阅读说明：本技术 血液泵 (Blood pump ) 是由 魏润杰 陈杰 刘星利 高琪 于 2020-11-27 设计创作，主要内容包括：本申请实施例公开了一种血液泵,所述血液泵包括：第一壳体,具有第一容纳腔；叶轮,设置于所述第一容纳腔内；驱动装置,与所述叶轮连接,用于驱动所述叶轮转动；插管,与第一壳体连接；所述插管的腔体与所述第一容纳腔连通。本申请实施例的血液泵,通过血液泵能够为血液提供流动的动力。(The embodiment of the application discloses blood pump, blood pump includes: a first housing having a first accommodating chamber; the impeller is arranged in the first accommodating cavity; the driving device is connected with the impeller and is used for driving the impeller to rotate; the cannula is connected with the first shell; the cavity of the cannula is communicated with the first accommodating cavity. The blood pump of this application embodiment can provide mobile power for blood through the blood pump.)

1. A blood pump, comprising:

a first housing having a first accommodating chamber;

the impeller is arranged in the first accommodating cavity;

the driving device is connected with the impeller and is used for driving the impeller to rotate;

the cannula is connected with the first shell; the cavity of the cannula is communicated with the first accommodating cavity.

2. The blood pump of claim 1, wherein a diameter of the cannula lumen is smaller than a diameter of the first receiving lumen.

3. The blood pump of claim 2, further comprising:

the connecting pipe is in a cone cylinder shape and is used for preventing the blood flowing in the first accommodating cavity from generating backflow; the large end of the connecting pipe is connected with the first shell, and the small end of the connecting pipe is connected with the insertion pipe; the cavity of the connecting pipe is respectively communicated with the first accommodating cavity and the cavity of the insertion pipe;

the insertion tube is flexible, a first included angle is formed between the inner wall surface of the connecting tube and the axis of the connecting tube, and the first included angle is smaller than or equal to 15 degrees.

4. The blood pump of claim 1, wherein the cannula comprises:

a first introduction port located on a distal end side close to the cannula; wherein the end of the cannula is the opposite end of the cannula to the first housing;

and a second introduction port located on a distal end side away from the cannula, the second introduction port being formed at a first distance from the first introduction port.

5. The blood pump of claim 1, comprising:

the outlet is arranged at the first end of the first shell; wherein the first end of the first housing is the opposite end of the first housing from the cannula connection end;

the detection device is used for detecting the rotating speed of the driving device;

the first pressure sensor is arranged on the outer side of the intubation tube and used for detecting first pressure at the entrance of the intubation tube;

a second pressure sensor for detecting a second pressure at the outlet;

and the processor is electrically connected with the first pressure sensor, the second pressure sensor and the detection device respectively, is used for determining the pressure difference of the second pressure minus the first pressure, and is also used for determining the flow rate of the blood pump based on the pressure difference and the rotating speed.

6. The blood pump of claim 5, further comprising:

the second shell is arranged at a distance from the first shell and is provided with a second accommodating cavity and an opening; the driving device is fixed at one end of the second shell, and a rotating part of the driving device is connected with the impeller through the opening;

the detection device includes:

the first vibration sensor is arranged in the second accommodating cavity, is positioned close to the driving device and is used for detecting vibration parameters of the driving device;

the processor is used for determining the rotating speed of the driving device based on the vibration parameters detected by the first vibration sensor and is also used for determining whether the blood pump is abnormal or not based on the vibration parameters detected by the first vibration sensor.

7. The blood pump of claim 5, wherein the detection device comprises:

the photoelectric sensor is arranged on the outer side of the driving device, is positioned on one side close to the impeller and is used for detecting the rotating speed of the driving device; or the like, or, alternatively,

the Hall sensor is arranged in the driving device and used for detecting the rotating speed of the driving device; or the like, or, alternatively,

the first pressure pulsation sensor is arranged at the outlet and used for detecting the pressure pulsation of the blood at the outlet; the processor determines a rotational speed of the drive device based on the pressure pulsations.

8. The blood pump of claim 5, further comprising:

the second shell is arranged at a distance from the first end of the first shell and is provided with a second accommodating cavity and an opening; the driving device is fixed at one end of the second shell, and a rotating part of the driving device is connected with the impeller through the opening; the first ends of the second shell and the first shell form the outlet;

the fixing port is arranged on the second shell and communicated with the second accommodating cavity;

the second pressure sensor is arranged in the fixed port; the detection surface of the second pressure sensor faces the outer side of the second accommodating cavity; the detection surface and the outer surface of the second shell meet the coplanar condition, or the detection surface is positioned in the fixing port.

9. The blood pump of claim 8, further comprising:

the controller is arranged in the driving device, is electrically connected with the detection device, the first pressure sensor and the processor respectively, and is used for transmitting the first pressure information, the second pressure information and the rotating speed information to the processor; the controller is electrically connected with the processor in a wired mode or in a wireless mode; or the like, or, alternatively,

the blood pump further includes: a first conductive line, a second conductive line, and a third conductive line; the first end of the first lead is electrically connected with the detection device; a portion of the first lead is positioned within the second receiving cavity; the second end of the first lead is led out of the second accommodating cavity to the outside of the second shell; the first end of the second lead is electrically connected with the first pressure sensor; a portion of the second lead is positioned within the second receiving cavity; the second end of the second lead is led out of the second accommodating cavity to the outside of the second shell; the first end of the third lead is electrically connected with the second pressure sensor; and the second end of the third lead is led out of the second accommodating cavity to the outside of the second shell.

