CN204972441U - Motor - two -way spiral drive formula artificial heart pump - Google Patents

Abstract

<b>The utility model discloses a motor</b><b>-</b><b>two-way spiral drive type artificial heart pump, in which an elastic blood pump for artificial heart with simple structure and convenient manufacture is adopted The artificial heart valve with extremely complex structure is replaced by two nipple-shaped protrusions facing inward and outward on the elastic blood sac with a hole in the middle, so as to realize one-way liquid suction and one-way discharge, and then through the motor</b ><b>-</b><b>The two-way helical drive mechanism is driven, so that the elastic blood sac is alternately switched between the diastolic working state and the contracting working state, thereby alternately realizing the process of absorbing and discharging liquid. The artificial heart pump can output pulsating blood flow similar to the natural heart, avoiding the technical directional error of the continuous blood pump, and well imitating the working process of the natural heart. At the same time, the elastic blood sac is made of elastic and stretchable material, and its interior is streamlined, which will not damage the cells in the blood and is not easy to form thrombus, so it can well replace the work of the natural heart of humans or vertebrates. </b>

Description

Motor-Bidirectional Helical Drive Artificial Heart Pump

technical field

The utility model relates to a motor-bidirectional spiral drive type artificial heart pump.

Background technique

Heart disease is the second leading killer of human death. When the human heart loses part or all of its function due to disease and injury and cannot maintain the normal circulation of the whole body, a mechanical device made of artificial materials can be transplanted to temporarily or permanently replace the heart function partially or completely to promote blood circulation, so that the device is Artificial heart, which is also an effective means to solve end-stage heart disease in addition to heart transplantation, has largely solved the problem that heart transplantation cannot be performed in time due to insufficient donors.

At present, the artificial heart mainly uses two blood pumps with different principles, namely, the pulse volume pump based on the artificial heart valve, and the continuous pump that pumps blood without interruption. However, these two artificial heart pumps still have problems of one kind or another, and cannot simulate the role and function of the natural heart well.

The working mode of the pulsating volumetric blood pump is very similar to the natural animal heart. Its key component is the artificial heart valve, which is a one-way valve that controls the blood flow of the heart. Its structure is closely related to the performance of the artificial heart. , which was first used clinically in 1960, after years of research, it has successively experienced mechanical valves, biological tissue valves, and interventional valves. However, artificial heart valves are extremely complex, expensive to manufacture and prone to blood clots, known as thrombi, forming in moving parts.

For example, Chinese Patent Publication No. 1093005, titled "Integrated Capsular Artificial Heart-Lung Pump", in this kind of artificial heart-lung pump, the blood storage bag is installed in the pump and inserted into the chest cavity of the human body. Blood clots form, and artificial heart valves are not easy to make. The Chinese Patent No. 99126700.1, titled "Pneumatic and Electric Integrated Blood Pump, Pneumatic and Electric Integrated Artificial Heart" provides a gas and electric integrated artificial heart. However, its internal structure is complicated, and it is basically impossible to manufacture, and Implementation costs are high. Another example is Chinese Patent Publication No. 103656770, titled "Artificial Heart Blood Pump Driven Based on Miniature Cylinder", which also has the same problem, and the miniature cylinder needs to connect two trachea to the outside of the body in the chest cavity of the human body, which is very easy to cause user's fatigue. discomfort.

Due to the technical bottleneck of artificial heart valves in pulsed volumetric blood pumps, most of the recently developed artificial hearts tend to use continuous pumps that pump blood without interruption. For example, Chinese Patent Publication No. 102019002A, titled "An Implantable Hollow Miniature Axial Blood Pump", and Chinese Patent Publication No. 10237598, titled "Compact Axial Flow Magnetic Levitation Artificial Heart Pump" Among them, both of them use an axial flow pump. Although it can damage the cells in the blood less than the gear pump and the vane pump, the high-speed operation of its components still destroys the cells in the blood. , and because the axial flow pump is a continuous pump, it cannot simulate the working process of the natural heart, so it can be said that it is a selective error in the direction of technology.

