CN113941086B - Manual auxiliary blood pumping device - Google Patents
Manual auxiliary blood pumping device Download PDFInfo
- Publication number
- CN113941086B CN113941086B CN202111211918.7A CN202111211918A CN113941086B CN 113941086 B CN113941086 B CN 113941086B CN 202111211918 A CN202111211918 A CN 202111211918A CN 113941086 B CN113941086 B CN 113941086B
- Authority
- CN
- China
- Prior art keywords
- driving unit
- blood pumping
- flexible transmission
- rotor
- motor
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
- 210000004369 blood Anatomy 0.000 title claims abstract description 64
- 239000008280 blood Substances 0.000 title claims abstract description 64
- 238000005086 pumping Methods 0.000 title claims abstract description 61
- 230000005540 biological transmission Effects 0.000 claims abstract description 86
- 238000007789 sealing Methods 0.000 claims abstract description 40
- 238000004804 winding Methods 0.000 claims abstract description 34
- 238000002955 isolation Methods 0.000 claims abstract description 28
- 230000008878 coupling Effects 0.000 claims abstract description 6
- 238000010168 coupling process Methods 0.000 claims abstract description 6
- 238000005859 coupling reaction Methods 0.000 claims abstract description 6
- 125000006850 spacer group Chemical group 0.000 claims description 10
- 239000012530 fluid Substances 0.000 claims description 9
- 230000017525 heat dissipation Effects 0.000 claims description 6
- 239000002184 metal Substances 0.000 claims description 5
- 229910052751 metal Inorganic materials 0.000 claims description 5
- 239000002473 artificial blood Substances 0.000 claims description 3
- 238000009954 braiding Methods 0.000 claims description 3
- 239000002131 composite material Substances 0.000 claims description 3
- 239000004020 conductor Substances 0.000 claims description 3
- 238000000034 method Methods 0.000 description 9
- 238000013146 percutaneous coronary intervention Methods 0.000 description 6
- 230000010412 perfusion Effects 0.000 description 6
- 230000008569 process Effects 0.000 description 6
- 238000010586 diagram Methods 0.000 description 5
- 238000005299 abrasion Methods 0.000 description 4
- 230000001954 sterilising effect Effects 0.000 description 4
- 238000004659 sterilization and disinfection Methods 0.000 description 4
- 238000001356 surgical procedure Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 238000005516 engineering process Methods 0.000 description 3
- 230000003993 interaction Effects 0.000 description 3
- 210000005240 left ventricle Anatomy 0.000 description 3
- 230000009467 reduction Effects 0.000 description 3
- 239000000243 solution Substances 0.000 description 3
- 230000002861 ventricular Effects 0.000 description 3
- 210000000709 aorta Anatomy 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 230000017531 blood circulation Effects 0.000 description 2
- 230000008081 blood perfusion Effects 0.000 description 2
- 238000001816 cooling Methods 0.000 description 2
- 230000006872 improvement Effects 0.000 description 2
- 230000006698 induction Effects 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 230000002980 postoperative effect Effects 0.000 description 2
- 238000003466 welding Methods 0.000 description 2
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 description 1
- 206010018910 Haemolysis Diseases 0.000 description 1
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical group [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 description 1
- 208000031481 Pathologic Constriction Diseases 0.000 description 1
- 206010052428 Wound Diseases 0.000 description 1
- 206010000891 acute myocardial infarction Diseases 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- WQZGKKKJIJFFOK-VFUOTHLCSA-N beta-D-glucose Chemical compound OC[C@H]1O[C@@H](O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-VFUOTHLCSA-N 0.000 description 1
- 210000000601 blood cell Anatomy 0.000 description 1
- 210000004027 cell Anatomy 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 208000029078 coronary artery disease Diseases 0.000 description 1
- 210000004351 coronary vessel Anatomy 0.000 description 1
- 230000006378 damage Effects 0.000 description 1
- 230000000916 dilatatory effect Effects 0.000 description 1
- 230000010339 dilation Effects 0.000 description 1
- 210000001105 femoral artery Anatomy 0.000 description 1
- 239000008103 glucose Substances 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 238000009434 installation Methods 0.000 description 1
- 230000003902 lesion Effects 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000002107 myocardial effect Effects 0.000 description 1
- 210000004165 myocardium Anatomy 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 238000010422 painting Methods 0.000 description 1
- 239000002504 physiological saline solution Substances 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 210000002321 radial artery Anatomy 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 238000010992 reflux Methods 0.000 description 1
- 229910001220 stainless steel Inorganic materials 0.000 description 1
- 239000010935 stainless steel Substances 0.000 description 1
- 230000036262 stenosis Effects 0.000 description 1
- 208000037804 stenosis Diseases 0.000 description 1
- 230000002966 stenotic effect Effects 0.000 description 1
- 230000008733 trauma Effects 0.000 description 1
- 230000002792 vascular Effects 0.000 description 1
- 231100000216 vascular lesion Toxicity 0.000 description 1
- 230000003612 virological effect Effects 0.000 description 1
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
- 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
- A61M60/20—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
Landscapes
- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Life Sciences & Earth Sciences (AREA)
- Mechanical Engineering (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Hematology (AREA)
- Cardiology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Vascular Medicine (AREA)
- Transplantation (AREA)
- External Artificial Organs (AREA)
Abstract
The invention discloses an artificial auxiliary blood pumping device, which comprises a flexible transmission structure, a driving module and a control module, wherein a blood pumping impeller is arranged at the distal end of the flexible transmission structure, the driving module comprises a main driving unit and a secondary driving unit which are separately arranged, the secondary driving unit is arranged at the proximal end of the flexible transmission structure, and the secondary driving unit, the flexible transmission structure and the blood pumping impeller form a catheter device together; the main driving unit is connected with the control module; the auxiliary driving unit comprises a driven rotor with a magnet and a sealing isolation sleeve, the main driving unit is composed of a motor winding coil and a motor framework, and a hollow part of the motor winding coil and the driven rotor are sleeved with each other to form a magnetic coupling structure. The main driving unit and the auxiliary driving unit are arranged separately, so that the transmission efficiency is greatly improved while the tightness is ensured, and the overall stability of the system can be improved.