10. The blood pump of any one of claims 1-9, further comprising:

the ultrasonic sensor is arranged on the cannula and used for detecting the flow velocity of the blood in the cavity of the cannula; wherein the flow rate is used to determine a flow rate of blood within the lumen of the cannula.

11. The blood pump of any one of claims 1-9, further comprising:

a processor for determining a flow rate of the blood pump based on the power of the blood pump, for determining a pressure differential of the blood pump based on the power of the blood pump; wherein the pressure differential is a pressure at which the blood pump increases blood.

12. The blood pump of any one of claims 1 to 9,

the blood pump further includes: the second vibration sensor is used for detecting vibration parameters of the driving device; a processor electrically connected with the second vibration sensor and used for determining whether the blood pump runs abnormally or not based on the vibration parameters detected by the second vibration sensor; and/or the presence of a gas in the gas,

the blood pump further includes: and the processor is electrically connected with the driving device and is used for determining whether the blood pump runs abnormally or not based on the power of the driving device.

13. The blood pump of claim 12, wherein the vibration parameter of the drive device is a first amplitude of the drive device when the blood pump includes a second vibration sensor; the processor to determine whether there is an abnormality in the blood pump operation based on the vibration parameter detected by the second vibration sensor comprises: the processor is used for determining that the blood pump runs abnormally when the first amplitude detected by the second vibration sensor is larger than a first set value; otherwise, the processor determines that the blood pump is operating properly;

where the processor is electrically connected to the drive device, the processor being configured to determine whether there is an abnormality in the blood pump operation based on the power of the drive device comprises: the processor is used for determining that the blood pump runs abnormally when the power of the driving device is determined to be smaller than a second set value; otherwise, the processor determines that the blood pump is operating properly.

Technical Field

The application relates to the technical field of medical equipment, especially, relate to a blood pump.

Background

The heart is the power organ of the human body, and the heart mainly functions to provide power for blood flow and convey blood to all parts of the body, so that when the heart of a patient is in trouble and cannot provide power, the life of the patient is very dangerous.

Disclosure of Invention

In view of the above, embodiments of the present application are directed to a blood pump.

In order to achieve the purpose, the technical scheme of the application is realized as follows:

the embodiment of the present application provides a blood pump, blood pump includes:

a first housing having a first accommodating chamber;

the impeller is arranged in the first accommodating cavity;

the driving device is connected with the impeller and is used for driving the impeller to rotate;

the cannula is connected with the first shell; the cavity of the cannula is communicated with the first accommodating cavity.

In some alternative implementations, the diameter of the lumen of the cannula is smaller than the diameter of the first receiving lumen.

In some optional implementations, the blood pump further comprises:

the connecting pipe is in a cone cylinder shape and is used for preventing the blood flowing in the first accommodating cavity from generating backflow; the large end of the connecting pipe is connected with the first shell, and the small end of the connecting pipe is connected with the insertion pipe; the cavity of the connecting pipe is respectively communicated with the first accommodating cavity and the cavity of the insertion pipe;

the insertion tube is flexible, a first included angle is formed between the inner wall surface of the connecting tube and the axis of the connecting tube, and the first included angle is smaller than or equal to 15 degrees.

In some optional implementations, the cannula includes:

a first introduction port located on a distal end side close to the cannula; wherein the end of the cannula is the opposite end of the cannula to the first housing;

and a second introduction port located on a distal end side away from the cannula, the second introduction port being formed at a first distance from the first introduction port.

In some optional implementations, the blood pump includes:

the outlet is arranged at the first end of the first shell; wherein the first end of the first housing is the opposite end of the first housing from the cannula connection end;

the detection device is used for detecting the rotating speed of the driving device;

the first pressure sensor is arranged on the outer side of the intubation tube and used for detecting first pressure at the entrance of the intubation tube;

a second pressure sensor for detecting a second pressure at the outlet;

and the processor is electrically connected with the first pressure sensor, the second pressure sensor and the detection device respectively, is used for determining the pressure difference of the second pressure minus the first pressure, and is also used for determining the flow rate of the blood pump based on the pressure difference and the rotating speed.

In some optional implementations, the blood pump further comprises:

the second shell is arranged at a distance from the first shell and is provided with a second accommodating cavity and an opening; the driving device is fixed at one end of the second shell, and a rotating part of the driving device is connected with the impeller through the opening;

the detection device includes:

the first vibration sensor is arranged in the second accommodating cavity, is positioned close to the driving device and is used for detecting vibration parameters of the driving device;

the processor is used for determining the rotating speed of the driving device based on the vibration parameters detected by the first vibration sensor and is also used for determining whether the blood pump is abnormal or not based on the vibration parameters detected by the first vibration sensor.

In some optional implementations, the detecting means includes:

the photoelectric sensor is arranged on the outer side of the driving device, is positioned on one side close to the impeller and is used for detecting the rotating speed of the driving device; or the like, or, alternatively,

the Hall sensor is arranged in the driving device and used for detecting the rotating speed of the driving device; or the like, or, alternatively,

the first pressure pulsation sensor is arranged at the outlet and used for detecting the pressure pulsation of the blood at the outlet; the processor determines a rotational speed of the drive device based on the pressure pulsations.

