CN112316297A - Hollow heart auxiliary pump - Google Patents
Hollow heart auxiliary pump Download PDFInfo
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- CN112316297A CN112316297A CN202011209272.4A CN202011209272A CN112316297A CN 112316297 A CN112316297 A CN 112316297A CN 202011209272 A CN202011209272 A CN 202011209272A CN 112316297 A CN112316297 A CN 112316297A
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Abstract
The invention discloses a hollow heart auxiliary pump which comprises a shell, a motor and a permanent magnet, wherein two ends of the shell are open ends, the motor is attached to the inner side of the shell, the permanent magnet is arranged on the inner side of the motor, a blood channel is formed on the inner side of the permanent magnet, a spiral blade is arranged on the inner wall of the permanent magnet, and when the hollow heart auxiliary pump is used, the blood channel is directly communicated with ascending aorta or pulmonary artery. According to the invention, the motor and the permanent magnet are sequentially arranged in the shell with openings at two ends in a clinging manner, the inner wall of the permanent magnet is provided with the helical blade, the center of the whole pump is free of column and is of a hollow structure, a blood channel is formed, the whole size of the pump can be reduced, foreign matters in blood can be reduced, infection can be reduced, and thrombosis can be avoided.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a hollow heart auxiliary pump.
Background
In the case of extremely scarce heart donors, the use of mechanical aids to assist the pumping of the heart brings new survival hopes to the end-stage heart failure patients. The basic principle is to pump blood from a failing heart into the aortic system.
There are mainly 2 types of heart assist pumps in clinical use: heartbeat-II, heartbeat-III are centrifugal pumps that rely on centrifugal force to provide power for blood flow; Heartrate-II is an axial flow pump, accelerated by blades, and provides power for blood flow.
The two heart assist pumps have the following common points:
1) the inlets are arranged at the apex of the left ventricle heart, a round incision is made at the apex of the left ventricle heart by a surgical means, the artificial blood vessel is sutured to the apex of the left ventricle heart and is connected with an artificial auxiliary pump; 2) the outlets are all positioned in ascending aorta; 3) and blood flow direction: the blood passes through the failing left ventricle, bypasses the aortic valve (located at the aortic root), and reaches the aorta, forming a bypass circulation; 4) the auxiliary pump is arranged between the heart and the diaphragm muscle, and the volume is large; 5) both are persistent blood flow; 6) and no valve exists between the left ventricle, the artificial auxiliary pump and the aorta, and the blood in the aorta is prevented from flowing back to the ventricle by depending on the pressure obtained by the rotating speed of the auxiliary pump in the diastole; 7) there are many foreign bodies in the blood stream, and more foreign bodies in the axial flow pump (heartbeat-II).
The two heart auxiliary pumps have the following defects:
1) right ventricle wall is thin, so that huge tension caused by an artificial auxiliary pump cannot be borne; b. the right ventricle is smaller, and the artificial blood vessel is sutured without space; c. a narrow chest cavity cannot be assisted with bixin help); 2) during the heart fibrillation, the auxiliary pump can not work; at the moment, the right ventricle can not pump blood into the lung, so that the left heart system receiving the pulmonary circulation blood is empty and deficient, and the auxiliary system can not work; 3) continuously pumping blood from the apex of the left ventricle; the operation trauma is large; 4) and control difficulty: when the pump speed is too high, negative pressure is generated in the heart chamber, and the wall of the heart chamber is tightly attached to block the inlet of the pump; if a large negative pressure spike occurs in the ventricle, it will result in: a. stopping the pump; b. sudden cessation of blood flow; the blood flows backwards, the ventricle is opened again, the auxiliary pump works again, and the forward blood flow is started again; 5) the continuous blood flow is different from the normal pulsating blood flow, which causes poor perfusion of important organs; 6) when the heart is completely exhausted, the valve can not be opened, the valve is adhered, and thrombus is formed in the heart chamber and close to the valve; 7) when the heart function is recovered, the blood flow speed in the pump is slow, and the risk of thrombus in the pump is increased; 8) more foreign bodies exist in the blood flow, and the risk of thrombosis is further increased; 9) for the axial flow pump (regenerative-II), the large distance between the rotor and the motor not only causes great loss of energy, but also heat generation, thereby increasing related complications; but also reduces the effective flow area of the blood flow; 10) the risk of infection is increased by longer artificial blood vessels, vessel walls and the like except for foreign matters contacting with blood flow; 11) the problems of anticoagulation and bleeding are prominent.
