Conduit pump assembly, conduit pump and ventricular assist device

Abstract

A kind of conduit pump assembly, conduit pump and ventricular assist device, conduit pump assembly includes shell and thrombus monitor.The first chamber with opening is formed in shell, and the first chamber side wall is opened with several fluid outlets in the periphery, and at least one fluid outlet in several fluid outlets is detection port.Thrombus monitor is set up with detection port one to one, and each thrombus monitor includes first probe and second probe, and first probe and second probe are all installed in shell side wall and located in the circumferential side of detection port.First probe has laser emission window, and second probe has laser receiving window, and laser emission window and laser receiving window are oppositely arranged to monitor the change of solid component in the fluid of detection port.By laser detection, different material components in blood are used to make medical staff obtain the change of blood component according to the result of laser detection in time, and thrombosis is effectively prevented.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more particularly to a catheter pump assembly, a catheter pump, and a ventricular assist device. Background Technology

[0002] Interventional ventricular assist devices (VADs) are percutaneous temporary cardiac support devices that help reduce the burden on the heart and meet the blood supply needs of heart failure patients by implanting a miniature pump. However, during long-term operation of the miniature pump, it is highly susceptible to the formation of potentially fatal blood clots. These clots can impede normal blood flow and, in severe cases, lead to vascular embolism, causing thrombotic complications such as myocardial infarction and cerebral infarction, thus affecting the patient's survival. Therefore, real-time monitoring and detection of blood clots during the operation of the miniature pump are crucial.

[0003] Currently, there are three main methods for in vivo thrombosis detection: CT-based methods, optical OCT-based methods, and Doppler ultrasound-based methods. CT-based methods have low imaging resolution and cannot distinguish small blood clots, thus failing to detect clots early and prevent thrombosis. Optical OCT-based methods use complex and bulky probes, which are incompatible with micropump structures and cannot achieve real-time imaging. Doppler ultrasound-based methods have low resolution for red blood cells and fibrinogen and are easily affected by blood microbubbles.

[0004] Therefore, how to improve the technical defects existing in the prior art has always been a problem that ordinary people skilled in the art need to solve. Summary of the Invention

[0005] The purpose of this application is to provide a catheter pump assembly, a catheter pump, and a ventricular assist device that can monitor blood flow in the human body in real time and detect blood clots in the blood in a timely manner, so that medical personnel can intervene in treatment in advance to prevent thrombosis.

[0006] The technical solution provided in this application is as follows: A conduit pump assembly, comprising: A housing having an opening in the first chamber, and a plurality of fluid outlets circumferentially formed on the sidewall of the first chamber; wherein at least one of the plurality of fluid outlets is a detection port; A thrombosis monitor is provided, corresponding to each of the detection ports, and each of the thrombosis monitors includes a first probe and a second probe. The first probe and the second probe are both installed on the side wall of the housing and located around the detection port. The first probe has a laser emitting window, and the second probe has a laser receiving window, and the laser emitting window and the laser receiving window are arranged opposite to each other to monitor changes in the solid components in the fluid at the detection port.

[0007] In some embodiments, the laser emitting window is used to emit infrared laser light, and the laser receiving window is used to receive the infrared laser light.

[0008] In some embodiments, the outer wall of the housing is provided with a first mounting base, the first mounting base being located on the side of the detection port facing the distal end of the housing, and the first mounting base is provided with a first fixing hole, through which the first probe passes; and The outer wall of the housing is provided with a second mounting base, which is located on the side of the detection port facing the near end of the housing, and the second mounting base is provided with a second fixing hole, through which the second probe passes.

[0009] In some embodiments, the diameter of the first fixing hole is larger than the outer contour size of the first probe, and the first probe is fixed to the first mounting base by adhesive; and The diameter of the second fixing hole is larger than the outer contour size of the second probe, and the second probe is fixed to the second mounting base by adhesive.

[0010] In some embodiments, the end of the first probe opposite to the second probe is connected to an optical fiber, which is used to connect to a laser generator; and the end of the second probe opposite to the first probe is connected to a conductive cable, which is used to connect to a control device. A support pillar is formed between each pair of adjacent fluid outlets. The optical fiber is fixed to a support pillar adjacent to the detection port and extends toward the near end of the housing. The optical fiber is located on the side of the detection port facing the near end of the housing and is arranged side by side with the conductive cable.

