Blood pump with microstructure super-hydrophobic surface

Abstract

The invention relates to a blood pump with a microstructure super-hydrophobic surface, which comprises a blade and a super-hydrophobic coating coated on the surface of the blade, and a micron-sized periodic pit array is etched on the surface of the blade through a femtosecond laser texturing technology to form a microstructure. A micron-sized periodic pit array is etched on an interface, in contact with blood, of a blood pump through a femtosecond laser texturing technology, so that a bionic micro-nano composite structure is formed; and a super-hydrophobic functional layer is constructed on the surface of the microstructure by further adopting a multi-scale coating technology (including but not limited to a plasma enhanced chemical vapor deposition method, a high-speed oxygen fuel thermal spraying method, a photoetching template guided self-assembly method and a directional electrostatic spinning method). Zero damage of blood cells under the dynamic shearing condition can be achieved, meanwhile, platelet adhesion and blood coagulation factor activation are effectively inhibited, and a breakthrough solution is provided for solving related complications of artificial heart clinical application.

Description

Technical Field

[0001] The present disclosure relates to the technical field of artificial organs, and in particular, to a blood pump having a microstructured super-hydrophobic surface. Background Art

[0002] Heart failure (HF) is the only cardiovascular disease with a steadily increasing incidence worldwide. The five-year mortality rate for HF is as high as 50%, even higher than some common cancers. Heart transplantation is the most effective treatment for HF, but the number of donor hearts is extremely limited. Therefore, artificial hearts have been developed in this context for transitional support prior to heart transplantation, cardiac rehabilitation, and even lifelong support.

[0003] Existing micro-invasive artificial hearts (MIACs) generate nonphysiological blood flow through their blood pump rotors, which drive the impellers to rotate. The high rotational speed of the blood pumps generates shear stress that can damage red blood cells, triggering hemolysis. This, in turn, leads to platelet activation and the coagulation cascade, inducing thrombosis. Furthermore, impeller surface texture and flow channel design flaws can easily create areas of stagnant or turbulent blood flow, exacerbating mechanical damage to blood cells and localized coagulation factor deposition. These issues collectively contribute to poor hemocompatibility of the blood pumps, manifesting as thrombocytopenia, cleavage of von Willebrand factor (vWF), and elevated free hemoglobin, ultimately leading to various adverse clinical events. Therefore, optimizing the hemodynamic properties of the blood pumps, reducing shear stress, and improving material surface biocompatibility through innovative design have become key research areas to overcome the technological bottlenecks of MIACs. Summary of the Invention

[0004] In order to overcome the problem of low hemocompatibility of existing blood pumps, the present invention provides a blood pump with a microstructured super-hydrophobic surface.

[0005] In order to achieve the above objectives, the present disclosure provides a blood pump with a microstructured superhydrophobic surface, comprising a blade and a superhydrophobic coating coated on the blade surface, wherein the blade surface is etched with a micron-scale periodic pit array by femtosecond laser texturing technology to form a microstructure.

[0006] Optionally, the microstructure is a lotus leaf-like protrusion.

[0007] Optionally, the diameter of the lotus leaf-like protrusion is 5 to 15 microns.

[0008] Optionally, the microstructure is a square columnar micro-protrusion.

[0009] Optionally, the side length of the square columnar micro-protrusion is 5 to 15 microns.

[0010] Optionally, the microstructure is a conical micro-protrusion.

[0011] Optionally, the bottom diameter of the conical micro-protrusion is 5-20 microns, and the height is 5-10 microns.

[0012] Optionally, the microstructure is a micropore.

[0013] Optionally, the micropores have a pore diameter of about 5 to 20 microns, and a pore depth to pore diameter ratio of 1:1 to 5:1.

[0014] Optionally, the microstructure mimics the structure of the vascular endothelium.

[0015] Optionally, the microstructure mimics the polygonal arrangement or long-axis oriented arrangement of vascular endothelial cells.

[0016] Optionally, the super-hydrophobic material system used for the super-hydrophobic coating includes polymer-based composite materials, inorganic-organic hybrid materials and smart response materials.