In some optional implementations, the blood pump further comprises:

the second shell is arranged at a distance from the first end of the first shell and is provided with a second accommodating cavity and an opening; the driving device is fixed at one end of the second shell, and a rotating part of the driving device is connected with the impeller through the opening; the first ends of the second shell and the first shell form the outlet;

the fixing port is arranged on the second shell and communicated with the second accommodating cavity;

the second pressure sensor is arranged in the fixed port; the detection surface of the second pressure sensor faces the outer side of the second accommodating cavity; the detection surface and the outer surface of the second shell meet the coplanar condition, or the detection surface is positioned in the fixing port.

In some optional implementations, the blood pump further comprises:

the controller is arranged in the driving device, is electrically connected with the detection device, the first pressure sensor and the processor respectively, and is used for transmitting the first pressure information, the second pressure information and the rotating speed information to the processor; the controller is electrically connected with the processor in a wired mode or in a wireless mode; or the like, or, alternatively,

the blood pump further includes: a first conductive line, a second conductive line, and a third conductive line; the first end of the first lead is electrically connected with the detection device; a portion of the first lead is positioned within the second receiving cavity; the second end of the first lead is led out of the second accommodating cavity to the outside of the second shell; the first end of the second lead is electrically connected with the first pressure sensor; a portion of the second lead is positioned within the second receiving cavity; the second end of the second lead is led out of the second accommodating cavity to the outside of the second shell; the first end of the third lead is electrically connected with the second pressure sensor; and the second end of the third lead is led out of the second accommodating cavity to the outside of the second shell.

In some optional implementations, the blood pump further comprises:

the ultrasonic sensor is arranged on the cannula and used for detecting the flow velocity of the blood in the cavity of the cannula; wherein the flow rate is used to determine a flow rate of blood within the lumen of the cannula.

In some optional implementations, the blood pump further comprises:

a processor for determining a flow rate of the blood pump based on the power of the blood pump, for determining a pressure differential of the blood pump based on the power of the blood pump; wherein the pressure differential is a pressure at which the blood pump increases blood.

In some alternative implementations of the method of the present invention,

the blood pump further includes: the second vibration sensor is used for detecting vibration parameters of the driving device; a processor electrically connected with the second vibration sensor and used for determining whether the blood pump runs abnormally or not based on the vibration parameters detected by the second vibration sensor; and/or the presence of a gas in the gas,

the blood pump further includes: and the processor is electrically connected with the driving device and is used for determining whether the blood pump runs abnormally or not based on the power of the driving device.

In some alternative implementations, where the blood pump includes a second vibration sensor, the parameter of vibration of the drive device is a first amplitude of the drive device; the processor to determine whether there is an abnormality in the blood pump operation based on the vibration parameter detected by the second vibration sensor comprises: the processor is used for determining that the blood pump runs abnormally when the first amplitude detected by the second vibration sensor is larger than a first set value; otherwise, the processor determines that the blood pump is operating properly;

where the processor is electrically connected to the drive device, the processor being configured to determine whether there is an abnormality in the blood pump operation based on the power of the drive device comprises: the processor is used for determining that the blood pump runs abnormally when the power of the driving device is determined to be smaller than a second set value; otherwise, the processor determines that the blood pump is operating properly.

The blood pump in the embodiment of this application, the blood pump includes: a first housing having a first accommodating chamber; the impeller is arranged in the first accommodating cavity; the driving device is connected with the impeller and is used for driving the impeller to rotate; the cannula is connected with the first shell; the cavity of the cannula is communicated with the first accommodating cavity; here, the blood pump can provide a motive force for the blood to flow.

Drawings

FIG. 1 is a cross-sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 2 is a cross-sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 3 is a schematic diagram of an alternative partial configuration of a cannula of a blood pump in accordance with an embodiment of the present application;

FIG. 4 is a schematic diagram of an alternative partial configuration of a cannula of a blood pump in accordance with an embodiment of the present application;

FIG. 5 is a schematic view of an alternative embodiment of a portion of a cannula of a blood pump of the present application;

FIG. 6 is a cross-sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 7 is a schematic diagram of an alternative partial configuration of a blood pump in accordance with an embodiment of the present application;

FIG. 8 is a cross-sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 9 is a sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 10 is a sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 11 is a sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 12 is a cross-sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 13 is a schematic view of an alternative embodiment of the blood pump of the present application;

FIG. 14 is a schematic view of an alternative embodiment of the blood pump of the present application;

FIG. 15 is a sectional view of an alternative embodiment of the blood pump of the present application;

FIG. 16 is a sectional view of an alternative embodiment of a blood pump of the present application;

FIG. 17 is a graph of an alternative pressure differential and flow rate for a blood pump in accordance with the present embodiments;

FIG. 18 is a graph of an alternative power and pressure differential for a blood pump in accordance with embodiments of the present application;

FIG. 19 is a graph of an alternative power and flow rate of the blood pump in accordance with the embodiments of the present application.

