CN112704812A - Centrifugal blood pump - Google Patents
Centrifugal blood pump Download PDFInfo
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- CN112704812A CN112704812A CN202011346879.7A CN202011346879A CN112704812A CN 112704812 A CN112704812 A CN 112704812A CN 202011346879 A CN202011346879 A CN 202011346879A CN 112704812 A CN112704812 A CN 112704812A
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Abstract
The invention relates to a centrifugal blood pump, which comprises a shell component, a supporting component and a rotor component, wherein the supporting component and the rotor component are arranged in the shell component; the rotor assembly comprises a first part and a second part connected with the first part, and the magnetic part is arranged between the first part and the second part; the medical extracorporeal blood pump further comprises an adjusting piece, and the adjusting piece is used for being matched with the first portion and/or the second portion so as to adjust the mass balance of the rotor assembly. Through increasing the uneven quality in the left side and the uneven quality in the right side that regulating part can reduce the rotor subassembly in the rotor subassembly, and then reduce the centrifugal force that the rotor subassembly received to reduce the radial load of axle subassembly, make the atress that the bearing capacity of the pressure liquid film that blood formed that uses as the emollient be greater than the axle subassembly, make the pressure liquid film be difficult to break, increase the lubricity of axle subassembly work.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a centrifugal blood pump.
Background
The centrifugal blood pump is used for establishing a blood circulation channel in vitro to assist the heart in pumping blood when a heart operation or a patient generates a voluntary shock. The network percutaneous left ventricular assist device (a plvad system), an extracorporeal membrane oxygenation system (ECMO), an extracorporeal circulation system and the like can be used as a power device through a centrifugal blood pump to replace a heart to pump blood.
At present, when the centrifugal blood pump is used, the bearing seriously damages blood due to friction and heating of the bearing, and hemolysis and thrombus are easily generated. Therefore, centrifugal blood pumps using sliding bearings are available on the market to overcome the above-mentioned drawbacks. Although widely used in the industrial field, the sliding bearing can be used in combination with lubricating liquid to realize friction with the liquid, thereby reducing the abrasion and the heat generation of the bearing. However, the lubricating liquid of the centrifugal blood pump is blood, the viscosity is low compared with the traditional industrial lubricating liquid, the bearing capacity of the formed pressure liquid film is insufficient, and the bearing capacity is smaller than the bearing capacity of the sliding bearing, so that the pressure liquid film is broken, the friction between the bearing and the liquid is difficult to realize, and the expected lubricating effect cannot be achieved. The bearing position of the blood pump is also prone to hemolysis and the formation of the blood pump makes it difficult to reduce the incidence of hemolysis and thrombosis.
Disclosure of Invention
In view of the above-mentioned shortcomings of the prior art, it is an object of the present invention to provide a centrifugal blood pump that solves one or more of the problems of the prior art.
In order to achieve the purpose, the technical scheme of the invention is as follows:
the centrifugal blood pump comprises a shell assembly, a supporting assembly and a rotor assembly, wherein the supporting assembly and the rotor assembly are arranged in the shell assembly; the rotor assembly comprises a first part and a second part connected with the first part, and a magnetic part is arranged between the first part and the second part; the centrifugal blood pump further comprises an adjuster for cooperating with the first and/or second portions to adjust the mass balance of the rotor assembly.
Furthermore, the first portion is provided with at least three first grooves and/or the second portion is provided with at least three second grooves for accommodating the adjusting member.
Further, the first grooves are uniformly distributed or non-uniformly distributed in the center of the first part; the second grooves are uniformly distributed or non-uniformly distributed in the center of the second part.
Further, the first groove and/or the second groove are both circular grooves.
Further, the second portion has a concave surface facing away from the first portion.
Further, the adjusting piece is of a solid structure or a non-solid structure.
Further, the support assembly includes a first bushing, a second bushing, and a shaft coupled between the first bushing and the second bushing.
Further, the proximal end of the shaft is in clearance fit with the first shaft sleeve, the distal end of the shaft is in clearance fit with the second shaft sleeve, and the clearance fit enables first clearances to be formed between the shaft and the first shaft sleeve and between the shaft and the second shaft sleeve respectively.