Contents of the invention

The purpose of the utility model is to provide a motor-bidirectional helical drive type artificial heart pump in order to overcome the shortcomings of the prior art.

For achieving the above object, the technical scheme that the utility model adopts is:

A motor-bidirectional helical drive type artificial heart pump, the artificial heart pump includes two elastic blood sacs, each elastic blood sac includes a sac-shaped body made of stretchable material with a closed inner cavity, so The end of the bladder has a first protrusion that is recessed into the closed inner cavity, and a second protrusion that protrudes outward from the closed inner cavity, and a second protrusion is opened on the first protrusion. A liquid flow hole, a second liquid flow hole is opened on the second protrusion, and a liquid supply part with a liquid supply chamber is provided on the outer side of the first protrusion on the bladder, and the bladder On the outside of the second protrusion, there is a drainage part with a drainage cavity. The elastic blood sac has a dilated working state and a contracted working state. When the sac is pulled laterally, the The elastic blood sac is in a dilated working state, and the first liquid flow hole is opened so that the liquid supply chamber communicates with the closed inner cavity to form a liquid-absorbing one-way valve, and blood enters the elastic blood from the liquid supply chamber. The closed cavity of the sac, the second liquid flow hole is closed; when the sac body is laterally pressed, the elastic blood sac is in a contracted working state, the first liquid flow hole is closed, and the second flow hole is closed. The liquid flow hole is opened so that the liquid discharge chamber communicates with the closed inner chamber to form a liquid discharge one-way valve, and the blood enters the liquid discharge chamber from the closed inner chamber of the elastic blood sac,

The artificial heart pump also includes a drive mechanism for driving the two elastic blood sacs to work, the drive mechanism includes a fixed miniature double output shaft motor, two output motors respectively arranged on the miniature double output shaft motor Two lead screws with opposite helical directions on the shaft, each lead screw is equipped with a lead screw nut, and the end of the lead screw nut is fixedly connected with one side of the capsule, the The other side of the bladder is fixedly arranged relative to the miniature double output shaft motor.

Preferably, both the first protrusion and the second protrusion are nipple-shaped.

Preferably, the first liquid flow hole is a streamlined horn hole whose diameter gradually decreases from outside to inside, and the second liquid flow hole is a streamlined horn hole whose diameter gradually decreases from inside to outside.

Preferably, both the liquid supply part and the liquid discharge part are streamlined.

Preferably, the closed lumens of the two capsules respectively constitute the left ventricle and the right ventricle of the artificial heart, and correspondingly, the liquid supply chambers of the two liquid supply parts respectively constitute the left atrium of the artificial heart with the right atrium.

Preferably, the lead screw nut includes a nut body matched with the lead screw, and a pressure plate fixedly connected with the nut body and used for connecting with the bladder.

Further preferably, the outer end surface of the pressure plate is an arc surface conforming to the contour of the side end surface of the bladder, and the outer end surface of the pressure plate is fixedly bonded to the side end surface of the bladder.

Due to the application of the above-mentioned technical solution, the utility model has the following advantages compared with the prior art: the motor of the utility model-two-way helical drive type artificial heart pump, wherein a kind of elastic blood pump for artificial heart with simple structure and convenient manufacture is adopted. The artificial heart valve with extremely complex structure is replaced by two nipple-shaped protrusions facing inward and outward on the elastic blood sac with a hole in the middle, so as to realize one-way liquid suction and one-way discharge, and then through the motor-two-way helical The driving mechanism is driven so that the elastic blood sac alternately switches between the diastolic working state and the contracting working state, thereby alternately realizing the process of absorbing liquid and discharging liquid. After it is installed in the thorax of a human or vertebrate, blood can continuously enter the two elastic blood sacs, and then flow out from the elastic blood sacs after contraction to supply blood to the human or animal body. The artificial heart pump can output pulsating blood flow similar to the natural heart, avoiding the technical directional error of the continuous blood pump, and well imitating the working process of the natural heart. At the same time, the elastic blood sac is made of elastic and stretchable material, and its interior is streamlined, which will not damage the cells in the blood and is not easy to form thrombus, so it can well replace the work of the natural heart of humans or vertebrates.