Description
Technical Field
The invention relates to medical equipment, in particular to an artificial auxiliary blood pumping device.
Background
Percutaneous Coronary Intervention (PCI) is a commonly used and effective method for treating coronary heart disease. The interventional operation is to implant an dilating catheter into the vascular lesion through the skin of femoral artery or radial artery, and to dredge the stenosis and even block the lumen of the vascular segment through the dilation of the stenotic lesion, thereby improving the blood perfusion of the cardiac muscle. Compared with the heart bypass surgery, the risk of the PCI surgery is lower, the trauma is smaller, the surgery difficulty is lower, and the postoperative recovery is faster. In addition, PCI surgery is also useful for rescuing acute myocardial infarction by rapidly restoring blood perfusion that occludes the vessel to restore the patient's myocardial state.
An artificial Left Ventricular Assist Device (LVAD) is a device for actively pumping blood in a left ventricle into an aorta through a blood pump, and the pumping blood energy is mainly determined by the performance and the operation mode of the blood pump, is independent of the physical state of a patient, and belongs to active blood circulation supporting equipment. The artificial left ventricle auxiliary device (pLVAD) which can be implanted through skin is miniaturized, can be implanted through PCI operation, can provide more stable blood circulation support for patients in high-risk PCI operation, can improve coronary artery and remote organ perfusion, and can relieve left ventricle burden at the same time, thereby being beneficial to the stability of physical signs of the patients in operation and postoperative rehabilitation.
WO201031020957A1 discloses a miniature blood pump for a pLVAD system loaded with a perfusion cooling system. The disclosed blood pump comprises a driving motor implanted in a body and a blood pumping impeller, wherein the impeller is driven by the motor to realize auxiliary blood pumping, and the cooling solution is poured into the motor to realize stable operation of the blood pump. The main purpose is to avoid the internal motor and dispel the heat the risk that bad influence the operating efficiency of inner structure in the operation in-process, lead to the local overheated risk of intravascular device.
The prior art CN106902404B of the applicant improves the technology, and the driving motor is moved out of the body, so that the use risk of the system and the implantation difficulty of the operation are reduced. For such a power transmission interventional medical device or a power transmission implantable medical device which is required to be powered outside the body, a power transmission method of a lightweight machine which can satisfy strict requirements such as no open wound, no viral side effects, no physical connection, high reliability, high durability, and lightweight in a closed and isolated state has been sought.
In the invention patent document of publication No. CN 10110643755A, a three-base-point-based linear contact bearing is matched with shaftless magnetic transmission, so that the low-hemolysis-rate heart pump based on the three-base-point-line bearing is provided, a magnetic driving seat and a magnetic transmission element of an external magnetic driving system form magnetic force matching, the contact area of a rotor and a stator is further reduced, the rotating speed can be flexibly adjusted according to the flow requirement, the biological cell rupture rate in blood is reduced, the damage to blood cells is reduced, the overall mass of the heart pump is lighter, the volume is smaller, and the mass production is convenient.
In another patent document of publication number CN1010743051a, a quick-connection magnetic transmission device for a medical interventional instrument is described, which can meet the application requirements of a small-size micro magnetic transmission structure on the medical interventional instrument and realize high transmission rotation speed and quick-connection operation. But its structural design is at first with the rotation that uses traditional brushless DC motor to drive the driving shaft, drives the magnet of driven end again and rotates and realize magnetic drive, and multistage drive can lead to transmission efficiency to descend, has increased the specification of structure simultaneously, has increased overall quality, and in addition, multistage transmission has increased technology assembly flow for the fault rate increases, has reduced the system reliability.
Patent document CN1010820933B discloses a catheter device, which uses a motor to connect with a clutch, the clutch is a magnetic clutch having a near magnet unit and a far magnet unit, the traditional motor drives the near magnet unit to rotate, and drives the far magnet unit to rotate to realize magnetic transmission, the power transmission is also multistage transmission, which inevitably leads to reduction of transmission efficiency, and the structure is also more complex. In summary, the problem of power transmission of an interventional or implantable medical device in a sealed and isolated state in a human body is still a process to be continuously updated and explored, and further, the power transmission technology for the interventional device still needs to be improved in many places, such as smaller transmission structure specifications, so that the miniature magnet is adopted, and meanwhile, the effective magnetic transmission torque can be ensured and can meet the clinical application; and also, as in clinical applications, higher magnetic drive speed requirements; there is also an improvement in the stability and reliability requirements of current drive trains; or the biocompatibility requirement of clinical application is ensured by more effective magnet tightness.
Disclosure of Invention
The invention aims to solve the technical problem of providing the manual auxiliary blood pumping device, which adopts a motor driving module with smaller specification, realizes single-stage transmission while ensuring tightness, has high transmission efficiency and greatly improves the stability and reliability of the system.
The technical scheme adopted by the invention for solving the technical problems is that the invention provides a blood pumping assisting device for manual work, which comprises a flexible transmission structure, a driving module and a control module, wherein a blood pumping impeller is arranged at the far end of the flexible transmission structure; the main driving unit is connected with the control module; the secondary driving unit comprises a driven rotor with a magnet and a sealing isolation sleeve, the primary driving unit consists of a motor winding coil and a motor framework, the sealing isolation sleeve enables the secondary driving unit and the primary driving unit to form fluid sealing, a hollow part of the motor winding coil and the driven rotor are sleeved with each other, a certain gap is reserved between the hollow part and the driven rotor to form a magnetic coupling structure, the motor winding coil generates a magnetic field after being electrified and generates torque with the magnet on the secondary driving unit, and therefore the driven rotor drives the blood pumping impeller to rotate after passing through the flexible transmission structure;
the driven rotor consists of a driven rotating shaft, a bearing and a magnet, and the magnet is a magnetic ring; the driven rotating shaft is of a circular shaft structure, a magnetic ring is fixed on the surface of one end, close to the motor winding coil, of the driven rotating shaft, the driven rotating shaft is fixed on the bearing, and the bearing is located on one side of the magnetic ring.
