CN116059522A - Prosthetic pump capable of being arranged in human blood vessel or heart - Google Patents
Prosthetic pump capable of being arranged in human blood vessel or heart Download PDFInfo
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- CN116059522A CN116059522A CN202310071950.2A CN202310071950A CN116059522A CN 116059522 A CN116059522 A CN 116059522A CN 202310071950 A CN202310071950 A CN 202310071950A CN 116059522 A CN116059522 A CN 116059522A
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- rotor
- mandrel
- heart
- pipe
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Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
- A61M60/139—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
- A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor pumps
Abstract
The invention discloses a prosthesis pump which can be arranged in a blood vessel or a heart of a human body, comprising: rotor, stator, notes liquid pipe and back flow, the rotor includes: the device comprises a cylinder shell and a mandrel, wherein an impeller is arranged on the outer ring surface of the far section of the cylinder shell; the stator is positioned between the cylinder shell and the mandrel and sleeved on the mandrel, and the stator seals the proximal end of the cylinder shell; a first bearing is arranged between the stator and the cylindrical shell, a second bearing is arranged between the stator and the mandrel, and the first bearing and the second bearing are mutually separated along the axial direction of the prosthesis pump; a first flow passage is formed between the stator and the cylindrical shell, and a second flow passage is formed between the stator and the mandrel; the liquid injection pipe is communicated with any one of the first flow channel and the second flow channel; the return pipe is communicated with the other of the first flow passage and the second flow passage; wherein, the rotor is provided with a magnet, the stator is provided with a coil, and a magnetic attraction force is generated between the coil and the magnet in an operable way to push the rotor to rotate; the coil and the magnet are disposed opposite the first flow path and/or the second flow path.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a prosthesis pump capable of being arranged in a blood vessel or a heart of a human body, and the prosthesis pump can be arranged in the blood vessel or the heart of the human body, for example, can be arranged in a blood vessel of a descending aorta.
Background
The prosthetic pump which can be arranged in the blood vessel or the heart of the human body can be arranged in the blood vessel (such as the blood vessel of the descending aorta) or the heart, so that the normal blood circulation flow required by the human body is provided for the patient after the operation, and the conditions of the kidney (such as the kidney blood supply by implanting the blood vessel of the descending aorta) or the heart blood supply deficiency of the patient after the operation are alleviated to a great extent.
The existing prosthesis pump capable of being arranged in the blood vessel or the heart of a human body has various problems, such as poor heat dissipation effect although the heat dissipation effect is achieved. In addition, most of the existing prosthetic pumps that can be installed in the blood vessels or the heart of the human body are complicated in structure, and the rotor is generally unstable in rotation, so that the blood is easily vibrated and turbulent, and once the turbulent is formed, red blood cells in the blood are easily destroyed.
Disclosure of Invention
The invention aims at overcoming the defects of the prior art and provides a prosthesis pump which can be arranged in a blood vessel or a heart of a human body.
In order to achieve the above purpose, the present invention adopts the following technical scheme: a prosthetic pump positionable within a human blood vessel or heart, the prosthetic pump positionable within a human blood vessel or heart comprising:
a rotor, the rotor comprising: the device comprises a cylinder shell and a mandrel coaxially arranged in the cylinder shell, wherein the far end of the cylinder shell is closed, and an impeller is arranged on the outer ring surface of the far section of the cylinder shell;
the stator is positioned between the cylinder shell and the mandrel and sleeved on the mandrel, and the stator seals the proximal end of the cylinder shell; a first bearing is arranged between the stator and the cylinder shell, a second bearing is arranged between the stator and the mandrel, and the first bearing and the second bearing are mutually separated along the axial direction of the prosthesis pump which can be arranged in a blood vessel or a heart of a human body; a first flow passage is formed between the stator and the cylindrical shell, and a second flow passage is formed between the stator and the mandrel;
a liquid injection pipe communicated with any one of the first flow channel and the second flow channel; and
a return pipe communicating with the other of the first flow passage and the second flow passage;
wherein the rotor has a magnet thereon, the stator has a coil thereon, and a magnetic attraction force is operatively generated between the coil and the magnet to push the rotor to rotate;
the coil and the magnet are disposed opposite the first flow channel and/or the second flow channel.
Compared with the prior art, the prosthetic pump capable of being arranged in a human blood vessel or a heart comprises: the rotor comprises a cylinder shell and a mandrel, the stator is inserted between the cylinder shell and the mandrel, meanwhile, a first bearing is arranged between the cylinder shell and the stator, a second bearing is arranged between the stator and the mandrel, and the first bearing and the second bearing are mutually separated along the axial direction of a prosthetic pump which can be arranged in a blood vessel or a heart of a human body. This results in a rotor having an inner and an outer support point between the rotor and the stator during rotation, so that the rotor will rotate very stably.
And the rotor is directly provided with a magnet, the coil is directly arranged on the stator, and magnetic attraction is generated between the magnet and the coil to drive the rotor to rotate. In the process, the rotor is a rotating shaft, the middle part is not required to be added with the rotating shaft for transition, and the influence on the rotating stability after the middle transition rotating shaft is added is avoided.
In summary, by adopting the structure, the rotation of the rotor can be more stable, and the prosthetic pump which can be arranged in the blood vessel or the heart of a human body is prevented from generating more intense oscillation in the blood, so that the blood is prevented from forming turbulence to destroy red blood cells.