Reference numerals: 101. a lead-out port; 110. a first housing; 111. a first accommodating chamber; 120. an impeller; 130. a drive device; 131. a rotating member; 140. inserting a tube; 141. a first introduction port; 142. a second introduction port; 143. a socket; 150. a connecting pipe; 151. an inner wall surface; 161. a first pressure sensor; 162. a second pressure sensor; 1621. detecting a surface; 163. a first vibration sensor; 164. a photoelectric sensor; 165. a first pressure pulsation sensor; 166. an ultrasonic sensor; 170. a second housing; 171. a second accommodating chamber; 172. an opening; 173. a fixed port; 181. a first conductive line; 182. a second conductive line; 183. and a third conductive line.

Detailed Description

The technical solution of the present application is further described in detail with reference to the drawings and specific embodiments of the specification.

In the description of the embodiments of the present application, it should be noted that, unless otherwise specified and limited, the term "connected" should be interpreted broadly, for example, as an electrical connection, a communication between two elements, a direct connection, or an indirect connection via an intermediate, and the specific meaning of the terms may be understood by those skilled in the art according to specific situations.

It should be noted that the terms "first \ second \ third" referred to in the embodiments of the present application are only used for distinguishing similar objects, and do not represent a specific ordering for the objects, and it should be understood that "first \ second \ third" may exchange a specific order or sequence order if allowed. It should be understood that "first \ second \ third" distinct objects may be interchanged under appropriate circumstances such that the embodiments of the application described herein may be implemented in an order other than those illustrated or described herein.

It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict. The blood pump according to the embodiment of the present application will be described in detail below with reference to fig. 1 to 19.

The blood pump includes: a first housing 110, an impeller 120, a drive device 130, and a cannula 140. The first housing 110 has a first accommodation chamber 111; the impeller 120 is disposed in the first accommodating cavity 111; the driving device 130 is connected with the impeller 120, and the driving device 130 is used for driving the impeller 120 to rotate; the cannula 140 is connected to the first housing 110; the cavity of the cannula 140 communicates with the first receiving cavity 111. The blood pump can provide the power for the blood to flow.

In the embodiment of the present application, the structure of the first housing 110 is not limited as long as the first housing 110 has the first accommodation chamber 111 so that blood can flow in the first accommodation chamber 111. For example, the first housing 110 has a cylindrical structure.

Here, the shape of the first receiving cavity 111 is not limited. For example, the first receiving cavity 111 has a cylindrical structure.

In the embodiment of the present application, the cross-sectional shape of the impeller 120 is not limited. For example, the cross-sectional shape of the impeller 120 may be an airfoil, in which case the thickness of the cross-section of the impeller 120 varies from place to place. Of course, the thickness of the cross section of the impeller 120 may be the same throughout.

In the embodiment of the present application, the structure of the driving device 130 is not limited, as long as the driving device 130 is connected to the impeller 120, and the driving device 130 is used for driving the impeller 120 to rotate. For example, the driving device 130 may be a motor or a motor.

Here, in the case that the driving device 130 drives the impeller 120 to rotate, the impeller 120 is used for pushing blood to flow in the first accommodating chamber 111 so as to make the blood reach a set flow rate and a set pressure.

In the embodiment of the present application, the structure of the cannula 140 is not limited. For example, the diameter of the cavity of the cannula 140 is equal to the diameter of said first housing cavity 111. Here, when the wall thickness of the insertion tube 140 and the wall thickness of the first receiving cavity 111 are substantially equal, the size of the insertion tube 140 and the size of the first receiving cavity 111 are substantially the same.

Here, the cannula 140 may be directly connected to the first housing 110, or may be connected to the first housing 110 through another structure.

Here, the cannula 140 may have flexibility so that the cannula 140 can change directions.

In some optional implementations of embodiments of the present application, a diameter of the lumen of the cannula is smaller than a diameter of the first receiving lumen. Here, when the wall thickness of the cannula 140 and the wall thickness of the first accommodation chamber 111 are substantially equal, the cannula 140 can be set small in size, the blood pump can be reduced in size at the cannula 140, and the blood pump insertion operation is facilitated.

In this implementation, the structure of the cannula 140 is not limited as long as the diameter of the cavity of the cannula 140 is smaller than the diameter of the first accommodating cavity 111. For example, the cannula 140 may be a tube of equal diameter throughout. For another example, the cannula 140 may be a cone-shaped tube.

It should be noted that, since the impeller 120 is disposed in the first accommodating chamber 111, the small diameter of the cannula 140 does not affect the blood flow.

In this embodiment, as shown in fig. 1 and 2, the blood pump may further include: a connection tube 150, wherein the connection tube 150 is in a cone cylinder shape, and the connection tube 150 is used for blocking the blood flowing in the first accommodating cavity 111 from generating a backflow; the large end of the connecting tube 150 is connected to the first housing 110, and the small end of the connecting tube 150 is connected to the insertion tube 140; the cavity of the connecting tube 150 is respectively communicated with the first accommodating cavity 111 and the cavity of the cannula 140.

Here, the structure of the connection pipe 150 is not limited as long as the connection pipe 150 has a tapered cylindrical shape, and the connection pipe 150 has a large end and a small end. For example, the connection pipe 150 may have a conical cylindrical shape, and the connection pipe 150 may have a circular cross-section. For example, the connection pipe 150 may have a pyramid cylinder shape, and the cross section of the connection pipe 150 may be polygonal.

