Shunting structure and modularized aorta inner entrainment pump

Abstract

The invention discloses a shunting structure and a modularized in-aorta entrainment pump, the shunting structure is located at an outflow window of the modularized in-aorta entrainment pump, the far end is provided with a blood pump rotor, and the shunting structure comprises an oblique flow hub and a shunting part; the diameter of the oblique flow hub is gradually increased from the far end to the near end, and the diameter of the far end of the oblique flow hub is equal to that of the near-end hub of the blood pump rotor; the flow dividing piece covers the side face of the oblique flow hub and comprises a first incident flow face, a second incident flow face and a back flow face, the first incident flow face is distributed at the position of an outflow window adjacent to the butt joint contact face of the blood pump, the second incident flow face is fixedly connected with a casing shell, and the flow dividing piece and the outer surface of the casing are equal in diameter and jointly form the butt joint contact face of the blood pump. The shunting structure is combined with the blood pump rotor, so that blood can be axially sucked in, shunted by the shunting part, bypassed by a narrow area in a butt joint contact surface and obliquely pumped out, a flowing stagnation area is prevented from being formed, the speed gradient is reduced, the mutual influence between parts is reduced, the blood pumping efficiency is improved, and the blood compatibility is improved.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical ventricular assist devices, and in particular relates to a shunt structure and a modular intra-aortic entrainment pump. Background Art

[0002] With the widespread development of interventional treatment for complex and high-risk cardiovascular diseases, percutaneous ventricular assist devices have been given more attention in the interventional treatment of cardiovascular diseases. They are mainly used to treat cardiogenic shock and provide protection during high-risk PCI procedures, improve patients' cardiac output and coronary artery perfusion, and reduce myocardial oxygen consumption.

[0003] At present, the percutaneous mechanical circulatory assist device used in clinical practice is mainly a micro-axial flow blood pump, which is based on the Archimedean principle and uses a micro-motor to drive the blood pump rotor to rotate at high speed, perform work on the blood, and pump blood from the left ventricle through the aortic valve to the ascending aorta through the inlet cannula, providing active forward blood flow, effectively reducing the left ventricular load, reducing myocardial oxygen consumption, and increasing cardiac output, coronary artery flow, and blood perfusion of end organs. However, the high shear stress generated by the high-speed rotation of the blood pump rotor (30,000-50,000 rpm) causes greater damage to the blood and is prone to cause damage to the aortic valve, which is the main reason limiting its long-term use.

[0004] The modular intra-aortic circulation assist device is a new percutaneous mechanical circulatory assist device. Its principle is that multiple axial blood pumps are delivered to the aorta through a delivery cannula, and multiple pumps are assembled in parallel on a specially designed anchor support at a designated location to provide hemodynamic support. The blood accelerated by the blood pump transfers energy to the naturally flowing blood, thereby accelerating the blood in the aorta to flow to peripheral organs such as the kidneys, and forming a certain cross-pump pressure gradient, which reduces the afterload of the heart while increasing the blood perfusion of peripheral organs such as the kidneys. The advantage of this device is that the blood pump can achieve a larger cumulative flow at a lower speed, causing less damage to the blood and no damage to the aortic valve.

[0005] The anchoring support and multiple axial flow blood pumps of the modular intra-aortic circulation assist device are fitted together through the docking surface, and the blood pumps are close to each other. The blood flowing out from the blood pump outlet at an accelerated speed will be affected by the adjacent blood pumps and the anchoring support, and areas with excessive velocity gradients and flow stagnation areas are prone to appear, which increases the shear stress in the area and increases the risk of blood damage. In addition, since there is no valve restriction, the blood accelerated by the blood pump is prone to backflow, making the blood flow in the coupling area between the components more complicated, and this phenomenon will become more obvious when the blood pump rotor speed increases.