In addition, after adopting above-mentioned structure, still can form first runner and second runner between stator and rotor, coil and magnet all are relative first runner and/or second runner setting, annotate liquid pipe and arbitrary one of first runner and second runner intercommunication, and the back flow is in first runner and the second runner intercommunication, consequently the injection liquid can flow into the second runner from first runner and then discharge outside through the back flow, in this process, the injection liquid can take away the heat that coil and magnet produced with high efficiency, effectively reduce the influence of the prosthetic pump that can be disposed in human blood vessel or heart to the human body.
In addition, since the distal end of the rotor is closed and the proximal end is also closed by the stator, most of the stator, the first bearing and the second bearing are all inside the rotor, so that waste generated between the stator, the rotor, the first bearing and the second bearing can be prevented from entering the blood.
However, since rotation is required between the stator and the rotor, the proximal end of the rotor may not be tightly closed, so that waste is easy to enter the blood, but since the invention also has the first flow passage and the second flow passage, the injection liquid can still carry the waste and the waste generated in the abrasion process of the first bearing and the second bearing out of the body, thereby avoiding the pollution of the blood.
In summary, since the prosthetic pump capable of being arranged in the blood vessel or the heart of the human body only adopts the hollow rotor and the hollow stator, and two loops can be formed between the rotor and the stator on the premise of ensuring the stable rotation of the rotor, the prosthetic pump capable of being arranged in the blood vessel or the heart of the human body in the embodiment of the invention achieves the expected ideal effect by adopting the simplest structure.
In another embodiment, the prosthetic pump positionable within a human blood vessel or heart further comprises a housing, the housing being disposed over the rotor, the housing being open at a distal end and sealed at a proximal end;
the shell and the rotor are mutually separated, a third flow passage is arranged between the shell and the rotor, and the liquid injection pipe is communicated with the third flow passage.
And a third flow passage is arranged between the shell and the rotor, and the liquid injection pipe is communicated with the third flow passage. Therefore, the liquid is injected into the blood through the third flow channel, and the flowing direction of the liquid in the third flow channel is opposite to the flowing direction of the blood, so that the blood can be prevented from entering the prosthesis pump which can be arranged in the blood vessel or the heart of the human body.
In another embodiment, the distal end of the housing has a plurality of hollow portions, each of the hollow portions being opposite to the impeller, each of the hollow portions being at an outlet of the third flow channel;
the prosthetic pump positionable within a human blood vessel or heart further comprises a delivery tube secured to the distal end of the housing.
In another embodiment, the proximal ends of the first flow channel and the third flow channel are communicated to form a liquid injection cavity, and the liquid injection pipe is communicated with the liquid injection cavity.
In another embodiment, the first bearing is located at a distal section of the stator and the second bearing is located at a proximal section of the stator.
In another embodiment, the stator includes:
a stator body located between the cylindrical housing and the mandrel;
a baffle plate fixed to the proximal end of the stator body, the baffle plate sealing the proximal ends of the housing and cylinder housing;
the baffle is provided with a filling hole, the filling hole is communicated with the liquid filling cavity, and the liquid filling pipe is communicated with the filling hole.
In another embodiment, the rotor further comprises a bulkhead within the cylindrical housing; the partition plate divides a space between the cylinder shell and the mandrel into a first cavity and a second cavity along the axial direction of the prosthetic pump which can be arranged in a blood vessel or a heart of a human body, and the first cavity is positioned at the far end of the second cavity; the rotor is positioned in the second cavity;
the core shaft is a hollow shaft, the proximal end of the core shaft is communicated with the liquid injection pipe, a first liquid outlet communicated with the first cavity is formed in the core shaft, a second liquid outlet communicated with the first cavity is formed in the cylindrical shell, and the second liquid outlet is located at the impeller.
Because the core shaft is a hollow shaft, after the injection liquid is injected into the core shaft, heat generated by the magnet and the coil can be diffused away. Meanwhile, the injection liquid can also be heparin solution, and when the heparin solution reaches the impeller, the heparin solution does not cause hemolysis and plays a role in reducing damage.
In another embodiment, the proximal end of the stator has a limiting cylinder in communication with the mandrel;
the prosthesis pump capable of being arranged in a blood vessel or a heart of a human body comprises a flange, wherein the flange is fixed in the limiting cylinder and is respectively communicated with the liquid injection pipe and the mandrel;
and/or, the first liquid outlet and the second liquid outlet are arranged oppositely, and the second liquid outlet is positioned on the far side of the first liquid outlet.
In another embodiment, the proximal end of the stator has a limiting cylinder in communication with the mandrel;
the prosthesis pump capable of being arranged in a blood vessel or a heart of a human body comprises a flange, the flange is fixed in the limiting cylinder, the flange is used for communicating the liquid injection pipe with the mandrel respectively, and the flange is used for communicating the second flow passage with the return pipe respectively;
the flange is hollow, a plurality of pore canals are formed in the periphery of the annular structure of the flange, each pore canal is communicated with the return pipe, and the return pipe can be sleeved outside the liquid injection pipe.
In another embodiment, the distal end of the cylindrical housing is a conical barrel, and the impeller is fixed on the outer annular surface of the conical barrel;
the impeller comprises a plurality of blades, each blade and the cylindrical shell are integrally formed, each blade is of a conical structure, and the area of the cross section of each blade from the distal end to the proximal end is gradually increased;
and/or, the liquid injected in the liquid injection pipe is heparin solution.