Thus, the current Heartrate-III, and in particular Heartrate-II, patients have a high incidence of complications and mortality.
Disclosure of Invention
The invention aims to provide a hollow heart auxiliary pump, which solves the problems that the existing heart auxiliary pump can not realize right ventricle assistance, has large operation wound and is easy to cause thrombosis, can reduce foreign matters in blood and infection, and has the advantage of small integral size.
The invention is realized by the following technical scheme:
the utility model provides a cavity heart assist pump, includes shell, motor and permanent magnet, the both ends of shell are the beginning, the motor subsides are established at the shell inboardly, the permanent magnet sets up at the motor inboardly, the permanent magnet inboard forms the blood passageway, the inner wall of permanent magnet is provided with helical blade, and during the use, the blood passageway is direct and ascending aorta or pulmonary artery intercommunication.
Preferably, the shell, the motor and the permanent magnet are coaxially arranged, the number of the helical blades is not limited, at least one helical blade is arranged, and the specific number is designed according to actual needs.
The integral structure of the hollow heart auxiliary pump is that a power motor system (comprising a coil) is arranged outside; the annular permanent magnet is abutted against the inner side of the annular permanent magnet, the permanent magnet is kept to rotate, the motor is not moved, the innermost side in the permanent magnet is connected with a pump blade (helical blade) which is spirally ascended and used for accelerating blood flow, the helical blade can reduce the impact on the blood flow, a hollow blood channel is formed on the inner side of the magnet, and the hollow design has the advantages that:
1) the motor system is close to the annular permanent magnet, so that energy consumption, work increase and heat generation caused by a long-distance magnetic field are avoided, and meanwhile, the power of the motor can be reduced, so that the miniaturization of the manual auxiliary pump is possible; 2) only the pump blade and the rotary cavity (inner wall of the permanent magnet) are contacted with blood, so that the contact between the blood and the surface of foreign matters is reduced to the maximum extent; 3) and the blood flow center has no foreign matters. These advantages result in reduced auxiliary pump power consumption, reduced heat generation, reduced irritation to the blood, thereby reducing thrombus formation, anti-coagulant dependence, and risk of infection.
Because the installation position of the hollow heart auxiliary pump is changed due to the structural characteristics, the hollow heart auxiliary pump is different from the existing heart rate-II and heart rate-III, and the hollow heart auxiliary pump is not accessed through the outlet of the heart apex and is installed on the artery (ascending aorta or pulmonary artery). When the left heart is needed to assist, the left heart is arranged on the ascending aorta; when the right ventricle is needed to assist, the right ventricle is arranged on the pulmonary artery; when full heart assistance is required, one ascending aorta and one pulmonary artery are respectively arranged.
The scheme for installing the empty heart auxiliary pump comprises the following two schemes:
the first scheme is as follows: after the chest is opened and the heart stops beating, the ascending aorta is blocked at a high position, the artery with the length of about 2cm is cut off, an artificial blood vessel is sutured at two ends and then cut off from the middle, and the invention is arranged at the broken end of the artificial blood vessel. In order to avoid cardiac ischemia, after the coronary artery is blocked at the proximal end, the blood vessel is used for bridging the main trunk of the left and right coronary arteries.
The advantage of this procedure is that the aortic valve is preserved; the left and right coronary arteries (ventricles) have blood flow in both systole and diastole (normal heart, left ventricular myocardium has no blood flow supply in systole), thereby increasing left ventricular blood flow and recovery of cardiac function; compared with the following operation scheme, the volume of the artificial auxiliary pump can be larger; the recovery of cardiac function can be judged using the power consumption and blood flow of the auxiliary pump; with the recovery of cardiac function, the artificial assist pump is easily removed. The disadvantage is that the coronary flow needs to be redirected because of the low pressure at the inlet end of the artificial assist pump (aortic root).
Scheme II: after the heart stops beating, the ascending aorta is blocked, the aortic/pulmonary root is dissected, the aortic/pulmonary valve is excised, and the artificial assist pump is installed in the left/right ventricular outflow tract.