Here, the inner wall surface 151 of the connection pipe 150 forms a first angle with the axis of the connection pipe 150, and here, the value of the first angle is not limited. For example, the first included angle may be 15 degrees or less.

Here, since the diameter of the cavity of the connection tube 150 is gradually reduced from the first housing 110 to the cannula 140, the inner wall of the connection tube 150 can block the blood between the impeller 120 and the inner wall of the first accommodating cavity 111 from flowing to the cannula 140 again, and prevent the impeller 120 and the inner wall of the first accommodating cavity 111 from forming a gap backflow; it should be noted that, when the impeller 120 pushes blood to flow in the first accommodating cavity 111, a gap exists between the peripheral end of the impeller 120 and the inner wall surface of the first accommodating cavity 111, and a gap backflow is generated during the rotation of the impeller 120, at this time, the prevention effect of the connecting pipe 150 inhibits the impeller 120 and the inner wall surface of the first accommodating cavity 111 from further developing to form a gap backflow, and a gap backflow region formed between the impeller 120 and the inner wall surface of the first accommodating cavity 111 can be reduced.

In some optional implementations of embodiments of the present application, the cannula 140 may include: a first introduction port 141 and a second introduction port 142. The first introduction port 141 is located near the distal end side of the insert tube 140; wherein the end of the cannula 140 is the opposite end of the cannula 140 connected to the first housing 110; the second introduction port 142 is located on the distal end side away from the insert tube 140, and the second introduction port 142 is formed at a first distance from the first introduction port 141; so that blood is simultaneously introduced into the cavity of the cannula 140 through the first introduction port 141 and the second introduction port, the flow rate of blood can be greatly increased.

In the present embodiment, the shape of the first introduction port 141 is not limited. For example, as shown in fig. 3 to 5, the first introduction port 141 is elongated.

Here, the number of the first introduction ports 141 is not limited. For example, the number of the first introduction ports 141 is at least two, and the at least two first introduction ports 141 are uniformly spaced apart in the circumferential direction of the insertion tube 140.

In the present embodiment, the cross-sectional shape of the second introduction port 142 is not limited. For example, as shown in fig. 3, the second introduction port 142 has a circular cross section. For another example, as shown in fig. 4, the second introduction port 142 has an elliptical cross section. For another example, as shown in fig. 5, the second introduction port 142 has a rectangular cross section.

Here, the number of the second introduction ports 142 is not limited. For example, the number of the second introduction ports 142 is at least two, and at least two second introduction ports 142 are uniformly spaced along the circumferential direction of the insertion tube 140, as shown in fig. 5. For another example, the number of the second introduction ports 142 is at least two, the first part second introduction ports 142 of the at least two second introduction ports 142 are uniformly spaced along the circumferential direction of the insert tube 140, and the second part second introduction ports 142 of the at least two second introduction ports 142 are uniformly spaced along the axial direction of the insert tube 140, as shown in fig. 3 and 4.

Here, the value of the first distance is not limited as long as the value of the first distance is greater than zero.

In some optional implementations of embodiments of the present application, the blood pump may include: the device comprises a lead-out port 101, a detection device, a first pressure sensor 161, a second pressure sensor 162 and a processor, wherein the lead-out port 101 is arranged at a first end of the first shell 110; wherein the first end of the first housing 110 is the opposite end of the end where the first housing 110 is connected with the cannula 140; the detection device is used for detecting the rotating speed of the driving device 130; a first pressure sensor 161 is disposed outside the cannula 140, the first pressure sensor 161 being configured to detect a first pressure at the inlet of the cannula 140; a second pressure sensor 162 for detecting a second pressure at the lead-out port 101; a processor is electrically connected to said first pressure sensor 161, said second pressure sensor 162 and said detection means, respectively, for determining a pressure difference of said second pressure minus said first pressure, and for determining a flow rate of said blood pump based on said pressure difference and said rotational speed, so as to be able to determine an operating flow rate of said blood pump.

In this embodiment, the outlet 101 is used for discharging the blood flowing in the first accommodating chamber 111.

In this implementation, the structure of the first pressure sensor is not limited as long as the first pressure sensor can detect the first pressure at the introduction port of the insertion tube 140. For example, the first pressure sensor may be a second pressure pulsation sensor, where the first pressure sensor is also used to detect the cardiac cycle if the blood pump is placed in the heart of a human.

Here, the position where the first pressure sensor 161 is disposed is not limited as long as the first pressure at the introduction port of the cannula 140 can be detected. For example, as shown in fig. 6 and 7, the first pressure sensor 161 is located on a side of the second introduction port 142 away from the first introduction port 141; here, blood flows from the first introduction port 141 toward the second introduction port 142.

In the present implementation, the structure of the second pressure sensor is not limited as long as the second pressure sensor can detect the second pressure at the outlet 101 of the cannula 140. For example, the second pressure sensor may be a third pressure pulsation sensor.

Here, the position where the second pressure sensor 162 is disposed is not limited as long as the second pressure at the lead-out port 101 can be detected.