Because the distal end of the cylinder shell is a conical cylinder body, and each blade is of a conical structure, after the structure is adopted, when the blades are driven by the rotor to rotate, laminar flow can be formed around the prosthesis pump which can be arranged in a blood vessel or a heart of a human body, so that the flow of blood is more gentle, and red blood cells in the blood are prevented from being broken.
In another embodiment, the pour tube comprises:
a main pipe;
a first branch pipe, which is communicated with the first flow channel, and is communicated with the main pipeline;
and the second branch pipe is respectively communicated with the main pipeline and an in-shaft channel in the mandrel.
In another embodiment, the conveying pipe is provided with a bending part, and the bending angle of the bending part is 150-170 degrees; the distal end of the conveying pipe is provided with a blood flow inlet, and the distal end of the blood flow inlet is provided with a balancing weight; the weight of the balancing weight is 0.5 g-1 g;
and the conveying pipe is also provided with a developing ring.
Drawings
FIG. 1 is a diagram of a prosthetic pump configured to be disposed within a human blood vessel or heart in accordance with one embodiment;
FIG. 2 is a schematic diagram of a rotor, stator, and housing connection provided in accordance with a first embodiment;
FIG. 3 is a cross-sectional view of a prosthetic pump positionable within a blood vessel or heart of a human subject according to one embodiment;
FIG. 4 is a schematic diagram of a rotor and stator connection provided in accordance with a first embodiment;
FIG. 5 is a schematic view of a rotor structure according to a first embodiment;
FIG. 6 is a cross-sectional view of a rotor provided by the first embodiment;
FIG. 7 is a schematic view of a stator according to a first embodiment;
FIG. 8 is a cross-sectional view of a stator provided by the first embodiment;
FIG. 9 is a schematic view of a housing structure provided in accordance with an embodiment;
FIG. 10 is a schematic view of a flange structure according to a first embodiment;
fig. 11 is a schematic view of a conveying pipe according to a first embodiment.
Wherein, 1, a conveying pipe; 11. a blood flow inlet; 12. a blood flow outlet; 13. a developing ring; 14. balancing weight; 2. a pump body; 21. a rotor; 211. a conical cylinder; 2111. a second liquid outlet; 212. a cylindrical housing; 213. a mandrel; 2131. a first liquid outlet; 214. a first cavity; 215. a second cavity; 216. an intra-shaft passage; 217. an impeller; 218. a magnet; 219. a partition plate; 22. a stator; 221. a stator body; 222. a baffle; 223. a limiting cylinder; 224. a coil; 225. pouring holes; 23. a housing; 231. a cylindrical barrel; 232. a mesh structure; 24. a flange; 241. a duct; 25. a liquid injection cavity; 3. a main pipe; 31. a first branch pipe; 32. a second branch pipe; 4. a bearing; 41. a first bearing; 42. a second bearing; 5. a third flow passage; 6. a first flow passage; 7. and a second flow passage.
Description of the embodiments
Other advantages and effects of the present invention will become apparent to those skilled in the art from the following disclosure, which describes the embodiments of the present invention with reference to specific examples. The invention may be practiced or carried out in other embodiments that depart from the specific details, and the details of the present description may be modified or varied from the spirit and scope of the present invention. It should be noted that the following embodiments and features in the embodiments may be combined with each other without conflict.
The invention aims at overcoming the defects of the prior art and provides a prosthesis pump which can be arranged in a blood vessel or a heart of a human body.
The present embodiment provides a prosthetic pump that is positionable within a blood vessel or heart of a human body, as shown in fig. 1-3, the prosthetic pump comprising: the rotor 21, the stator 22, the liquid filling pipe (the liquid filling pipe may comprise a main pipe 3, a first branch pipe 31 and a second branch pipe 32) and a return pipe (the return pipe is not shown in the figure), wherein the rotor 21 is made of cobalt-chromium alloy, and of course, other medical alloys can be adopted. The rotor 21 comprises an internally hollow cylinder housing 212 and an internally hollow spindle 213, the spindle 213 being coaxially arranged within the cylinder housing 212, the distal end of the cylinder housing 212 being closed, and an impeller 217 being further arranged on the outer circumferential surface of the distal end of the cylinder housing 212, whereby the impeller 217 is rotated so that blood will be driven to flow, the impeller 217 and the cylinder housing 212 forming a hub having a maximum diameter of phi 5mm. Preferably, the distal end of the cylindrical housing 212 is a conical barrel 211, and the impeller 217 is secured to the outer annular surface of the conical barrel 211.
The stator 22 is sleeved between the cylinder shell 212 and the mandrel 213, and the stator 22 is connected with the cylinder shell 212 through a first bearing 41 with the diameter of 4 mm; the stator 22 is connected to the spindle 213 by a second bearing 42 having a diameter of 2 mm; the first bearing 41 and the second bearing 42 are spaced apart from each other in an axial direction of a prosthetic pump that can be disposed in a blood vessel or heart of a human body.
With the above-described structure, the first flow path 6 and the second flow path 7 are naturally formed between the stator 22 and the rotor 21, the first flow path 6 is located between the stator 22 and the cylindrical housing 212, and the second flow path 7 is located between the stator 22 and the spindle 213, the liquid injection pipe communicates with the first flow path 6, and the return pipe communicates with the second flow path 7, so that the injection liquid can flow from the first flow path 6 into the second flow path 7 and then be discharged outside the body through the return pipe. Of course, in some embodiments, the filler pipe may also be in communication with the second flow channel 7, while the return pipe is in communication with the first flow channel 6, so that the filler fluid can flow from the second flow channel 7 into the first flow channel 6 and out of the body through the return pipe.