The advantage of this procedure is that there is no need to redirect coronary blood flow. The disadvantage is that the aortic valve is destroyed; because the outflow tract is smaller, the manual auxiliary pump needs to be smaller; after the prosthetic pump is removed, a valve replacement procedure is required.
The mounting position of the invention has the advantages that:
1) the hollow heart auxiliary pump is connected with the failing ventricle in parallel, so that a normal heart blood flow passage can be kept unchanged, the flow speed is high, and normal blood flow can be maintained; 2) the problem of thrombosis caused by the 'fight' between the artificial auxiliary pump and the heart is solved; 3) blood enters the aorta through the failing heart, the valve and the artificial auxiliary pump, so that the valve can keep a normal opening and closing period; the problem of valve adhesion is avoided; 4) different auxiliary modes can be selected according to different heart failure types of patients; 5) when the biventricular assist is implemented, even if ventricular fibrillation occurs to a patient, normal blood flow can still be maintained through the cooperative work of the double pumps.
The working principle of the invention is as follows:
when the blood spiral type heart assist pump is used, the hollow heart assist pump is directly arranged on ascending aorta or pulmonary artery, under the power of a magnetic field provided by the motor, the permanent magnet rotates to further drive the spiral blade to rotate, and blood at the inlet end is spirally led into the outlet end to maintain normal blood flow.
In conclusion, the motor and the permanent magnet are sequentially arranged in the shell with the openings at the two ends in a clinging manner, the inner wall of the permanent magnet is provided with the helical blade, the center of the whole pump is free of column and is of a hollow structure, a blood channel is formed, the whole size of the pump can be reduced, foreign matters in blood can be reduced, infection can be reduced, and thrombosis can be avoided to the maximum extent. Due to the structural characteristics of the invention, the mounting position of the pump is changed, so that the blood path is changed, the thrombosis and valve adhesion can be avoided, the apical incision can be avoided, the operative wound is reduced, and the right ventricle assisting device can be used for right ventricle assistance.
The mechanism by which the invention can reduce thrombosis is as follows:
1) the blood flow through the heart and the artificial auxiliary pump is equal, the flow rate through the heart and the artificial auxiliary pump is higher no matter what functional state the heart is in, and the problem of competition between the heart and the artificial auxiliary pump does not exist, so that the risk of thrombus caused by smaller blood flow in the heart and the artificial auxiliary pump is reduced; the high-speed flowing blood also avoids the probability of attaching cells, fibrin, bacteria and the like, thereby prolonging the service life of the pump and reducing the risk of blood-borne infection.
2) Besides the necessary pump blade provides power, no other foreign matters exist in the blood flow. The center of the pump has no column, so that the activation effect on blood coagulation is reduced.
3) The motor and the permanent magnet are close to each other, so that useless work caused by prolonging of the conduction distance of the magnetic field is reduced, the work is converted into heat energy, and coagulation activation caused by increase of heat is reduced.
4) And because the tube walls of the pump blade and the permanent magnet rotate simultaneously, the 2 interact to provide power for blood flow. This makes the contact time of the blood with the vessel wall extremely short, further avoiding thrombosis; (currently available products, the tube walls are kept still).
Further, the spiral blade is in a spiral ascending trend from the inlet end to the outlet end of the hollow heart auxiliary pump, namely the slope of the spiral blade at the inlet end is relatively slow, and the slope of the outlet end is relatively steep, so that blood can be rapidly pumped from the inlet end to the outlet end.
Further, the one end of the wall connection of helical blade and permanent magnet forms the thickening link, the width of thickening link is greater than helical blade's width.
The width of the invention specifically refers to the radial width.
The thickened connecting end is specifically characterized in that the permanent magnet is connected with the spirally rising pump blade in a thickened mode, so that dead corners/dead cavities are further avoided, and the pump blade can bear higher pressure (generate power).
Further, the thickening link is the arc, the minimum width of thickening link is greater than helical blade's width.
Further, the outer wall of the shell is provided with fixing grooves at two ends.
The fixing groove is of an annular structure and is used for fixing the pump on the artificial blood vessel.
