CN215309683U - Heart auxiliary device in blood vessel - Google Patents
Heart auxiliary device in blood vessel Download PDFInfo
- Publication number
- CN215309683U CN215309683U CN202023225769.3U CN202023225769U CN215309683U CN 215309683 U CN215309683 U CN 215309683U CN 202023225769 U CN202023225769 U CN 202023225769U CN 215309683 U CN215309683 U CN 215309683U
- Authority
- CN
- China
- Prior art keywords
- motor
- impeller shaft
- impeller
- assist device
- heart assist
- 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
- 210000004204 blood vessel Anatomy 0.000 title description 4
- 239000007787 solid Substances 0.000 claims 1
- 238000012800 visualization Methods 0.000 claims 1
- 239000008280 blood Substances 0.000 abstract description 28
- 210000004369 blood Anatomy 0.000 abstract description 28
- 230000004217 heart function Effects 0.000 abstract description 11
- 230000006870 function Effects 0.000 abstract description 6
- 230000005540 biological transmission Effects 0.000 abstract description 4
- 230000007812 deficiency Effects 0.000 abstract description 4
- 206010019280 Heart failures Diseases 0.000 description 7
- 238000005086 pumping Methods 0.000 description 7
- 230000000747 cardiac effect Effects 0.000 description 6
- 238000000034 method Methods 0.000 description 6
- 238000011282 treatment Methods 0.000 description 6
- 230000002861 ventricular Effects 0.000 description 5
- 210000000709 aorta Anatomy 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 210000005240 left ventricle Anatomy 0.000 description 4
- 230000017531 blood circulation Effects 0.000 description 3
- 238000002054 transplantation Methods 0.000 description 3
- 230000001154 acute effect Effects 0.000 description 2
- 230000008034 disappearance Effects 0.000 description 2
- 239000003814 drug Substances 0.000 description 2
- 238000003698 laser cutting Methods 0.000 description 2
- 238000013146 percutaneous coronary intervention Methods 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 208000024891 symptom Diseases 0.000 description 2
- 206010018910 Haemolysis Diseases 0.000 description 1
- 206010024119 Left ventricular failure Diseases 0.000 description 1
- 206010034567 Peripheral circulatory failure Diseases 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- 230000009471 action Effects 0.000 description 1
- 238000009098 adjuvant therapy Methods 0.000 description 1
- 210000001765 aortic valve Anatomy 0.000 description 1
- 206010003119 arrhythmia Diseases 0.000 description 1
- 230000006793 arrhythmia Effects 0.000 description 1
- 230000004872 arterial blood pressure Effects 0.000 description 1
- 210000001367 artery Anatomy 0.000 description 1
- 238000013473 artificial intelligence Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 210000005242 cardiac chamber Anatomy 0.000 description 1
- 206010007625 cardiogenic shock Diseases 0.000 description 1
- 208000029078 coronary artery disease Diseases 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 208000035475 disorder Diseases 0.000 description 1
- 229940079593 drug Drugs 0.000 description 1
- 230000004064 dysfunction Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 210000001105 femoral artery Anatomy 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 230000008588 hemolysis Effects 0.000 description 1
- 230000003211 malignant effect Effects 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
- 208000031225 myocardial ischemia Diseases 0.000 description 1
- 230000009090 positive inotropic effect Effects 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 230000033764 rhythmic process Effects 0.000 description 1
- 208000011580 syndromic disease Diseases 0.000 description 1
- 238000011277 treatment modality Methods 0.000 description 1
- 210000003462 vein Anatomy 0.000 description 1
- 238000003466 welding Methods 0.000 description 1
Images
Abstract
The utility model discloses an intravascular heart assist device, which comprises: a driving part including a motor and a motor case; a body part including an inflow chamber, a sleeve, an outflow chamber, and an impeller, the inflow chamber being connected to the sleeve, the sleeve being connected to the outflow chamber, the outflow chamber being connected to the driving part; the impeller is arranged in the sleeve and/or the outflow chamber; the impeller comprises an impeller shaft and blades arranged on the periphery of the impeller shaft; the outflow end of the impeller shaft is directly connected with the output shaft of the motor. According to the utility model, through the structural design of the driving part and the body part, the motor drives the blood to flow as the driving element, the function of the heart of the patient is not limited, the patient with serious heart function deficiency can use the motor, and the problem that the IABP cannot be suitable for the patient with serious heart function deficiency is solved. And further, the motor is directly connected with the impeller shaft, a built-in transmission device is not needed, the designed rotating speed of the motor can be directly transmitted to the impeller shaft, the high-speed rotation is ensured without energy loss, the volume of the auxiliary device is reduced, and the adaptability is improved.
