CN114504728A - Sensor for heart blood pump and heart blood pump - Google Patents
Sensor for heart blood pump and heart blood pump Download PDFInfo
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- CN114504728A CN114504728A CN202011289526.8A CN202011289526A CN114504728A CN 114504728 A CN114504728 A CN 114504728A CN 202011289526 A CN202011289526 A CN 202011289526A CN 114504728 A CN114504728 A CN 114504728A
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Abstract
The invention provides a sensor for a heart blood pump and the heart blood pump, wherein the sensor comprises a static pressure sensing end arranged on a conveying sleeve of the heart blood pump, and the static pressure sensing end is used for detecting the static pressure of blood flowing through the outer side of the conveying sleeve; the static pressure sensing end comprises a pressure sensing membrane chip and an optical signal transmission line, the pressure sensing membrane chip is provided with a pressure sensing surface which is in contact with blood, the pressure sensing surface is parallel to the axial direction of the conveying sleeve, and the pressure sensing membrane chip acquires a static pressure signal which is perpendicular to the flowing direction of blood flow and transmits the static pressure signal out through the optical signal transmission line. According to the sensor provided by the invention, the pressure sensing surface is parallel to the blood flowing direction, the blood static pressure is directly measured, and a blood stagnation area is not required to be arranged at the static pressure sensing end to measure the blood static pressure, so that the formation of thrombus is avoided, the blood static pressure can be measured when the blood flows, and the sensor can be used for supporting a blood pump in a short-term heart and a long-term heart.
Description
Technical Field
The invention relates to the technical field of medical instrument design, in particular to a sensor for a heart blood pump and the heart blood pump.
Background
The heart failure refers to the heart circulatory disturbance syndrome caused by the insufficient discharge of venous return blood volume from the heart due to the dysfunction of the systolic function and/or diastolic function of the heart, resulting in the blood stasis of the venous system and the insufficient perfusion of the arterial system. The current means for treating heart failure include drug treatment, surgical heart replacement and left ventricle auxiliary devices. The left ventricle auxiliary device sucks blood through the heart blood pump to promote the flow of the heart blood, and the scheme has the advantages of good treatment effect, low cost and the like.
For current intracardiac blood pumps, pressure sensors are typically employed in order to sense intravascular pressure. The patent (US9669142) provides a pressure sensor fixed on the blood pump conduit, which needs to add extra 'fence' parts around the sensor sensing surface in order to measure the static pressure of blood without being affected by the blood flow speed, thereby creating a blood stagnation area to measure the static pressure of blood; this solution is, on the one hand, complicated and, on the other hand, prone to thrombus formation in the region of the blood stagnation over a long period of time. In addition, the pressure sensing surface in the pressure sensor is orthogonal to the axis of the pipe, so that the requirement on an assembly process is high, and the assembly is troublesome.
Disclosure of Invention
The invention provides a sensor for a heart blood pump, which aims to solve the problems in the prior art and comprises a static pressure sensing end arranged on a conveying sleeve of the heart blood pump, wherein the static pressure sensing end is used for detecting the static pressure of blood flowing through the outer side of the conveying sleeve; the static pressure sensing end comprises a pressure sensing membrane chip and an optical signal transmission line, the pressure sensing membrane chip is provided with a pressure sensing surface which is in contact with blood, the pressure sensing surface is parallel to the axial direction of the conveying sleeve, and the pressure sensing membrane chip acquires a static pressure signal which is perpendicular to the flowing direction of blood flow and transmits the static pressure signal out through the optical signal transmission line.
In some embodiments, the pressure sensing membrane chip and the optical signal transmission line are both disposed parallel to the axial direction of the delivery cannula, and a path element for converting a vertical optical signal into a horizontal optical signal is disposed between the pressure sensing membrane chip and the optical signal transmission line.
In some embodiments, the path element is a right-angle reflecting prism, the right-angle reflecting prism includes a first right-angle surface and a second right-angle surface which are adjacent to each other, and an inclined surface connecting the first right-angle surface and the second right-angle surface, the first right-angle surface is parallel to the pressure sensing film chip connection arrangement, the second right-angle surface is parallel to the optical signal transmission line distal end surface and is connected, and a reflecting film is arranged on the inclined surface.
In some embodiments, a self-focusing lens is disposed between the second right-angle surface and the optical signal transmission line.