In addition, as shown in fig. 4-6, in the present embodiment, the rotor 21 has a magnet 218 thereon, and the stator 22 has a coil 224 thereon, where a magnetic attraction force is operatively generated between the coil 224 and the magnet 218 to push the rotor 21 to rotate, and preferably, the coil 224 and the magnet 218 are disposed in the first flow channel 6 and/or the second flow channel 7, and the magnet 218 may be a magnet.
In this process, since the coil 224 and the magnet 218 are disposed in the first flow channel 6 and/or the second flow channel 7, after the injection liquid enters the first flow channel 6 and the second flow channel 7, the heat generated by the coil 224 and the magnet 218 can be efficiently taken away, so that the influence of the prosthetic pump which can be disposed in the blood vessel or the heart of the human body on the human body can be effectively reduced.
The application embodiment is compared with the prior art, as shown in fig. 3, since the prosthetic pump which can be disposed in a blood vessel or heart of a human body comprises: the rotor 21 and the stator 22, and the rotor 21 includes a cylinder housing 212 and a spindle 213, the stator 22 is interposed between the cylinder housing 212 and the spindle 213, and at the same time, a first bearing 41 is provided between the cylinder housing 212 and the stator 22, and a second bearing 42 is provided between the stator 22 and the spindle 213. Preferably, the first bearing 41 and the second bearing 42 are spaced apart from each other in the axial direction of a prosthetic pump that may be placed in a blood vessel or heart of a human body, i.e. the first bearing 41 is located at the distal section of the stator 22 and the second bearing 42 is located at the proximal section of the stator 22, although vice versa. This allows the rotor 21 to have an inner and an outer support points with the stator 22 during rotation, so that the rotor 21 will rotate very stably.
And the rotor 21 is directly provided with the magnet 218, the stator 22 is provided with the coil 224, and magnetic attraction is generated between the magnet 218 and the coil 224 to drive the rotor 21 to rotate. In the process, the rotor 21 is a rotating shaft, the middle part is not required to be added with the rotating shaft for transition, and the influence on the rotating stability is avoided after the middle transition rotating shaft is added.
In summary, by adopting the above structure, the rotation of the rotor 21 can be stabilized, and the generation of a relatively strong oscillation in blood by a prosthetic pump which can be arranged in a blood vessel or a heart of a human body can be avoided, so that the damage of red blood cells due to the turbulent flow in the blood can be avoided.
In addition, as shown in fig. 2 and 3, since the distal end of the rotor 21 is closed and the proximal end is also closed by the stator 22, most of the stator 22, the first bearing 41 and the second bearing 42 are all inside the rotor 21, so that the generation of waste and trash between the stator 22, the rotor 21, the first bearing 41 and the second bearing 42 can be prevented from entering the blood.
However, since rotation is required between the stator 22 and the rotor 21, the proximal end of the rotor 21 may not be tightly closed when the stator 22 is closed, so that waste is easily introduced into the blood, but since the present invention further has the first and second fluid passages 6 and 7, the injection liquid can also carry the waste generated during the abrasion of the first and second bearings 41 and 42 out of the body, avoiding the contamination of the blood.
In summary, since the prosthetic pump capable of being disposed in a blood vessel or a heart of a human body according to the embodiment of the present invention only uses the hollow rotor 21 and the stator 22, and two loops (the two loops facilitate bringing heat out of the body) can be formed between the rotor 21 and the stator 22 on the premise of ensuring stable rotation of the rotor 21, the prosthetic pump capable of being disposed in a blood vessel or a heart of a human body according to the embodiment of the present invention achieves the expected ideal effect by using the simplest structure.
Specifically, the first bearing 414 and the second bearing 424 in this embodiment are both ceramic bearings, which have the characteristics of high temperature resistance, cold resistance, wear resistance, corrosion resistance, anti-magnetic and electric insulation, oil-free self-lubrication, high rotation speed, and the like. The characteristic of the bearing 4 is that garbage is not easy to generate, and blood is prevented from being polluted.
As shown in fig. 7-8, the distal end of the cylindrical housing 212 in this embodiment is a conical barrel 211, and the impeller 217 is secured to the outer annular surface of the conical barrel 211. The impeller 217 includes a plurality of blades integrally formed with the conical housing 211, the blades having a tapered configuration, each blade having a cross-sectional area that increases from the distal end to the proximal end. After the cylindrical barrel 211 and the blades are in the conical structures, when the blades are driven to rotate by the rotor 21, laminar flow can be formed around the prosthesis pump which can be arranged in a blood vessel or a heart of a human body, so that the flow of blood is more gentle, and red blood cells in the blood are prevented from being broken.
In some embodiments, as shown in fig. 9, the prosthetic pump that may be disposed in a blood vessel or heart of a human body further comprises a housing 23, the housing 23 is sleeved outside the rotor 21, the housing 23 is open at a distal end and sealed at a proximal end, the housing 23 and the rotor 21 are separated from each other to form a third flow channel 5 between the housing 23 and the rotor 21, and the filling tube is in communication with the third flow channel 5. Meanwhile, the prosthetic pump that can be disposed in a blood vessel or heart of a human body further includes a delivery tube 1, and the delivery tube 1 is fixed to a distal end of the housing 23.