Description
Technical Field
The utility model relates to the technical field of interventional medical instruments, in particular to an intravascular heart assist device.
Background
Heart failure is primarily characterized by failure of the heart to function adequately, resulting in failure of blood to drain from the veins and failure of adequate blood to be obtained from the arteries, thereby causing a cardiac circulatory disorder syndrome. Left heart failure is generally more common. In the existing traditional heart failure treatment, the medicine is mainly used in the early and middle stages, and the heart transplantation is adopted as the effective treatment in the final stage, but the heart transplantation is the only treatment way for severe heart failure patients. However, heart transplantation needs to be greater than supplies and patients often suffer from lengthy waiting periods. Left Ventricular Assist Device (LVAD) has therefore emerged as a transitional treatment modality. Conventionally, a blood pump is implanted outside the apex of the heart through a surgical thoracotomy, and blood paths on two sides of the blood pump respectively enter the left ventricle through the apex of the heart and enter the blood vessel through the aorta, so that a path for pumping the blood in the left ventricle into the aorta is realized. The control unit is arranged outside the body and worn by a patient, and the control pipeline is connected with the blood pump through the skin. The service life can last at least 2 years. Heart failure may also occur as a complication or acute symptom, and there are common cases: (1) high-risk coronary disease patients need to receive Percutaneous Coronary Intervention (PCI), such patients often have heart failure, and meanwhile, myocardial ischemia or arrhythmia may occur during the treatment process, so that the patients are difficult to tolerate, and the risk of malignant hemodynamics exists, so that the heart chamber, especially the left chamber, needs to be restored by a heart auxiliary device during the treatment process; (2) cardiogenic shock is a very advanced manifestation of heart failure, with severe heart failure causing acute peripheral circulatory failure. This sudden illness also requires a quick and efficient heart assist device to help the patient restore ventricular function and relieve symptoms. These two types of patients do not have an excessively long usage time for the ventricular assist device, and are only used as an adjuvant therapy, and the traditional LVAD operation mode and the larger size are not suitable. A rapid, efficient, safe, small and easy-to-operate percutaneous left ventricle auxiliary device is produced.
At present, a main percutaneous catheter ventricular assist device is an Intra-aortic balloon pump (IABP), which is punctured through a femoral artery, a catheter with a balloon is placed in the aorta, and the balloon is inflated, expanded and emptied correspondingly according to a cardiac cycle to realize an auxiliary blood pumping function. However, when the device is used, the heart rhythm synchronization is needed, and medicines with positive inotropic action on the heart are supplemented, the myocardial contractility is enhanced, and the cardiac output is improved, so the complexity and the limitation of the IABP clinical operation are increased, especially for patients with serious cardiac function deficiency, the IABP cannot provide an effective treatment environment, and meanwhile, the introduction of the air bag increases the operation risk.
In view of the above, there is an urgent need to improve the conventional ventricular assist device and provide a cardiac assist device suitable for patients with severe cardiac dysfunction.
SUMMERY OF THE UTILITY MODEL
The utility model discloses an intravascular heart assist device, which is used for solving the problem that an IABP (artificial intelligence BP) technology in the prior art cannot be suitable for patients with serious heart function deficiency and further solving the problem that an implanted assist device is too long.
In order to solve the problems, the utility model adopts the following technical scheme:
provided is an intravascular heart assist device, comprising:
a driving part including a motor and a motor case disposed outside the motor;
a body part including an inflow chamber, a sleeve, an outflow chamber, and an impeller, the inflow chamber being connected with the sleeve, the sleeve being connected with the outflow chamber, the outflow chamber being connected with the driving part;
the impeller is disposed within the cannula and/or the outflow chamber;
the impeller comprises an impeller shaft and at least two blades arranged on the periphery of the impeller shaft, the blades are arranged at intervals on the periphery of the impeller shaft, the blades are approximately spiral, and the blades extend from the inflow end to the outflow end of the impeller shaft; one side of the outflow end of the impeller shaft is directly connected with the output shaft of the motor.
