Blood pump with a flow straightener and ventricular assist device

Abstract

This invention provides a blood pump with a shroud and a ventricular assist device. The blood pump includes: a suction tube, a pump housing, a pump rotor, and a shroud. The distal end of the suction tube is located in the ventricle, and the proximal end of the suction tube is connected to the pump housing. The suction tube crosses the valve between the ventricle and the blood vessel. The pump housing is arranged in the blood vessel, and the distal end of the pump housing is connected to the proximal end of the suction tube. At least one window is opened at the proximal end of the pump housing for draining blood. The pump rotor is located in the pump housing and rotates around the axis of the pump housing to pump blood along the axis, allowing the blood to drain from the window of the pump housing. The shroud is arranged in the blood vessel, and the distal end of the shroud is fixed to the distal end of the window of the pump housing to cover the window of the pump housing. This reduces the speed and increases the pressure of the blood drained from the window of the pump housing, effectively reducing the flow loss caused by the mixing of high-speed flowing blood drained by the blood pump and low-speed flowing blood in the blood vessel, increasing the pressurization energy of the blood pump, and thus improving the overall hydraulic performance of the blood pump.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a blood pump with a rectifier and a ventricular assist device. Background Technology

[0002] Heart failure causes thousands of deaths worldwide each year because the heart cannot pump enough blood to maintain the body's normal metabolic processes. Common treatments for heart failure include medication, heart transplantation, and ventricular assist devices (VADs). For severe heart failure, medication has limited effectiveness, and most patients require heart transplantation or VADs. However, the availability of transplanted hearts is limited, making VADs the primary option for both patients and doctors.

[0003] A key component of a ventricular assist device is the blood pump. The blood inflow window is located in the left ventricle, and the blood outflow window is located in the aorta. The blood pump draws blood from the left ventricle into the aorta, assisting or even replacing the ventricle in pumping blood to maintain the blood supply needed for the normal metabolism of body tissues.

[0004] In existing technology, blood is directly discharged into the blood vessels through the blood outflow window of the blood pump. The high-speed blood discharged by the blood pump mixes with the low-speed blood flowing in the blood vessels, resulting in a large flow loss and a low efficiency of the dynamic and static pressure conversion of the blood, which in turn weakens the actual pressurization energy of the blood pump.

[0005] Reducing blood loss during flow and improving the pump's pressurization capacity are among the challenges faced by this type of product. Summary of the Invention

[0006] The purpose of this invention is to provide a blood pump with a rectifier and a ventricular assist device, which smoothly decelerates and pressurizes the high-speed flowing blood discharged by the blood pump, reduces blood flow loss, increases the pressurization energy of the blood pump, and improves the overall hydraulic performance of the blood pump.

[0007] To solve the above-mentioned technical problems, the present invention provides a blood pump with a shroud, comprising: a suction tube, a pump housing, a pump rotor, and a shroud, wherein,

[0008] The distal end of the suction tube is located in the ventricle, the proximal end of the suction tube is connected to the pump housing, and the suction tube crosses the valve between the ventricle and the blood vessel.

[0009] The pump housing is disposed in the blood vessel, the distal end of the pump housing is connected to the proximal end of the suction tube, and at least one window is opened at the proximal end of the pump housing for draining blood.

[0010] The pump rotor is located in the pump housing and rotates about the axis of the pump housing to pump blood along the direction of the axis, so that the blood is discharged from the window of the pump housing;

[0011] The shroud is arranged in the blood vessel, and the distal end of the shroud is fixed to the distal end of the pump housing window to cover the pump housing window, thereby slowing down and pressurizing the blood discharged from the pump housing window.

[0012] Optionally, the shroud includes an expansion section and a constriction section from the distal end to the proximal end; the distal end of the expansion section is located at the distal end of the pump housing window, and the expansion section is used to control the degree of blood diffusion; the constriction section constricts the shroud onto the catheter tubing, and the constriction section is used to constrict the shroud and drain the blood.

[0013] Optionally, a flow stabilizing section is provided between the expansion section and the contraction section, the flow stabilizing section being used to stabilize blood flow.

[0014] Optionally, the expansion line of the expansion segment can be a straight line or a curve.

[0015] Optionally, the convergence section consists of at least one traction member, one end of which is connected to the proximal end of the flow stabilization section, and the other end is fixed to the catheter tubing.