[0006] In view of this, it is necessary to design a reasonable axial flow blood pump flow structure to meet the flow output while avoiding the influence of adjacent components on the blood pump outlet flow field and reducing blood damage. Summary of the invention

[0007] The purpose of the present invention is to provide a shunt structure and a modular intra-aortic entrainment pump to improve the flow field at the outlet of the modular intra-aortic circulation auxiliary pump, reduce the velocity gradient to avoid the formation of a flow stagnation zone, so that the blood accelerated by the axial flow pump can enter the aorta efficiently, reduce blood damage, and provide good hemodynamic support.

[0008] To achieve the above object, the present invention adopts the following technical solution:

[0009] A flow splitting structure includes an oblique flow hub and a flow splitting member.

[0010] The radius r(l) of the diagonal flow hub increases gradually from the distal end to the proximal end along the elliptical line and the circular arc line, and a through hole is provided at the hub axis;

[0011] The diverter is coated on the side of the oblique flow hub, and comprises a first frontal surface, a second frontal surface and a rear surface. The two frontal surfaces are distributed in a herringbone shape. The first frontal surface is distributed at the outflow window of the blood pump, and the second frontal surface is fixedly connected to the casing shell. The outer edge of the diverter has the same diameter as the outer surface of the casing, and together they constitute the docking contact surface of the blood pump.

[0012] r(l) is the quantitative relationship between the radius r of the diagonal flow hub and its axial length l from the far end of the hub.

[0013] Furthermore, the ratio of the axial length of the elliptical gradient section to the circular arc gradient section of the diagonal flow hub is 15:1, and the ratio of the radial length of the circular arc gradient section to the proximal radius of the diagonal flow hub is 1:8; the elliptical gradient section and the circular arc gradient section of the diagonal flow hub are tangent, and the angle between the tangent at the tangent position and the axis is 30°, and the angle between the tangent at the proximal end of the circular arc gradient and the axis is 60°.

[0014] Furthermore, the ratio of the axial length of the diagonal flow hub to the axial length of the diverter is in the range of 1.5 to 2; the axial length of the first oncoming surface of the diverter is greater than the axial length of the second oncoming surface: 1 -l 0 >l 2 -l 0 .

[0015] Among them, l 0 is the distance between the inlet of the frontal surface and the far end of the diagonal flow hub, l 1 is the distance between the outlet of the first oncoming surface and the far end of the diagonal flow hub, l 2 The distance between the outlet position of the second flow surface and the far end of the inclined flow hub.

[0016] Furthermore, the top inlet angle of the first oncoming surface of the flow splitter is equal to the inlet angle of the second oncoming surface, and the calculation formula is as follows:

[0017]

[0018] Among them, β 0 is the top inlet angle of the first and second oncoming surfaces, r 1 is the hub radius of the leading edge of the blood pump rotor blade, r 2 is the hub radius of the blood pump rotor blade trailing edge, r 3 is the radius of the blood pump rotor blade tip, β 1 is the average inlet angle of the axial flow blade, β 2 is the average outlet angle of the axial flow blade.

[0019] Furthermore, the top placement angle of the first flow-facing surface of the diverter gradually increases, and the range of variation is β 0 ~β 3 , β 3 The preferred range is 80-90°, and the continuous change mode is β 1 (l) is a linear function; the placement angle of the top of the second flow-facing surface of the diverter gradually decreases, and the range of change is β 0 ~β 4 , β 4 The preferred range is 0~15°, and the continuous change mode is β 2 (l) is a linear function.

[0020] Among them, β 3 is the top outlet angle of the first flow surface, β 4 is the top outlet angle of the second flow surface, β 1 (l) is the quantitative relationship between the top placement angle of the first flow surface and the axial length, β 2 (l) is the quantitative relationship between the top placement angle of the second flow surface and the axial length.

[0021] Furthermore, the top wrap angle θ of the first flow-facing surface of the flow splitter is 11 (l) and the wrap angle θ of the top of the second oncoming surface 21 (l) satisfies the following formula:

[0022]

[0023] Among them, θ 11 (l) is the quantitative relationship between the top wrap angle of the first flow surface and the axial length, θ 21 (l) is the quantitative relationship between the top wrap angle of the second flow-facing surface and the axial length, and R is the outer edge radius of the diverter.