Further, the inner diameter of the blood passage is matched to the inner diameter of the ascending aorta or pulmonary artery.
The invention has larger diameter, which has the following advantages:
1) the effective blood circulation diameter of the artificial auxiliary pump can reach 1.5-2.5cm (for adults). Well above other auxiliary pumps (<1 cm); 2) the thicker effective area can reduce the rotation speed of the pump, and the effective blood ejection can be achieved under the condition that the increase of the pump speed is smaller; 3) this will reduce the activation and destruction of blood; 4) the small change of the pump speed can achieve the large change of the blood flow, so the regulation and control (pulsation and maintenance conversion) of the pump are easy; 5) even if the pump fails to work, the existing aortic valve is relied on to avoid the backflow of blood to the ventricle, thereby avoiding the expansion of the ventricle; depending on the larger diameter and hollow channel of the auxiliary pump, the blood flow ejected from the heart can still pass through the auxiliary pump without immediate death.
Further, the lateral wall both ends of shell all are provided with the arcwall face.
Further, the arcwall face is 1/4 arc surfaces, the tangent line at arcwall face both ends is parallel with the axial of shell and radial respectively.
The setting of above-mentioned arcwall face is convenient for be connected entry end and the exit end and the artificial blood vessel of cavity heart auxiliary pump on the one hand, and on the other hand can install photoelectric devices such as sensors on the arcwall face, for example pressure sensor.
Further, a certain gap is formed between the permanent magnet and the motor, and the gap is smaller than or equal to 3 mm.
The motor is actually a coil, and a very small gap is needed between the permanent magnet and the motor, so that collision and friction between the permanent magnet and the motor can be avoided, the distance between the permanent magnet and the motor is shortened, and further energy loss is reduced.
Further, still include blood flow speed control system, blood flow speed control system is including setting up the pressure sensor at cavity heart auxiliary pump entry end and exit end, and the controller, pressure sensor responds to the pressure of cavity heart auxiliary pump entry end and exit end in real time to transmit the pressure signal of response for the controller, make the analysis and send the instruction by the controller and adjust external power source's current-voltage, adjust the magnetic field that the motor produced through adjusting current-voltage, adjust the rotational speed of permanent magnet through changing the magnetic field, drive helical blade through the permanent magnet and rotate and realize blood flow speed and adjust.
The specific working process is as follows:
the inlet of the hollow heart assist pump was fitted with a baroreceptor (measured pressure P1). After the heart paces, the heart contracts, the pressure at the inlet end rises rapidly, and after the signal is transmitted into the control system of the artificial auxiliary pump, the control system changes the current/voltage of the auxiliary pump immediately, the rotating speed rises rapidly, and a rapid rising blood flow appears. Then diastole is carried out, the pressure at the inlet end is rapidly reduced, after the signal is transmitted into a control system of the artificial auxiliary pump, the control system immediately changes the current/voltage of the auxiliary pump, the rotating speed is rapidly reduced, and the blood flow speed is reduced.
The invention can realize the matching and the pulse perfusion of the pump and the autologous heart by arranging the blood flow speed control system: the rise and the decline of the blood flow velocity are matched with the self heart, and simultaneously, the effect of pulsation is achieved, the blood flow perfusion of important visceral organs can be improved through the pulsation perfusion, the incidence rate of organ failure is reduced, a pressure sensor (the measured pressure is P2) is installed at the outlet end, the rotating speed and the calculated flow of the pump can be controlled according to the difference value between P1 and P2, and the safety and the controllability of the pump are higher.
The assessment of cardiac function by the invention is easier:
through P1, P2, pump diameter; calculating the flow rate and the total work;
the heart does work as total work-the actual work of the pump. If the actual power is the calculated power, the heart is not functional; such as actual power < calculated power. The heart is functional and the difference between 2 can assess the heart function; power calculated as actual power >: there is a deposition of material such as fibers on the pump surface.
Further, the inner wall of shell is provided with the ring channel, motor and permanent magnet are all installed in the ring channel, the inner wall of permanent magnet flushes with the inner wall of shell.
The internal resistance of the pump can be avoided by the arrangement, the generation of blood vortex is avoided, and the flowing speed of blood in the pump is improved.