Further, at least one external convex part is arranged on the outer side of the shaft along the axial direction.
Further, the first portion is provided with a first hole matched with the shaft, and at least one concave portion used for being matched with the convex portion is arranged on the inner wall of the first hole.
Further, a second gap is provided between the rotor assembly and the housing assembly, the second gap increasing along the flow path toward the outlet of the housing assembly.
Further, the housing assembly has a partial radius of curvature that is quadratically proportional to the partial angle containing the radius of curvature.
Compared with the prior art, the invention has the following beneficial technical effects:
(one) can reduce the unbalanced mass in the left side and the unbalanced mass in the right side of rotor subassembly through increase the regulating part in the rotor subassembly, and then reduce the centrifugal force that the rotor subassembly received to reduce the radial load of axle subassembly, make the atress that the bearing capacity of the pressure liquid film that blood formed that uses as the emollient is greater than the axle subassembly, make the pressure liquid film be difficult to break, increase the lubricity of axle subassembly work.
Further, a concave surface is formed at the bottom of the second portion, and an inclination angle is formed between the concave surface and the horizontal plane, so that a part of hydraulic force can be offset by hydraulic force component force at the bottom of the second portion, and therefore, the load of the rotor assembly in the radial direction is reduced, hemolysis and thrombosis are reduced, and the blood performance of the centrifugal blood pump is improved.
And (III) further, the first shell and the second shell both adopt a volute structure, and the volute structure enables a gap between the rotor assembly and the shell assembly to gradually increase towards an outlet of the shell assembly along a flow path, so that smooth transition of a middle point of the rear half part of the volute structure is realized, red blood cells are prevented from being damaged, blood is further damaged, and hemolysis and thrombus are reduced.
And (IV) further, the arrangement of the first gap between the shaft and the first shaft sleeve and the first gap between the shaft and the second shaft sleeve enables the supporting force of a pressure liquid film formed by blood to be large, and further enables the shaft assembly to smoothly realize friction with the blood.
Drawings
Fig. 1 shows a schematic structural diagram of an embodiment of the centrifugal blood pump according to the present invention.
Fig. 2 shows an enlarged axial view of a bearing assembly in a centrifugal blood pump according to an embodiment of the present invention.
Fig. 3 shows a radially enlarged schematic view of a support assembly in a centrifugal blood pump according to an embodiment of the present invention.
Fig. 4 shows a schematic structural view of a rotor assembly in a centrifugal blood pump according to an embodiment of the present invention.
Fig. 5 shows a schematic structural view of a rotor assembly in a centrifugal blood pump according to a second embodiment of the present invention.
Fig. 6 is a partial schematic view showing the first housing of the centrifugal blood pump according to the embodiment of the present invention hidden.
Fig. 7 is a schematic diagram showing the relationship between radius of curvature and angle in a centrifugal blood pump according to an embodiment of the present invention.
Fig. 8 shows a schematic view of an adjuster of a centrifugal blood pump according to an embodiment of the present invention in a solid configuration.
Fig. 9 is a schematic view of a first non-solid configuration of an adjuster for a centrifugal blood pump in accordance with an embodiment of the present invention.
Fig. 10 is a schematic view of a second non-solid configuration of an adjuster for a centrifugal blood pump in accordance with an embodiment of the present invention.
In the drawings, the reference numbers: 1. a housing assembly; 101. a first housing; 102. a second housing; 103. a spiral profile; 2. a support assembly; 201. a first bushing; 202. a shaft; 2021. an outer convex portion; 203. a second shaft sleeve; 3. a rotor assembly; 301. a first part; 3011. a first groove; 3012. a first hole; 3013. an inner concave portion; 302. a magnetic member; 303. a second section; 3031. a second groove; 3032. a concave surface; 3033. mounting grooves; 4. a first gap; 5. an adjustment member; 501. a through hole; 502. a non-through hole; 6. a second gap.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the centrifugal blood pump according to the present invention will be described in further detail with reference to the accompanying drawings and the detailed description. The advantages and features of the present invention will become more apparent from the following description. It is to be noted that the drawings are in a very simplified form and are all used in a non-precise scale for the purpose of facilitating and distinctly aiding in the description of the embodiments of the present invention. To make the objects, features and advantages of the present invention comprehensible, reference is made to the accompanying drawings. It should be understood that the structures, ratios, sizes, and the like shown in the drawings and described in the specification are only used for matching with the disclosure of the specification, so as to be understood and read by those skilled in the art, and are not used to limit the implementation conditions of the present invention, so that the present invention has no technical significance, and any structural modification, ratio relationship change or size adjustment should still fall within the scope of the present invention without affecting the efficacy and the achievable purpose of the present invention.