[0017] The technical solutions provided by the embodiments of the present disclosure may have the following beneficial effects: At the blood-contacting interface of the blood pump, a periodic array of micron-scale pits is etched using femtosecond laser texturing technology, forming a biomimetic micro-nano composite structure. Furthermore, a super-hydrophobic functional layer is constructed on the microstructure using multi-scale coating techniques (including but not limited to plasma-enhanced chemical vapor deposition, high-velocity oxygen-fuel thermal spraying, photolithography template-guided self-assembly, and directional electrospinning). This achieves zero damage to blood cells under dynamic shear conditions while effectively inhibiting platelet adhesion and coagulation factor activation, providing a breakthrough solution for addressing complications associated with the clinical application of artificial hearts. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] Figure 1 This is the design diagram of the papillary topology (lotus leaf-like) microstructure on the surface of the blood pump.

[0019] Figure 2 for Figure 1 Spherical protrusions on the surface of the blood pump with a papillary topology (lotus leaf-like) microstructure design.

[0020] Figure 3 This is the design diagram of the square column microstructure on the surface of the blood pump.

[0021] Figure 4 for Figure 3 A diagram of the square pillar protrusions on the surface of the blood pump, which is designed with a square pillar microstructure.

[0022] Figure 5 This is the design diagram of the conical microstructure on the surface of the blood pump.

[0023] Figure 6 for Figure 5Image of the conical protrusions on the surface of the blood pump with a conical microstructure design.

[0024] Figure 7 This is the design diagram of the porous microstructure on the blood pump surface.

[0025] Figure 8 for Figure 7 Hole shape diagram of the porous microstructure design on the blood pump surface.

[0026] Figure 9 This is the design diagram of the blood pump surface that imitates the vascular endothelial layer.

[0027] Figure 10 for Figure 9 Topological structure diagram of the endothelial layer mimicking the surface of the blood pump.

[0028] Explanation of the accompanying figures: 10, blade; 11, microstructure. DETAILED DESCRIPTION

[0029] The following describes the specific embodiments of the present disclosure in detail with reference to the accompanying drawings. It should be understood that the specific embodiments described herein are only used to illustrate and explain the present disclosure and are not intended to limit the present disclosure.

[0030] In this disclosure, unless otherwise indicated, directional terms such as "upper, lower, front, rear, left, and right" are used for ease of description and are defined based on the drawing orientation of the corresponding drawings. "Inside" and "outside" are defined based on the inherent contours of the corresponding components. Terms such as "first" and "second" used in this disclosure are intended to distinguish one element from another and do not convey order or importance. Furthermore, when the following description refers to the drawings, unless otherwise indicated, identical numbers in different drawings represent identical or similar elements.

[0031] See also Figures 1 to 3 The embodiment of the present disclosure provides a blood pump with a microstructured super-hydrophobic surface, including a blade 10 and a super-hydrophobic coating coated on the surface of the blade 10. The blade 10 is provided with a plurality of microstructures 11, and the plurality of microstructures 11 are arranged in a topological manner.

[0032] As can be understood, femtosecond laser texturing technology etches a micron-scale periodic pit array at the blood-contact interface of the blood pump, forming a biomimetic micro-nano composite structure. Multi-scale coating technologies (including but not limited to plasma-enhanced chemical vapor deposition, high-velocity oxygen-fuel thermal spraying, photolithography template-guided self-assembly, and directional electrospinning) are then used to construct a superhydrophobic functional layer on the microstructure surface. This layer achieves zero damage to blood cells under dynamic shear conditions while effectively inhibiting platelet adhesion and coagulation factor activation, providing a breakthrough solution to address complications associated with the clinical application of artificial hearts.

[0033] Beneficial effects of the present invention: By combining superhydrophobic properties with microstructured microstructure design, artificial hearts with microstructured superhydrophobic surfaces demonstrate significant advantages in biocompatibility, fluid dynamics, and safety. Key benefits include: (1) Antithrombotic: Mechanism: Superhydrophobic surfaces reduce platelet adhesion, fibrin deposition, and coagulation factor activation by reducing the contact area between blood and the material (similar to the "lotus effect").