[0024] Furthermore, the wrap angle of the outlet position at the top of the second oncoming surface and the wrap angle of the outlet position at the top of the first oncoming surface meet the following conditions:

[0025]

[0026] Among them, θ 11 (l 1 ) is the wrap angle value at the top outlet position of the first flow surface, θ 21 (l 2 ) is the wrap angle value at the top outlet position of the second flow surface, and n is the number of axial flow pumps.

[0027] Furthermore, the bottom wrap angle and the top wrap angle of the first flow-facing surface of the flow splitter satisfy the following calculation formula:

[0028]

[0029] Among them, θ 12 (l) is the quantitative relationship between the bottom wrap angle of the first oncoming surface and the axial length, α is the angle between the bottom of the first oncoming surface and the tangent of the hub circumference; the angle α between the first oncoming surface of the diverter and the tangent of the hub circumference ranges from 45° to 60°.

[0030] Furthermore, the bottom wrap angle θ of the second flow-facing surface of the flow splitter is 22 (l) and the top wrap angle θ 21 The difference between (l) decreases linearly with the increase of axial length, satisfying the following formula:

[0031]

[0032] θ 22 (l) is the quantitative relationship between the top wrap angle of the second flow surface and the axial length, θ 12 (l 0 ) is the bottom inlet wrap angle of the first flow surface, θ 11 (l 0 ) is the value of the inlet wrap angle at the top of the first flow surface.

[0033] Furthermore, the first frontal surface and the second frontal surface of the diverter are connected and transitioned by a standard fillet, and the fillet size ranges from 0.4 to 0.5 mm; the height range of the inlet position of the diverter is 1 to 1.5 mm, and the height range of the outlet position of the second frontal surface is 0.7 to 1 mm; the back flow surface of the diverter coincides with the axis of the oblique flow hub, and is connected to the hub surface by a fillet transition, and the fillet range is 0.1 to 0.2 mm.

[0034] A modular intra-aortic entrainment pump comprises a shunt structure of any of the above technical solutions, wherein the shunt structure is located at the outflow window of the modular intra-aortic entrainment pump, a blood pump rotor is arranged at the distal end, and the distal diameter of the oblique flow hub is equal to the proximal hub diameter of the blood pump rotor; the through hole is used for the installation of the motor shaft and the blood pump rotor.

[0035] The beneficial effects of the present invention are as follows: the diversion structure provided by the present invention is composed of an oblique flow hub and a diversion piece, and is located at the outflow window of the modular intra-aortic entrainment pump. The first oncoming surface and the second oncoming surface of the diversion piece can bend and guide the liquid flow flowing toward the docking contact surface to the adjacent outflow window; combined with the blood pump rotor, axial suction of blood can be achieved, and the blood can be diverted through the diversion piece to bypass the narrow area inside the docking contact surface and be pumped out obliquely to avoid the formation of a flow stagnation zone, reduce the velocity gradient, improve the blood pumping efficiency, and improve blood compatibility. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] Figure 1 It is a flow schematic diagram of the flow diversion structure of the present invention unfolded along the flow surface.

[0037] Figure 2 It is a schematic longitudinal section diagram of the diagonal flow hub of the present invention.

[0038] Figure 3 It is the rectangular coordinate system of the diagonal flow hub of the present invention.

[0039] Figure 4A Schematic diagram of the placement angle of the impeller and the diversion structure according to an embodiment of the present invention.

[0040] Figure 4B Schematic diagram of the wrap angle of the frontal surface of the flow splitting structure according to an embodiment of the present invention.

[0041] Figure 4C Schematic diagram of the top and bottom of the flow-impacting surface of an embodiment of the present invention.

[0042] Figure 4D FIG. 4 is a schematic diagram showing an angle α according to an embodiment of the present invention.