[0016] Optionally, the traction element is in the form of a filament or a trapezoidal fan shape.

[0017] Optionally, the converging section includes at least one outflow hole, and a flow guide fan is provided above the outflow hole. The flow guide fan is fixed on the converging section to adjust the flow direction of the blood flowing out of the outflow hole.

[0018] Optionally, the length of the expansion section is between 1mm and 30mm, the length of the stabilizing section is no more than 70mm, and the length of the converging section is no more than 30mm; the maximum cross-sectional area of ​​the expansion section, the stabilizing section, and the converging section are equal.

[0019] Optionally, the length of the fairing is between 1mm and 100mm, and the outer diameter of the fairing is no greater than 20mm.

[0020] Optionally, the fairing has a petal-shaped structure, with the gap between adjacent petals not exceeding 1 mm.

[0021] Optionally, the fairing comprises two opposing lobes.

[0022] Optionally, the fairing has a mesh structure; the expansion section has a dense mesh, and the flow stabilization section has a sparse mesh.

[0023] Optionally, the shroud is provided with streamlined corrugations to adjust the circumferential flow of blood to axial flow.

[0024] Optionally, the blood pump also includes a motor, which is disposed inside the shroud. The motor housing is provided with a fin structure to adjust the circumferential flow of blood to axial flow.

[0025] Accordingly, the present invention also provides a ventricular assist device, including a blood pump with a shroud as described above.

[0026] The blood pump with a rectifier and the ventricular assist device provided by the present invention have a rectifier installed on the blood pump. The rectifier is fixed to the far end of the pump housing window of the blood pump and covers the pump housing window. The rectifier can effectively adjust the direction of blood flow at the outlet by expanding the flow channel, so that the high-speed blood discharged by the blood pump is gradually decelerated and discharged into the blood vessel. The high-speed blood discharged by the blood pump is smoothly decelerated and pressurized, which can effectively reduce the flow loss caused by the mixing of the high-speed blood discharged by the blood pump and the low-speed blood in the blood vessel, improve the pressurization energy of the blood pump, and thus improve the overall hydraulic performance of the blood pump.

[0027] Furthermore, the convergence section consists of at least one traction member, one end of which is connected to the proximal end of the flow stabilization section, and the other end is fixed to the catheter tubing. The position and angle of the rectifier opening can be dynamically adjusted by the traction member, so that blood flows smoothly into the blood vessel to reduce mixing loss (mixing of blood at the blood pump outlet with the mainstream).

[0028] Furthermore, a flow guide fan is provided above the outflow hole. The flow guide fan is fixed on the converging section, which can effectively adjust the flow direction of the blood flowing out of the outflow hole, change the circumferential flow of the blood to axial flow, reduce flow mixing loss, improve the efficiency of blood conversion from dynamic pressure to static pressure, and thus improve the pumping capacity of the blood pump.

[0029] Furthermore, the shroud has a petal-shaped structure, which can effectively adjust the direction of blood at the outlet, changing the blood flow from circumferential to axial, reducing flow mixing losses, improving the efficiency of blood conversion from dynamic pressure to static pressure, and thus improving the pumping capacity of the blood pump.

[0030] Furthermore, the shroud has a mesh structure, which has better contractility, allowing it to adapt to the pumping volume of the blood pump and automatically adjust the form of the expansion line to improve the efficiency of blood flow control and enhance the overall performance of the blood pump.

[0031] Furthermore, the shroud is equipped with streamlined corrugations, which can adjust the circumferential flow of blood to axial flow, reduce flow mixing losses, and improve the efficiency of blood conversion from dynamic pressure to static pressure, thereby improving the pumping capacity of the blood pump.

[0032] Furthermore, the shroud also includes a blood pump, and the motor is disposed inside the shroud. The motor housing is provided with a fin structure, which can effectively control the rotation direction of the blood flow inside the shroud, gradually changing the blood flow direction from axial spiral flow to axial approximately straight flow, thereby improving the efficiency of blood conversion from dynamic pressure to static pressure and reducing flow mixing loss. Attached Figure Description

[0033] Those skilled in the art will understand that the accompanying drawings are provided to better understand the invention and do not constitute any limitation on the scope of the invention.

[0034] Figure 1 This is a schematic diagram of the positional relationship between the blood pump and the ventricle provided in an embodiment of the present invention.