Furthermore, annular sliding grooves are formed in the upper end and the lower end of each annular groove, sliding blocks matched with the annular sliding grooves are arranged at the two end portions of each permanent magnet, the sliding blocks can slide in the annular sliding grooves, and the sliding blocks can stabilize the permanent magnets in the shell.
Furthermore, sealing rings are arranged at the positions where the two ends of the permanent magnet are contacted with the inner wall of the shell, and on one hand, the arrangement of the sealing rings can avoid blood from entering; on the other hand, the friction force between the shell and the permanent magnet can be reduced.
Furthermore, the motor-driven electric fan further comprises a connecting wire, wherein one end of the connecting wire is connected with the motor, and the other end of the connecting wire extends out of the shell.
The connecting wire can realize providing power, pressure monitoring and pump speed and adjust, is connected the tip and the external power source of connecting wire during the use, is the motor power supply by external power source, and the motor circular telegram produces magnetic field, makes the permanent magnet rotate through magnetic field.
Further, an external power source is connected to the controller, and there is a current and a voltage output by the controller.
Compared with the prior art, the invention has the following advantages and beneficial effects:
1. the hollow heart auxiliary pump is simple to install and small in wound.
2. The invention can realize the matching and the pulse perfusion of the pump and the autologous heart by arranging the blood flow speed control system: the rising and the falling of the blood flow speed are matched with the self heart, and simultaneously, the effect of pulsation is achieved, the pulsation perfusion can improve the blood flow perfusion of important visceral organs, and the incidence rate of organ failure is reduced.
3. The risk of forming thrombus by adopting the hollow heart auxiliary pump is reduced.
4. The pressure sensor (the measured pressure is P2) is arranged at the outlet end, so that the safety and controllability are higher.
5. The hollow heart assist pump of the present invention has a large diameter: the thicker effective area can reduce the rotation speed of the pump, and under the condition of smaller increase of the pump speed, effective blood ejection can be achieved, and the activation and damage to blood are reduced; the control (pulsation, maintenance and conversion) of the pump is easy; even if the pump fails to operate, the blood flow ejected from the heart can still pass through the auxiliary pump without immediate death.
6. The present invention provides for easier assessment of cardiac function.
7. The invention can assist the whole heart: when the left ventricle and the right ventricle are in failure at the same time, an auxiliary pump is respectively arranged on the aorta and the pulmonary artery, so that the whole heart can be assisted; relative independence: each ventricle needs different auxiliary procedures and feedback conditions; relative consistency: the beats of the left and right ventricles are identical, and the flow rates of the beats are identical within a certain time.
Drawings
The accompanying drawings, which are included to provide a further understanding of the embodiments of the invention and are incorporated in and constitute a part of this application, illustrate embodiment(s) of the invention and together with the description serve to explain the principles of the invention. In the drawings:
FIG. 1 is a schematic diagram of the overall structure of a hollow heart assist pump;
FIG. 2 is an axial cross-sectional view of a hollow heart assist pump;
FIG. 3 is a radial top view of a hollow heart assist pump;
FIG. 4 is a schematic structural view of the connection between the helical blade and the permanent magnet;
FIG. 5 is a schematic view of a hollow heart assist pump mounted on the ascending aorta;
FIG. 6 is a schematic view of a hollow heart assist pump installed in a pulmonary artery;
FIG. 7 is a schematic view of a hollow heart assist pump mounted on both the ascending aorta and the pulmonary artery.
Reference numbers and corresponding part names in the drawings:
1-shell, 2-motor, 3-permanent magnet, 4-helical blade, 5-connecting wire, 11-fixed groove, 12-arc surface and 41-thickened connecting end.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is further described in detail below with reference to examples and accompanying drawings, and the exemplary embodiments and descriptions thereof are only used for explaining the present invention and are not meant to limit the present invention.