Description of drawings

Accompanying drawing 1, accompanying drawing 2 are an embodiment of the utility model that is used for single ventricle, wherein accompanying drawing 1 is the schematic diagram when the cystic body of elastic blood sac is in diastolic working state; Accompanying drawing 2 is the saccular shape of elastic blood sac Schematic diagram of the body in contraction working state;

Accompanying drawing 3, accompanying drawing 4 are an embodiment that the utility model is used for double ventricle, and wherein, accompanying drawing 3 is the schematic diagram when the artificial heart pump of the present utility model is in diastolic working state; Accompanying drawing 4 is the artificial heart pump of the present utility model Schematic diagram of the heart pump in its systolic working state.

Among them: 100, elastic blood sac; 1, cystic body; 10, closed inner cavity; 11, first protrusion; 12, first liquid flow hole; 13, second protrusion; 14, second liquid flow hole; 2. Liquid supply part; 21. Liquid supply cavity; 22. Liquid supply port; 3. Liquid discharge part; 31. Liquid discharge cavity; 32. Liquid discharge port;

200, driving mechanism; 4, miniature double output motor; 5, lead screw; 6, lead screw nut; 61, nut body; 62, pressure plate.

detailed description

The technical solution of the present utility model will be further elaborated below in conjunction with the accompanying drawings and specific embodiments.

Referring to Fig. 1 and Fig. 2, it shows an embodiment of an elastic blood bag 100 used in a single ventricle. The elastic blood sac 100 includes a sac body 1 made of stretchable material with a closed lumen 10, the end of the sac body 1 has a first protrusion 11 recessed into the closed lumen 10. The second protrusion 13 that protrudes outward from the closed inner cavity 10, the first protrusion 11 is provided with a first liquid flow hole 12, and the second protrusion 13 is provided with a second liquid flow hole 14, wherein the bladder 1 The upper first protrusion 11 and the second protrusion 13 are respectively disposed on two ends of the capsule body 1 . When the sac 1 is subjected to lateral tension, its internal volume expands, and the so-called "negative pressure" will be generated inside the sac 1, that is, the elastic blood sac 100 is subjected to the environmental pressure, as shown by the arrow in Figure 1. Under the action of this pressure, the second liquid flow hole 14 at the second protrusion 13 protruding outward is closed, while the first liquid flow hole 12 at the first protrusion 11 protruding inward is opened, and the blood flow is caused by The outside flows into the inside of the bladder 1 . When the bladder 1 is subjected to lateral pressure, its internal volume shrinks, and the internal pressure of the bladder 1 will be greater than the pressure of the external environment. The internal pressure distribution is shown by the arrow in Figure 2. Under the action of this pressure, the inner convex The first liquid flow hole 12 at the protruding first protrusion 11 is closed, and the second liquid flow hole 14 at the outwardly protruding second protrusion 13 is opened, so that blood flows from the inside of the bladder 1 to the outside.

Referring to FIG. 3 and FIG. 4 , a motor-bidirectional helical-driven biventricular artificial heart pump mainly includes two elastic blood sacs 100 and a driving mechanism 200 for driving the elastic blood sacs 100 to work.

These two elastic blood sacs 100 all include a sac body 1 made of stretchable material with a closed lumen 10, and the end of the sac body 1 has a first protrusion concaved into the closed lumen 10 11. The second protrusion 13 protruding outward from the closed inner chamber 10 , the first protrusion 11 is provided with a first liquid flow hole 12 , and the second protrusion 13 is provided with a second liquid flow hole 14 . When the capsule body 1 is subjected to lateral tension, the capsule body 1 expands to cause its internal volume to expand, and the first fluid flow hole 12 can be opened to communicate with the closed inner cavity 10, while the second fluid flow hole 14 Closed; when the bladder 1 is subjected to lateral pressure, the bladder 1 shrinks to cause its internal volume to shrink, the first flow hole 12 is closed, and the second flow hole 14 is opened to close the inner cavity 10 connected.