Further, the motor winding coil is wound in a cylindrical shape.
Further, after the slave driving unit and the master driving unit are sleeved with each other, the gap range between the motor winding coil and the driven rotor is not smaller than 0.2mm, smaller specifications are adopted, and abrasion consumption of the driven end rotor can be prevented.
Further, the wall thickness of the sealing isolation sleeve is not less than 0.1mm.
Further, the bottom of the end cover of the motor framework is provided with a heat dissipation hole, so that the heat dissipation performance of the motor during operation is improved.
Further, the driven rotating shaft is fixed via two ball bearings arranged side by side in parallel.
Further, the driven rotating shaft is fixed on the inner side of one end of the shell through a bearing, the inner side of the other end of the shell is of a hollow structure to form a rotor fixing cylinder, and the rotor fixing cylinder and the motor framework are mutually and coaxially matched.
Further, the rotor fixing cylinder and the motor framework adopt 3% -5% of matching taper.
Further, the flexible transmission structure comprises a flexible transmission shaft and a sheath, wherein the flexible transmission shaft is positioned in the sheath, and the flexible transmission shaft is connected with the slave driving unit.
Further, the flexible drive shaft is a drive skein formed by braiding at least 2 strands of metal wires.
Further, the sheath tube is composed of a hollow metal spiral tube, a high molecular tube or a composite tube.
Further, the control module comprises a driving control unit and a main control unit, the driving control unit is used for controlling the operation of the driving module to realize the rotation of the blood pumping impeller, and the main control unit transmits and receives the operation parameters of the driving control unit and sets the operation parameters through a software system so as to control the driving module and dynamically monitor the motion state of the driving module in real time.
The invention also provides a driving device for the artificial auxiliary blood pumping device, which further comprises a flexible transmission structure and a control device, wherein the distal end of the flexible transmission structure is provided with a blood pumping impeller, the driving device comprises a main driving unit and a secondary driving unit which are separately arranged, the secondary driving unit is arranged at the proximal end of the flexible transmission structure, and the secondary driving unit, the flexible transmission structure and the blood pumping impeller form a catheter device together; the main driving unit is connected with the control device; the secondary driving unit comprises a driven rotor with a magnet and a sealing isolation sleeve, the primary driving unit consists of a motor winding coil and a motor framework, the sealing isolation sleeve enables the secondary driving unit and the primary driving unit to form fluid sealing, a hollow part of the motor winding coil and the driven rotor are sleeved with each other, a certain gap is reserved between the hollow part and the driven rotor to form a magnetic coupling structure, the motor winding coil generates a magnetic field after being electrified and generates torque with the magnet on the secondary driving unit, and therefore the driven rotor drives the blood pumping impeller to rotate after passing through the flexible transmission structure;
the driven rotor consists of a driven rotating shaft, a bearing and a magnet, and the magnet is a magnetic ring; the driven rotating shaft is of a circular shaft structure, a magnetic ring is fixed on the surface of one end, close to the motor winding coil, of the driven rotating shaft, the driven rotating shaft is fixed on the bearing, and the bearing is located on one side of the magnetic ring.
Compared with the prior art, the invention has the following beneficial effects: the artificial auxiliary blood pumping device provided by the invention has the following advantages: 1. the main driving unit and the auxiliary driving unit of the manual auxiliary blood pumping device are separately arranged, are nested into an integral structure during operation, only the motor winding coil electrified by the main driving unit generates an induced magnetic field, and the driven rotor is directly driven to rotate by the interaction force between the magnetic fields, so that the blood pumping impeller is driven to rotate. 2. The simplified structure is less high in tolerance requirements than the precision assembly size requirements of the external transmission bearing compared with the multistage transmission, so that the installation efficiency is improved. As the process manufacturing flow is reduced, the flow error rate is reduced, the stability of the system is improved, and the operation reliability of the whole device is improved. 3. The structure design is simplified, the external transmission bearing is reduced, the number of assembly parts is reduced, and the transmission efficiency is improved, and meanwhile, the cost of the whole device is reduced. 4. The service life of the external magnetic transmission system is further prolonged due to the reduction of the external transmission bearing. 5. According to the manual auxiliary blood pumping device, in the working state, the reflux perfusion fluid flows through the secondary driving unit, so that heat generated by the working of the secondary driving unit is brought out of the body, an additional heat dissipation device is not needed, the structure of the whole device is further simplified, and the system stability is improved.
Drawings
FIG. 1 is a schematic diagram of the structure of an artificial auxiliary blood pumping device of the present invention;
FIG. 2 is a schematic diagram of a driving module in a first embodiment of an artificial blood pumping device according to the present invention;
FIG. 3 is a schematic view of a cross-sectional structure of a magnetic actuator before connection according to the present invention;
FIG. 4 is a schematic cross-sectional view of the magnetic actuator of the present invention after connection;
FIG. 5 is a schematic diagram of the assembly of the driven rotor, magnets and driven shaft spacer sleeve of the present invention;
fig. 6 is a schematic diagram of a driving module structure according to a third embodiment of the present invention;
Fig. 7 is a schematic cross-sectional structure of fig. 6.
Fig. 8 is a schematic structural diagram of a control module of the artificial auxiliary blood pumping device of the present invention.
In the figure:
1 drive module 2 catheter device 3 control module
10 Slave drive unit
101 Driven shaft 102 first bearing 103 second bearing
104 Magnet 105 sealing isolation sleeve 106 rotor fixing cylinder
107 Outer shell 108 driven rotating shaft isolation sleeve 109 arc-shaped groove
110 End cap
20 Main drive unit
21 Motor winding coil 22 motor skeleton 23 external wire harness
31 Drive control unit 32 active unit
Detailed Description
The invention is further described below with reference to the drawings and examples.