[0034] Clinical significance: Significantly reduce the risk of thrombosis and reduce embolic events or pump blockage caused by thrombosis.

[0035] (2) Reduce blood damage (low hemolysis) Microstructure optimization: Surface microgrooves or textures guide laminar flow, reduce turbulence and high shear stress areas, and protect red blood cells and platelets from mechanical damage.

[0036] Results: The hemolysis rate was significantly reduced (the release of free hemoglobin was reduced), the service life of the blood pump was extended, and the complications caused by hemolysis in patients (such as kidney damage, etc.) were reduced.

[0037] (3) Inhibit biological contamination and infection Superhydrophobic antifouling: The surface repels proteins, lipids and bacteria, reducing biofilm formation and the risk of infection (such as catheter-related bloodstream infections).

[0038] Maintenance advantages: Reduce blood pump performance degradation due to contamination and reduce the frequency of cleaning or replacement.

[0039] (4) Improve fluid dynamics efficiency Drag reduction effect: The microstructured surface reduces blood flow resistance, reduces energy loss, and improves blood pump output efficiency.

[0040] Energy saving: Reduces the power consumption of the driver and extends battery life (especially important for implantable devices).

[0041] (5) Enhance material durability Anti-corrosion and wear: Super-hydrophobic coating combined with microstructure design can resist electrolyte corrosion in the blood and mechanical friction, delaying material aging.

[0042] Long-term stability: Extend the working life of the blood pump in the body and reduce the risk of secondary surgery.

[0043] (6) Reduce dependence on anticoagulants Clinical value: Traditional blood pumps require long-term anticoagulant therapy (such as warfarin), which can easily lead to bleeding risks; superhydrophobic surfaces provide passive antithrombotic effects, reducing the need for anticoagulant drug dosage and improving patient safety.

[0044] Applicable population: It has more advantages for patients with high risk of bleeding (such as the elderly and patients with coagulation disorders).

[0045] (7) Improve biocompatibility Low immune response: The superhydrophobic surface reduces the interaction between the material and the immune system, inhibiting the release of inflammatory factors and foreign body reactions.

[0046] Tissue compatibility: Reduce the risk of rejection, promote selective adhesion of endothelial cells, and improve biocompatibility.

[0047] Through physical-chemical synergy, microstructured superhydrophobic surface treatment technology solves the three core problems faced by traditional blood pumps: thrombosis, blood damage and biological contamination. At the same time, it optimizes the fluid performance and material durability of the blood pump, which can significantly reduce the incidence of complications, improve the quality of life of patients, and provide key technical support for the research and development of a new generation of miniaturized and highly durable artificial hearts.

[0048] In one embodiment, the microstructure is a lotus leaf-like protrusion. The diameter of the lotus leaf-like protrusion is 5 to 15 microns and is arranged regularly or irregularly. The specific size can be adjusted according to the blood flow velocity and shear force requirements. Example 1: Surface bionic lotus leaf design (such as Figure 1 ): The bionic lotus leaf design transforms the anti-adhesion mechanism of nature into a key technological innovation for blood pumps. Through the super-hydrophobic interface, self-cleaning function and coordinated regulation of blood flow, it systematically solves the problems of thrombosis, hemolysis and infection in traditional blood pumps. Figure 1 As shown in the figure, the surface of the blood pump adopts a lotus leaf-like surface topology to form a regularly arranged submicron spherical papilla array. This bionic interface engineering has achieved three major innovative breakthroughs: ① The super-hydrophobic surface significantly reduces the platelet adhesion rate, systematically solving the problem of thrombosis; ② The self-cleaning effect is dynamically regulated by the solid-liquid-gas three-phase contact line, effectively inhibiting the formation of biofilm; ③ The optimized surface curvature radius works synergistically with hemodynamics to improve the uniformity of shear stress distribution, fundamentally breaking through the bottleneck of hemolysis. Figure 2 shown.