In some embodiments, the pressure sensing diaphragm chip is perpendicularly connected to the distal end of the optical signal transmission line, and the axial direction of the distal end of the optical signal transmission line is perpendicular to the axial direction of the delivery sleeve.
In some embodiments, the optical signal transmission line is arranged in the sheath and extends along the axial direction of the sheath; the pressure sensing membrane chip is arranged at the far end of the sheath to form the static pressure sensing end, and an opening used for exposing the pressure sensing surface and contacting with blood is arranged at the corresponding position on the sheath.
In some embodiments, the pressure sensing diaphragm chip is disposed in the opening, and the pressure sensing surface does not extend beyond the outer wall surface of the sleeve structure.
In some embodiments, the sheath is a sleeve structure disposed on an outer wall surface or on an inner wall surface or within a wall of the delivery sleeve;
or, a channel is arranged in the pipe wall of the conveying sleeve to form the sheath.
In some embodiments, the sleeve structure is disposed on an outer wall surface of the delivery sleeve; the outer wall surface of the conveying sleeve is provided with a groove, and the sleeve structure is at least partially positioned in the groove.
In some embodiments, the sleeve structure is bonded within the groove by a biocompatible glue.
In some embodiments, the material of the sleeve structure is polyimide.
In some embodiments, the diameter of the sleeve structure does not exceed 0.5mm
In some embodiments, the end of the sleeve structure is radiused.
In some embodiments, the optical signal transmission line employs an optical fiber.
The invention also provides a heart blood pump, wherein at least one pressure sensor is arranged on the conveying sleeve of the heart blood pump, and the pressure sensor adopts the sensor.
Due to the adoption of the technical scheme, compared with the prior art, the invention has the following advantages and positive effects:
the pressure sensing surface of the sensor provided by the invention is parallel to the blood flowing direction, and is used for directly measuring the blood static pressure without arranging a blood stagnation area at the static pressure sensing end to measure the blood static pressure, so that the formation of thrombus is avoided, the blood static pressure can be measured when the blood flows, and the sensor can be used for supporting a short-term and long-term blood pump in the heart; the sensor system has the advantages that extra enclosing wall parts are not needed, the structure is simple, the diameter size of the sensor system is smaller, and the damage to human tissues is smaller when the sensor system is implanted; in addition, the pressure sensing surface and the conveying sleeve are designed to be axially parallel, the static pressure of blood is directly measured, the pressure sensing surface is not required to be orthogonal to the axis of the conveying sleeve, and the requirement on an assembly process is low.
Drawings
The above and other features and advantages of the present invention will be more clearly understood from the following detailed description taken in conjunction with the accompanying drawings, in which:
FIG. 1 is a schematic representation of hydrostatic pressure;
fig. 2 is a schematic structural diagram of a sensor for a heart blood pump in embodiment 1 of the present invention;
FIG. 3 is a schematic sectional view of a static pressure sensing terminal in embodiment 1 of the present invention;
FIG. 4 is a schematic structural diagram of a right-angle reflecting prism in example 1 of the present invention;
FIG. 5 is a schematic view of the radial seal shown in the view A in FIG. 2;
FIG. 6 is a schematic structural diagram of a sensor for a heart blood pump in embodiment 2 of the present invention;
FIG. 7 is a schematic sectional view of a static pressure sensing terminal in embodiment 2 of the present invention;
FIG. 8 is an enlarged schematic view at D of FIG. 6;
FIG. 9 is a view taken along line B in FIG. 6;
fig. 10 is a schematic view of fig. 6 taken along direction C.
Detailed Description
The present invention will be described in more detail below with reference to the accompanying drawings, which illustrate embodiments of the invention. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art. In the drawings, the size and relative sizes of layers and regions may be exaggerated for clarity.
It should be noted that all the directional indicators (such as up, down, left, right, front, and rear … …) in the embodiment of the present invention are only used to explain the relative position relationship between the components, the movement situation, etc. in a specific posture (as shown in the drawing), and if the specific posture is changed, the directional indicator is changed accordingly.