Referring to fig. 1 and 2, an embodiment of an artificial auxiliary blood pumping device provided by the present invention includes a flexible transmission structure, a driving module 1 and a control module 3, wherein a blood pumping impeller is disposed at a distal end of the flexible transmission structure, the driving module 1 includes a main driving unit 20 and a secondary driving unit 10 which are separately disposed, and the secondary driving unit is disposed at a proximal end of the flexible transmission structure and forms a catheter device 2 together with the flexible transmission structure and the blood pumping impeller; the main driving unit 20 is connected with the control module 3; the secondary driving unit 10 comprises a driven rotor 101 with a magnet 104 and a sealing isolation sleeve 105, the primary driving unit 20 is composed of a motor winding coil 21 and a motor framework 22, the sealing isolation sleeve 105 enables the secondary driving unit 10 and the primary driving unit 20 to form fluid sealing, a hollow part of the motor winding coil 21 is sleeved with the driven rotor 101 with a certain gap to form a magnetic coupling structure, a magnetic field is generated after the motor winding coil 21 is electrified, and torque is generated by acting with the magnet 104 on the secondary driving unit 10, so that the driven rotor 101 drives a blood pumping impeller to rotate after passing through the flexible transmission structure.
It should be noted that "distal" refers to a direction away from an operator, such as a doctor, and "proximal" refers to a direction closer to the operator when the manually assisted blood pumping device is in operation. The gap mentioned above is also understood to be an air gap.
The artificial auxiliary blood pumping device of this embodiment is a percutaneous implanted ventricular auxiliary device for assisting the ventricle to realize the blood pumping function, and the drive module of the device is located outside the body, and the pump blood impeller that is located in the body is driven via flexible transmission structure and is realized doing work, so the transmission efficiency requirement to the drive module is higher, simultaneously because the perfusion fluid that needs to flow through in the flexible transmission structure, thereby forming pressure and avoiding blood to get into the flexible transmission structure, the perfusion fluid is usually normal physiological saline or glucose solution etc.. If the driving module directly utilizes the conventional motor to drive, the motor can generate electric leakage accidents when contacting the perfusate, and the safety of human body is threatened, so that the conventional motor is required to be sealed, but the sealing is difficult to realize, and the effect after sealing can necessarily lead to the reduction of energy transmission efficiency.
Therefore, the embodiment of the invention designs a brand new motor structure, and only the energized motor winding coil of the main driving unit 20 is used for generating an induction magnetic field to directly drive the driven rotor 101 to rotate. The main driving unit 20 and the auxiliary driving unit 10 are separately arranged, and are nested into an integral structure during working, so that the function of power supply is realized, compared with the case of multistage transmission, the structure is greatly simplified, the loss is reduced, and the energy transmission efficiency is higher. Meanwhile, the structure can realize quick plug-in connection, sealing and single-stage transmission.
With continued reference to fig. 3 and 4, specifically, the hollow portion of the motor winding coil 21 and the rotor portion of the driven end magnet are sleeved with each other with a certain gap, the gap range is greater than or equal to 0.2mm, so as to form a new motor structure, wherein the gap refers to the distance between the motor winding coil 21 and the magnet 104, the motor winding coil 21 is wound into a cylindrical shape in a certain manner, and leads are led out from the bottom, and when the external wire harness 23 is energized, a stable magnetic field magnetically opposite to the driven magnet 104 is formed, so that the driven rotor starts to rotate at a constant speed. In addition, the bottom of the end cover of the motor framework 22 is provided with a heat dissipation hole, so that the heat dissipation performance of the motor during operation is improved, and the phenomenon of short circuit of internal electric elements caused by the fact that heat cannot be timely dissipated is prevented. The other end of the external wiring harness 23 is connected with a drive control unit in the drive module and is used as a path for coil power supply and signal feedback.
Specifically, the slave drive unit 10 of the present invention is composed of a driven rotation shaft 101, a bearing, a magnet 104 and a seal spacer 105, and the driven rotation shaft 101, the bearing and the magnet 104 constitute a driven rotor. The driven rotating shaft 101 is fixed on the inner side of one end of the shell 107 through a bearing, the inner side of the other end of the shell 107 is of a hollow structure to form a rotor fixing barrel 106, and the rotor fixing barrel 106 and the motor framework 22 are mutually and coaxially matched; the rotor fixing barrel 106 and the motor framework 22 can be matched with taper of 3% -5%.
As shown in fig. 5, the driven rotating shaft 101 is designed to be a circular shaft structure, and an arc-shaped groove 109 is designed on one end surface of the rotating shaft 101 to serve as a magnet retainer, and the magnet 104 is placed and embedded in the arc-shaped groove 109 and assembled and sleeved in the driven rotating shaft isolating sleeve 108. Wherein the arcuate recesses 109 may be selected as even pairs, the magnets 104 being placed in pairs in opposite pairs, adjacent magnets being of opposite polarity when circumferentially expanded; the driven shaft isolating sleeve 108 has a cylindrical structure, so that the magnet 104 can be prevented from slipping off in the rotation process, and the driven shaft isolating sleeve 108 can be made of stainless steel or other materials meeting requirements.
The bearing comprises a first bearing 102 and a second bearing 103, the first bearing 102 and the second bearing 103 are arranged side by side in parallel to play a role in supporting and fixing, the driven rotating shaft 101 is prevented from shifting in the rotating process, meanwhile, the friction coefficient in the rotating process of the rotating shaft can be reduced, and the abrasion of the rotating shaft is reduced, wherein the two bearings can be ball bearings. The two bearings in this implementation are located the same side of magnet, compare the bearing that traditional hollow cup motor is located magnet rotor both ends, not only can realize sealedly, and the design of this kind of new motor structure can further reduce drive module's size and size moreover, and quick plug's maneuverability is strong.