Since the third flow passage 5 is also provided between the housing 23 and the rotor 21, the filler pipe communicates with the third flow passage 5. Therefore, the liquid is injected into the blood through the third flow channel 5, and the direction of the liquid flow in the third flow channel 5 is opposite to the direction of the blood flow, so that the blood can be prevented from entering the prosthesis pump which can be arranged in the blood vessel or the heart of the human body.
Specifically, the shell 23 is made of cobalt-chromium alloy, so that the shell 23 has better biocompatibility, and the diameter of the shell 23 is phi 8mm, so that the femoral artery access can be ensured, and the wound is smaller. Of course, in other embodiments, the housing 23 may be made of nitinol or stainless steel.
As shown in fig. 2, the distal end of the housing 23 has a plurality of hollow portions, each of which is opposite to the impeller 217, and each of which is an outlet of the third flow channel 5. The delivery tube 1 is fixed at the hollow portion, so that when the impeller 217 rotates, blood can enter from the delivery tube 1 and then overflows from the hollow portion, and at this time, the blood just collides with the injection liquid flowing out of the third flow passage 5, so that the blood can be prevented from entering the pump body 2.
As shown in fig. 2 and 9, the housing 23 includes a cylindrical barrel 231 having a hollow interior and a mesh structure 232, the mesh structure 232 being disposed at a distal end of the cylindrical barrel 231, the mesh structure 232 being disposed at a position of the proximal blood flow outlet 12 of the delivery tube 1. The mesh structure 232 is a hollowed-out portion of the housing 23.
In addition, as shown in fig. 3 and 8, the rotor 21 further includes a partition 219 in the present embodiment, the partition 219 being located in the cylinder housing 212, the partition 219 dividing the space in the rotor 21 into a first cavity 214 and a second cavity 215. The first cavity 214 is located distally of the second cavity 215 and the rotor 21 is located within the second cavity 215.
The hollow mandrel 213 has an intra-axial passage 216 therein, the proximal end of the intra-axial passage 216 being in communication with the fill tube, preferably the mandrel 213 has a diameter of 1mm and the intra-axial passage 216 has a diameter of 0.3mm.
As shown in fig. 8, the mandrel 213 is provided with a first liquid outlet 2131, the cylinder housing 212 is provided with a second liquid outlet 2111, and the second liquid outlet 2111 is located at the impeller of the conical cylinder 211. The injection liquid enters the shaft inner channel 216 from the injection pipe, enters the first cavity 214 from the first liquid outlet 2131, and flows out of the pump body 2 from the second liquid outlet 2111.
Preferably, the first liquid outlet 2131 and the second liquid outlet 2111 are opposite, and the second liquid outlet 2111 is located at a distal side of the first liquid outlet 2131, such that the injection liquid is sprayed from the first liquid outlet 2131 to the second liquid outlet 2111, so that the injection liquid flows out of the pump body 2 more easily.
Since the mandrel 213 is a hollow shaft, heat generated by the magnet and the coil 224 can be dissipated after the injection liquid is injected into the mandrel 213. The injection liquid can also be heparin solution, and when the heparin solution reaches the impeller 217, the impeller 217 does not generate hemolysis.
Preferably, as shown in FIG. 3, the first flow channel 6 and the third flow channel 5 communicate proximally and form a fluid injection chamber 25, and the fluid injection tube communicates with the fluid injection chamber 25. As shown in fig. 3 to 6, the stator 22 includes: a stator body 221 and a baffle 222, the stator body 221 being located between the cylinder housing 212 and the spindle 213, the baffle 222 being fixed to the proximal end of the stator body 221, the baffle 222 sealing the proximal ends of the housing 23 and the cylinder housing 212. The baffle 222 is provided with a filling hole 225, the filling hole 225 is communicated with the filling cavity 25, and the filling hole 225 is also communicated with a filling pipe. The injection liquid thus introduced from the injection tube passes through the injection chamber 25 into the first flow passage 6 and the third flow passage 5. Since the filling hole 225 is formed at one side of the baffle 222 so that the external filling liquid enters the filling hole 225 and then enters the filling cavity 25, the structure can be simplified and the number of pipes entering the human body can be reduced.
The inner diameter of the stator body 221 is phi 2mm, and the length of the stator body 221 is smaller than the length of the cylinder housing 212. The baffle 222 has a circular ring structure, and the baffle 222 is fixed to the proximal end of the stator body 221, and seals the proximal end of the housing 23 and the cylinder housing 212.
As shown in fig. 3-6, the proximal end of the stator 22 has a stop barrel 223, the prosthetic pump that can be placed in a blood vessel or heart of a human body comprises a flange 24, the flange 24 is fixed in the stop barrel 223, and this flange 24 is also in communication with the filling tube and the mandrel 213, respectively, so that the liquid in the filling tube can flow into the mandrel 213, and in particular, the flange 24 is also in communication with the second flow channel 7 and a return tube (not shown), respectively, so that the liquid in the second flow channel 7 can flow out of the body through the return tube (not shown).
In addition, as shown in fig. 7, the proximal end of the cylindrical housing 212 is provided with an opening adapted to the mandrel 213, so that the distal end of the mandrel 213 is exposed from the proximal opening of the cylindrical housing 212, i.e. the proximal end of the mandrel 213 is disposed outside the cylindrical housing 212, i.e. the length of the mandrel 213 is greater than the length of the cylindrical housing 212, so that the mandrel 213 is conveniently connected to the flange 24.