[0049] In one embodiment, the microstructure 11 is a square columnar microprotrusion. The side length of the square columnar microprotrusion is 5 to 15 microns, and the specific size can be adjusted according to the blood flow velocity and shear force requirements. Specifically, Example 2: Surface square column microstructure structure (such as Figure 3 The geometric regularity of the square column microstructure combined with the chemical properties of the superhydrophobic surface significantly improves the blood compatibility and long-term stability of the artificial heart through multiple mechanisms such as physical repulsion, fluid optimization, and chemical anticoagulation. This design not only reduces the risk of hemolysis in patients, but also provides an innovative paradigm for the functional engineering of complex biological interfaces. Figure 3As shown in the figure, the surface of the blood pump is composed of regularly arranged square columnar micro-protrusions. By regulating the contact angle and shear stress distribution of the cell interface, a bio-friendly surface is established at the molecular-cell-fluid multi-scale level. Figure 4 shown.

[0050] In one embodiment, the microstructure 11 is a conical micro-protrusion. The microstructure is conical (such as a cone, a pyramid or a gradient cone), with a sharp or smooth top, a bottom diameter of about 5 to 20 microns, and a height of about 5 to 10 microns. The specific parameters are adjusted according to the shear force requirements of the blood flow. Specifically, Example 3: Surface conical microstructure structure (such as Figure 5 ): The surface of the blood pump adopts a conical microstructure and gives it superhydrophobicity. By forming a stable air cushion (Cassie-Baxter state) and low adhesion properties (contact angle>150°), it significantly reduces the adhesion of platelets and proteins and inhibits thrombosis. The superhydrophobic surface also optimizes hemodynamics, reduces shear stress peaks and turbulence, and reduces blood cell damage. This design achieves long-term anti-thrombotic effect through a physical repulsion mechanism, reduces dependence on anticoagulant drugs, and has the advantages of antibacterial and mechanical durability. Figure 5 As shown in the figure, the surface of the blood pump is a regularly arranged conical protrusion, which realizes molecular-level protein rejection, cell-level platelet impedance and macroscopic blood flow optimization. Figure 6 shown.

[0051] In one embodiment, the microstructure 11 is a micropore. The pore size of the micropore is about 5 to 20 microns, the pore depth to pore size ratio (1:1 to 5:1) is adjustable, and the pore wall can be designed to be rough or smooth. The specific parameters are adjusted according to the blood flow shear force requirements. Example 4: Surface porous microstructure construction (such as Figure 7 ): The surface of the blood pump adopts a porous microstructure and gives it superhydrophobicity. Through multi-level roughness and low surface energy coating, it significantly reduces protein adsorption and platelet adhesion, and inhibits thrombosis. The porous structure also optimizes the hemodynamic characteristics, reduces turbulence and shear stress peaks, and reduces blood cell damage. The superhydrophobic surface has both antibacterial and mechanical durability, while providing anchor points for endothelial cells and promoting endothelialization. This design achieves long-term anti-thrombosis through the synergy of physical repulsion and biological functions, reduces dependence on anticoagulant drugs, and improves the safety and durability of the blood pump. Figure 7 As shown in the figure, the surface of the blood pump is a regularly arranged porous microstructure, which realizes the establishment of a dynamic protection system in the molecular-cell-tissue multi-dimensional, increases the contact angle of the blood pump surface, reduces the amount of protein adsorption, and controls the platelet adhesion density. Figure 8 shown.

[0052] In one embodiment, the microstructure 11 is a structure that mimics the vascular endothelial layer. The microstructure mimics the polygonal arrangement or long axis oriented arrangement (similar to the direction of blood flow) of vascular endothelial cells, with a size of about 10 to 50 microns and a wavy or serrated edge to fit the natural form. The specific parameters are adjusted according to the shear force requirements of the blood flow. Example 5: Surface mimicking the vascular endothelial layer structure (such as Figure 9 ): The super-hydrophobic surface that mimics the structure of the vascular endothelium provides an anti-thrombotic solution for blood pumps through the synergistic effect of physical repulsion, chemical regulation and biomimetic topology. Its core value lies in breaking through the limitations of traditional drug-dependent coatings and achieving long-term and safe blood compatibility from the perspective of interface science. Figure 9 As shown in the figure, the surface of the blood pump is a vascular endothelial topology, which constructs a dynamic biomimetic interface of "physical barrier-chemical inertness-fluid adaptation" to increase the contact angle of the blood pump surface, reduce the amount of protein adsorption on the blood pump surface, control the platelet adhesion density, and promote the oriented growth of endothelial cells along the vascular grooves. Figure 10 shown.