Referring to Fig. 3 and Fig. 4, a liquid supply part 2 with a liquid supply cavity 21 is provided on the capsule body 1 outside the first protrusion 11, and a liquid supply part 2 with a liquid supply chamber 21 is provided on the capsule body 1 outside the second protrusion 13. The drain unit 3 is provided with a drain chamber 31 . The liquid supply part 2 has a liquid supply port 22 communicated with the liquid supply chamber 21 , and the liquid discharge part 3 has a liquid discharge port 32 communicated with the liquid discharge chamber 31 .

The elastic blood sac 100 has a dilated working state and a contracted working state. When the sac 1 is pulled laterally, the elastic blood sac 100 is in the dilated working state and the internal volume expands. At this time, the first fluid flow hole 12 is opened to make the The liquid supply chamber 21 communicates with the closed inner cavity 10 through the first liquid flow hole 12, and the second liquid flow hole 14 is closed. At this time, the liquid flow can enter the liquid supply chamber 21 from the liquid supply port 22 and then pass through the first liquid flow hole. 12 enters the closed inner cavity 10 of the sac 1 to realize liquid supply; when the sac 1 is laterally pressed, the elastic blood sac 100 is in the working state of contraction and the internal volume shrinks, at this time the first liquid flow hole 12 is closed, and the second liquid flow hole 14 is opened so that the liquid discharge chamber 31 communicates with the closed inner cavity 10 through the second liquid flow hole 14. At this time, the liquid flow can enter the drain chamber 10 from the closed inner cavity 10 through the second liquid flow hole 14. The liquid cavity 31 is discharged through the liquid discharge port 32 to realize liquid discharge.

In this way, that is, the first protrusion 11 provided with the first liquid flow hole 12 constitutes a liquid suction one-way valve, while the second protrusion 13 provided with the second liquid flow hole 14 constitutes a liquid discharge one-way valve. On each elastic blood sac 100 , the closed lumen 10 of the capsule body 1 constitutes the ventricle of the artificial heart, while the liquid supply cavity 21 of the liquid supply part 2 constitutes the atrium.

In the above-mentioned embodiment, both the first protrusion 11 and the second protrusion 13 are nipple-shaped, the first liquid flow hole 12 is a streamlined trumpet hole whose diameter gradually becomes smaller from the outside to the inside, and the second liquid flow hole 14 is from the inside to the inside. Streamlined trumpet hole with gradually smaller outer diameter, so that when the bladder 1 is subjected to lateral tension, the first protrusion 11 is pulled to open the first liquid flow hole 12, and the second protrusion 13 is pulled The second liquid flow hole 14 is closed; when the bladder 1 is subjected to lateral pressure, the first protrusion 11 is pressed to close the first liquid flow hole 12, and the second protrusion 13 is pressed to make the first liquid flow hole 12 closed. The second liquid flow hole 14 is opened. Both the liquid supply part 2 and the liquid discharge part 3 are arranged in a streamlined shape. During specific arrangement, the capsule body 1 is integrally provided with the liquid supply part 2 and the liquid discharge part 3 , and the liquid supply part 2 and the liquid discharge part 3 are located at the same end of the capsule body 1 .

The drive mechanism 200 includes a fixedly arranged miniature double output shaft motor 4, the left and right ends of the miniature double output shaft motor 4 have output shafts respectively, and the output shafts at both ends are respectively connected with lead screws 5 with opposite helical directions, each lead screw 5 are all fitted with lead screw nuts 6, the end of the lead screw nut 6 close to the bladder 1 is fixedly connected to one side of the bladder 1, and the other side of the bladder 1 is opposite to the miniature double output Shaft motor 4 is fixedly arranged.