In the above scheme, the inflow end of the impeller shaft is a spherical structure, and the impeller shaft is a three-dimensional structure with a diameter increasing from the inflow end to the outflow end and in a cross section perpendicular to the axis of the impeller shaft.
In the scheme, the length of the impeller shaft is 5-7 mm, the diameter of the impeller shaft is 1.5-4 mm, and the inflow angle between the blade and the impeller shaft is 10-30 DEG
In the scheme, the length of the impeller shaft is 7-10 mm, the diameter of the impeller shaft is 1.5-4 mm, and the inflow angle between the blade and the impeller shaft is 20-40 degrees.
In the above scheme, the method further comprises: and the controller is in signal connection with the motor and is used for controlling the speed of the motor for driving the impeller.
In the above aspect, the outflow chamber includes a plurality of outflow chamber brackets, and the outflow chamber brackets are connected to the motor case.
In the above aspect, the outflow housing holder is substantially helical.
In the above aspect, the body portion further includes:
one end of the pump stator is connected with the motor box, the other end of the pump stator is arranged close to the impeller shaft, and the pump stator is arranged in the outflow chamber;
the periphery of pump stator sets up at least three stator, the stator is attached the inboard of outflow room support.
In the scheme, the inflow angle between the guide vane and the pump stator is 30-50 degrees.
In the above scheme, the method further comprises: an extension pipe connected with the inflow chamber.
In the above scheme, the method further comprises: the guide pipe is connected with the motor, and a circuit line used for being electrically connected with the motor is arranged in the guide pipe.
In the above scheme, at least one developing ring is arranged on the periphery of the sleeve in a pressing and holding mode.
In the above aspect, the outer diameter of the catheter is not greater than 7 mm.
In the above solution, the combined length of the impeller and the outflow chamber does not exceed 15mm, and the length of the motor does not exceed 25 mm.
In the above scheme, the blades are arranged in three pieces.
In the scheme, the rotating speed of the impeller shaft is 30000-50000 r/min.
The technical scheme adopted by the utility model can achieve the following beneficial effects:
through the structural design of drive division and body part, the motor is as drive element drive blood flow, and is unrestricted to patient's heart function own, and the serious patient of heart function disappearance also can use, has solved the problem that IABP can't be applicable to the serious patient of heart function disappearance among the prior art, and application scope is wide, has reduced the operation risk. And further, the motor is directly connected with the impeller shaft, a built-in transmission device is not needed, the motor can stably control the impeller shaft, the designed rotating speed of the motor can be directly transmitted to the impeller shaft, the high-speed rotation is ensured without energy loss, the length of the auxiliary device is shortened, the size is reduced, the operation is convenient, and the adaptability is improved.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings used in the description of the embodiments will be briefly introduced below to form a part of the present invention, and the exemplary embodiments and the description thereof illustrate the present invention and do not constitute a limitation of the present invention. In the drawings:
fig. 1 is a schematic overall structure diagram of an intravascular heart assist device disclosed in embodiment 1 of the present invention;
fig. 2 is a front view of the intravascular heart assist device disclosed in embodiment 1 of the present invention;
FIG. 3 is a schematic view of an inflow chamber of an intravascular cardiac assist device disclosed in example 1 of the present invention;
FIG. 4 is a schematic view of the impeller and motor connection of the endovascular heart assist device disclosed in example 1 of the present invention;
FIG. 5 is a front view of the impeller and motor connection of the intravascular heart assist device disclosed in embodiment 1 of the present invention;
fig. 6 is a perspective view of an impeller of the intravascular heart assist device disclosed in embodiment 1 of the present invention;
FIG. 7 is a front view of the impeller of the endovascular heart assist device disclosed in embodiment 1 of the present invention;
FIG. 8 is a perspective view of another preferred embodiment of the impeller of the endovascular heart assist device disclosed in example 1 of the present invention;
FIG. 9 is a front view of another preferred embodiment of the impeller of the endovascular heart assist device disclosed in embodiment 1 of the present invention;
FIG. 10 is a schematic view of the impeller and motor connection of the endovascular heart assist device disclosed in embodiment 2 of the present invention;
FIG. 11 is a front view of the impeller and motor connection of the endovascular heart assist device disclosed in embodiment 2 of the present invention;
fig. 12 is a perspective view of the impeller of the endovascular heart assist device disclosed in embodiment 3 of the present invention;
fig. 13 is a front view of the impeller of the endovascular heart assist device disclosed in embodiment 3 of the present invention.