[0053] In one embodiment, the preparation method of the super-hydrophobic coating includes: plasma-enhanced chemical vapor deposition, high-speed oxygen-fuel thermal spraying, photolithography template-guided self-assembly and directional electrospinning. The super-hydrophobic material system used in the preparation method includes polymer-based composite materials, inorganic-organic hybrid materials and smart response materials. The super-hydrophobic coating generally includes the following layers from the inside to the outside: 1. Substrate pretreatment layer (primer layer / bonding layer): physical roughening such as femtosecond laser texturing technology to etch out microstructures 2. Micro-nanostructure layer (functional layer): materials include polymer-based composite materials, inorganic-organic hybrid materials, smart response materials, etc. 3. Low surface energy modification layer (hydrophobic layer): materials include fluorosilane, fluorocarbon polymers, etc.

[0054] Coating preparation process Vapor deposition method: Using physical / chemical vapor deposition (PVD / CVD) technology, superhydrophobic materials (such as carbon fluoride, silane derivatives) are deposited on the substrate surface with atomic-level precision in a vacuum environment. It is suitable for full coverage coating of complex three-dimensional microstructures.

[0055] Thermal spraying: Through plasma spraying or flame spraying, the super-hydrophobic ceramic / polymer composite material is melt-sprayed onto the surface to form a micron-scale rough coating with high bonding strength, which is particularly suitable for impeller areas subjected to high shear forces.

[0056] Template-assisted method: Using photolithography or soft etching templates to guide the formation of coating microstructures can accurately replicate biomimetic topologies (such as lotus leaf-like micropapillary structures) and achieve coordinated regulation of wettability and fluid dynamics.

[0057] Electrospinning: A nanofiber network coating is prepared through a high-voltage electrostatic field, which has both superhydrophobicity and porous permeability, and is suitable for surface design that requires drug sustained release function.

[0058] 2) Coating parameter control Thickness gradient design: Layered coating construction based on fluid dynamics (0.01-100μm) 0.01-1μm: Atomic layer deposition (ALD) is used to construct nanoscale ultra-thin coatings, preserving the microstructural features of the substrate and suitable for precision flow channel surfaces.

[0059] 1-50μm: Form a functional strengthening layer by solution dipping or spin coating to improve mechanical durability.

[0060] 50-100μm: Using additive manufacturing technology to stack microstructure units to achieve active flow control.

[0061] Process adaptability: By flexibly selecting deposition parameters (temperature 80-400°C, pressure 10 -3 ~10 2 Pa) and process paths to achieve precise construction from nano-scale ultra-thin coatings to micron-scale functional structures.

[0062] 3.) Superhydrophobic material system: Polymer-based composites: Using a polymer as a matrix, nanoparticles or fibers are introduced to enhance hydrophobicity and mechanical properties, achieving both flexibility and processability. Representative polymer-based composite combinations include PDMS (silicon-based polymer) + SiO2 (silicon dioxide) nanoparticles (classic "lotus effect" biomimetic coatings), PDMS + graphene composite membranes (superhydrophobic and electromagnetic shielding), PU (polyurethane) + (zinc oxide) ZnO nanorod composites (wear-resistant superhydrophobic textiles), and water-based PU + montmorillonite composites (environmentally friendly superhydrophobic coatings).

[0063] Inorganic-organic hybrid materials: These materials combine inorganic components with organic molecules through chemical bonds or physical mixing, combining the high stability of inorganic materials with the hydrophobicity of organic materials. Typical examples of inorganic-organic hybrid materials include Al₂O₃ nanopillar arrays modified with fluorosilane (a wear-resistant, superhydrophobic metal surface).