Specifically, as shown in fig. 6, in this embodiment, the limiting cylinder 223 has a columnar structure, the diameter of the baffle 222 is greater than the diameter of the limiting cylinder 223, and the diameter of the limiting cylinder 223 is greater than the diameter of the stator body 221; the baffle 222, the limiting cylinder 223 and the stator body 221 are provided with through channels. The proximal end of the stator body 221 is connected to the distal end of the baffle 222, and the proximal end of the baffle 222 is connected to the distal end of the stopper cylinder 223.
As shown in fig. 3, 4 and 10, the flange 24 is hollow, the flange 24 is disposed in the limiting cylinder 223, the distal end of the flange 24 is in an annular structure, the proximal end is provided with a boss, the periphery of the annular structure of the flange 24 is provided with a plurality of holes 241, each hole 241 is communicated with a return pipe (not shown in the drawings), and the return pipe can be sleeved outside the liquid injection pipe. The annular structure is internally connected with the limit cylinder 223; the boss at the proximal end of flange 24 is nested within the distal end of the filler neck so that the filler neck can communicate with the intra-axial passage 216 of the spindle 213.
As shown in fig. 3, the flange 24 forms a transition chamber between the mandrel 213 and the pouring spout, so that the mandrel 213 is rotated without rotating the pouring spout. The plurality of channels 241 of the flange 24 serve as channels of the flange 24 providing outlets for the injection liquid of the second channel 7, i.e. each channel 241 communicates with a return pipe (not shown in the figures). The return pipe (not shown in the figure) is sleeved on the limiting cylinder 223 and is communicated with the limiting cylinder 223, the return pipe can be sleeved outside the liquid injection pipe, and the return pipe is connected with a negative pressure device which can suck back the returned liquid, so that the waste, garbage and blood are prevented from being polluted. Since the return pipe (not shown) is sleeved outside the liquid injection pipe, the amount of the pipe entering the human body can be reduced.
As shown in fig. 3, the liquid injection tube in this embodiment includes: the main pipe 3, the first branch pipe 31 and the second branch pipe 32, the main pipe 3 is a conduit for transporting the injection liquid, and an opening is provided at a position of the main pipe 3 near the distal end so that the distal end of the main pipe 3 is brought into communication with the first branch pipe 31 and the second branch pipe 32 based on the opening. In this embodiment, the first branch pipe 31 and the second branch pipe 32 have an inner diameter ratio of 1.5:1, and the ratio can be adjusted according to different requirements. Specifically, the first branch pipe 31 communicates with the first flow passage 6, and at the same time, the first branch pipe 31 also communicates with the main pipe 3. The second branch pipe 32 communicates with the main pipe 3 and the flange 24, respectively, and the second branch pipe 32 can communicate with an intra-shaft passage 216 in the spindle 213 through the flange 21.
It should be noted that, the return pipe may be sleeved outside the second branch pipe 32 and the main pipe 3, and a through hole (not shown in the figure) may be formed on a side wall of the return pipe, so as to facilitate the first branch pipe 31 to pass through the through hole.
In the above embodiment, the injection liquid enters the first branch pipe 31 and the second branch pipe 32 through the main pipe 3, respectively, the injection liquid flowing through the first branch pipe 31 enters the second flow passage 7 through the first flow passage 6, and finally enters the return pipe (not shown) through the orifice 241 to be discharged.
In addition, in this embodiment, the conveying pipe 1 is a blood flow tube with a hollow interior, and a bending part is arranged on the conveying pipe 1, that is, the conveying pipe 1 is a sleeve made of a shaping skeleton woven by polyurethane coated nickel titanium wires, the skeleton woven by the nickel titanium wires can enable the sleeve to form a certain bending angle, the bending angle can be selected from 150 degrees to 170 degrees, and is preferably 165 degrees, so that the sleeve can be conveniently placed in a left ventricle through an aortic arch in operation. The conveying pipe 1 of the embodiment has the diameter of 18F to 21F, the maximum outer diameter of 8mm and the length of 80mm to 120mm. At the proximal end of the delivery tube 1 is a blood flow outlet 12, which blood flow outlet 12 serves for letting out blood.
As shown in fig. 11, in the present embodiment, the distal end of the conveying pipe 1 is a stainless steel metal head and is provided with a plurality of blood flow inlets 11, in the present embodiment, the blood flow inlets 11 are waist-shaped openings, and 4 waist-shaped openings are provided at the distal end of the conveying pipe 1; blood flows into the transfer tube 1 from the blood flow inlet 11, and flows out from the blood flow outlet 12. The stainless steel metal head and the number of waist-shaped apertures contribute to a sufficient blood-stabilisation of the inflow duct 1.
The distal end of the conveying pipe 1 is also provided with a balancing weight 14, and the weight of the balancing weight 14 is 0.5 g-1 g, preferably 0.5g, 0.8g and 1g; the weight 14 enables the whole delivery tube 1 to better stabilize the pumping.
The catheter 1 is provided with a visualization ring 13 at a position of 50mm from the blood flow inlet 11 and 5mm from the kink, the visualization ring 13 helping the operator to better see if the blood flow inlet 11 and the blood flow outlet 12 cross the aortic valve under x-rays.
