitated pressurizing device for a blood pump according to claim 2, wherein a central axis of the inflow port is perpendicular to a central axis of the outflow port, and the outflow port is disposed in a tangential direction of an inner side wall of the volute.
4. The magnetically suspended supercharging device for a blood pump according to claim 2, wherein the first volute comprises a first metal casing and a first ceramic sheet, and the first ceramic sheet corresponds to the second permanent magnet assembly in position, so that magnetic lines of force can pass through the first ceramic sheet to reach the second permanent magnet assembly;
the second volute comprises a second metal shell and a second ceramic piece, and the second ceramic piece corresponds to the second permanent magnet assembly in position, so that magnetic lines of force can penetrate through the second ceramic piece to reach the second permanent magnet assembly.
5. The magnetic suspension supercharging device for a blood pump according to claim 4, wherein the first metal housing has a plurality of blind mounting holes formed along a circumferential direction thereof, the second metal housing has through-holes formed at positions corresponding to the blind mounting holes, and each through-hole has a countersunk hole, a fastener is disposed at each through-hole, the fastener passes through the through-hole and is connected to the blind mounting hole, and a head of the fastener is disposed in the countersunk hole.
6. The magnetic suspension supercharging device for the blood pump according to claim 1, wherein the impeller body comprises an impeller main body and a plurality of blades uniformly distributed along the circumference of the impeller main body, the blades are integrally arc-shaped, a second groove is formed in each blade, a liquid flow channel is formed between each two adjacent blades and the impeller main body, and an included angle between the bottom surface of the liquid flow channel and the horizontal plane is an angle of repose of the bottom surface of the liquid flow channel.
7. A magnetically levitated pressurizing device for a blood pump according to claim 6, wherein the end surface of the blade facing away from the impeller cover is inclined gradually outward in the direction of the outer side surface thereof, and the inclination angle is 1.5-3.5 °.
8. The magnetically levitated pressurizing device for a blood pump according to claim 7, wherein a fluid channel corresponding to the fluid channel is formed in each of the impeller covers at a position corresponding to the fluid channel, the inner end surfaces of the impeller covers respectively abut against the first permanent magnet assembly and the second permanent magnet assembly, the outer end surfaces of the impeller covers gradually incline outwards in the direction of the outer side surfaces thereof, and the outer end surfaces of the impeller covers are in smooth transition with the corresponding end surfaces of the impeller body.
9. The magnetically levitated pressurizing device for a blood pump according to claim 8, wherein the outer end surface of the impeller cover is inclined outwardly in the direction of the outer side surface thereof at an angle of 1.5-3.5 °.
10. The magnetic levitation supercharging device for the blood pump according to claim 1, wherein a side of the impeller body facing the impeller cover is provided with a first step, a second step and a third step in sequence along a radial direction, a first groove is formed between the first step and the second step, a second groove is formed between the second step and the third step, an end surface of the first step facing the impeller cover and an end surface of the second step facing the impeller cover are flush, and an end surface of the second step facing the impeller cover is lower than an end surface of the third step facing the impeller cover.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202211213987.6A CN115337534B (en) | 2022-09-30 | 2022-09-30 | Magnetic suspension supercharging device for blood pump |
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| Application Number | Priority Date | Filing Date | Title |
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| CN202211213987.6A CN115337534B (en) | 2022-09-30 | 2022-09-30 | Magnetic suspension supercharging device for blood pump |
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| CN115337534B CN115337534B (en) | 2024-06-14 |
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| CN101371041A (en) * | 2006-01-13 | 2009-02-18 | 哈特威尔公司 | Rotary blood pump |
| CN102247628A (en) * | 2010-05-17 | 2011-11-23 | 北京天高智机技术开发公司 | Implantable magnetic liquid suspension centrifugal blood pump |
| CN105343950A (en) * | 2015-09-25 | 2016-02-24 | 济南大学 | Artificial blood pump adopting hydraulic suspension bearing |
| CN105833368A (en) * | 2016-05-11 | 2016-08-10 | 北京精密机电控制设备研究所 | Centrifugal impeller for blood pump |
| CN205964586U (en) * | 2016-05-11 | 2017-02-22 | 北京精密机电控制设备研究所 | Centrifugal impeller is used to blood pump |
| EP3173108A1 (en) * | 2015-11-30 | 2017-05-31 | Fundacja Rozwoju Kardiochirurgii Im. Prof. Zbigniewa Religi | Impeller with closed channels for a centrifugal implantable ventricular assist pump |
| WO2019019206A1 (en) * | 2017-07-25 | 2019-01-31 | 中国医学科学院阜外医院 | Magnetic suspension axial flow blood pump with axial feedback control |
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2022
- 2022-09-30 CN CN202211213987.6A patent/CN115337534B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101371041A (en) * | 2006-01-13 | 2009-02-18 | 哈特威尔公司 | Rotary blood pump |
| CN102247628A (en) * | 2010-05-17 | 2011-11-23 | 北京天高智机技术开发公司 | Implantable magnetic liquid suspension centrifugal blood pump |
| CN105343950A (en) * | 2015-09-25 | 2016-02-24 | 济南大学 | Artificial blood pump adopting hydraulic suspension bearing |
| EP3173108A1 (en) * | 2015-11-30 | 2017-05-31 | Fundacja Rozwoju Kardiochirurgii Im. Prof. Zbigniewa Religi | Impeller with closed channels for a centrifugal implantable ventricular assist pump |
| CN105833368A (en) * | 2016-05-11 | 2016-08-10 | 北京精密机电控制设备研究所 | Centrifugal impeller for blood pump |
| CN205964586U (en) * | 2016-05-11 | 2017-02-22 | 北京精密机电控制设备研究所 | Centrifugal impeller is used to blood pump |
| WO2019019206A1 (en) * | 2017-07-25 | 2019-01-31 | 中国医学科学院阜外医院 | Magnetic suspension axial flow blood pump with axial feedback control |
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| CN115337534B (en) | 2024-06-14 |
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