The sealing isolation sleeve 105 is sleeved outside the driven rotating shaft isolation sleeve 108, so that the sealing isolation sleeve has a liquid leakage sealing effect. The sealing isolation sleeve 105 is made of non-magnetic conductive materials, so that attractive force and repulsive force of inner and outer magnetic blocks or upper and lower magnetic blocks are not influenced, and a torque transmission function is realized.
The shape of the sealing spacer is generally designed to be step-shaped according to the driven rotating shaft, the placement position of the magnet and the position of the bearing, for example, the sealing spacer 105 of the embodiment is designed to be an elliptical head, and is composed of a half elliptical shell and a short cylindrical section. The short cylinder saves energy, so that boundary line edge stress with larger change of section curvature and welding stress at the welding joint of the sealing head and the cylinder body are separated, and the stress condition of the sealing isolation sleeve 105 can be effectively improved.
In addition, in order to ensure the coaxiality of the two ends of the master and slave, and further to ensure the requirements of high rotation speed and stability of the motor, the rotation gaps of the master end and the slave end at the inner side and the outer side of the sealing isolation sleeve 105 need to be set, the gap between the optional driving end and the driven end is not smaller than 0.2mm in consideration of the processing size and the motor transmission efficiency, the smaller the gap is, the better the smaller the gap is under the same working condition, and the preferable range is 0.25-0.4mm.
The wall thickness of the sealing isolation sleeve is not smaller than 0.1mm so as to prevent abrasion consumption of the driven end rotor, and the smaller the wall thickness is, the better the processing feasibility and the sealing isolation strength are ensured.
The sealing isolation sleeve is arranged between the slave driving unit 10 and the master driving unit 20, can prevent the perfusion solution at the slave end from entering the master end, and plays a role in sealing isolation. The catheter device 2 on the left side of the sealing isolation sleeve 105 belongs to an internal sterilization area, sterilization treatment is needed, the main driving unit 20 and the control module 3 on the right side belong to a non-sterilization area, sterilization treatment is not needed, and the structure can meet the requirements of interventional medical instruments.
It will be appreciated that a sealing spacer is a seal for fluid sealing, the seal being of a material and shape which is satisfactory. In other application scenarios, the housing of the slave drive unit and the sealing spacer may also be provided as an integral structure.
The second embodiment of the invention provides a driven rotor, which consists of a driven rotating shaft, a bearing and a magnet, wherein the magnet is a magnetic ring; the driven rotating shaft is of a circular shaft structure, a magnetic ring is fixed on the surface of the driven rotating shaft, which is close to one end of the motor winding coil, the driven rotating shaft is fixed on the bearing, and the bearing is located on one side of the magnetic ring.
The number of the bearings is one or more, the plurality of bearings are positioned on the same side of the magnetic ring, and the bearings can be ball bearings.
Compared with the first embodiment, the magnet of the present embodiment is a magnetic ring, the magnetic ring is disposed at one end of the driven rotating shaft, which is close to the motor winding coil, and optionally is fixed on the driven rotating shaft by using an adhesive manner, the arrangement of the driven rotating shaft isolation sleeve 108 is not needed after special treatment such as painting is performed on the surface of the magnetic ring, the structure is simplified, and the design of the rest parts is similar, and details are not repeated here.
In a third embodiment of the present invention, as shown in fig. 6 and 7, a driven rotor of a manual auxiliary blood pumping device includes a driven rotating shaft 101, two bearings 102/103 and a magnet 104, wherein the driven rotating shaft 101 is fixed on the bearings 102 and 103, the magnet 104 is a magnetic ring, and the magnet 104 is fixed on the driven rotating shaft 101 and located between the bearings 102 and 103.
Further, the slave drive unit 10 further comprises a housing 106 and an end cap 110, the end cap 110 is located at a distal end side of the housing 106 and is used for fixing the bearing 102, two side walls of the end cap 110 extend through the magnet 104 and then abut against the bearing 103, and the sealing spacer 105 is sleeved on the bearing 103 and is matched with the end cap 110, so that the slave drive unit and the master drive unit are in a sealed state.
The housing 106 forms a hollow structure on a side of the housing 106 adjacent to the motor winding coil, and the housing 106 and the motor armature 22 are coaxially mated with each other.
The bearings 102/103 in this embodiment are disposed at two ends of the magnetic ring 104, and the sealing spacer 105 is spaced between the secondary driving unit and the primary driving unit.
The magnet 104 in this embodiment may be a magnetic sheet, which is fixed on the driven shaft, and a driven shaft spacer may be added as appropriate, which is not limited.
The invention utilizes the magnetic field to transmit torque through the working gap of the magnetic circuit, realizes the power transmission process, and ensures the stable operation of the system because of no rigid connection structure. Meanwhile, the invention eliminates the iron core abrasion influence of the traditional motor through the design based on the magnetic transmission motor, generates an induction magnetic field under the condition of electrifying the cylindrical coil at the driving end, drives the rotor of the permanent magnet at the driven end to rotate through the interaction force between the magnetic fields, simplifies the design of the motor structure, ensures the tightness and greatly improves the transmission efficiency and the overall stability of the system. Thereby realizing the power transmission application of the external magnetic transmission system to the internal pumping blood conduit and meeting the sealing requirement of the interventional medical instrument.
The flexible transmission structure of the invention is composed of a flexible transmission shaft and a sheath tube, the flexible transmission shaft is positioned in the sheath tube, and the flexible transmission shaft is connected with a slave driving unit. The flexible transmission shaft is a transmission twisted wire formed by braiding at least 2 strands of metal wires, and the sheath tube consists of a hollow metal spiral tube, a high polymer tube or a composite tube.
As shown in fig. 8, the control module 3 includes a driving control unit 31 and a main control unit 32, the driving control unit 31 is used for controlling the operation of the driving module to realize the rotation of the blood pumping impeller, the main control unit 32 transmits and receives the operation parameters of the driving control unit 31, and sets the operation parameters through a software system, so as to control the driving module, and simultaneously, dynamically monitor the motion state of the driving module in real time.