[0064] Smart responsive materials: These materials dynamically control surface wettability through external stimuli (such as temperature, light, pH, and electric fields), achieving a "switchable" superhydrophobicity. Typical examples of these materials include pH / temperature dual-responsive copolymers (such as P(NIPAM-co-AAc)), which can switch between antimicrobial and anti-adhesion modes depending on the pH and temperature at the site of infection.

[0065] In one embodiment, the size and arrangement of the microstructures can be changed, and the superhydrophobic material can be replaced.

[0066] In one embodiment, the blood pump device as a whole includes an impeller, a catheter, an external drive system, a sensor system, and a flushing system. The blood pump consists of three core components: a blood flow channel, an impeller, and a fluid dynamic bearing. Its structural design and surface treatment process are as follows: The blood flow channel adopts a high-precision smooth inner wall design. The streamlined geometric structure is optimized to significantly reduce the turbulent shear force of blood, thereby inhibiting platelet activation and the risk of thrombosis. The impeller, as the power core of the blood pump, is selected from metal or special engineering plastics combined with a medical polymer composite layer. While ensuring mechanical strength, it also improves blood compatibility through surface passivation. The fluid dynamic bearing is a non-contact support structure based on the principle of liquid film lubrication, which can eliminate wear particle contamination caused by mechanical friction and reduce the probability of mechanical hemolysis of red blood cells. The surface functionalization process is as follows: On the interface of the blood pump that contacts the blood (blade 10), a micron-scale periodic pit array is etched using femtosecond laser texturing technology to form a biomimetic micro-nano composite structure. Multi-scale coating technologies (including but not limited to plasma-enhanced chemical vapor deposition, high-speed oxygen fuel thermal spraying, photolithography template-guided self-assembly, and directional electrospinning) are further used to construct a superhydrophobic functional layer on the microstructure surface. This composite treatment scheme achieves superhydrophobic properties with a contact angle greater than 150° through the synergistic effect of reducing surface energy and non-smooth effects, effectively reducing protein adhesion and inhibiting thrombus formation.

[0067] The catheter consists of key components, including the catheter body, catheter tip, lumen, connector, marker ring, guidewire channel, balloon, electrode, sensor, and protective sheath. The catheter body is made of highly flexible and biocompatible polymer materials such as polyurethane, silicone, or polyethylene. Its length can be adjusted between 50 and 150 cm to meet clinical needs. The catheter tip is designed in various shapes, including straight, J-shaped, or pigtail, to suit different clinical scenarios. It is constructed from low-hardness materials to minimize mechanical damage to the vascular and ventricular linings. The lumen is designed with either a single or multiple lumens. Single-lumen configurations are suitable for single-function procedures, while multi-lumen configurations can simultaneously support multiple diagnostic and therapeutic procedures, such as drug infusion and pressure monitoring. The inner diameter directly affects fluid flow rate and device passability. The connector features standardized connection ports for quick connection to medical devices such as syringes and pressure sensors. Its built-in hemostasis valve effectively prevents blood backflow and maintains a sterile operating environment. The marker ring is made of X-ray-visible material, providing real-time visual positioning for intraoperative interventional procedures.