[0011] In some embodiments, the first probe includes a first housing, a first focusing lens, and a collimating lens; The first outer casing has a fiber optic inlet window at its distal end for connecting to the fiber optic cable, and the laser emission window is located at the proximal end of the first outer casing; and Both the first focusing lens and the collimating lens are disposed inside the first housing, with the first focusing lens positioned close to the fiber optic inlet window and the collimating lens positioned close to the laser emission window; The first focusing lens and the collimating lens are used to magnify the cross-sectional area of ​​the laser beam that enters the interior of the first housing through the fiber optic guide window.

[0012] In some embodiments, the sidewall of the housing is provided with a perforation, and the near end of the housing is provided with an opening communicating with the perforation; The end of the optical fiber furthest from the first probe and the end of the conductive cable furthest from the second probe pass through the perforation inside the housing and exit through the opening inside the housing.

[0013] In some embodiments, the outer wall of the housing is provided with a first mounting groove adapted to mount the optical fiber, and the first mounting groove is at least partially located on a support adjacent to the detection port; and the size of the opening of the first mounting groove is larger than the outer diameter of the optical fiber, and the optical fiber is fixed to the first mounting groove by adhesive. The outer wall of the housing is provided with a second mounting groove, which is suitable for mounting the optical fiber and the conductive cable. The size of the second mounting groove is larger than the sum of the outer diameter of the optical fiber and the outer diameter of the conductive cable. The optical fiber and the conductive cable are fixed to the second mounting groove by adhesive.

[0014] This application also provides a conduit pump, comprising: An impeller, a motor that drives the impeller to rotate, and a duct pump assembly provided by any of the above; A second chamber is formed inside the shell, and the first chamber and the second chamber are arranged sequentially from the distal end to the proximal end along the length of the shell. The impeller is located in the first chamber, and the motor is located in the second chamber. Driven by the motor, the impeller draws fluid into the first chamber through the opening and then discharges the fluid through the fluid outlet.

[0015] This application also provides a ventricular assist device, including: Cable conduit and the conduit pump provided above; The housing has a first docking portion at its distal end, suitable for docking with the pipe body; the housing has a second docking portion at its proximal end, suitable for docking with the cable conduit.

[0016] The technical advantages of this application are as follows: 1. This application incorporates a first probe with a laser emission window and a second probe with a laser receiving window around the detection port to form a laser detection segment at the port. Because different components in the blood exhibit varying abilities to absorb and scatter laser light in both back and side directions, the electrical signal of the second probe with the laser receiving window fluctuates as blood flows out of the detection port. This is especially true when the blood contains numerous tiny particles or blood clots, in which case the electrical signal of the second probe will significantly weaken. This allows medical personnel to detect blood clots promptly and intervene early to prevent further aggregation and thrombus formation, effectively reducing the probability of complications and demonstrating strong practicality.

[0017] 2. In this application, the laser emitted by the first probe is an infrared laser with a wavelength of 600-800nm. Under normal circumstances, blood is 90% water and the remaining 10% is protein and cells, etc., so its density is low. It mainly absorbs blue-violet light below 600nm and absorbs less light with wavelengths of 600-800nm. Blood clots, on the other hand, are aggregates of a large number of proteins, red blood cells, and white blood cells, etc., and have a higher density, thus absorbing a large amount of light with wavelengths of 600-800nm. Therefore, the infrared laser with a wavelength of 600-800nm ​​used in this application can effectively detect changes in the composition of blood clots in the blood, thereby assisting medical personnel in quickly identifying the appearance of blood clots and intervening in treatment in a timely manner to prevent the formation of thrombosis.

[0018] 3. In this application, the optical fiber extends toward the near end of the housing via a support pillar adjacent to the detection port. On the one hand, this avoids the detection port, so as not to affect the outflow of fluid or the monitoring of the thrombosis monitor. On the other hand, the support pillar can provide a certain degree of support and fixation for the optical fiber, which is more conducive to the fixation of the optical fiber and prevents it from shifting. Attached Figure Description

[0019] The present application will be further described in detail below with reference to the accompanying drawings and specific embodiments: Figure 1 This is a plan view of a conduit pump provided in an embodiment of this application; Figure 2 This is a partial three-dimensional structural diagram of the distal end of a shell provided in an embodiment of this application; Figure 3 This is a structural view of a thrombosis monitor provided in an embodiment of this application.