[0035] Figure 2 This is a schematic diagram of a blood pump with a shroud provided in an embodiment of the present invention.

[0036] Figure 3 This is a schematic diagram of a blood pump with a shroud provided in an embodiment of the present invention.

[0037] Figure 4 This is a cross-sectional view of the fairing provided in an embodiment of the present invention.

[0038] Figure 5 This is a cross-sectional view of the fairing provided in an embodiment of the present invention.

[0039] Figure 6 This is a schematic diagram of the convergence segment provided in an embodiment of the present invention.

[0040] Figure 7 This is a schematic diagram of the convergence segment provided in an embodiment of the present invention.

[0041] Figure 8 This is a schematic diagram of a fairing with a flow guide fan provided in an embodiment of the present invention.

[0042] Figure 9 This is a cross-sectional view of a fairing with a traction component provided in an embodiment of the present invention.

[0043] Figure 10 This is a cross-sectional view of a fairing with a petal-shaped structure provided in an embodiment of the present invention.

[0044] Figure 11 This is a cross-sectional view of a mesh-structured fairing provided in an embodiment of the present invention.

[0045] Figure 12 This is a schematic diagram of the structure inside the fairing provided in an embodiment of the present invention.

[0046] Figure 13 This is a schematic diagram of the fish fin structure on the motor housing inside the rectifier according to an embodiment of the present invention.

[0047] Figure 14 These are the hydraulic performance curves of a blood pump with and without a fairing.

[0048] Reference numerals: 1-Blood pump; 2-Ventrifuge; 11-Suction tube; 12-Pump housing; 121-Pump housing window; 13-Straightener; 14-Catheter tubing; 131-Expansion section; 132-Flow stabilization section; 133-Contraction section; 134-Motor; 1321-Traction component; 1331-Outlet orifice; 1332-Flow guide fan. Detailed Implementation

[0049] To make the objectives, advantages, and features of this invention clearer, the invention will be further described in detail below with reference to the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to facilitate and clarify the explanation of the embodiments of this invention. Furthermore, the structures shown in the drawings are often part of the actual structures. In particular, different figures may emphasize different aspects and may sometimes use different scales.

[0050] As used in this invention, the singular forms “a,” “an,” and “the” include plural objects; the term “or” is generally used to mean “and / or”; the term “a number” is generally used to mean “at least one”; and the term “at least two” is generally used to mean “two or more”. Furthermore, the terms “first,” “second,” and “third” are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Thus, a feature defined as “first,” “second,” or “third” may explicitly or implicitly include one or at least two of that feature, unless otherwise expressly indicated.

[0051] The present invention provides an axial flow pump or a diagonal flow pump for a ventricular assist device, the pump having a rectifier. Figure 1 This is a schematic diagram illustrating the positional relationship between the blood pump and the ventricle according to an embodiment of the present invention. Figure 2 This is a schematic diagram of a blood pump with a shroud provided in an embodiment of the present invention. Figure 3 This is a schematic diagram of a blood pump with a shroud provided according to an embodiment of the present invention. Figures 1 to 3As shown, the present invention provides a blood pump 1 with a shroud. The blood pump 1 includes a suction tube 11, a pump housing 12, a pump rotor (not shown) and a shroud 13. The distal end of the suction tube 11 is located in the ventricle 2, and the proximal end of the suction tube 11 is connected to the pump housing 12. The suction tube 11 crosses the valve between the ventricle 2 and the blood vessel.

[0052] The pump housing 12 is disposed in the blood vessel, the distal end of the pump housing 12 is connected to the proximal end of the suction tube 11, and at least one window is opened at the proximal end of the pump housing 12 for draining blood.

[0053] The pump rotor is located in the pump housing 12, and the pump rotor rotates about the axis of the pump housing 12 to pump blood along the direction of the axis, so that the blood is discharged from the pump housing window 121;

[0054] The shroud 13 is arranged in the blood vessel, and the distal end of the shroud 13 is fixed to the distal end of the pump housing window 121 to cover the pump housing window 121, thereby slowing down and increasing the pressure of the blood discharged from the pump housing window 121.