[0068] A guidewire made of stainless steel or nickel-titanium alloy is embedded within the guidewire channel. This guidewire combines excellent flexibility and mechanical strength, ensuring precise catheter placement. Electrodes are integrated into the catheter surface for performing electrical diagnostic and therapeutic functions such as electrophysiological testing and cardiac pacing. Sensors monitor key physiological parameters such as pressure and temperature in real time, providing important data support for clinical diagnosis. The protective sheath, as an external protective device for the catheter, provides effective protection during implantation and can be easily removed once the catheter is in place. The drive system consists of three core components: the power system, the control module, and the human-machine interface. The power system utilizes a dual power supply design, consisting of two power supply units: a main power supply and a backup battery. The main power supply utilizes 220V AC to meet normal operating requirements; the backup power supply utilizes a high-performance lithium battery pack, providing at least 30 minutes of continuous power supply. This ensures rapid failover in the event of a main power failure during surgery, ensuring continuous and stable system operation. The control module integrates an advanced flow regulation system and intelligent feedback algorithm. The flow regulation system dynamically adjusts the pump speed based on the patient's real-time cardiac output requirements through a closed-loop control mechanism to ensure hemodynamic stability. The feedback system collects and processes pressure / flow sensor data in real time, intelligently identifying abnormal operating conditions and effectively preventing risks such as ventricular collapse, thereby improving safety and reliability. The human-machine interface combines a touchscreen with a physical knob. The high-definition touchscreen displays key physiological indicators such as arterial pressure waveforms, pump flow curves, and speed parameters in real time, and provides multi-level alarms. The ergonomically designed physical knob supports precise manual adjustment of the pump speed and switching between automatic and manual operating modes, ensuring that medical staff can quickly and accurately operate the device.

[0069] The sensor system consists of a pressure sensor, a flow sensor, and a position detection sensor. The pressure sensor performs the following functions: real-time monitoring of left ventricular pressure (LVP) and aortic pressure (AoP), accurately calculating the actual pump workload, and automatically triggering a speed reduction protection mechanism when the LVP is too low and / or the AoP is too high, effectively preventing ventricular collapse. The flow sensor uses electromagnetic or ultrasonic principles to achieve high-precision measurement of the pump's blood flow. The position detection sensor ensures that the catheter tip is always accurately positioned in the target area between the left ventricle and the aorta, providing reliable protection for the stable operation of the system.

[0070] The flushing system's primary functions are the flushing fluid and the flushing pump. Heparinized saline is used as the flushing fluid, which continuously flushes through the flushing channel within the catheter to prevent blood from stagnating and forming thrombi. The flushing pump is integrated into the drive system to ensure a steady flow of the flushing fluid.

[0071] The present invention is described by way of example, and those skilled in the art will appreciate that various changes or equivalent substitutions may be made to these features and embodiments without departing from the spirit and scope of the present invention. Furthermore, under the teachings of the present invention, these features and embodiments may be modified to suit specific circumstances and materials without departing from the spirit and scope of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed herein, and all embodiments falling within the scope of the claims of this application are intended to be within the scope of the present invention.

Claims

1. A blood pump having a microstructured super-hydrophobic surface, characterized in that: The invention comprises a blade (10) and a super-hydrophobic coating coated on the surface of the blade (10), wherein the blade (10) is provided with a plurality of microstructures (11), and the plurality of microstructures (11) are arranged in a topological manner.

2. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The microstructure (11) is a lotus leaf-like protrusion.

3. The blood pump with a microstructured super-hydrophobic surface according to claim 2, characterized in that: The diameter of the lotus leaf-like protrusion is 5 to 15 microns.

4. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The microstructure (11) is a square columnar micro-protrusion.

5. The blood pump with a microstructured super-hydrophobic surface according to claim 4, characterized in that: The side length of the square columnar micro-protrusion is 5 to 15 microns.

6. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The microstructure (11) is a conical micro-protrusion.

7. The blood pump with a microstructured super-hydrophobic surface according to claim 6, characterized in that: The bottom diameter of the conical micro-protrusion is 5-20 microns, and the height is 5-10 microns.

8. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The microstructure (11) is a micropore.

9. The blood pump with a microstructured super-hydrophobic surface according to claim 8, characterized in that: The micropores have a pore diameter of about 5 to 20 microns, and a pore depth to pore diameter ratio of 1:1 to 5:

1.

10. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The microstructure (11) is a structure that mimics the vascular endothelial layer.

11. The blood pump with a microstructured super-hydrophobic surface according to claim 10, characterized in that: The microstructure mimics the polygonal arrangement or long-axis oriented arrangement of vascular endothelial cells.

12. The blood pump with a microstructured super-hydrophobic surface according to claim 1, characterized in that: The super-hydrophobic material system used in the super-hydrophobic coating includes polymer-based composite materials, inorganic-organic hybrid materials and intelligent response materials.

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