[0043] Figure 5 A schematic diagram of a flow diversion structure from one viewing angle of an embodiment of the present invention.

[0044] Figure 6 A schematic diagram of the flow diversion structure from another perspective of an embodiment of the present invention.

[0045] Figure 7 Schematic diagram of the structure of a modular intra-aortic entrainment pump according to an embodiment of the present invention.

[0046] Figure 8 This is a schematic diagram of a modular intra-aortic entrainment pump assembled in parallel according to an embodiment of the present invention.

[0047] In the picture

[0048] 1 micro axial flow pump; 2 anchor support; 3 descending aorta;

[0049] 11 flow splitting structure; 12 blood pump rotor; 13 casing; 14 motor; 15 control line; 111 diagonal flow hub; 112 first oncoming surface; 113 second oncoming surface; 114 backflow surface; 115 mounting hole; 131 connecting support rod; 132 connecting arc member; DETAILED DESCRIPTION

[0050] The following, combined Figures 1 to 8 The present invention is described in detail in the following examples. The present invention provides a shunt structure and a modular intra-aortic entrainment pump. The shunt structure 11 includes an oblique flow hub 111 and a shunt member 110, which are installed at the outflow window of the modular intra-aortic entrainment pump, and a blood pump rotor is arranged at the distal end. Figure 1 This is a flow diagram of the shunt structure of the present invention unfolded along the flow surface. The shunt structure diverts and drains the high-speed, swirling blood formed by the work of the axial blood pump rotor into two paths, bypassing the docking contact surface, thereby preventing the blood from directly entering the narrow area of ​​the docking contact surface or directly impacting the docking contact surface.

[0051] Figure 2 It is a schematic diagram of the longitudinal section of the oblique flow hub of the present invention. From the distal end to the proximal end, the radius of the oblique flow hub gradually increases along the elliptical line and then along the circular arc line. The elliptical gradient section and the circular arc gradient section are tangent to each other. The angle between the tangent at the tangent position and the axis is 30°, and the angle between the tangent at the proximal end of the circular arc gradient and the axis is 60°. The ratio of the axial length of the elliptical gradient section to the circular arc gradient section is 15:1, and the ratio of the radial length of the circular arc gradient section to the proximal end radius of the oblique flow hub is 1:8. In the embodiment of the present invention, the overall outer diameter of the axial flow pump is 4.8mm, the outer diameter of the diverter is 4.8mm, the distal diameter of the oblique flow hub is 2.2mm, the length of the oblique flow hub is 4.8mm, the axial length of the elliptical transition section is 4.5mm, and the axial length and radial length of the circular arc transition section are both 0.3mm.

[0052] In order to elaborate the design scheme of the diagonal flow hub with split flow structure, the following Figure 3 In the rectangular coordinate system shown, the abscissa represents the axial length 1 from the far end of the hub, and the ordinate represents the hub radius r.

[0053] According to the above coordinate system, the quantitative relationship r(l) between the radius r of the diagonal flow hub and its axial length l from the far end of the hub is established.

[0054] The radius of the hub of the elliptical transition section satisfies the following equation:

[0055]

[0056] The radius of the hub in the arc transition section satisfies the following equation:

[0057] (l-4.09) 2 +(r-2.81) 2 =0.822 4.5≤l≤4.8

[0058] Furthermore, the ratio of the axial length of the diagonal flow hub and the diverter is in the range of 1.5 to 2. In the embodiment of the present invention, the axial length ratio of the diagonal flow hub 111 to the diverter 110 is 1.5. A through hole 115 is provided at the axis of the diagonal flow hub 111 for mounting the motor shaft and the blood pump rotor. The diverter 110 is coated on the side of the diagonal flow hub and includes a first oncoming surface 112, a second oncoming surface 113 and a back-flow surface 114. The two oncoming surfaces are distributed in a herringbone shape. The first oncoming surface is distributed at the outflow window adjacent to the blood pump docking contact surface. The second oncoming surface is fixedly connected to the casing housing. The outer edge of the diverter and the outer surface of the casing have the same diameter, and together constitute the docking contact surface of the blood pump. The axial length of the first oncoming surface is greater than the axial length of the second oncoming surface: l 1 -l 0 >l 2 -l 0 Among them, l 0 is the distance between the inlet of the frontal surface and the far end of the diagonal flow hub, l 1 is the distance between the outlet of the first oncoming surface and the far end of the diagonal flow hub, l 2 The distance between the outlet position of the second oncoming surface and the far end of the diagonal flow hub; In this embodiment, the distance between the inlet position of the oncoming surface and the far end of the diagonal flow hub is l 0 =1.6mm, the distance between the outlet of the first frontal surface and the far end of the diagonal flow hub is l 1 =4.8mm, and the distance between the outlet of the second oncoming surface and the far end of the diagonal flow hub is l 2 =3.5mm.

[0059] See also Figures 4A to 4D In the flow diversion structure provided by the present invention, the placement angle β refers to the angle between the tangent at a certain point on the oncoming surface and the circumferential direction there, and the definitions of the inlet angle and the outlet angle are consistent with the placement angle β; the wrap angle θ refers to the distribution angle of the oncoming surface along the circumferential direction on the projection diagram of the cross section; the top of the oncoming surface refers to the intersection line of the oncoming surface and the outer edge of the diverter, and the bottom of the oncoming surface refers to the intersection line of the oncoming surface and the hub; the angle α refers to the angle between the bottom of the first oncoming surface and the tangent of the hub circumference on the projection diagram of the cross section, and the placement angle β, the wrap angle θ and the angle α are all in degrees.

[0060] In the embodiment of the present invention, the leading edge hub radius r of the blood pump rotor blade is 1 The radius of the rear hub of the blood pump rotor is 0.58 mm. 2 is 1.1 mm, and the radius of the blood pump rotor blade tip is r 3 is 2mm, the average blade inlet angle β 1 is 35°, the average outlet angle β 2is 58.5°, and the inlet angle β of the first and second flow-facing surfaces of the splitter is calculated according to the formula 0 Equal to 58°.

[0061]

[0062] In the embodiment of the present invention, the axial length of the first flow-facing surface 112 of the flow splitter is in the range of (1.6, 4.8), and the top outlet angle β 3 =85°, that is, the top placement angle range is 58°~85°, and the continuous change method satisfies the following formula:

[0063] β 1 (l)=8.47×l+44.45l∈(1.6, 4.8)

[0064] β 1 (l) is the quantitative relationship between the top placement angle of the first flow surface and the axial length.

[0065] In the embodiment of the present invention, the top wrap angle θ of the first frontal surface 112 is 11 (l) The range is 0° to -26°, and the continuous change mode satisfies the following formula:

[0066]

[0067] θ 11 (l) is the quantitative relationship between the top wrap angle of the first flow surface and the axial length.

[0068] In the embodiment of the present invention, the tangential angle between the bottom of the first oncoming surface 112 and the circumference of the hub is α=45°, and the change mode of the bottom wrap angle of the first oncoming surface θ1 2 (l) Determined according to the following formula:

[0069]

[0070] θ 12 (l) is the quantitative relationship between the bottom wrap angle of the first flow surface and the axial length.

[0071] In the embodiment of the present invention, the axial length of the second flow-facing surface 113 is in the interval (1.6, 3.5), and the top outlet angle β 4 =10°, that is, the top placement angle range is 58°~10°, and the continuous change mode satisfies the following formula:

[0072] β 2 (l)=--25.474×l+98.758l∈(1.6, 3.5)

[0073] β 2 (l) is the quantitative relationship between the top placement angle of the second flow surface and the axial length.

[0074] In the embodiment of the present invention, the wrap angle of the top of the second flow-facing surface 113 ranges from -5° to -90°, and the continuous change mode satisfies the following formula:

[0075]

[0076] θ 21 (l) is the quantitative relationship between the top wrap angle of the second flow surface and the axial length.