For example, as shown in fig. 8 and 9, the blood pump may further include: a second housing 170 and a fixing port 173. A second housing 170 spaced apart from the first end of the first housing 110, the second housing 170 having a second receiving chamber 171 and an opening 172; the driving device 130 is fixed at one end of the second housing 170, and the rotating member 131 of the driving device 130 is connected to the impeller 120 through the opening 172; the second housing 170 and the first end of the first housing 110 form the outlet 101; a fixing port 173 is provided in the second housing 170, and the fixing port 173 communicates with the second receiving chamber 171; the second pressure sensor 162 is disposed within the fixed port 173; the detection surface 1621 of the second pressure sensor 162 faces the outside of the second accommodation chamber 171; so that the second pressure sensor 162 can detect the pressure of the blood flowing out of the lead-out port 101; by disposing the second pressure sensor 162 in the fixing port 173, the installation space of the second pressure sensor 162 can be reduced, and the overall size of the blood pump can be further reduced.

In this example, the structure of the second housing 170 is not limited. For example, the second housing 170 may have a straight cylindrical structure. For another example, as shown in fig. 8, the second housing 170 may have a tapered cylindrical structure.

In this example, the structure of the rotation member 131 is not limited. For example, when the driving device 130 is a motor, the rotating member 131 may be a rotating shaft. It should be noted that the rotation speed of the driving device 130 is the rotation speed of the rotating member 131.

In this example, the second pressure sensor 162 detects the blood pressure outside the second accommodating chamber 171 through the detection surface 1621, that is, the second pressure sensor 162 detects the blood lead-out pressure of the lead-out port 101 through the detection surface 1621.

Here, the detecting surface 1621 and the outer surface of the second casing 170 may satisfy a coplanar condition, that is, the detecting surface 1621 and the outer surface of the second casing 170 may be coplanar or substantially coplanar; so that the second pressure sensor 162 is disposed without increasing the size of the outside of the second casing 170, thereby reducing the overall size of the blood pump. The detection surface 1621 may be positioned inside the fixing port 173, and in this case, as shown in fig. 9, the second pressure sensor 162 may be provided without increasing the size of the outside of the second casing 170, and the blood pump may be reduced in size as a whole. Of course, the detecting surface 1621 may protrude from the outer surface of the second housing 170, and the second pressure sensor 162 may be partially disposed in the fixing port 173.

In this embodiment, the structure of the detection device is not limited as long as the detection device can detect the rotation speed of the driving device 130.

For example, as shown in fig. 11, the detection means may include: the photoelectric sensor 164, the photoelectric sensor 164 is disposed outside the driving device 130, the photoelectric sensor 164 is located at a side close to the impeller 120, and the photoelectric sensor 164 is used for detecting a rotation speed of the driving device 130.

For another example, the detection device may include: and the hall sensor is arranged in the driving device 130 and is used for detecting the rotating speed of the driving device 130.

For another example, as shown in fig. 12, the detecting means may include: a first pressure pulsation sensor 165, the first pressure pulsation sensor 165 being disposed at the outlet port 101, the first pressure pulsation sensor 165 being configured to detect pressure pulsation of blood at the outlet port 101; the processor determines the rotational speed of the drive 130 based on the pressure pulsations.

Here, the processor determining the rotation speed of the driving device 130 based on the pressure pulsation may include the processor obtaining a frequency of rotation of the rotator 131 of the driving device 130 through fast fourier transform FFT of the pressure pulsation, and the processor determining the rotation speed n of the rotator 131 based on the frequency f of rotation of the rotator 131, for example, where n is 60 × f.

For another example, the blood pump may further include: a second housing 170, as shown in fig. 13 and 14, the second housing 170 being spaced apart from the first housing 110, the second housing 170 having a second receiving chamber 171 and an opening 172; the driving device 130 is fixed at one end of the second housing 170, and the rotating member 131 of the driving device 130 is connected to the impeller 120 through the opening 172; the detection means may comprise: a first vibration sensor 163, wherein the first vibration sensor 163 is disposed in the second accommodating cavity 171, the first vibration sensor 163 is located at a side close to the driving device 130, as shown in fig. 8 and 10, and the first vibration sensor 163 is used for detecting a vibration parameter of the driving device 130; the processor is configured to determine a rotational speed of the driving device 130 based on the vibration parameter detected by the first vibration sensor 163.

Here, the first vibration sensor 163 may be adhered to an inner wall of the second receiving chamber 171 by glue.

Here, the processor for determining the rotation speed of the driving device 130 based on the vibration parameter detected by the first vibration sensor 163 may include: the processor obtains the frequency of rotation of the rotor 131 of the driving device 130 by fast fourier transform FFT of the vibration parameter detected by the first vibration sensor 163, and determines the rotation speed n1 of the rotor 131 based on the frequency f1 of rotation of the rotor 131, for example, n1 is 60 × f 1.

Here, the processor is also configured to determine whether there is an abnormality in the blood pump based on the vibration parameter detected by the first vibration sensor 163, so that two functions can be realized by one sensor. The processor for determining whether an abnormality exists in the blood pump based on the vibration parameter detected by the first vibration sensor 163 may include: the processor is configured to determine that there is an abnormality in the operation of the blood pump when it is determined that the second amplitude detected by the first vibration sensor 163 is greater than a third set value; otherwise, the processor determines that the blood pump is operating properly; here, when the blood pump is inserted into the heart of the human body, the blood pump may be abnormal, such as the inlet is blocked or the blood pump is close to the wall surface of the ventricle, the blood flow rate is reduced, the vibration value of the driving device 130 is fluctuated, and whether the blood pump is operated abnormally or not can be determined from the vibration parameter of the driving device 130.