Here, the lead screw nut 6 includes a nut body 61 screwed with the lead screw 5, and a pressure plate 62 fixed on the nut body 61. The main body of the pressure plate 62 is in the shape of a hollow sleeve, which is fixedly sleeved on the nut body 61. , and the lead screw 5 can move axially relative to the pressure plate 62 and penetrates therein. The outer end of the pressure plate 62 is used to be fixedly connected with the bladder 1. Here, the outer end surface of the pressure plate 62 is in the shape of the bladder 1 The outer end surface of the pressure plate 62 and the side end surface of the bladder 1 are fixedly bonded together. In this way, when the lead screw 5 rotates, the lead screw nut 6 moves along the lead screw 5 , so that the pressure plate 62 can press the bladder 1 in the lateral direction or exert a lateral pulling force on the bladder 1 .

In this way, the elastic blood sac 100 on the left side of the driving mechanism 200 constitutes the left atrium and left ventricle of the heart, and the elastic blood sac 100 on the right side of the driving mechanism 200 constitutes the right atrium and right ventricle of the heart.

During the specific setting, the helical direction of the threads on the two lead screws 5 on both sides of the miniature double output shaft motor 4 should be set oppositely. spiral, then the screw thread direction on the lead screw 5 on the right side of the miniature double output shaft motor 4 should be reverse spiral. In this way, when the miniature double output shaft motor 4 works, it can drive the lead screw nuts 6 on the lead screws 5 on both sides to move inward or outward at the same time.

When the two output shafts of the miniature double output shaft motor 4 rotated in a certain direction, the leading screws 5 on both sides were driven to rotate synchronously. Simultaneously moving inward along the lead screw 5, this makes the pressure plate 62 apply a lateral pulling force to the capsule body 1, and then the elastic blood capsules 100 on both sides switch to a dilated working state, the second fluid flow hole 14 is closed, and the first fluid flow hole 14 is closed. The liquid flow hole 12 is opened, and the external liquid flow enters the liquid supply chamber 21 through the liquid supply port 22 and then enters the closed inner cavity 10 of the bladder 1 through the first liquid flow hole 12, as shown in Figure 3; When the two output shafts of the shaft motor 4 and the two lead screws 5 rotate in opposite directions, the lead screw nuts 6 on both sides move outwards simultaneously along the axial direction of the lead screws 5 , which causes the pressure plate 62 to exert a lateral force on the bladder 1 . Pressure, which makes the elastic blood sac 100 switch to the contraction working state, the first liquid flow hole 12 is closed, and the second liquid flow hole 14 is opened, and the liquid flow in the closed cavity 10 of the capsule body 1 passes through the second liquid flow hole 14 It enters the drainage cavity 31 and is discharged through the drainage port 32 to supply blood to the body, as shown in FIG. 4 .

When the artificial heart pump is installed in the chest cavity of the human body, it is only necessary to fix the outer sides of the miniature double output shaft motor 4 and the upper capsule body 1 of the two elastic blood sacs 100 in the chest cavity of the human body, and only one motor can be used to make the two The elastic blood sacs 100 work at the same time, and the structure is also very symmetrical. Since the pressures of the left ventricle and the right ventricle of the human heart are not consistent, here there is a pressure difference between the pressures of the two ventricles by adjusting the pitches of the lead screws 5 on both sides.

To sum up, the motor-bidirectional helical drive type artificial heart pump of the present utility model adopts an elastic blood bag 100 for artificial heart with a simple structure and is easy to manufacture. Two pacifier-shaped protrusions with holes replace artificial heart valves with extremely complex structures to realize one-way liquid suction and one-way liquid discharge, and then driven by the driving mechanism 200, so that the elastic blood bag 100 is alternately in the diastolic working state and The working state of contraction is switched, so as to realize the process of liquid suction and liquid discharge alternately. After it is installed in the thorax of a human or a vertebrate, blood can continuously enter the two elastic blood sacs 100, and then flow out from the elastic blood sacs 100 after contraction to supply blood to the human or animal body. The artificial heart pump can output pulsating blood flow similar to the natural heart, avoiding the technical directional error of the continuous blood pump, and well imitating the working process of the natural heart. At the same time, the elastic blood sac 100 is made of elastic and stretchable material, and its interior is streamlined, which will not damage the cells in the blood and is not easy to form thrombus, so it can well replace the work of the natural heart of humans or vertebrates.