[0077] In the embodiment of the present invention, the bottom wrap angle of the second frontal surface 113 ranges from 18° to -90°, and the continuous change mode satisfies the following formula:

[0078]

[0079] θ 22 (l) is the quantitative relationship between the bottom wrap angle of the second flow surface and the axial length.

[0080] Furthermore, the first oncoming surface and the second oncoming surface of the diverter are connected and transitioned by a standard fillet, and the fillet size ranges from 0.4 to 0.5 mm. The height of the inlet position of the diverter is in the range of 1 to 1.5 mm, and the height of the outlet position of the second oncoming surface is 0.7 to 1 mm. The back surface of the diverter coincides with the axis of the oblique flow hub, and is connected to the hub surface by a fillet transition, and the fillet range is 0.1 to 0.2 mm.

[0081] See also Figure 7 , Figure 8 The modular intra-aortic entrainment pump of the embodiment of the present invention comprises a shunt structure 11, a blood pump rotor 12 (not shown in the figure), a casing 13, a motor 14, and a control line 15, wherein the shunt structure 11 is located at the outflow window of the pump, and the casing has two connecting support rods 131 and a connecting arc member 132, the connecting support rods 131 are fixedly connected to the oblique flow hub of the shunt structure, and the connecting arc member 132 is fixedly connected to the second oncoming surface of the shunt structure; Figure 8 , within the descending aorta 3, three pumps 1 are assembled with an anchor support 2 to form a modular assembly to jointly provide hemodynamic support.

[0082] The shunt structure and modular intra-aortic entrainment pump of the embodiments of the present invention divide the swirling blood generated by the blood pump rotor into two paths for drainage, bypassing the docking contact surface and the anchoring support, preventing blood from directly entering the narrow area of ​​the docking contact surface or directly hitting the docking contact surface, and having good blood compatibility.

Claims

1. A diversion structure, characterized in that: Including diagonal flow hub and splitter, The radius r(l) of the diagonal flow hub increases gradually from the distal end to the proximal end along the elliptical line and the circular arc line, and a through hole is provided at the hub axis; The flow divider is coated on the side of the oblique flow hub, and includes a first flow-facing surface, a second flow-facing surface and a back flow surface. The two flow-facing surfaces are distributed in a herringbone shape. The first flow-facing surface is distributed at the outflow window of the blood pump, and the second flow-facing surface is fixedly connected to the casing shell. The outer edge of the flow divider and the outer surface of the casing have the same diameter, and together constitute a docking contact surface of the blood pump; r(l) is the quantitative relationship between the radius r of the diagonal flow hub and its axial length l from the far end of the hub.

2. The flow diversion structure according to claim 1, characterized in that: The ratio of the axial length of the elliptical gradient section and the circular gradient section of the diagonal flow hub is 15:1, and the ratio of the radial length of the circular gradient section to the proximal radius of the diagonal flow hub is 1:8; the elliptical gradient section and the circular gradient section of the diagonal flow hub are tangent, the angle between the tangent at the tangent position and the axis is 30°, and the angle between the proximal tangent of the circular gradient section and the axis is 60°; and / or the ratio of the axial length of the diagonal flow hub and the diverter is in the range of 1.5 to 2; the axial length of the first oncoming surface of the diverter is greater than the axial length of the second oncoming surface: l1-l0>l2-l0; Among them, l0 is the distance between the inlet position of the oncoming surface and the far end of the diagonal flow hub, l1 is the distance between the outlet position of the first oncoming surface and the far end of the diagonal flow hub, and l2 is the distance between the outlet position of the second oncoming surface and the far end of the diagonal flow hub.