The invention provides a sensor for a heart blood pump, which comprises a static pressure sensing end arranged on a conveying sleeve of the heart blood pump, wherein the static pressure sensing end is used for detecting the static pressure of blood flowing through the outer side of the conveying sleeve; the static pressure sensing end comprises a pressure sensing membrane chip and an optical signal transmission line, the pressure sensing membrane chip is provided with a pressure sensing surface which is in contact with blood, the pressure sensing surface is parallel to the axial direction of the conveying sleeve, and the pressure sensing membrane chip acquires a static pressure signal which is vertical to the flowing direction of blood flow and transmits the static pressure signal out through the optical signal transmission line.
The axial direction of a conveying sleeve of the heart blood pump is along the flowing direction of blood in the heart, a sensor is sent into the heart along with the conveying sleeve to measure the static pressure of the blood in the heart, the static pressure can represent the working performance (flow, aortic pressure, left ventricular pressure and pump blood power) of the heart blood pump, and the static pressure can reflect whether the blood pump is in a normal working state or not, so that the subsequent operations such as data adjustment and the like of the heart blood pump can be conveniently carried out.
The sensor provided by the invention can directly measure the static pressure of blood by arranging the pressure sensing surface which is in contact with the blood to be parallel to the axial direction of the conveying sleeve, namely, the pressure sensing surface is parallel to the flow direction of the blood (wherein the explanation about the static pressure is shown in figure 1, and the pressure in the direction vertical to the flow direction of the fluid is the hydrostatic pressure); the pressure sensing membrane chip transmits the obtained static pressure to the background controller through the optical signal transmission line, and the background controller is used for processing and displaying the optical fiber signals. The pressure sensing surface is parallel to the blood flowing direction, the blood static pressure is directly measured, and a blood stagnation area is not required to be arranged at the static pressure sensing end to measure the blood static pressure, so that the formation of thrombus is avoided, the blood static pressure can be measured when the blood flows, and the device can be used for supporting a short-term and long-term blood pump in the heart; the sensor system has the advantages that extra enclosing wall parts are not needed, the structure is simple, the diameter size of the sensor system is smaller, and the damage to human tissues is smaller when the sensor system is implanted; in addition, the pressure sensing surface and the conveying sleeve are designed to be axially parallel, so that the static pressure of blood is directly measured, the pressure sensing surface is not required to be orthogonal to the axis of the conveying sleeve, and the requirement on an assembly process is low.
The following further description is made with respect to specific embodiments:
example 1
Referring to fig. 2-5, in the present embodiment, the sensor 1 includes a pressure sensing diaphragm 101 and an optical signal transmission line 102, both the pressure sensing diaphragm 101 and the optical signal transmission line 102 being disposed parallel to the axial direction of the delivery casing 3; the near end of the optical signal transmission line 102 is connected to the background controller 2, the far end is connected to the pressure sensing diaphragm chip 101 through a path element, and the path element 103 is used for converting a vertical optical signal (an optical signal in a direction perpendicular to the pressure sensing diaphragm chip 101) into a horizontal optical signal (an optical signal in a direction parallel to the optical signal transmission line 102).
In this embodiment, the optical signal transmission line 102 is preferably an optical fiber, but in other embodiments, other optical signal transmission lines with the same function may be used, and the present invention is not limited herein.
In this embodiment, the pressure sensing membrane chip is composed of a pressure sensing membrane and a chip, the pressure sensing membrane and the chip are arranged in parallel, a gap is left between the pressure sensing membrane and the chip to enable the pressure sensing membrane and the chip to form a standard cavity length, the pressure sensing membrane is in contact with blood to sense and compress the blood, and the chip is connected with the optical signal transmission line to realize the transmission of the optical signal; after the pressure sensing film is subjected to static pressure, the pressure sensing film is inwards concave and deformed towards one side of the chip, the distance between the pressure sensing film and the chip is shortened, and the cavity length is changed; therefore, the formation of light transmission is changed, the background controller can obtain the light transmission formation before and after the static pressure, the stroke is calculated by the background controller, the different light transmission strokes can correspond to the pressure values one by one, and the static pressure value can be obtained.
In this embodiment, the pressure sensing membrane is a biocompatible ceramic membrane or glass membrane, which is not limited herein and can be adjusted according to specific situations.