Specifically, the drive control unit 31 mainly amplifies the control signal output from the controller to operate the main drive unit 20, while receiving the feedback signal when the main drive unit 20 is operated; the main control unit 32 includes an embedded controller and a software system. The drive control unit 31 and the main control unit 32 are connected in a plug-in manner. The main control unit 32 transmits and receives the operation parameters of the driving control unit 31, and sets the operation parameters of the system through a software system, so as to effectively control the main driving unit 20, such as start and stop, rotation speed control, direction control and the like of the main driving unit 20, and simultaneously can dynamically monitor the motion state of the main driving unit 20 in real time.
The manual auxiliary blood pumping device has the following power transmission working process:
Firstly, motor control information, such as setting the motor rotation speed, is input through a man-machine interaction interface, and is converted into operation parameters by a main control unit 32 to send driving signals to a driving control unit 31, then the driving module starts to rotate under the driving of the driving signals, and meanwhile, the driving control unit 31 feeds back the motor operation state to the main control unit 32, so that the main control unit 32 estimates the actual rotation speed to form closed-loop control.
The driven end magnet rotor of the driving module transmits rotation torque to the pumping impeller through the flexible transmission structure, so that the pumping impeller rotates at a set rotation speed, blood in a ventricle is pumped into an aorta, and the ventricular auxiliary pumping function is realized.
The driving module provided by the invention controls the rotation of the flexible transmission structure through the motor structure in a nested design and finally drives the rotation of the blood pumping impeller, thereby realizing the function of pumping blood in vivo. The invention reduces the specification of the driving module structure and can ensure the stable operation of the system at the maximum rotation speed of 55000 RPM.
While the invention has been described with reference to the preferred embodiments, it is not intended to limit the invention thereto, and it is to be understood that other modifications and improvements may be made by those skilled in the art without departing from the spirit and scope of the invention, which is therefore defined by the appended claims.
Claims (12)
1. The artificial auxiliary blood pumping device is characterized by comprising a flexible transmission structure, a driving module and a control module, wherein a blood pumping impeller is arranged at the distal end of the flexible transmission structure, the driving module comprises a main driving unit and a secondary driving unit which are arranged separately, the secondary driving unit is arranged at the proximal end of the flexible transmission structure, and the secondary driving unit, the flexible transmission structure and the blood pumping impeller form a catheter device together; the main driving unit is connected with the control module; the secondary driving unit comprises a driven rotor with a magnet and a sealing isolation sleeve, and the sealing isolation sleeve is made of a non-magnetic conductive material; the main driving unit consists of a motor winding coil and a motor framework, the sealed isolation sleeve enables the slave driving unit and the main driving unit to form fluid seal, a hollow part of the motor winding coil and the slave rotor are sleeved with each other, a certain gap is reserved between the hollow part and the slave rotor to form a magnetic coupling structure, a magnetic field is generated after the motor winding coil is electrified, and the magnetic field acts with a magnet on the slave driving unit to generate torque, so that the slave rotor drives the blood pumping impeller to rotate after passing through the flexible transmission structure;
The driven rotor consists of a driven rotating shaft, a bearing and a magnet, and the magnet is a magnetic ring; the driven rotating shaft is of a circular shaft structure, a magnetic ring is fixed on the surface of one end, close to the motor winding coil, of the driven rotating shaft, the driven rotating shaft is fixed on the bearing, and the bearing is located on one side of the magnetic ring;
The driven rotating shaft is fixed on the inner side of one end of the shell through a bearing, the inner side of the other end of the shell is of a hollow structure to form a rotor fixing cylinder, and the rotor fixing cylinder and the motor framework are mutually and coaxially matched; and the rotor fixing cylinder is in taper fit with the motor framework.
2. The artificial auxiliary blood pumping device of claim 1, wherein the motor winding coil is wound in a cylindrical shape.
3. The artificial auxiliary blood pumping device according to claim 1, wherein a gap between the motor winding coil and the driven rotor is not less than 0.2mm after the slave driving unit and the master driving unit are fitted into each other.
4. The artificial blood pumping device of claim 1, wherein the wall thickness of the sealing spacer is not less than 0.1mm.
5. The artificial auxiliary blood pumping device according to claim 1, wherein a heat dissipation hole is formed at the bottom of the end cover of the motor frame.
6. The artificial auxiliary blood pumping device according to claim 1, wherein the driven rotation shaft is fixed via two ball bearings arranged side by side in parallel.
7. The artificial auxiliary blood pumping device according to claim 1, wherein a matching taper of 3% -5% is adopted between the rotor fixing cylinder and the motor framework.
8. The artificial assist blood pumping device of claim 1, wherein the flexible transmission structure comprises a flexible transmission shaft and a sheath, the flexible transmission shaft being located within the sheath, the flexible transmission shaft being connected to the slave drive unit.
9. The artificial auxiliary blood pumping device of claim 8, wherein the flexible drive shaft is a drive twisted wire formed by braiding at least 2 strands of metal wires.
10. The artificial blood pumping apparatus of claim 8, wherein the sheath comprises a hollow metallic spiral tube, a polymeric tubing, or a composite tubing.
11. The artificial auxiliary blood pumping device according to claim 1, wherein the control module comprises a driving control unit and a main control unit, the driving control unit is used for controlling the operation of the driving module to realize the rotation of the blood pumping impeller, and the main control unit transmits and receives the operation parameters of the driving control unit and sets the operation parameters through a software system so as to control the driving module and dynamically monitor the motion state of the driving module in real time.