[0055] The rectifier 13 can effectively adjust the direction of blood flow at the outlet of the blood pump 1, gradually slowing down the high-speed blood discharged from the blood pump 1 before it is discharged into the blood vessel. The high-speed blood discharged from the blood pump 1 is smoothly decelerated and pressurized, which can effectively reduce the flow loss caused by the mixing of the high-speed blood discharged from the blood pump 1 and the low-speed blood in the blood vessel, improve the pressurization energy of the blood pump 1, and thus improve the overall hydraulic performance of the blood pump 1.

[0056] Please continue to refer to this. Figure 3 As shown, the shroud 13 includes an expansion section 131 and a converging section 133 from its distal end to its proximal end. The distal end of the expansion section 131 is located at the distal end of the pump housing window 121, meaning the starting position of the expansion section 131 is at the distal end of the pump housing window 121, so that the expansion section 131 completely covers the pump housing window 121. This ensures that all blood discharged from the pump housing window 121 passes through the expansion section 131. The expansion section 131 can effectively control the degree of blood diffusion, slow down the blood flow, reduce flow loss, and effectively improve the pumping capacity of the blood pump 1.

[0057] The retracting section 133 retracts the rectifier 13 onto the catheter tubing 14, and the retracting section 133 is used to retract the rectifier 13 and drain blood. The catheter tubing 14 is used to supply power to the blood pump 1.

[0058] In one embodiment of the present invention, please refer to Figure 4 As shown, the fairing 13 may consist only of the expansion section 131 and the contraction section 133. In another embodiment of the invention, please refer to... Figure 5 As shown, the shroud 13 also includes a flow stabilizing section 132, which is located between the expanding section 131 and the converging section 133. The main function of the flow stabilizing section 132 is to stabilize blood flow and improve the efficiency of converting dynamic blood pressure into static pressure.

[0059] Key parameters of the expansion segment 131 include the expansion line, expansion angle, and maximum diameter. Please refer to [link / reference needed]. Figure 5 As shown, preferably, the expansion line of the expansion section 131 can be a straight line or a curve. When the expansion line is a straight line, the expansion angle α is the angle between the expansion line and the axis of the pump housing 121, and the expansion angle α is not greater than 60 degrees. When the expansion line is a curve, the expansion angle α is the angle between the tangent at any point on the curve and the axis of the pump housing 121, and the expansion angle α can first increase and then decrease, and the expansion angle α is not greater than 60 degrees.

[0060] The converging section 133 includes at least one outflow hole 1331. Blood flows out from the pump housing window 121, passes through the expansion section 131 and the flow stabilizing section 132, where the high-speed blood gradually decelerates and increases in pressure, finally flowing out from the outflow hole 1331 of the converging section 133. The outflow hole 1331 can be in the shape known to those skilled in the art, such as circular, elliptical, or trapezoidal, and multiple outflow holes 1331 can be evenly distributed on the converging section 133.

[0061] Please refer to Figure 9 As shown, the convergence section 133 consists of at least one traction member, and the flow stabilization section 132 is constrained by at least one traction member 1321. One end of the traction member 1321 is connected to the proximal end of the flow stabilization section 132, and the other end is fixed to the catheter tubing 14 to constrain the position of the flow stabilization section 132. The position and angle of the opening of the flow rectifier 13 can be dynamically adjusted by the traction member 1321, thereby allowing blood to flow smoothly into the blood vessel and reducing mixing losses. The traction member 1321 can be filamentous, such as... Figure 9 As shown. The traction component 1321 can also be a trapezoidal fan-shaped surface with a certain area, such as... Figure 8 As shown. For preferred options, please refer to... Figure 6 and Figure 7 As shown, the flow stabilizing section 132 can be gathered onto the conduit hose 14 by a ladder-shaped connecting rod, that is, the gathering section 133 can be composed of multiple ladder-shaped connecting rods. However, it is not limited to this.

[0062] Please refer to Figure 8As shown, a flow guide fan 1332 is provided above the outflow orifice 1331. The flow guide fan 1332 is fixed on the converging section 133. The flow guide fan 1332 can effectively adjust the flow direction of the blood flowing out of the outflow orifice 1331, changing the circumferential flow of the blood to axial flow and reducing flow mixing losses. Here, mixing refers to the blood at the blood pump outlet mixing with the mainstream at a relatively high circumferential velocity, and mixing loss refers to the flow loss caused by mixing.