The following describes a specific structure of the centrifugal blood pump according to the first embodiment:
referring to fig. 1, the centrifugal blood pump includes a housing assembly 1, a support assembly 2 and a rotor assembly 3 disposed on the housing assembly 1, wherein the support assembly 2 is connected to the rotor assembly 3, so that the rotor assembly 3 is rotatably disposed on the housing assembly 1 through the support assembly 2.
With reference to fig. 1, the rotor assembly 3 includes a first portion 301 and a second portion 303 connected to the first portion 301, and a magnetic element 302 is disposed between the first portion 301 and the second portion 303. Specifically, in the centrifugal blood pump according to the first embodiment of the present invention, the first portion 301 refers to an upper impeller, the second portion 303 refers to a lower impeller, the magnetic member 302 refers to a passive magnetic steel, and the magnetic member 302 is installed in an installation groove 3033 of the lower impeller. The upper impeller and the lower impeller are connected through ultrasonic welding or glue, so that the passive magnetic steel is sealed inside the upper impeller and the lower impeller.
Referring to fig. 5, the centrifugal blood pump according to the first embodiment of the present invention further includes an adjusting member 5, and the adjusting member 5 is used in combination with the first portion 301 and the second portion 303 to adjust the mass balance of the rotor assembly 3.
Referring to fig. 4 and 5, specifically, at least three first slots 3011 are formed on the first portion 301, at least three second slots 3031 are formed on the second portion 303, and the adjusting member 5 is connected to the first slots 3011 and the second slots 3031.
Further, in the centrifugal blood pump according to the first embodiment of the present invention, the number of the first grooves 3011 formed in the first portion 301 is preferably four, each of the first grooves 3011 is a circular groove, the first grooves 3011 are formed in the lower surface of the upper impeller, and the first grooves 3011 are uniformly distributed at an angle of 90 ° around the axis of the first portion 301. Similarly, in the centrifugal blood pump according to the first embodiment of the present invention, the number of the second grooves 3031 is also preferably four, each of the second grooves 3031 is a circular groove, the second grooves 3031 are opened on the groove bottom surface of the mounting groove 3033 in the second portion 303, and each of the second grooves 3031 is centered on the axis of the second portion 303 and is also uniformly distributed at an angle of 90 °.
Referring to fig. 8 to 10, the following describes a specific structure of the adjusting member as follows:
in the centrifugal blood pump of the first embodiment, the adjusting member 5 is a balancing piece and is inserted into the first slot 3011 and the second slot 3031 by an interference fit. The balancing sheet is of a structure matched with the shape of the groove, and in the centrifugal blood pump in the first embodiment, the balancing sheet is circular. The balancing sheets with different qualities can be selected according to the use requirement, and the balancing sheets can be solid structures as shown in fig. 7, and can also be non-solid structures as shown in fig. 9 or fig. 10.
Further, referring to fig. 9, the non-solid structure may be formed by forming a through hole 501 on the balancing sheet body, or forming a non-through hole 502 on the balancing sheet body, and the aperture of the through hole 501 and the aperture of the non-through hole 502 may be increased or decreased according to the difference of the mass of the balancing sheet.
Furthermore, the number of the balancing sheets is different according to different test results of the unbalance mass. Specifically, the balancing sheet may be completely installed in the first slot 3011 and the second slot 3031 as in the first embodiment, or may be partially installed in the first slot 3011 and the second slot 3031 according to requirements in other embodiments, or may be partially installed in the first slot 3011 or the second slot 3031.