The following reference signs are specifically included:
a motor-10; impeller-20; an outflow chamber-30; a sleeve-40; an inflow chamber-50; an extension tube-60; a conduit-70; an impeller shaft-21; a blade-22; a pump stator-23; a guide vane-24; an effluent chamber support-31; a developing ring 41; blood inlet-51.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the technical solutions of the present invention will be clearly and completely described below with reference to the specific embodiments of the present invention and the accompanying drawings. It is to be understood that the described embodiments are merely exemplary of the utility model, and not restrictive of the full scope of the utility model. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Example 1
As shown in fig. 1 to 5, the intravascular heart assist device provided by the utility model comprises a driving part, a driving part and a control part, wherein the driving part comprises a motor 10 and a motor box arranged outside the motor 10; the main body part includes an inflow chamber 50, a sleeve 40, an outflow chamber 30, and an impeller 20, the inflow chamber 50 is connected to the sleeve 40, the sleeve 40 is connected to the outflow chamber 30, and the outflow chamber 30 is connected to the driving part.
The impeller 20 is disposed within the sleeve 40 and/or the outflow chamber 30. The impeller 20 comprises an impeller shaft 21 and at least two blades 22 arranged on the periphery of the impeller shaft 21, the blades 22 are arranged at intervals on the periphery of the impeller shaft 21, the blades 22 are approximately spiral, and the blades 22 extend from the inflow end to the outflow end of the impeller shaft 21; the outflow end side of the impeller shaft 21 is directly connected to the output shaft of the motor 10.
Through the structural design of the driving part and the body part, the motor 10 is used as a driving element to drive blood to flow, the function of the heart of a patient is not limited, the patient with serious heart function loss can use the motor, and the problem that the IABP in the prior art cannot be suitable for the patient with serious heart function loss is solved. Further motor 10 and impeller shaft 21 lug connection need not built-in transmission, have guaranteed that motor 10 can stable control impeller shaft 21, and the design rotational speed of motor 10 can directly be conducted to impeller shaft 21 moreover, guarantee that high-speed rotation does not have the energy loss to make auxiliary device length shorten, the volume reduces, makes things convenient for the operation, has improved the adaptability.
In the present embodiment, the inflow end of the impeller shaft 21 is preferably a spherical structure, and the impeller shaft 21 is a three-dimensional structure in which the diameter of the cross section perpendicular to the axis of the impeller shaft 21 increases from the inflow end to the outflow end.
Referring to fig. 6 to 9, it is preferable that the number of the blades 22 is 2 or 3, the length of the impeller shaft 21 is 5mm to 7mm, the diameter thereof is 1.5mm to 4mm, and the inflow angle between the blades 22 and the impeller shaft 21 is 10 to 30 °.
In a preferred embodiment, as shown in fig. 8 and 9, the vanes 22 are 3 pieces. The design of the inflow angle between the blades 22 and the impeller shaft 21 can effectively reduce the phenomena of rotational flow, mixed flow and hemolysis inevitably generated when the impeller 20 pumps blood, and ensure the axial kinetic energy with the best effect of pumping blood. Since the number of blades 22 is approximately proportional to the amount of energy that the impeller shaft 21 can provide to the blood flow, providing three blades 22 provides better pumping.
In the present embodiment, the inflow chamber 50 is preferably fixed to the sleeve 40, and the outflow chamber 30 is preferably fixed to the driving unit.
The device provided by the utility model also comprises: and the controller is in signal connection with the motor 10 and is used for controlling the speed of the motor 10 for driving the impeller 20.
The outflow chamber 30 includes a plurality of outflow chamber holders 31, and the outflow chamber holders 31 are connected to the motor case. In the present embodiment, the connection is preferably made by welding, the effusion cell holder 31 is formed by laser cutting, and the effusion cell holder 31 is substantially spiral-shaped. The outflow chamber holder 31 is designed to conform to the outflow direction of blood.