In the present embodiment, the path element employs a right-angle reflecting prism 103; specifically, referring to fig. 3-4, the right-angle reflecting prism 103 includes a first right-angle surface 1031 and a second right-angle surface 1032 which are adjacent to each other, and a slope 1033 connecting the first right-angle surface 1031 and the second right-angle surface 1032; the first rectangular surface 1031 is oppositely arranged parallel to the pressure sensing membrane chip 101, and the first rectangular surface 1031 is connected with the pressure sensing membrane chip 101; the second right-angle surface 1032 is parallel to the end face of the far end of the optical signal transmission line 102 and is oppositely arranged, and the second right-angle surface 1032 is connected with the far end of the optical signal transmission line 102; the inclined plane 1033 is provided with a reflecting film, and through the arrangement of the right-angle reflecting prism 103, the optical signal is bent by 90 degrees under the action of the reflecting film, so that the transmission of the optical signal between the optical signal transmission line 102 and the pressure sensing film chip 101 which are arranged in parallel is realized.
Of course, the specific structure of the path element in other embodiments is not limited to the above, and prisms or optical elements with other structures may be selected as long as the transmission direction of the optical signal can be changed, which is not limited herein and can be selected according to specific situations.
Further, a self-focusing lens is added between the second right-angle surface 1032 and the optical signal transmission line 102, so that the sensitivity of the optical signal is increased, and the measurement error is reduced; of course, in other embodiments, the arrangement of the self-focusing lens can be omitted, and is not limited herein.
In this embodiment, the sensor 1 further includes a sheath, and the pressure sensing membrane chip 101, the path element and the optical signal transmission line 102 are all disposed in the sheath to perform a protection function; the optical signal transmission line 102 extends along the axial direction of the sheath, the pressure sensing membrane chip 101 is located at the far end of the sheath 4, so that the far end of the sheath 4 forms a static pressure sensing end, and an opening for exposing the pressure sensing surface to make the pressure sensing surface contact with blood is arranged on the sheath corresponding to the pressure sensing membrane chip 101.
In this embodiment, the sheath is a sleeve structure 4, the sleeve structure 4 is arranged on the outer wall of the delivery sleeve 3 along the axial direction of the delivery sleeve 3, the proximal end of the sleeve structure 4 extends to the background controller 2, and the distal end of the sleeve structure extends to the static pressure sensing end; of course, in other embodiments the sleeve structure 4 may also be arranged on or in the inner wall of the delivery sleeve 3, without limitation.
Furthermore, an opening is formed in the side wall of the far end of the sleeve structure 4, the pressure sensing membrane chip 101 is arranged in the opening, and the pressure sensing surface of the pressure sensing membrane chip 101 is ensured not to exceed the outer wall surface of the sleeve structure 4, so that the pressure sensing membrane chip 101 is prevented from scraping the intracardiac tissue when the sleeve structure 4 is implanted into the heart along with the conveying sleeve 3; further preferably, the pressure sensing surface of the pressure sensing membrane chip 101 is flush with the outer wall surface of the casing structure 4, so as to avoid scratching tissues and prevent blood from being retained to form thrombus.
Further, a groove 301 is provided on the outer wall surface of the delivery cannula 3, at least the distal end of the cannula structure 4 is positioned in the groove 301, and the cannula structure 4 is fixed in the groove 301 by gluing with a biocompatible glue, as shown in fig. 5. In the embodiment, the arrangement of the groove 301 ensures that the axial direction of the far end of the sleeve structure is parallel to the axial direction of the conveying sleeve 3, so that the static pressure sensing surface can be accurately parallel to the blood flowing direction, and the detection accuracy is ensured; the sleeve structure 4 may be positioned entirely or partially through the groove 301, as long as it is ensured that the distal end (i.e., the static pressure sensing end) of the sleeve structure 4 is positioned in the groove 302 to achieve accurate positioning, and the positioning is not limited herein and may be adjusted according to specific situations. Of course, in other embodiments, the positioning structure of the sleeve structure 4 is not limited to the groove structure described above, and can be adjusted according to specific situations, and is not limited herein.
Further, the material of the sleeve structure 4 is preferably polyimide, but in other embodiments, other materials may be used as the sleeve structure, as long as biocompatibility, mechanical strength, and processability are ensured, and the material is not limited herein.
Furthermore, the diameter of the sleeve structure 4 is not more than 0.5mm, so that the size of the whole delivery sleeve is reduced and increased while the sensor can be packaged, and the implantation of the delivery sleeve is facilitated; the specific value of the diameter of the sleeve structure 4 can be adjusted according to specific conditions, and is not limited here.