In this implementation, the implementation of the processor for determining the flow rate of the blood pump based on the pressure difference and the rotational speed is not limited.

For example, the processor stores a relationship table in which the pressure difference and the rotational speed correspond to the flow rate of the blood pump, and the processor determines the flow rate of the blood pump based on the relationship table.

For another example, as shown in fig. 17, a curve in which the pressure difference P and the rotational speed n correspond to the flow rate Q of the blood pump is stored in the processor, and the flow rate of the blood pump can be determined based on the corresponding curve.

Here, it should be noted that fig. 17 shows curves of only three rotational speeds by way of example, and those skilled in the art may set curves of more rotational speeds.

In this embodiment, the blood pump may further include: and a controller. The controller is arranged in the driving device 130, is electrically connected with the detection device, the first pressure sensor 161 and the processor, and is used for transmitting the first pressure information, the second pressure information and the rotating speed information to the processor; so that the processor determines the flow rate of the blood pump.

Here, the processor may be located outside the blood pump; for example, the processor may be located in an intelligent device or in the cloud.

Here, the controller may be electrically connected to the processor in a wired manner. Of course, the controller can also be electrically connected in a wireless manner; the wireless mode can be Bluetooth transmission, 4G/5G, VPN network transmission and the like.

Here, the blood pump may further include: a first conductive line 181, a second conductive line 182, and a third conductive line 183. A first end of the first conducting wire 181 is electrically connected with the detection device; a portion of the first lead 181 is located within the second receiving cavity 171; wherein, the second end of the first conducting wire 181 is electrically connected with the controller in the driving device 130; a first end of the second wire 182 is electrically connected to the first pressure sensor 161; a portion of the second lead 182 is located within the second receiving cavity 171; wherein a second end of the second wire 182 is electrically connected to a controller in the driving device 130; a first end of the third wire 183 is electrically connected to the second pressure sensor 162; wherein a second end of the third wire 183 is electrically connected to a controller in the driving device 130; when the controller is electrically connected with the processor in a wired mode, all the sensors can be electrically connected with the processor only through one conducting wire, and the structure is simple.

It should be noted that, when the blood pump includes: when the first vibration sensor 163, the photoelectric sensor 164, the first pressure pulsation sensor 165, or the ultrasonic sensor 166 is used, the first vibration sensor 163, the photoelectric sensor 164, the first pressure pulsation sensor 165, or the ultrasonic sensor 166 may be electrically connected to the controller.

Of course, the blood pump may not include a controller, as shown in fig. 8 and 13, and the first end of the first wire 181 is electrically connected to the detection device; a portion of the first lead 181 is located within the second receiving cavity 171; a second end of the first lead wire 181 is led out of the second accommodating cavity 171 to the outside of the second shell 170; a first end of the second wire 182 is electrically connected to the first pressure sensor 161; a portion of the second lead 182 is located within the second receiving cavity 171; a second end of the second wire 182 is led out of the second housing 170 from the second accommodating cavity 171; a first end of the third wire 183 is electrically connected to the second pressure sensor 162; a second end of the third wire 183 is led out of the second housing 170 from the second accommodating cavity 171; here, the leads of the plurality of sensors are led out of the second accommodating cavity 171 to the outside of the second housing 170, so that the volume of the leads of the plurality of sensors exposed to the second housing 170 is reduced, and the leads of the plurality of sensors are prevented from being pulled.

In some optional implementations of embodiments of the present application, the blood pump may further include: an ultrasonic sensor 166, the ultrasonic sensor 166 being disposed at the cannula 140, the ultrasonic sensor 166 being configured to detect a flow rate of blood within the lumen of the cannula 140; wherein the flow rate is used to determine the flow rate of blood within the lumen of the cannula 140.

In this implementation, the manner in which the ultrasonic sensor 166 detects the flow rate of blood within the lumen of the cannula 140 is not limited.

For example, as shown in fig. 15, the cannula 140 has a socket 143, the socket 143 communicates with the cavity of the cannula 140, the socket 143 is located on a side of the second introduction port 142 away from the first introduction port 141, a sound wave direction of the ultrasonic sensor 166 forms a second angle with an axial direction of the cannula 140, the ultrasonic sensor 166 emits ultrasonic waves to blood flowing in the cavity of the cannula 140, after the ultrasonic waves are accelerated by the blood, a doppler shift is generated in a signal received by the ultrasonic sensor 166, the doppler shift is proportional to the blood flow velocity v, the blood flow velocity v can be determined based on the doppler shift, and the flow value Q in the cannula 140 can be determined when the diameter D of the cannula 140 is known.

Here, the angle of the second angle is not limited. For example, the second included angle may be an acute angle.

For example, as shown in fig. 16, the transmitting end of the ultrasonic sensor 166 is provided on the outer side surface of the cannula 140, the transmitting end of the ultrasonic sensor 166 is located on the side of the second introduction port 142 away from the first introduction port 141, the receiving end of the ultrasonic sensor 166 is provided on the outer side surface of the cannula 140, the receiving end of the ultrasonic sensor 166 is provided opposite to the transmitting end of the ultrasonic sensor 166, the transmitting end of the ultrasonic sensor 166 emits ultrasonic waves, the receiving end of the ultrasonic sensor 166 receives the ultrasonic waves of the blood flowing therethrough, and the ultrasonic waves passing through the flowing blood generate a doppler shift that is proportional to the blood flow velocity v and that is affected by the flow velocity v of the flowing blood, and the blood flow velocity v can be determined based on the doppler shift, and the flow rate Q in the cannula 140 can be determined when the.