The body portion further includes: one end of the pump stator 23 is connected with the motor box, the other end of the pump stator 23 is arranged close to the impeller shaft 21, and the pump stator 23 is arranged inside the outflow chamber 30; at least one guide vane 24 is arranged on the periphery of the pump stator 23, and the guide vane 24 is attached to the inner side of the outflow chamber bracket 31. Preferably, the outflow housing holder 31 conforms completely to the shape of the guide vane 24. The fluid design of the outflow chamber 30 and the pump stator 23 is not affected by the ease of assembly, and the rotational energy of the blood flow pumped out of the outflow chamber 30 is further converted into axial kinetic energy, and the blood is made to flow along the motor housing, somewhat reducing the temperature at the surface of the high speed motor 10. The length of the pump stator 23 can be properly shortened, so that the whole size is smaller, and the requirement of clinical intervention through blood vessels with different inner diameters is met.
In the embodiment, the inflow angle between the guide vane 24 and the pump stator 23 is preferably 30-50 °, so that the axial kinetic energy with the best blood pumping effect is ensured.
The device provided by the utility model also comprises: the extension pipe 60 is connected to the inflow chamber 50, and preferably, the extension pipe 60 is fixed to the inflow chamber 50. A conduit 70 connected to the motor 10, preferably, the conduit 70 is fixed to the motor 10, and a circuit line is provided in the conduit 70 for electrically connecting to the motor 10.
At least one developing ring 41 is press-fitted to the outer periphery of the sleeve 40. In operation, the position of the sleeve 40 is determined by observing the developer ring 41.
The inflow chamber 50 is further provided with at least one blood inlet 51, the blood inlet 51 is formed by laser cutting, and blood enters the sleeve 40 from the blood inlet 51.
In the present embodiment, it is preferable that the outer diameter of the duct 70 is not more than 7mm, the combined length of the impeller 20 and the outflow chamber 30 (the total length from the tip on the inflow end side of the impeller 20 to the tip on the outflow end side of the outflow chamber 30) is not more than 15mm, and the length of the motor 10 is not more than 25 mm. The whole volume is small, the operation is convenient, and the application range is wide.
The rotating speed of the impeller shaft 21 is 30000-50000 r/min, and the rotating speed of the impeller shaft 21 is 40000r/min in the embodiment.
In the utility model, the using method of the intravascular heart assist device comprises the following steps:
the elongated tube 60, the inflow chamber 50, the cannula 40 are positioned through the aortic valve into the left ventricle through the catheter 70, and the impeller 20, the outflow chamber 30, the motor 10 are positioned in the ascending aorta. The circuit lines controlling the motor 10 are in signal connection with an extracorporeal controller along the conduit 70 within the lumen of the conduit 70. The motor 10 drives the impeller shaft 21 to rotate at a high speed in blood, and positive and negative pressures are generated on both surfaces of the blades 22, respectively. The negative pressure has a flow suction effect, the positive pressure has a flow discharge effect, the blood is pushed to flow axially under the combined action, enters from the blood inlet 51 of the inflow chamber 50, passes through the sleeve 40, is discharged from the outflow chamber 30, and is continuously pumped, so that the average arterial pressure is 60-80 mmHg, and the pumping flow is not lower than 3L/min.
Practice ofExample 2
As shown in fig. 10 and 11, unlike embodiment 1, the present embodiment does not include a pump stator, thereby simplifying the overall structure, reducing the contact area between blood and foreign matter, and reducing the probability of thrombus formation. In a preferred embodiment of this example 2, the impeller 20 may be partially disposed within the sleeve 40 and another portion located within the outflow chamber 30. Preferably, only a small portion of the impeller 20 is located within the outflow chamber 30.
As a preferable mode, in example 2, a part of the driving portion, that is, a partial region of the motor case in the vicinity of the motor output shaft, protrudes into the outflow chamber 30. This preferred solution provides a very compact structure, enabling the auxiliary device to provide a shorter overall length.
Example 3
As shown in fig. 12 and 13, unlike example 1, in this example, the impeller shaft 21 has a length of 7mm to 10mm and a diameter of 1.5mm to 4mm, and preferably, the impeller shaft 21 has a length of 2 mm to 4mm longer than the impeller shaft 21 of example 1, and in a preferred embodiment, the impeller shaft 21 has a length of 3mm longer than the impeller shaft 21 of example 1.
In the present embodiment, the number of the blades 22 is preferably 3, and the inflow angle of the blades 22 to the impeller shaft 21 is preferably 20 to 40 °.
By adjusting the shape and size of the impeller shaft 21 and the rotating curved surface of the blades 22, the flow of blood along the impeller shaft 21 and the shear stress of the blades 22 are improved, and the compatibility of blood pumping efficiency and blood compatibility is realized.