Further, as shown in fig. 3, the distal end of the cannula instrument 4 is smoothly rounded to facilitate the smooth implantation of the cannula instrument 4 into the heart along with the delivery cannula 3.
The sheath provided by the present embodiment has a simple structure and is easy to install, but in other embodiments, the implementation of the sheath is not limited to the above, for example, a channel is formed in the tube wall of the delivery sleeve 3 to form the sheath, and the present invention is not limited thereto.
The working principle of the sensor provided in this embodiment is further explained as follows:
after the sensor is implanted into the heart along with the delivery cannula, blood flows through the outside of the delivery cannula in parallel with the axial direction of the delivery cannula, and the pressure sensing membrane chip 101 parallel to the blood flow direction can detect the static pressure of the blood and then transmit the static pressure to the background controller through the optical signal transmission line 102.
Example 2
This example is an adjustment made on the basis of example 1.
Specifically, referring to fig. 6 to 10, in the present embodiment, the sensor includes a sleeve structure 4, an optical signal transmission line 102 and a pressure sensing membrane chip 101 are disposed in the sleeve structure 4, the optical signal transmission line 102 is disposed along an axial direction of the sleeve structure 4, a distal end face of the optical signal transmission line 102 has an opening, the pressure sensing membrane chip 101 is mounted in the opening, and the pressure sensing membrane chip 101 is perpendicular to the axial direction of the optical signal transmission line 102 and is connected thereto.
The present embodiment omits the arrangement of path elements, so that the pressure sensing membrane chip 101 is vertically connected with the optical signal transmission line 102, and the transmission of the optical signal is directly realized.
In the present embodiment, the cannula instrument 4 is fixed on the delivery cannula 3 in a winding manner, and the distal end section of the cannula instrument 4 is curved in a 90 ° arc shape, so that the end surface of the distal end of the cannula instrument 4 is parallel to the axial direction of the delivery cannula 3, and the pressure sensing diaphragm chip 101 on the distal end surface of the cannula instrument 4 is parallel to the flow direction of the blood, so as to ensure that the static pressure of the blood is measured. As shown in fig. 7-8.
Furthermore, the outer wall surface of the conveying sleeve 3 is also provided with a groove so as to facilitate the fixing of the sleeve structure in the groove to realize positioning and installation; the far end of the sleeve structure 4 is not provided with a groove structure, the far end of the sleeve structure 4 is directly fixed on the outer wall surface of the conveying sleeve 3 through biocompatible glue, and the glue back to one side of the blood flowing direction is streamline, as shown in fig. 10, the far end of the sleeve structure 4 is arranged to prevent a blood stagnation area from being formed on the side back to the blood flowing direction, so that thrombus is prevented from being formed.
Other structures of the sensor in the present embodiment can be described with reference to embodiment 1.
Example 3
The embodiment provides a heart blood pump, wherein at least one pressure sensor is arranged on a delivery sleeve of the heart blood pump, and the pressure sensor adopts the sensor described in embodiment 1 or embodiment 2.
The heart blood pump is suitable for a right ventricle auxiliary device and a left ventricle auxiliary device; the left ventricle assists in detecting the aortic root blood pressure, and right atrium blood pressure is detected correspondingly to the right ventricle; the left ventricle assists in detecting the left ventricular blood pressure and correspondingly the right ventricle assists in detecting the pulmonary artery blood pressure.
Taking left ventricle assistance as an example, at least one pressure sensor, preferably one pressure sensor, is arranged on the heart blood pump, and the static pressure sensing end of the pressure sensor is fixed on the outer surface of the sleeve at the proximal end of the heart blood pump and is used for detecting the aortic root blood pressure; the heart blood pump can also be provided with two pressure sensors, and the static pressure sensing end of the second pressure sensor is fixed on the outer surface of the sleeve at the far end of the heart blood pump and used for detecting the blood pressure of the left ventricle.
The setting position and the setting number of the pressure sensors on the heart blood pump can be selected according to specific conditions, and the setting position and the setting number are not limited here.