Example 1:
as shown in fig. 1-4, a hollow heart auxiliary pump comprises a housing 1, a motor 2 and a permanent magnet 3, wherein both ends of the housing 1 are open ends, the motor 2 is attached to the inside of the housing 1, the permanent magnet 3 is disposed on the inside of the motor 2, a blood channel is formed on the inside of the permanent magnet 3, a helical blade 4 is disposed on the inner wall of the permanent magnet 3, the helical blade 4 has a helical ascending trend from an inlet end to an outlet end of the hollow heart auxiliary pump, and can guide blood at the inlet end into the outlet end in a helical manner, as shown in fig. 2, the upper end is the inlet end, and the lower end is the outlet end, when in use, the blood channel is directly communicated with an ascending aorta or a pulmonary artery, the inner diameter of the blood channel is matched with the inner diameter of the ascending aorta or the pulmonary artery, and a connecting wire 5 is further included, one end of, the motor 2 is a coil.
The number of the helical blades 4 is not limited, at least one helical blade is arranged, and the specific number is designed according to actual needs.
The working principle of the embodiment is as follows:
when the external power supply is started, the motor 2 is powered on, the motor 2 is electrified to generate a magnetic field, the permanent magnet 3 is rotated through the magnetic field, and the magnet 3 rotates to drive the helical blade 4 (pump blade) to rotate.
The hollow heart assist pump of the present embodiment can be installed on the ascending aorta, and as shown in fig. 5, when in use, the left and right coronary arteries need to be bridged (post-pump aorta blood vessel — left and right coronary arteries) to avoid myocardial ischemia caused by too low pressure at the blood inlet end.
The hollow heart assist pump of this embodiment can be mounted on the pulmonary artery, as shown in fig. 6, for right ventricular failure assist.
The hollow heart assist pump of this embodiment can be installed on the pulmonary artery and the ascending aorta as shown in fig. 7 for full heart failure assist.
Example 2:
as shown in fig. 1 to 4, in the present embodiment, based on embodiment 1, one end of the helical blade 4 connected to the inner wall of the permanent magnet 3 forms a thickened connecting end 41, and the width of the thickened connecting end 41 is greater than that of the helical blade 4.
Example 3:
as shown in fig. 1 to 4, in the present embodiment, based on embodiment 1, the outer wall of the housing 1 is provided with fixing grooves 11 at both ends; arc-shaped surfaces 12 are arranged at two ends of the side wall of the shell 1; the arc-shaped surface 12 is 1/4 arc-shaped surfaces, and the tangent lines at the two ends of the arc-shaped surface 12 are respectively parallel to the axial direction and the radial direction of the shell 1.
Example 4:
as shown in fig. 1-4, this embodiment is based on embodiment 1, and further includes a blood flow speed control system, where the blood flow speed control system includes pressure sensors disposed at an inlet end and an outlet end of the hollow heart assist pump, and a controller, the pressure sensors sense pressures at the inlet end and the outlet end of the hollow heart assist pump in real time, and transmit sensed pressure signals to the controller, the controller analyzes the sensed pressure signals and sends out instructions to adjust current and voltage of an external power supply, the magnetic field generated by the motor 2 is adjusted by adjusting the current and voltage, the rotation speed of the magnetic field adjusting permanent magnet 3 is changed, and the permanent magnet 3 drives the helical blade 4 to rotate to realize blood flow speed adjustment.
Example 5:
as shown in fig. 1 to 4, in the present embodiment, based on embodiment 1, the inner wall of the housing 1 is provided with an annular groove, the motor 2 and the permanent magnet 3 are both installed in the annular groove, and the inner wall of the permanent magnet 3 is flush with the inner wall of the housing 1.
Example 6:
as shown in fig. 1 to 4, in the present embodiment, based on embodiment 5, annular sliding grooves are provided at both the upper end and the lower end of the annular groove, and sliding blocks that are engaged with the annular sliding grooves are provided at both end portions of the permanent magnet 3, and the sliding blocks can slide in the annular sliding grooves, and can stabilize the permanent magnet 3 in the housing 1; sealing rings are arranged at the contact positions of the two ends of the permanent magnet 3 and the inner wall of the shell 1, and on one hand, the arrangement of the sealing rings can avoid blood from entering; on the other hand, the friction between the housing 1 and the permanent magnet 3 can be reduced.
Example 7:
as shown in fig. 1 to 4, in the present embodiment, based on embodiment 1, a certain gap is formed between the permanent magnet 3 and the motor 2, and the gap is not more than 3 mm.