According to the utility model, through the structural design of the driving part and the body part, the motor is used as a driving element to drive blood to flow, so that the function of the heart of a patient is not limited, the patient with serious heart function loss can use the motor, the problem that the IABP in the prior art cannot be suitable for the patient with serious heart function loss is solved, the application range is wide, and the operation risk is reduced. And further, the motor is directly connected with the impeller shaft, a built-in transmission device is not needed, the motor can stably control the impeller shaft, the designed rotating speed of the motor can be directly transmitted to the impeller shaft, the high-speed rotation is ensured without energy loss, the length of the auxiliary device is shortened, the size is reduced, the operation is convenient, and the adaptability is improved.
While the present invention has been described with reference to the embodiments shown in the drawings, the present invention is not limited to the embodiments, which are illustrative and not restrictive, and it will be apparent to those skilled in the art that various changes and modifications can be made therein without departing from the spirit and scope of the utility model as defined in the appended claims.
Claims (16)
1. An intravascular heart assist device, comprising:
a driving part including a motor and a motor case disposed outside the motor;
a body part including an inflow chamber, a sleeve, an outflow chamber, and an impeller, the inflow chamber being connected with the sleeve, the sleeve being connected with the outflow chamber, the outflow chamber being connected with the driving part;
the impeller is disposed within the cannula and/or the outflow chamber;
the impeller comprises an impeller shaft and at least two blades arranged on the periphery of the impeller shaft, the blades are arranged at intervals on the periphery of the impeller shaft, the blades are approximately spiral, and the blades extend from the inflow end to the outflow end of the impeller shaft; one side of the outflow end of the impeller shaft is directly connected with the output shaft of the motor.
2. The endovascular heart assist device of claim 1, wherein the inflow end of the impeller shaft is of spherical configuration, and the impeller shaft is of solid configuration with increasing diameter in a cross-section perpendicular to the axis of the impeller shaft from the inflow end to the outflow end.
3. The endovascular heart assist device of claim 1, wherein the impeller shaft has a length of 5mm to 7mm, the impeller shaft has a diameter of 1.5mm to 4mm, and the inflow angle of the vane to the impeller shaft is 10 ° to 30 °.
4. The endovascular heart assist device of claim 1, wherein the impeller shaft has a length of 7mm to 10mm, a diameter of 1.5mm to 4mm, and an inflow angle of the vane to the impeller shaft is 20 to 40 °.
5. The endovascular heart assist device of claim 1, further comprising: and the controller is in signal connection with the motor and is used for controlling the speed of the motor for driving the impeller.
6. The endovascular heart assist device of claim 1, wherein the outflow chamber comprises a plurality of outflow chamber brackets, the outflow chamber brackets being connected to the motor housing.
7. The endovascular heart assist device of claim 6, wherein the outflow housing stent is generally helical.
8. The endovascular heart assist device of claim 1, wherein the body portion further comprises:
one end of the pump stator is connected with the motor box, the other end of the pump stator is arranged close to the impeller shaft, and the pump stator is arranged in the outflow chamber;
the periphery of pump stator sets up at least three stator, the stator is attached the inboard of outflow room support.
9. The endovascular heart assist device of claim 8, wherein an inflow angle of the guide vane to the pump stator is 30-50 °.
10. The endovascular heart assist device of claim 1, further comprising: an extension pipe connected with the inflow chamber.
11. The endovascular heart assist device of claim 1, further comprising: the guide pipe is connected with the motor, and a circuit line used for being electrically connected with the motor is arranged in the guide pipe.
12. The endovascular heart assist device of claim 1, wherein the sleeve is crimped around its periphery with at least one visualization ring.
13. The endovascular heart assist device of claim 11, wherein the catheter has an outer diameter of no greater than 7 mm.
14. The endovascular heart assist device of claim 1, wherein the combined length of the impeller and outflow chamber is no more than 15mm, and the length of the motor is no more than 25 mm.