Further, the connection manner of the balancing sheet and the first slot 3011 or the second slot 3031 may not be limited to the manner of interference fit in the first embodiment of the present invention, and the balancing sheet may also be detachably connected or non-detachably connected to the first slot 3011 or the second slot 3031 through other connection relationships, for example, the connection may be a snap connection, a screw connection, a threaded connection, or the like, as long as the purpose of installing the balancing sheet in the first slot 3011 or the second slot 3031 and achieving mass balancing is satisfied.
The design purpose that the number of the first slots 3011 and the second slots 3031 is at least three is to meet the requirement that the unbalanced mass can be balanced at an angle of 0-360 degrees, taking the first slot 3011 as an example, when the first slot 3011 is two and is respectively arranged on the upper impeller at 0 degrees and 90 degrees, and the unbalanced mass of the test result is 180 degrees, the mass of the upper impeller at 180 degrees cannot be balanced.
Further, with continued reference to fig. 4 and 5, when the rotor assembly 3 is in operation, if the dynamic balance of the rotor assembly 3 is not good, the unbalanced mass of the rotor assembly 3 in dynamic balance will generate a centrifugal force due to rotation, thereby increasing the load at the supporting assembly 2. By providing the balancing pieces in the first slot 3011 and the second slot 3031, respectively, the unbalanced left and right mass of the rotor assembly 3 is balanced, thereby reducing the load on the support assembly 2 due to the centrifugal force.
Further, with continued reference to fig. 4 and 5, before the balancing tab is installed in the first slot 3011 or the second slot 3031, the unbalanced mass of the rotor assembly 3 needs to be tested, so as to obtain the left and right unbalanced mass of the rotor assembly 3, and then according to the specific value and direction obtained after the test, the balancing tab with proper mass is installed in the first slot 3011 or the second slot 3031 in the corresponding direction. The test process is a known technique for those skilled in the art, and specifically, a dynamic balancing machine is used for measurement, and the test process is not described in detail herein.
Further, with continued reference to fig. 4 and 5, the trim tab mounted in the first slot 3011 of the upper impeller (i.e., the first portion 301) is made of a metal material, including but not limited to one or more of stainless steel and copper. The balancing sheet installed in the second groove 3031 of the lower impeller (i.e., the second portion 303) is made of a non-metallic material, because if the balancing sheet in the second groove 3031 of the lower impeller is also made of a metallic material, a magnetic field between the passive magnetic steel (i.e., the magnetic member 302) and the active magnetic steel (which is used for generating a stable rotating magnetic field with the passive magnetic steel to form an eddy current and generate a torque to drive the rotor assembly 3 to rotate at a high speed) is disturbed, thereby affecting the rotation and axial force of the centrifugal blood pump.
Further, with continued reference to fig. 5, a concave surface 3032 is formed at the lower impeller (i.e. the second portion 303) opposite to the upper impeller (i.e. the first portion 301), specifically, the concave surface 3032 is formed at the bottom of the lower impeller (i.e. the second portion 303), the concave depth of the concave surface 3032 gradually increases from the outer diameter of the lower impeller (i.e. the second portion 303) to the central point of the lower impeller, so that the concave depth of the concave surface 3032 forms the maximum depth at the center of the lower impeller, an inclination angle α can be formed between the concave surface 3032 and the horizontal plane, by increasing the inclination angle α, the hydraulic force direction at the bottom of the lower impeller is increased by a radial hydraulic force component in addition to a vertically upward force, the hydraulic force component is distributed from the center of the lower impeller to the outer diameter of the lower impeller from inside to outside, and the hydraulic force at the outer surface of the lower impeller is from outside to inside in the radial direction, the higher pressure on the lower impeller surface in any one direction leads to a larger hydraulic force from outside to inside in that direction, and a hydraulic force component is provided at the bottom of the lower impeller, so that a hydraulic force action can be counteracted, and the load of the rotor assembly 3 in the radial direction is reduced.