The method of using a prosthetic pump that can be placed in a human blood vessel or heart is described herein as being placed in the left atrium, but in some embodiments, the prosthetic pump that can be placed in a human blood vessel or heart can be placed in other locations where pumping is needed, for example, the prosthetic pump can be implanted in the descending aortic blood vessel to supply blood to the kidney.
When the prosthetic pump, which can be placed in a blood vessel or heart of a human body, is introduced into the left ventricle, the operator is better informed of whether the inflow port 11 and the outflow port 12 cross the aortic valve by means of the visualization ring 13 under x-rays, and if so, the next operation is performed, and the auxiliary device is better stabilized in the left ventricle through the whole delivery tube 1 based on the balancing weight 14, and blood in the left ventricle is discharged from the outflow port 12 under high-speed rotation of the impeller 217 after entering from the inflow port 11 and passing through the channel of the delivery tube 1.
As shown by the arrow direction in fig. 3, an operator pushes 5% glucose injection liquid (containing 25% -50% iu/ml heparin) at the proximal end of the main pipe 3, and when the injection liquid reaches the distal end of the main pipe 3 through the main pipe 3, the injection liquid is split into two paths, and enters the first branch pipe 31 and the second branch pipe 32 respectively.
The injection liquid passing through the second branch pipe 32 enters the first cavity 214 through the first liquid outlet 2131 after entering the shaft inner channel 216, and the injection liquid entering the first cavity 214 is discharged through the second liquid outlet 2111, so that the coagulation generated by the blood passing through the impeller 217 when the rotor 21 rotates at a high speed is better solved, the damage to the blood is avoided, the blood circulation flow is increased, and the damage effect is reduced.
The injection liquid passing through the first branch pipe 31 enters the third flow passage 5 and the first flow passage 6 through the injection hole 225, and the injection liquid entering the third flow passage 5 takes away the heat generated when the rotor 21 rotates, so that the heat is prevented from being concentrated at the pump body 2, and the blood can be prevented from entering the pump body 2. At the same time, since the injection liquid also enters the first flow passage 6, the waste and heat generated by the first bearing 41 and the second bearing 42 when the rotor 21 rotates at a high speed can be discharged outside the body through the second flow passage 7, the plurality of holes 241 and the return pipe (not shown).
Compared with the prior art, the invention has the following beneficial effects:
1. the conveying pipe 1 is provided with 0.5-0.8 g of counterweight, and the conveying pipe 1 is provided with a developing ring 13 which can help an operator observe under X rays.
2. The rotor 21 is of an integrated hollow cup structure, and the heparin solution is introduced into the shaft inner cavity 216 and discharged to the impeller 217 through the second liquid outlet 2111, so that the blood is not easy to hemolyze and damage is reduced near the impeller 217.
3. The stator 22 with the inner cavity channel enables the inside of the pump body 2 to form a third flow passage 5 and a second flow passage 7 through the ceramic bearings 4 with different diameters, blocks the components in the pump body 2 from external blood, and discharges waste and garbage in the pump body 2 out of the body.
The specific embodiments described herein are offered by way of example only to illustrate the spirit of the invention. Those skilled in the art may make various modifications or additions to the described embodiments or substitutions thereof without departing from the spirit of the invention or exceeding the scope of the invention as defined in the accompanying claims.
Claims (12)
1. A prosthetic pump positionable within a human blood vessel or heart, said prosthetic pump positionable within a human blood vessel or heart comprising:
a rotor, the rotor comprising: the device comprises a cylinder shell and a mandrel coaxially arranged in the cylinder shell, wherein the far end of the cylinder shell is closed, and an impeller is arranged on the outer ring surface of the far section of the cylinder shell;
the stator is positioned between the cylinder shell and the mandrel and sleeved on the mandrel, and the stator seals the proximal end of the cylinder shell; a first bearing is arranged between the stator and the cylinder shell, a second bearing is arranged between the stator and the mandrel, and the first bearing and the second bearing are mutually separated along the axial direction of the prosthesis pump which can be arranged in a blood vessel or a heart of a human body; a first flow passage is formed between the stator and the cylindrical shell, and a second flow passage is formed between the stator and the mandrel;
a liquid injection pipe communicated with any one of the first flow channel and the second flow channel; and
a return pipe communicating with the other of the first flow passage and the second flow passage;
wherein the rotor has a magnet thereon, the stator has a coil thereon, and a magnetic attraction force is operatively generated between the coil and the magnet to push the rotor to rotate;
the coil and the magnet are disposed opposite the first flow channel and/or the second flow channel.
2. The prosthetic pump of claim 1, further comprising a housing, wherein the housing is disposed over the rotor, wherein the housing is open at a distal end and sealed at a proximal end;
the shell and the rotor are mutually separated, a third flow passage is arranged between the shell and the rotor, and the liquid injection pipe is communicated with the third flow passage.
3. The prosthetic pump of claim 2, wherein the distal end of the housing has a plurality of hollowed-out portions, each hollowed-out portion being opposite to the impeller, each hollowed-out portion being at an outlet of the third flow channel;
the prosthetic pump positionable within a human blood vessel or heart further comprises a delivery tube secured to the distal end of the housing.
4. The prosthetic pump of claim 2, wherein the proximal ends of the first and third flow passages communicate to form an infusion lumen, the infusion tube communicating with the infusion lumen.