15. The endovascular heart assist device of claim 1, wherein the vane is provided in three pieces.
16. The endovascular heart assist device of claim 1, wherein the impeller shaft rotates at a speed of 30000-50000 r/min.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202023225769.3U CN215309683U (en) | 2020-12-28 | 2020-12-28 | Heart auxiliary device in blood vessel |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202023225769.3U CN215309683U (en) | 2020-12-28 | 2020-12-28 | Heart auxiliary device in blood vessel |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN215309683U true CN215309683U (en) | 2021-12-28 |
Family
ID=79570627
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202023225769.3U Active CN215309683U (en) | 2020-12-28 | 2020-12-28 | Heart auxiliary device in blood vessel |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN215309683U (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20230086096A1 (en) * | 2021-09-17 | 2023-03-23 | Abiomed, Inc. | Intravascular blood pump |
| WO2023226779A1 (en) * | 2022-05-24 | 2023-11-30 | 苏州心岭迈德医疗科技有限公司 | Catheter interventional heart pump |
| WO2024037119A1 (en) * | 2022-08-18 | 2024-02-22 | 航天泰心科技有限公司 | Interventional blood pump with outlet flow guide structure |
-
2020
- 2020-12-28 CN CN202023225769.3U patent/CN215309683U/en active Active
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20230086096A1 (en) * | 2021-09-17 | 2023-03-23 | Abiomed, Inc. | Intravascular blood pump |
| WO2023226779A1 (en) * | 2022-05-24 | 2023-11-30 | 苏州心岭迈德医疗科技有限公司 | Catheter interventional heart pump |
| WO2024037119A1 (en) * | 2022-08-18 | 2024-02-22 | 航天泰心科技有限公司 | Interventional blood pump with outlet flow guide structure |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN215309683U (en) | Heart auxiliary device in blood vessel | |
| CN106512117B (en) | Flexible transmission system, percutaneous auxiliary blood pumping device and intravascular thrombus aspiration system | |
| JP5339161B2 (en) | Manifold | |
| EP3471794B1 (en) | Self-propelled venous blood pump | |
| JP4022372B2 (en) | Non-thoracotomy aortic balloon type ventricular assist device | |
| US4625712A (en) | High-capacity intravascular blood pump utilizing percutaneous access | |
| US20040024285A1 (en) | Blood pump with impeller | |
| CN105498002A (en) | Blood pumping impeller | |
| WO2023134695A1 (en) | Catheter pump housing structure and catheter pump apparatus | |
| WO2023134693A1 (en) | Blood pumping device | |
| CN113153804B (en) | Blood pumping impeller and ventricular assist device | |
| CN111097077B (en) | External magnetic drive liquid suspension axial-flow type blood pump | |
| JPH04176471A (en) | Circulation auxiliary pump | |
| CN219148993U (en) | Interventional type heart and kidney combined auxiliary assembly | |
| JP2004057817A (en) | Blood pump with impeller | |
| CN216571189U (en) | Heart blood pump | |
| CN115192893A (en) | Left ventricle auxiliary device | |
| CN114602055A (en) | Multistage catheter blood pump for emergency type rapid minimally invasive implantation | |
| CN219539244U (en) | Outflow chamber and device for ventricular assist device | |
| CN113769259A (en) | Extracorporeal circulation magnetic suspension axial flow blood pump | |
| CN219804146U (en) | External magnetic suspension centrifugal ventricular assist device implanted through periphery | |
| CN115779257B (en) | Interventional catheter pump | |
| CN219539243U (en) | Outflow chamber and device for ventricular assist device | |
| CN216136569U (en) | Aorta internal circulation auxiliary blood pump rotor | |
| CN113153805B (en) | Blood pumping impeller and ventricular assist device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CP01 | Change in the name or title of a patent holder |
Address after: Room 301, No.23, Lane 908, Ziping Road, Zhoupu Town, Pudong New Area, Shanghai, 201321 Patentee after: Shanghai newpulse Medical Technology Co.,Ltd. Address before: Room 301, No.23, Lane 908, Ziping Road, Zhoupu Town, Pudong New Area, Shanghai, 201321 Patentee before: SHANGHAI NEWMED MEDICAL Co.,Ltd. |
|
| CP01 | Change in the name or title of a patent holder | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20230313 Address after: 201321 Floor 4, No. 6, Lane 500, Furonghua Road, Pudong New Area, Shanghai Patentee after: Shanghai Huanqing Medical Technology Co.,Ltd. Address before: Room 301, No.23, Lane 908, Ziping Road, Zhoupu Town, Pudong New Area, Shanghai, 201321 Patentee before: Shanghai newpulse Medical Technology Co.,Ltd. |
|
| TR01 | Transfer of patent right |