The specific structure of the support assembly 2 is described below:
referring to fig. 1 and 2, the support assembly 2 includes a first shaft sleeve 201, a second shaft sleeve 203, and a shaft 202 connected between the first shaft sleeve 201 and the second shaft sleeve 203, in the centrifugal blood pump according to an embodiment of the present invention, the shaft 202 is made of a metal material, such as one or more of stainless steel and titanium alloy. The first shaft sleeve 201 and the second shaft sleeve 203 are made of wear-resistant polymer materials, such as polyetheretherketone (peek) or pom plastics.
With continued reference to FIG. 1, because blood has a certain viscosity, the proximal and distal ends of the blood shaft 202 form pressurized liquid films that support the bearing assembly 2 according to the principles of plain bearings. The supporting force of the pressure liquid film is related to the size of the first gap 4, and the smaller the first gap 4 is, the larger the supporting force of the pressure liquid film is. However, if the first gap 4 is too small, it will cause the shaft to interfere with the bearing, so it is necessary to control the straightness and roughness of the shaft 202, the roughness of the first and second bushings 201, 203, and the concentricity between the first and second bushings 201, 203 to ensure that the bearing assembly 2 smoothly rubs against the liquid. Further, referring to fig. 1 and 5, at least one outer protrusion 2021 is axially disposed outside the shaft 202, a first hole 3012 matched with the shaft 202 is formed in the center of the upper impeller (i.e., the first portion 301), and at least one inner recess 3013 for matching the outer protrusion 2021 is disposed along the axial direction on the inner wall of the first hole 3012. By matching the convex portion 2021 with the concave portion 3013, the connection strength of the shaft 202 and the upper impeller assembly is further enhanced, so that the rotational friction is lower, and the shaft 202 is prevented from being displaced.
As will be understood by those skilled in the art, the above-mentioned bearing assembly 2 can also be referred to as a sliding bearing, and the working principle and the using effect of the sliding bearing are the same as those of the bearing assembly 2. The male portion 2021 may be radially protruded and circumferentially surround the shaft 202 entirely, or may only partially surround the shaft 202, but it is sufficient that the male portion 2021 can be engaged with the female portion 3013 to enhance the connection strength between the shaft 202 and the upper impeller.
The specific structure of the housing assembly 1 is described below as follows:
referring to fig. 1 and 6, the rotor assembly 3 disposed inside the housing assembly 1 has a second gap 6 with the inside of the housing assembly 1, and the second gap 6 is gradually increased toward the outlet of the housing assembly 1 along the flow path of the blood (the direction of the arrow in fig. 6).
Specifically, with continuing reference to fig. 1 and fig. 6, the housing assembly 1 is formed by connecting a first housing 101 and a second housing 102, and both the first housing 101 and the second housing 102 adopt a volute structure. Specifically, with continuing reference to fig. 1 and fig. 6, the housing assembly 1 is formed by connecting a first housing 101 and a second housing 102, and both the first housing 101 and the second housing 102 adopt a volute structure. The volute structure has a spiral profile 103 corresponding to the shape of the volute, the spiral profile is similar to a spiral line, and specifically, the spiral profile is a curve formed by winding outward one by one circle at a fixed point (for example, the starting point a, but of course, any point other than the starting point a) and gradually expanding outward. Wherein the first housing 101 and the second housing 102 each have a partial radius of curvature that is quadratically proportional to the angle of the portion containing the radius of curvature.
The relationship between the radius of curvature and the angle is explained in detail by taking the second housing 102 as an example:
referring to fig. 6 and 7, a start point a, a middle point B, and an end point C are respectively distributed along the spiral profile, the axis of the spiral casing structure is a center point E, and the start point a, the middle point B, the end point C, and the center point E are all located on a center line F of the spiral casing structure. The spiral line is connected with a starting point A and a middle point B to form a front half part of the spiral case structure, a connecting line between the starting point A and a middle point E is the curvature radius of the head part of the spiral case structure of the front half part, and the curvature radius values formed by connecting any one point in the spiral line 103 from the starting point A to the middle point B with a center point E are equal. The spiral line connects a middle point B and an end point C to form a rear half part of the spiral case structure, a connecting line between the middle point B and the center point E is a tail curvature radius of the spiral case structure of the front half part, the curvature radius formed by connecting any one point of the spiral line 103 between the middle point B and the end point C and the center point E increases progressively along the liquid flow direction by taking the tail curvature radius as a reference, the increasing progressively ends at an outlet close to the spiral case structure, and the outlet is used for leading blood fluid to flow out.