[0063] The length of the expansion section 131 is between 1 mm and 30 mm, the length of the flow stabilizing section 132 is no greater than 70 mm, and the length of the convergence section 133 is no greater than 30 mm. Here, length refers to axial length. The maximum cross-sectional area of ​​the expansion section 131, the flow stabilizing section 132, and the convergence section 133 is equal. The length of the fairing is between 1 mm and 100 mm, and the outer diameter of the fairing is no greater than 20 mm.

[0064] Please refer to Figure 10 As shown, the shroud 13 has a petal-like structure, with the gap between adjacent petals not exceeding 1 mm. This structure can effectively adjust the direction of blood at the blood pump outlet, changing the blood flow from circumferential to axial, improving the efficiency of converting blood pressure from dynamic to static pressure, thereby enhancing the pumping capacity of the blood pump. The shroud can have multiple petals. Preferably, the shroud includes two oppositely arranged petals, which are symmetrically arranged.

[0065] Please refer to Figure 11 As shown, the shroud 13 has a mesh structure. This mesh structure provides better contractility, allowing it to adapt to the pumping volume and automatically adjust the form of the expansion lines, thereby improving the efficiency of blood flow control and enhancing the overall performance of the pump. Preferably, the expansion section 131 has a dense mesh, while the flow stabilization section 132 has a sparse mesh.

[0066] It is understood that the terms "dense mesh" and "sparse mesh" used in the text are relative. The dense mesh has a denser mesh size than the sparse mesh, and the sparse mesh has a sparser mesh size than the dense mesh.

[0067] Please refer to Figure 12 As shown, the shroud 13 has streamlined corrugations inside to adjust the circumferential flow of blood to axial flow and reduce flow loss.

[0068] Please continue to refer to this. Figure 3 As shown, the blood pump also includes a motor 134, which is disposed within the fairing 13. Preferably, please refer to... Figure 13As shown, the motor housing of the motor is provided with a fin structure, which can effectively control the rotation direction of the blood flow in the rectifier 13, gradually changing the blood flow direction from axial spiral flow to axial approximately straight flow, thereby improving the efficiency of blood conversion from dynamic pressure to static pressure and reducing flow loss.

[0069] It should be noted that the reference Figure 2 As shown, in one embodiment of the present invention, the fairing may consist only of the expansion section. (See reference...) Figure 10 As shown, in one embodiment of the present invention, the fairing may include an expansion section and a flow stabilization section, but does not include a convergence section.

[0070] Figure 14 These are the hydraulic performance curves of a blood pump with and without a fairing, derived from... Figure 14 It can be seen that, compared with a blood pump without a rectifier, a blood pump with a rectifier can increase the pressurization capacity by about 1.5 times at the same flow rate.

[0071] Accordingly, the present invention also provides a ventricular assist device, including a blood pump with a shroud as described above.

[0072] In summary, the blood pump with a rectifier and the ventricular assist device provided by the present invention have a rectifier installed on the blood pump. The rectifier is fixed to the far end of the pump housing window and covers the pump housing window. By expanding the flow channel, the rectifier can effectively adjust the direction of blood flow at the outlet, gradually decelerating the high-speed blood discharged by the blood pump before it is discharged into the blood vessel. The high-speed blood discharged by the blood pump is smoothly decelerated and pressurized, which can effectively reduce the flow loss caused by the mixing of the high-speed blood discharged by the blood pump and the low-speed blood in the blood vessel, improve the pressurization energy of the blood pump, and thus improve the overall hydraulic performance of the blood pump.

[0073] Furthermore, the convergence section consists of at least one traction member, one end of which is connected to the proximal end of the flow stabilization section, and the other end is fixed to the catheter tubing. The position and angle of the rectifier opening can be dynamically adjusted by the traction member, so that blood flows smoothly into the blood vessel to reduce mixing loss (mixing of blood at the blood pump outlet with the mainstream).

[0074] Furthermore, a flow guide fan is provided above the outflow hole. The flow guide fan is fixed on the converging section, which can effectively adjust the flow direction of the blood flowing out of the outflow hole, change the circumferential flow of the blood to axial flow, reduce flow mixing loss, improve the efficiency of blood conversion from dynamic pressure to static pressure, and thus improve the pumping capacity of the blood pump.