The above-mentioned embodiments are only to illustrate the technical concept and characteristics of the present utility model, and its purpose is to enable those familiar with this technology to understand the content of the present utility model and implement it accordingly, and not to limit the protection scope of the present utility model. All equivalent changes or modifications made according to the spirit of the utility model shall fall within the protection scope of the utility model.

Claims (7)

1. A motor-bidirectional helical drive type artificial heart pump, characterized in that: the artificial heart pump comprises two elastic blood sacs, each of which includes an elastic blood sac with a closed inner cavity made of stretchable material a bladder, the end of the bladder has a first protrusion recessed into the closed lumen, a second protrusion protruding outward from the closed lumen, the first A first liquid flow hole is opened on the protrusion, a second liquid flow hole is opened on the second protrusion, and a liquid supply chamber with a liquid supply chamber is provided on the bladder outside the first protrusion. part, the bladder is located on the outside of the second protrusion is provided with a drainage part with a drain cavity, the elastic blood sac has a dilated working state and a contracted working state, when the bladder is sideways When stretched, the elastic blood sac is in a dilated working state, and the first liquid flow hole is opened so that the liquid supply cavity communicates with the closed inner cavity to form a liquid suction one-way valve, and the blood is supplied by the liquid supply chamber. The cavity enters the closed inner cavity of the elastic blood sac, and the second flow hole is closed; when the sac is laterally pressed, the elastic blood sac is in a contracted working state, and the first flow hole closed, the second liquid flow hole is opened so that the drainage cavity communicates with the closed inner cavity to form a drainage one-way valve, blood enters the drainage cavity from the closed inner cavity of the elastic blood bag, The artificial heart pump also includes a drive mechanism for driving the two elastic blood sacs to work, the drive mechanism includes a fixed miniature double output shaft motor, two output motors respectively arranged on the miniature double output shaft motor Two lead screws with opposite helical directions on the shaft, each lead screw is equipped with a lead screw nut, and the end of the lead screw nut is fixedly connected with one side of the capsule, the The other side of the bladder is fixedly arranged relative to the miniature double output shaft motor. 2 . The motor-bidirectional helical drive type artificial heart pump according to claim 1 , wherein the first protrusion and the second protrusion are both nipple-shaped. 3 . 3. The motor-bidirectional helical drive type artificial heart pump according to claim 1 or 2, characterized in that: the first liquid flow hole is a streamlined horn hole whose diameter gradually decreases from the outside to the inside, and the second liquid flow hole The orifice is a streamlined trumpet hole whose diameter gradually decreases from the inside to the outside. 4. The motor-bidirectional helical drive type artificial heart pump according to claim 1, characterized in that: the liquid supply part and the liquid discharge part are both streamlined. 5. The motor-bidirectional helical drive type artificial heart pump according to claim 1, characterized in that: the closed lumens of the two capsules respectively constitute the left ventricle and the right ventricle of the artificial heart, correspondingly, The liquid supply chambers of the two liquid supply parts respectively constitute the left atrium and the right atrium of the artificial heart. 6. The motor-bidirectional helical drive type artificial heart pump according to claim 1, characterized in that: the lead screw nut includes a nut body matched with the lead screw, fixedly connected with the nut body and On the pressure plate connected to the bladder. 7. The motor-bidirectional helical drive type artificial heart pump according to claim 6, characterized in that: the outer end surface of the pressing plate is an arc surface consistent with the profile of the side end surface of the capsule, and the pressing plate The outer end surface of the capsule body is fixedly bonded to the side end surface of the capsule.