The invention takes left ventricle assistance as an example for explanation, and can also be used for right ventricle assistance, wherein the left ventricle assists in detecting the aortic root blood pressure and detects the right atrial blood pressure correspondingly to the right ventricle assistance; the left ventricle assists in detecting the left ventricular blood pressure and correspondingly the right ventricle assists in detecting the pulmonary artery blood pressure.
It will be appreciated by those skilled in the art that the invention can be embodied in many other specific forms without departing from the spirit or scope thereof. Although embodiments of the present invention have been described, it is to be understood that the present invention should not be limited to those precise embodiments, and that various changes and modifications can be effected therein by one skilled in the art without departing from the scope or spirit of the invention as defined by the appended claims.
Claims (15)
1. A sensor for a heart blood pump is characterized by comprising a static pressure sensing end arranged on a conveying sleeve of the heart blood pump, wherein the static pressure sensing end is used for detecting the static pressure of blood flowing through the outer side of the conveying sleeve; the static pressure sensing end comprises a pressure sensing membrane chip and an optical signal transmission line, the pressure sensing membrane chip is provided with a pressure sensing surface which is in contact with blood, the pressure sensing surface is parallel to the axial direction of the conveying sleeve, and the pressure sensing membrane chip acquires a static pressure signal which is perpendicular to the flowing direction of blood flow and transmits the static pressure signal out through the optical signal transmission line.
2. The sensor for a heart blood pump of claim 1, wherein the pressure sensing membrane chip and the optical signal transmission line are both disposed parallel to the axial direction of the delivery cannula, and a path element for converting a vertical optical signal into a horizontal optical signal is disposed between the pressure sensing membrane chip and the optical signal transmission line.
3. The sensor for the heart blood pump as claimed in claim 2, wherein the path element is a right-angle reflecting prism, the right-angle reflecting prism comprises a first right-angle surface and a second right-angle surface which are adjacent to each other, and an inclined surface connecting the first right-angle surface and the second right-angle surface, the first right-angle surface is arranged in parallel with the pressure sensing film chip, the second right-angle surface is arranged in parallel with the distal end face of the optical signal transmission line and is connected with the optical signal transmission line, and a reflecting film is arranged on the inclined surface.
4. The sensor for the heart blood pump of claim 3, wherein a self-focusing lens is arranged between the second right-angle surface and the optical signal transmission line.
5. The sensor for a heart blood pump of claim 2, wherein the pressure sensing membrane chip is vertically connected to a distal end of the optical signal transmission line, and an axial direction of the distal end of the optical signal transmission line is perpendicular to an axial direction of the delivery sleeve.
6. The sensor for a heart blood pump according to claim 1, 2 or 4, further comprising a sheath, wherein the optical signal transmission line is disposed in the sheath and extends axially along the sheath; the pressure sensing membrane chip is arranged at the far end of the sheath to form the static pressure sensing end, and an opening for exposing the pressure sensing surface to be contacted with blood is arranged at the corresponding position on the sheath.
7. The sensor for a heart blood pump of claim 6, wherein said pressure sensing diaphragm chip is disposed within said opening and said pressure sensing surface does not extend beyond an outer wall surface of said sleeve structure.
8. The sensor for a heart blood pump of claim 6, wherein the sheath is a sleeve structure disposed on an outer wall surface or on an inner wall surface or within a tube wall of the delivery sleeve;
or, a channel is arranged in the pipe wall of the conveying sleeve to form the sheath.
9. The sensor for a heart blood pump of claim 8, wherein said sleeve structure is disposed on an outer wall surface of said delivery sleeve; the outer wall surface of the conveying sleeve is provided with a groove, and the sleeve structure is at least partially positioned in the groove.
10. The sensor for a heart blood pump of claim 9, wherein said sleeve structure is bonded within said recess by a biocompatible glue.
11. The sensor for a heart blood pump of claim 8, wherein the material of the sleeve structure is polyimide.
12. A sensor for a heart blood pump according to claim 8, wherein the diameter of the sleeve structure is no more than 0.5 mm.
13. The sensor for a cardiac blood pump according to claim 8, wherein the distal end of the sleeve structure is radiused.
14. The sensor for a heart blood pump of claim 1, wherein said optical signal transmission line is an optical fiber.
15. A heart blood pump, characterized in that at least one pressure sensor is arranged on a delivery sleeve of the heart blood pump, and the pressure sensor adopts a sensor as claimed in any one of claims 1 to 14.
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