In some optional implementations of embodiments of the present application, the blood pump may further include: a second vibration sensor for detecting a vibration parameter of the driving device 130; the processor is electrically connected with the second vibration sensor and is used for determining whether the blood pump runs abnormally or not based on the vibration parameters detected by the second vibration sensor; so that it is determined whether there is an abnormality in the blood pump by the second vibration sensor.

In this implementation, when the blood pump is placed in the heart of a human body, the blood pump may be abnormal, such as the inlet is blocked or the blood pump is close to the wall surface of the ventricle, the blood flow rate may change, the vibration value of the driving device 130 may fluctuate, and thus, whether the blood pump operates abnormally or not may be determined from the vibration parameters of the driving device 130; at the same time, the power of the driving device 130 also changes, so that whether the blood pump is running abnormally can be judged based on the power of the driving device 130.

In this implementation, the second vibration sensor is similar to the first vibration sensor 163 described above and will not be described in detail here.

In this implementation, the vibration parameter of the driving device 130 may be a first amplitude of the driving device 130; the processor for determining whether there is an abnormality in the blood pump operation based on the vibration parameter detected by the second vibration sensor may include: the processor is used for determining that the blood pump runs abnormally when the first amplitude detected by the second vibration sensor is larger than a first set value; otherwise, the processor determines that the blood pump is operating properly; when the blood pump is inserted into a heart of a human body, the inlet of the blood pump is blocked or the blood pump approaches a wall surface of a ventricle, the first amplitude increases.

Of course, in other implementations, the blood pump may determine whether there is an abnormality in the operation of the blood pump in other ways.

For example, the blood pump may further include: a processor electrically connected to the driving device 130, the processor being configured to determine whether there is an abnormality in the operation of the blood pump based on the power of the driving device 130.

Here, the processor for determining whether there is an abnormality in the blood pump operation based on the power of the driving device 130 may include: the processor is used for determining that the blood pump runs abnormally when the power of the driving device 130 is determined to be smaller than a second set value; otherwise, the processor determines that the blood pump is operating properly.

Here, the second set value is a normal power at which the driving means 130 drives the blood flow. When the introduction port is blocked or comes close to the insertion object, the power of the driving means 130 for driving the blood flow becomes small.

In some optional implementations of embodiments of the present application, a processor may be used to determine a flow rate of the blood pump based on a power of the blood pump; so that the flow rate of the blood pump is quickly determined by the power of the blood pump. A processor may be used to determine a differential pressure of the blood pump based on the power of the blood pump so that the differential pressure of the blood pump is quickly determined by the power of the blood pump.

In this implementation, the pressure differential is a pressure at which the blood pump increases blood.

It should be noted that the pressure difference may also be determined by subtracting the first pressure at the inlet from the second pressure at the outlet, and the manner of determining the pressure difference by subtracting the first pressure at the inlet from the second pressure at the outlet has been described above, and will not be described herein again.

In this implementation, the implementation of the processor for determining the pressure differential of the blood pump based on the power of the blood pump is not limited.

For example, the processor stores a correspondence between the power of the blood pump and the pressure difference of the blood pump, and the processor can determine the pressure difference of the blood pump based on the correspondence between the power of the blood pump and the pressure difference of the blood pump.

For another example, as shown in fig. 18, a graph of power and pressure difference is stored in the processor; the processor can determine a pressure differential for the blood pump based on the power and pressure differential plots. Note that the pressure difference in fig. 18 is a pressure difference.

In this implementation, the implementation of the processor for determining the flow rate of the blood pump based on the power of the blood pump is not limited.

For example, the processor stores a correspondence between the power of the blood pump and the flow rate of the blood pump, and the processor can specify the flow rate of the blood pump based on the correspondence between the power of the blood pump and the flow rate of the blood pump.

For another example, as shown in fig. 19, a graph of power and flow rate is stored in the processor; the processor can determine the flow rate of the blood pump based on the power and flow rate graph.

The blood pump in the embodiment of this application, the blood pump includes: a first housing 110 having a first accommodation chamber 111; an impeller 120 disposed in the first receiving chamber 111; the driving device 130 is connected with the impeller 120 and is used for driving the impeller 120 to rotate; a cannula 140 connected with the first housing 110; the cavity of the cannula 140 is communicated with the first accommodating cavity 111; wherein the diameter of the cavity of the cannula 140 is smaller than the diameter of the first accommodating cavity 111; here, when the wall thickness of the cannula 140 and the wall thickness of the first accommodation chamber 111 are substantially equal, the cannula 140 can be set small in size, the blood pump can be reduced in size at the cannula 140, and the blood pump insertion operation is facilitated.

The above description is only for the specific embodiments of the present application, but the scope of the present application is not limited thereto, and any person skilled in the art can easily conceive of the changes or substitutions within the technical scope of the present application, and shall be covered by the scope of the present application. Therefore, the protection scope of the present application shall be subject to the protection scope of the claims.