12. A driving device for an artificial auxiliary blood pumping device, which is characterized by further comprising a flexible transmission structure and a control device, wherein a blood pumping impeller is arranged at the distal end of the flexible transmission structure, the driving device comprises a main driving unit and a secondary driving unit which are separately arranged, the secondary driving unit is arranged at the proximal end of the flexible transmission structure, and the secondary driving unit, the flexible transmission structure and the blood pumping impeller form a catheter device together; the main driving unit is connected with the control device; the secondary driving unit comprises a driven rotor with a magnet and a sealing isolation sleeve, and the sealing isolation sleeve is made of a non-magnetic conductive material; the main driving unit consists of a motor winding coil and a motor framework, the sealed isolation sleeve enables the slave driving unit and the main driving unit to form fluid seal, a hollow part of the motor winding coil and the slave rotor are sleeved with each other, a certain gap is reserved between the hollow part and the slave rotor to form a magnetic coupling structure, a magnetic field is generated after the motor winding coil is electrified, and the magnetic field acts with a magnet on the slave driving unit to generate torque, so that the slave rotor drives the blood pumping impeller to rotate after passing through the flexible transmission structure;
The driven rotor consists of a driven rotating shaft, a bearing and a magnet, and the magnet is a magnetic ring; the driven rotating shaft is of a circular shaft structure, a magnetic ring is fixed on the surface of one end, close to the motor winding coil, of the driven rotating shaft, the driven rotating shaft is fixed on the bearing, and the bearing is located on one side of the magnetic ring;
The driven rotating shaft is fixed on the inner side of one end of the shell through a bearing, the inner side of the other end of the shell is of a hollow structure to form a rotor fixing cylinder, and the rotor fixing cylinder and the motor framework are mutually and coaxially matched; and the rotor fixing cylinder is in taper fit with the motor framework.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111211918.7A CN113941086B (en) | 2021-07-06 | 2021-07-06 | Manual auxiliary blood pumping device |
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111211918.7A CN113941086B (en) | 2021-07-06 | 2021-07-06 | Manual auxiliary blood pumping device |
| CN202110759320.5A CN113244526B (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
Related Parent Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110759320.5A Division CN113244526B (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN113941086A CN113941086A (en) | 2022-01-18 |
| CN113941086B true CN113941086B (en) | 2024-05-03 |
Family
ID=77190739
Family Applications (3)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110759320.5A Active CN113244526B (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
| CN202111210392.0A Pending CN113941085A (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
| CN202111211918.7A Active CN113941086B (en) | 2021-07-06 | 2021-07-06 | Manual auxiliary blood pumping device |
Family Applications Before (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110759320.5A Active CN113244526B (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
| CN202111210392.0A Pending CN113941085A (en) | 2021-07-06 | 2021-07-06 | Artificial auxiliary blood pumping device |
Country Status (1)
| Country | Link |
|---|---|
| CN (3) | CN113244526B (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116603163A (en) * | 2022-01-26 | 2023-08-18 | 心擎医疗（苏州）股份有限公司 | Device for assisting heart in the event of failure |
| CN115430037A (en) * | 2022-07-20 | 2022-12-06 | 苏州心擎医疗技术有限公司 | Device for assisting the heart in the occurrence of functional failure |
| CN115920227B (en) * | 2022-12-01 | 2024-03-08 | 心擎医疗（苏州）股份有限公司 | Catheter pump external power structure and catheter pump device |
Citations (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1242643A (en) * | 1998-07-21 | 2000-01-26 | 三星电子株式会社 | Slot-less motor for super high speed driving |
| CN201928112U (en) * | 2010-11-23 | 2011-08-10 | 奇鋐科技股份有限公司 | Fan motor structure with waterproof and dustproof functions and fan provided with same |
| CN104852514A (en) * | 2014-02-14 | 2015-08-19 | 宁波腾隆户外用品有限公司 | Device for connecting motor with oil pump |
| CN106512117A (en) * | 2016-10-09 | 2017-03-22 | 丰凯医疗器械（上海）有限公司 | A flexible transmission system, a percutaneous blood pumping assisting device and an intravascular thrombus suction system |
| CN106902404A (en) * | 2015-12-23 | 2017-06-30 | 丰凯医疗器械（上海）有限公司 | Percutaneous auxiliary blood pumping device |
| CN108068988A (en) * | 2016-11-18 | 2018-05-25 | 杨明芳 | Realize the stepless speed change device of bicycle variable speed |
| CN108136090A (en) * | 2015-10-09 | 2018-06-08 | Ecp发展有限责任公司 | Blood pump |
| CN109432572A (en) * | 2018-10-16 | 2019-03-08 | 昕涌医疗器械(上海)有限公司 | A kind of rotary drive interposing catheter having perfusion functional |
| CN110743051A (en) * | 2019-12-24 | 2020-02-04 | 丰凯医疗器械（上海）有限公司 | Quick-connection type magnetic transmission device for medical interventional instrument |
| CN110829787A (en) * | 2019-09-30 | 2020-02-21 | 青岛海洋科学与技术国家实验室发展中心 | Linear rotation magnetic transmission mechanism and wing changing device of underwater vehicle |
| CN111106701A (en) * | 2020-01-13 | 2020-05-05 | 中山市英为拓电器有限公司 | Temperature-resistant waterproof motor with separated rotor structure |
| CN112350546A (en) * | 2020-11-17 | 2021-02-09 | 江苏鼎智智能控制科技股份有限公司 | Voice coil motor with low friction force |