3. The flow diversion structure according to claim 1, characterized in that: The top inlet angle of the first oncoming surface of the flow splitter is equal to the top inlet angle of the second oncoming surface, and the calculation formula is as follows: Among them, β0 is the top inlet angle of the first oncoming surface and the second oncoming surface, r1 is the hub radius of the leading edge of the blood pump rotor blade, r2 is the hub radius of the trailing edge of the blood pump rotor blade, r3 is the blade tip radius of the blood pump rotor, β1 is the average inlet angle of the axial flow blade, and β2 is the average outlet angle of the axial flow blade.

4. The flow diversion structure according to claim 3, characterized in that: The top placement angle of the first oncoming surface of the flow splitter gradually increases, and the range of change is β0-β3, the preferred range of β3 is 80-90°, and the continuous change mode β1(l) is a linear function; the top placement angle of the second oncoming surface of the flow splitter gradually decreases, and the range of change is β0-β4, the preferred range of β4 is 0-15°, and the continuous change mode β2(l) is a linear function; Among them, β3 is the outlet angle of the top of the first oncoming surface, β4 is the outlet angle of the top of the second oncoming surface, β1(l) is the quantitative relationship between the top installation angle of the first oncoming surface and the axial length, and β2(l) is the quantitative relationship between the top installation angle of the second oncoming surface and the axial length.

5. The flow diversion structure according to claim 4, characterized in that: The top wrap angle θ of the first flow-facing surface of the flow divider 11 (l) and the wrap angle θ of the top of the second oncoming surface 21 (l) satisfies the following formula: Among them, θ 11 (l) is the quantitative relationship between the top wrap angle of the first flow surface and the axial length, θ 21 (l) is the quantitative relationship between the top wrap angle of the second flow-facing surface and the axial length, and R is the outer edge radius of the diverter.

6. The flow diversion structure according to claim 5, characterized in that: The wrap angle of the second oncoming surface top outlet position and the wrap angle of the first oncoming surface top outlet position meet the following conditions: Among them, θ 11 (l1) is the wrap angle value at the top outlet of the first flow surface, θ 21 (l2) is the wrap angle value at the top outlet position of the second flow surface, and n is the number of axial flow pumps.

7. The flow diversion structure according to claim 6, characterized in that: The bottom wrap angle and the top wrap angle of the first flow-facing surface of the flow splitter satisfy the following calculation formula: Among them, θ 12 (l) is the quantitative relationship between the bottom wrap angle of the first oncoming surface and the axial length, α is the angle between the bottom of the first oncoming surface and the tangent of the hub circumference; the angle α between the bottom of the first oncoming surface of the diverter and the tangent of the hub circumference ranges from 45 to 60°.

8. The flow diversion structure according to claim 7, characterized in that: The bottom wrap angle θ of the second flow-facing surface of the flow divider 22 (l) and the top wrap angle θ 21 The difference between (l) decreases linearly with the increase of axial length, satisfying the following formula: Among them, θ 22 (l) is the quantitative relationship between the top wrap angle of the second flow surface and the axial length, θ 12 (l0) is the bottom inlet wrap angle of the first flow surface, θ 11 (l0) is the inlet wrap angle value at the top of the first flow surface.

9. The flow diversion structure according to claim 1, characterized in that: The first oncoming surface and the second oncoming surface of the diverter are connected and transitioned by a standard fillet, and the fillet size range is 0.4 to 0.5 mm; the height range of the inlet position of the diverter is 1 to 1.5 mm, and the height range of the outlet position of the second oncoming surface is 0.7 to 1 mm; the back flow surface of the diverter coincides with the axis of the oblique flow hub, and is connected to the hub surface by a fillet transition, and the fillet range is 0.1 to 0.2 mm.

10. A modular intra-aortic entrainment pump, characterized in that: It comprises a shunt structure as described in any one of claims 1 to 9, which is located at the outflow window of the modular intra-aortic entrainment pump, with a blood pump rotor arranged at the distal end, and the distal diameter of the oblique flow hub is equal to the proximal hub diameter of the blood pump rotor; the through hole is used for the installation of the motor shaft and the blood pump rotor.

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