[0075] Furthermore, the shroud has a petal-shaped structure, which can effectively adjust the direction of blood at the outlet, changing the blood flow from circumferential to axial, reducing flow mixing losses, improving the efficiency of blood conversion from dynamic pressure to static pressure, and thus improving the pumping capacity of the blood pump.

[0076] Furthermore, the shroud has a mesh structure, which has better contractility, allowing it to adapt to the pumping volume of the blood pump and automatically adjust the form of the expansion line to improve the efficiency of blood flow control and enhance the overall performance of the blood pump.

[0077] Furthermore, the shroud is equipped with streamlined corrugations, which can adjust the circumferential flow of blood to axial flow, reduce flow mixing losses, and improve the efficiency of blood conversion from dynamic pressure to static pressure, thereby improving the pumping capacity of the blood pump.

[0078] Furthermore, the shroud also includes a blood pump, and the motor is disposed inside the shroud. The motor housing is provided with a fin structure, which can effectively control the rotation direction of the blood flow inside the shroud, gradually changing the blood flow direction from axial spiral flow to axial approximately straight flow, thereby improving the efficiency of blood conversion from dynamic pressure to static pressure and reducing flow mixing loss.

[0079] The above description is merely a description of preferred embodiments of the present invention and is not intended to limit the scope of the present invention in any way. Any changes or modifications made by those skilled in the art based on the above disclosure shall fall within the protection scope of the claims.

Claims

1. A blood pump with a flow straightener, characterized in that The blood pump comprises: a suction tube, a pump housing, a pump rotor, and a fairing, wherein, a distal end of the suction tube is located in a ventricle, a proximal end of the suction tube is connected to the pump housing, and the suction tube crosses a valve between the ventricle and a blood vessel; the pump housing is arranged in the blood vessel, a distal end of the pump housing is connected to the proximal end of the suction tube, and a proximal end of the pump housing is provided with at least one window for discharging blood; the pump rotor is located in the pump housing, and rotates around an axis of the pump housing to pump blood in the direction of the axis, so that the blood is discharged from the pump housing window; the fairing is arranged in the blood vessel, a distal end of the fairing is fixed to a distal end of the pump housing window to cover the pump housing window, so that the blood discharged from the pump housing window is decelerated and pressurized; the fairing comprises, from the distal end to the proximal end, a dilatation section and a convergence section in sequence; the distal end of the dilatation section is located at the distal end of the pump housing window, and the dilatation section is used for controlling the diffusion degree of the blood; the convergence section converges the fairing on a catheter tube, and is used for converging the fairing and discharging the blood; a flow stabilizing section is further arranged between the dilatation section and the convergence section, and is used for stabilizing the blood flow; the fairing has a mesh structure; the dilatation section has a dense mesh, and the flow stabilizing section has a sparse mesh.

2. The caged blood pump of claim 1, wherein, The dilatation line of the dilatation section is a straight line or a curve.

3. The caged blood pump of claim 2, wherein, The convergence section is composed of at least one traction member, one end of the traction member is connected to a proximal end of the flow stabilizing section, and the other end of the traction member is fixed to the catheter tube.

4. The caged blood pump of claim 3, wherein, The traction member has a filament shape or a ladder-shaped fan shape.

5. The caged blood pump of claim 2, wherein, The convergence section comprises at least one outflow hole, and a flow guide fan is arranged above the outflow hole and is fixed to the convergence section, so as to adjust the flow direction of the blood flowing out of the outflow hole.

6. The caged blood pump of claim 1, wherein, The length of the dilatation section is between 1 mm and 30 mm, the length of the flow stabilizing section is not greater than 70 mm, and the length of the convergence section is not greater than 30 mm; the maximum cross-sectional areas of the dilatation section, the flow stabilizing section, and the convergence section are equal.

7. The caged blood pump of claim 1, wherein, The length of the fairing is between 1 mm and 100 mm, and the outer diameter of the fairing is not greater than 20 mm.

8. The caged blood pump of claim 1, wherein, A flow line-shaped corrugation is arranged inside the fairing, so as to adjust the circumferential flow of the blood to axial flow.

9. The caged blood pump of claim 1, wherein, A motor is arranged in the fairing, and a fish fin structure is arranged on a motor housing of the motor, so as to adjust the circumferential flow of the blood to axial flow.

10. A ventricular assist device, characterized by The blood pump with the fairing comprises any one of claims 1-9.

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