Family Cites Families (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE502007005015C5 (en) * | 2007-10-08 | 2020-02-20 | Ais Gmbh Aachen Innovative Solutions | Catheter device |
| CN201726299U (en) * | 2010-03-31 | 2011-01-26 | 谭定忠 | Magnetic coupling seal driver |
| DE102012202411B4 (en) * | 2012-02-16 | 2018-07-05 | Abiomed Europe Gmbh | INTRAVASAL BLOOD PUMP |
| EP4186557A1 (en) * | 2012-07-03 | 2023-05-31 | Tc1 Llc | Motor assembly for catheter pump |
| EP3804797A1 (en) * | 2015-01-22 | 2021-04-14 | Tc1 Llc | Motor assembly with heat exchanger for catheter pump |
| US11491322B2 (en) * | 2016-07-21 | 2022-11-08 | Tc1 Llc | Gas-filled chamber for catheter pump motor assembly |
| CN108561651A (en) * | 2018-03-13 | 2018-09-21 | 西安理工大学 | A kind of pipe joint arrangement of automatic butt |
| CN207939307U (en) * | 2018-03-29 | 2018-10-02 | 杨斌 | A kind of waterproof machine |
| CN209278679U (en) * | 2018-11-30 | 2019-08-20 | 天津鑫凯建业科技有限公司 | A kind of oil transportation pipe fitting |
| CN211127389U (en) * | 2020-01-13 | 2020-07-28 | 中山市英为拓电器有限公司 | Temperature-resistant waterproof motor with separated rotor structure |
| CN111643755A (en) * | 2020-06-18 | 2020-09-11 | 浙江清科博动医疗科技有限公司 | Low-hemolysis-rate heart pump based on three-base point-line bearing |
| CN112392738A (en) * | 2020-11-27 | 2021-02-23 | 浙江鸿吉智能控制有限公司 | Novel non-contact electromagnetic drive pump |
-
2021
- 2021-07-06 CN CN202110759320.5A patent/CN113244526B/en active Active
- 2021-07-06 CN CN202111210392.0A patent/CN113941085A/en active Pending
- 2021-07-06 CN CN202111211918.7A patent/CN113941086B/en active Active
Patent Citations (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1242643A (en) * | 1998-07-21 | 2000-01-26 | 三星电子株式会社 | Slot-less motor for super high speed driving |
| CN201928112U (en) * | 2010-11-23 | 2011-08-10 | 奇鋐科技股份有限公司 | Fan motor structure with waterproof and dustproof functions and fan provided with same |
| CN104852514A (en) * | 2014-02-14 | 2015-08-19 | 宁波腾隆户外用品有限公司 | Device for connecting motor with oil pump |
| CN108136090A (en) * | 2015-10-09 | 2018-06-08 | Ecp发展有限责任公司 | Blood pump |
| CN106902404A (en) * | 2015-12-23 | 2017-06-30 | 丰凯医疗器械（上海）有限公司 | Percutaneous auxiliary blood pumping device |
| CN106512117A (en) * | 2016-10-09 | 2017-03-22 | 丰凯医疗器械（上海）有限公司 | A flexible transmission system, a percutaneous blood pumping assisting device and an intravascular thrombus suction system |
| CN108068988A (en) * | 2016-11-18 | 2018-05-25 | 杨明芳 | Realize the stepless speed change device of bicycle variable speed |
| CN109432572A (en) * | 2018-10-16 | 2019-03-08 | 昕涌医疗器械(上海)有限公司 | A kind of rotary drive interposing catheter having perfusion functional |
| CN110829787A (en) * | 2019-09-30 | 2020-02-21 | 青岛海洋科学与技术国家实验室发展中心 | Linear rotation magnetic transmission mechanism and wing changing device of underwater vehicle |
| CN110743051A (en) * | 2019-12-24 | 2020-02-04 | 丰凯医疗器械（上海）有限公司 | Quick-connection type magnetic transmission device for medical interventional instrument |
| CN111106701A (en) * | 2020-01-13 | 2020-05-05 | 中山市英为拓电器有限公司 | Temperature-resistant waterproof motor with separated rotor structure |
| CN112350546A (en) * | 2020-11-17 | 2021-02-09 | 江苏鼎智智能控制科技股份有限公司 | Voice coil motor with low friction force |
Also Published As
| Publication number | Publication date |
|---|---|
| CN113941085A (en) | 2022-01-18 |
| CN113244526A (en) | 2021-08-13 |
| CN113941086A (en) | 2022-01-18 |
| CN113244526B (en) | 2021-11-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN113941086B (en) | Manual auxiliary blood pumping device | |
| US10111996B2 (en) | Ventricular assist devices | |
| US10646630B2 (en) | Cantilevered rotor pump and methods for axial flow blood pumping | |
| US6723039B2 (en) | Methods, systems and devices relating to implantable fluid pumps | |
| EP3539584A1 (en) | Microaxial pump for assisting blood circulation (variants) | |
| US9616157B2 (en) | Blood pump | |
| AU683994B2 (en) | Cannula pumps for temporary cardiac support | |
| EP2506888B1 (en) | Total artificial heart | |
| US20060245959A1 (en) | Multiple rotor, wide blade, axial flow pump | |
| WO2003071932A2 (en) | Permanent heart assist system | |
| JP2017517306A (en) | Intravascular implantation pump | |
| CN106902404A (en) | Percutaneous auxiliary blood pumping device | |
| CN114215792A (en) | Micropump with totally-enclosed cleaning fluid circulating system | |
| CN204121481U (en) | Left ventricle assist axle pump | |
| CN111298225A (en) | Balloon heart counterpulsation device comprising electromagnet | |
| US11617875B2 (en) | Positive displacement shuttle pump heart and VAD | |
| Nosé | Totally implantable artificial organ: cardiac prosthesis | |
| CN114177516B (en) | High-flow two-stage catheter pump for left ventricle assistance and application method thereof | |
| TW202320881A (en) | Intravascular blood pump | |
| Fukui et al. | Development of the assisted artificial heart with linear motor actuator | |
| Gieras et al. | Electric motors for medical and clinical applications | |
| KR20240058137A (en) | intravascular blood pump | |
| De Paulis et al. | Bloodpumps | |
| Topaz et al. | History of the Kolff Laboratory turbine driven electrohydraulic artificial heart |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| CB02 | Change of applicant information | ||
| CB02 | Change of applicant information |
Country or region after: China Address after: No.36, Lane 100, Banxia Road, Pudong New Area, Shanghai, 201318 Applicant after: Fengkaili medical instrument (Shanghai) Co.,Ltd. Address before: No.36, Lane 100, Banxia Road, Pudong New Area, Shanghai, 201318 Applicant before: FORQALY MEDICAL (SHANGHAI) Co.,Ltd. Country or region before: China |
|
| GR01 | Patent grant |