The above-mentioned embodiments are intended to illustrate the objects, technical solutions and advantages of the present invention in further detail, and it should be understood that the above-mentioned embodiments are merely exemplary embodiments of the present invention, and are not intended to limit the scope of the present invention, and any modifications, equivalent substitutions, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (10)
1. The utility model provides a cavity heart assist pump, includes shell (1), motor (2) and permanent magnet (3), its characterized in that, the both ends of shell (1) are the beginning, motor (2) are pasted and are established in shell (1) inboard, permanent magnet (3) set up in motor (2) inboard, permanent magnet (3) inboard forms the blood passageway, the inner wall of permanent magnet (3) is provided with helical blade (4), and during the use, the blood passageway is direct and ascending aorta or pulmonary artery intercommunication.
2. Hollow heart assist pump according to claim 1, characterized in that the helical blades (4) have a helical ascending trend from the inlet end to the outlet end of the hollow heart assist pump.
3. Hollow heart assist pump according to claim 1, characterized in that the end of the helical blade (4) that is connected to the inner wall of the permanent magnet (3) forms a thickened connection end (41), the width of the thickened connection end (41) being greater than the width of the helical blade (4).
4. Hollow heart assist pump according to claim 1, characterized in that the outer wall of the housing (1) is provided with fixation grooves (11) at both ends.
5. The hollow heart assist pump of claim 1 wherein the blood passage has an inner diameter that matches an inner diameter of the ascending aorta or pulmonary artery.
6. Hollow heart assist pump according to claim 1, characterized in that the side walls of the housing (1) are provided with an arc-shaped surface (12) at both ends.
7. Hollow heart assist pump according to claim 1, characterized in that there is a gap between the permanent magnet (3) and the motor (2), which gap is equal to or less than 3 mm.
8. The hollow heart auxiliary pump according to claim 1, characterized by further comprising a blood flow speed control system, wherein the blood flow speed control system comprises pressure sensors arranged at the inlet end and the outlet end of the hollow heart auxiliary pump, and a controller, the pressure sensors sense the pressure at the inlet end and the outlet end of the hollow heart auxiliary pump in real time and transmit sensed pressure signals to the controller, the controller analyzes the pressure signals and sends out instructions to adjust current voltage, the magnetic field generated by the motor (2) is adjusted by adjusting the current voltage, the rotating speed of the permanent magnet (3) is adjusted by changing the magnetic field, and the helical blade (4) is driven by the permanent magnet (3) to rotate to realize blood flow speed adjustment.
9. Hollow heart assist pump according to claim 1, characterized in that the inner wall of the housing (1) is provided with an annular groove, in which both the motor (2) and the permanent magnet (3) are mounted, the inner wall of the permanent magnet (3) being flush with the inner wall of the housing (1).
10. A hollow heart assist pump according to any of claims 1 to 9, further comprising a connecting wire (5), wherein one end of the connecting wire (5) is connected to the motor (2) and the other end extends out of the housing (1).
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202011209272.4A CN112316297A (en) | 2020-11-03 | 2020-11-03 | Hollow heart auxiliary pump |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202011209272.4A CN112316297A (en) | 2020-11-03 | 2020-11-03 | Hollow heart auxiliary pump |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN112316297A true CN112316297A (en) | 2021-02-05 |
Family
ID=74322965
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202011209272.4A Pending CN112316297A (en) | 2020-11-03 | 2020-11-03 | Hollow heart auxiliary pump |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN112316297A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113197669A (en) * | 2021-05-19 | 2021-08-03 | 广州大学 | Variable-caliber magnetic control internal spiral vascular robot |
| WO2023108606A1 (en) * | 2021-12-17 | 2023-06-22 | 四川大学华西医院 | Shaftless blood pump |
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| US20150190561A1 (en) * | 2012-06-21 | 2015-07-09 | Avci Elif Oran | Endovascular heart assist device |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113197669A (en) * | 2021-05-19 | 2021-08-03 | 广州大学 | Variable-caliber magnetic control internal spiral vascular robot |
| CN113197669B (en) * | 2021-05-19 | 2022-03-22 | 广州大学 | Variable-caliber magnetic control internal spiral vascular robot |
| WO2023108606A1 (en) * | 2021-12-17 | 2023-06-22 | 四川大学华西医院 | Shaftless blood pump |
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Application publication date: 20210205 |