5. The prosthetic pump of claim 1, wherein the first bearing is located at a distal segment of the stator and the second bearing is located at a proximal segment of the stator.
6. The prosthetic pump positionable within a human blood vessel or heart of claim 4, wherein said stator comprises:
a stator body located between the cylindrical housing and the mandrel;
a baffle plate fixed to the proximal end of the stator body, the baffle plate sealing the proximal ends of the housing and cylinder housing;
the baffle is provided with a filling hole, the filling hole is communicated with the liquid filling cavity, and the liquid filling pipe is communicated with the filling hole.
7. The prosthetic pump of claim 1, wherein the rotor further comprises a diaphragm, the diaphragm being positioned within the cylindrical housing; the partition plate divides a space between the cylinder shell and the mandrel into a first cavity and a second cavity along the axial direction of the prosthetic pump which can be arranged in a blood vessel or a heart of a human body, and the first cavity is positioned at the far end of the second cavity; the rotor is positioned in the second cavity;
the core shaft is a hollow shaft, the proximal end of the core shaft is communicated with the liquid injection pipe, a first liquid outlet communicated with the first cavity is formed in the core shaft, a second liquid outlet communicated with the first cavity is formed in the cylindrical shell, and the second liquid outlet is located at the impeller.
8. The prosthetic pump of claim 7, wherein the proximal end of the stator has a stop cartridge in communication with the mandrel;
the prosthesis pump capable of being arranged in a blood vessel or a heart of a human body comprises a flange, the flange is fixed in the limiting cylinder, the flange is used for communicating the liquid injection pipe with the mandrel respectively, and the flange is used for communicating the second flow passage with the return pipe respectively;
and/or, the first liquid outlet and the second liquid outlet are arranged oppositely, and the second liquid outlet is positioned on the far side of the first liquid outlet.
9. The prosthetic pump of claim 7, wherein the proximal end of the stator has a stop cartridge in communication with the mandrel;
the prosthesis pump capable of being arranged in a blood vessel or a heart of a human body comprises a flange, the flange is fixed in the limiting cylinder, the flange is used for communicating the liquid injection pipe with the mandrel respectively, and the flange is used for communicating the second flow passage with the return pipe respectively;
the flange is hollow, a plurality of pore canals are formed in the periphery of the annular structure of the flange, each pore canal is communicated with the return pipe, and the return pipe can be sleeved outside the liquid injection pipe.
10. The prosthetic pump of claim 1, wherein the distal end of the cylindrical housing is a conical barrel, the impeller being secured to an outer annulus of the conical barrel;
the impeller comprises a plurality of blades, each blade and the cylindrical shell are integrally formed, each blade is of a conical structure, and the area of the cross section of each blade from the distal end to the proximal end is gradually increased;
and/or, the liquid injected in the liquid injection pipe is heparin solution.
11. The prosthetic pump of claim 7, wherein the infusion tube comprises:
a main pipe;
a first branch pipe, which is communicated with the first flow channel, and is communicated with the main pipeline;
and the second branch pipe is respectively communicated with the main pipeline and an in-shaft channel in the mandrel.
12. The prosthetic pump of claim 3, wherein the delivery tube is provided with a bending portion, and the bending angle of the bending portion is 150-170 degrees; the distal end of the conveying pipe is provided with a blood flow inlet, and the distal end of the blood flow inlet is provided with a balancing weight; the weight of the balancing weight is 0.5 g-1 g;
and the conveying pipe is also provided with a developing ring.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310071950.2A CN116059522B (en) | 2023-02-07 | Prosthetic pump capable of being arranged in human blood vessel or heart |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310071950.2A CN116059522B (en) | 2023-02-07 | Prosthetic pump capable of being arranged in human blood vessel or heart |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN116059522A true CN116059522A (en) | 2023-05-05 |
| CN116059522B CN116059522B (en) | 2024-04-26 |
Family
ID=
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20090118567A1 (en) * | 2007-11-01 | 2009-05-07 | Thorsten Siess | Purge-free miniature rotary pump |
| CN114215792A (en) * | 2021-12-06 | 2022-03-22 | 上海炫脉医疗科技有限公司 | Micropump with totally-enclosed cleaning fluid circulating system |
| CN114225214A (en) * | 2022-01-11 | 2022-03-25 | 丰凯利医疗器械(上海)有限公司 | Catheter pump housing structure and catheter pump device |
| CN216456526U (en) * | 2021-11-17 | 2022-05-10 | 上海微创心力医疗科技有限公司 | Intervention type blood vessel pump |
| CN115282468A (en) * | 2022-08-03 | 2022-11-04 | 上海炫脉医疗科技有限公司 | Intervention type blood pump |
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20090118567A1 (en) * | 2007-11-01 | 2009-05-07 | Thorsten Siess | Purge-free miniature rotary pump |
| CN216456526U (en) * | 2021-11-17 | 2022-05-10 | 上海微创心力医疗科技有限公司 | Intervention type blood vessel pump |
| CN114215792A (en) * | 2021-12-06 | 2022-03-22 | 上海炫脉医疗科技有限公司 | Micropump with totally-enclosed cleaning fluid circulating system |
| CN114225214A (en) * | 2022-01-11 | 2022-03-25 | 丰凯利医疗器械(上海)有限公司 | Catheter pump housing structure and catheter pump device |
| CN115282468A (en) * | 2022-08-03 | 2022-11-04 | 上海炫脉医疗科技有限公司 | Intervention type blood pump |
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