Referring to fig. 6, since the radius of the second half of the volute structure is increased, the angle between any one radius and the center line F is gradually increased along the liquid flowing direction. Referring to fig. 6, in the rear half of the volute structure, the length of the second radius of curvature D2 is smaller than the length of the third radius of curvature D3, and the included angle between the second radius of curvature D2 and the center line F is smaller than the included angle between the third radius of curvature D3 and the center line F, so that the partial radii of curvature of the first housing 101 and the second housing 102 are both proportional to the square of the partial angle including the radius of curvature.
Further, the partial curvature radius refers to a curvature radius of a connecting line between any point on the spiral line 103 and the central point E from the middle point B to the end point C, i.e., a rear half of the spiral casing structure, taking the curvature radius D2 as an example, a partial angle including the curvature radius refers to an included angle β, specifically, the included angle β is an included angle between a head curvature radius (i.e., a connecting line between the central point E and the initial point a) and the second curvature radius D2, and the curvature radius of the rear half of the spiral casing structure of the included angle β changes in a direct relation.
Further, the relationship between the angle and the radius of curvature can be demonstrated by the following formula:
r(θ)＝r0+α(θ-π)2
wherein alpha is a constant in the range of 0.5 to 2mm/rad2Theta is the angle between the changing radius of curvature and the radius of curvature of the head, r0The initial radius value is the tail curvature radius, and r (theta) is the curvature radius value of the changed volute structure. According to the formula, the radius of the rear half part of the volute structure is in direct proportion to the square of the angle, so that smooth transition from the middle point B to the end point C of the volute structure can be ensured, and damage to red blood cells and damage to blood can be avoided. The design of the rear half of the volute structure also allows the outlet location of the volute structure to be wider and larger than in a conventional circular structure, thereby avoiding crowding of blood at the outlet location and further creating high pressure.
Of course, in other embodiments, the first housing 101 and the second housing 102 may adopt a structure other than a volute, as long as it is satisfied that the second gap 6 is provided between the rotor assembly 3 and the housing assembly 1, and the second gap 6 may gradually increase toward the outlet of the housing assembly 1 along the flow path of the blood.
The spiral contour line is similar to a spiral line, and specifically refers to a curve formed by winding one fixed point (for example, the center point E, but may be any point other than the center point E) outward one by one.
The following describes the specific structure of the centrifugal blood pump according to the second embodiment:
referring to fig. 1, a difference between the second embodiment and the first embodiment is a structure of the second portion 303.
Specifically, with continuing reference to fig. 1, the structure of the first portion 301 in the second embodiment is the same as that of the first portion 301 in the first embodiment, and the second portion 303 is not provided with the second groove 3031, so that the mass balancing manner of the first embodiment is no longer adopted for the right uneven mass of the lower impeller (i.e., the second portion 303), but the relationship between the magnetic member 302 and the first portion 301 and the second portion 303 is adjusted. Specifically, the angle of the magnetic member 302 with respect to the second portion 303 can be changed by manually rotating the magnetic member 302. After the right unbalanced mass of the lower impeller reaches an expected value through a dynamic balancing machine test, the compensation of the left unbalanced mass of the upper impeller is realized through a mode that the balancing sheet is installed in the first groove 3011. Compared with the first embodiment, the adjusting part 5 of the centrifugal blood pump of the second embodiment omits a second groove 3031 added in the lower impeller, so that the thickness of the lower impeller is effectively reduced, and the balancing sheet in the upper impeller can also be directly made of metal materials, so that the processing is simple and convenient.
Of course, in other embodiments of the present invention, the adjustment manner between the magnetic member 302 and the first portion 301 and the second portion 303 may also not be limited to one set of adjusting members 5 in the embodiments of the present invention, which may be multiple sets of adjusting members 5, and the angle between the magnetic member 302 in each set of adjusting members 5 and the first portion 301 and the second portion 303 may be changed.
In the centrifugal blood pumps according to the first and second embodiments of the present invention, the shapes of the first and second grooves 3011 and 3031 in the adjustment member 5 may be any shapes other than circular, and the shape of the balancing piece may be changed according to the change in the shapes of the first and second grooves 3011 and 3031, provided that the balancing piece can be fitted in the first and second grooves 3011 and 3031.
Correspondingly, in the centrifugal blood pumps according to the first and second embodiments of the present invention, the arrangement manner between the first groove 3011 and the upper impeller and the arrangement manner between the second groove 3031 and the lower impeller are not limited to be uniform and need to be uniform, and the first groove 3011 and the upper impeller and the second groove 3031 and the lower impeller can be non-uniformly arranged according to different use requirements.
The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.
The above-mentioned embodiments only express several embodiments of the present invention, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention. Therefore, the protection scope of the present patent shall be subject to the appended claims.
Claims (12)
1. Centrifugal blood pump, its characterized in that: the supporting assembly is connected with the rotor assembly so that the rotor assembly can be rotatably arranged in the shell assembly through the supporting assembly; the rotor assembly comprises a first part and a second part connected with the first part, and a magnetic part is arranged between the first part and the second part; the centrifugal blood pump further comprises an adjuster for cooperating with the first and/or second portions to adjust the mass balance of the rotor assembly.
2. The centrifugal blood pump of claim 1, wherein: the first portion is provided with at least three first grooves and/or the second portion is provided with at least three second grooves for accommodating the adjusting piece.
3. The centrifugal blood pump of claim 2, wherein: the first grooves are uniformly distributed or non-uniformly distributed in the center of the first part; the second grooves are uniformly distributed or non-uniformly distributed in the center of the second part.
4. The centrifugal blood pump of claim 3, wherein: the first groove and/or the second groove are both circular grooves.
5. The centrifugal blood pump of claim 2, wherein: the second portion has a concave surface facing away from the first portion.
6. The centrifugal blood pump of claim 2, wherein: the adjusting piece is of a solid structure or a non-solid structure.
7. The centrifugal blood pump of claim 1, wherein: the support assembly includes a first bushing, a second bushing, and a shaft connected between the first bushing and the second bushing.
8. The centrifugal blood pump of claim 7, wherein: the proximal end of the shaft is in clearance fit with the first shaft sleeve, the distal end of the shaft is in clearance fit with the second shaft sleeve, and the clearance fit enables first clearances to be formed between the shaft and the first shaft sleeve and between the shaft and the second shaft sleeve respectively.
9. The centrifugal blood pump of claim 8, wherein: at least one external convex part is arranged on the outer side of the shaft along the axial direction.
10. The centrifugal blood pump of claim 9, wherein: the first part is provided with a first hole matched with the shaft, and the inner wall of the first hole is provided with at least one inner concave part matched with the outer convex part.
11. The centrifugal blood pump of claim 1, wherein: a second gap is between the rotor assembly and the housing assembly, the second gap progressively increasing along the flow path toward the outlet of the housing assembly.
12. The centrifugal blood pump of claim 11, wherein: the housing assembly has a partial radius of curvature that is quadratically proportional to a partial angle containing the radius of curvature.
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| CN202011346879.7A CN112704812A (en) | 2020-11-26 | 2020-11-26 | Centrifugal blood pump |
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| CN202011346879.7A CN112704812A (en) | 2020-11-26 | 2020-11-26 | Centrifugal blood pump |
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Effective date of registration: 20211201 Address after: Room 102, Zone C, No. 1601 Zhangdong Road, China (Shanghai) Free Trade Pilot Area, Pudong New Area, Shanghai, 201203 Applicant after: CARDIOPOWER MEDTECH (SHANGHAI) Co.,Ltd. Address before: 201203, 501, Newton Road, Zhangjiang hi tech park, Shanghai, Pudong New Area Applicant before: SHANGHAI MICROPORT MEDICAL (GROUP) Co.,Ltd. |