[0020] Explanation of icon numbers: 100. Housing; 101. Opening; 102. Fluid outlet; 103. Detection port; 104. First mounting base; 1041. First fixing hole; 105. Second mounting base; 1051. Second fixing hole; 106. Support column; 107. Through hole; 108. First mounting groove; 109. Second mounting groove; 110. First mating part; 111. Second mating part; 200. Thrombosis monitor; 210. First probe; 211. Laser emission window; 212. First housing; 213. Fiber optic cable entry window; 214. First focusing lens; 215. Collimating lens; 220. Second probe; 221. Laser receiving window; 222. Second housing; 223. Second focusing lens; 224. Light shield; 2241. Light shielding hole; 225. Photoelectric conversion element; 300. Fiber optic cable; 400. Conductive cable; 500. Laser generator 600. Cable conduit. Detailed Implementation

[0021] In the following description, specific details such as particular system architectures and techniques are set forth for illustrative purposes and not for limitation, in order to provide a thorough understanding of the embodiments of this application. However, those skilled in the art will understand that this application can also be implemented in other embodiments without these specific details. In other instances, detailed descriptions of well-known systems, apparatuses, circuits, and methods have been omitted so as not to obscure the description of this application with unnecessary detail.

[0022] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the specific implementation methods of this application will be described below with reference to the accompanying drawings. Obviously, the accompanying drawings described below are only some embodiments of this application. For those skilled in the art, other drawings and other implementation methods can be obtained based on these drawings without creative effort.

[0023] To keep the drawings concise, only the parts relevant to this application are shown schematically in each drawing, and they do not represent the actual structure of the product. In addition, to make the drawings concise and easy to understand, in some drawings, only one of the components with the same structure or function is shown schematically, or only one of them is labeled.

[0024] In this document, it should be noted that, unless otherwise explicitly specified and limited, the term "connection" should be interpreted broadly. For example, it can refer to a fixed connection, a detachable connection, or an integral connection; or it can refer to a mechanical connection or an electrical connection; or it can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0025] In the embodiments shown in the accompanying drawings, the directional indications (such as up, down, left, right, front, and back) are relative rather than absolute when describing the structure and movement of the various components, and are not intended to limit the direction of the product during actual use.

[0026] Furthermore, in the description of this application, ordinal numbers, such as "first" and "second," are used only to distinguish related objects and should not be construed as indicating or implying the relative importance or order between related objects. Also, in the description of this application, "proximal end" refers to the end along the length of the duct pump that is closer to the operator, and "distal end" refers to the end along the length of the duct pump that is farther from the operator.

[0027] During the long-term operation of the microcatheter pump in interventional ventricular assist devices (VADs), blood clots of varying sizes can easily form at the blood flow outlet of the pump, typically ranging from tens to hundreds of micrometers, or even reaching the centimeter level. If medical personnel can detect and promptly intervene with treatment when the blood clot is only tens of micrometers in size, they can effectively prevent further aggregation of the blood clot, prevent thrombosis, thereby greatly improving the therapeutic effect of VADs, reducing the probability of complications, and ultimately improving the patient's quality of life.

[0028] For this, see Figure 1 and Figure 2 This application provides a catheter pump assembly, specifically including a housing 100 and a thrombus monitor 200. The housing 100 has a first chamber with an opening 101. The sidewall of the first chamber has a plurality of fluid outlets 102 arranged circumferentially, and at least one of the fluid outlets 102 is a detection port 103. The thrombus monitor 200 is configured to correspond one-to-one with each detection port 103 to monitor changes in the composition of the fluid (i.e., blood flow in the human body) at the detection port 103, so that medical personnel can promptly detect blood clots in the blood and intervene in treatment in advance to prevent thrombosis.

[0029] Specifically, each thrombosis monitor 200 includes a first probe 210 and a second probe 220, both of which are mounted on the side wall of the housing 100 and located around the detection port 103. For example, the first probe 210 has a laser emitting window 211, and the second probe 220 has a laser receiving window 221, with the laser emitting window 211 and the laser receiving window 221 arranged opposite to each other.

[0030] In this embodiment, a laser detection segment is formed at the detection port 103 of the housing 100 by setting a first probe 210 with a laser emission window 211 and a second probe 220 with a laser receiving window 221. Because different components in the blood have varying abilities to absorb and scatter laser light in reverse / lateral directions, the electrical signal of the second probe 220 with the laser receiving window 221 will fluctuate when blood flows out of the detection port 103. This is especially true when the blood contains many tiny particles or blood clots, in which case the electrical signal of the second probe 220 will be significantly weakened. Thus, medical personnel can promptly detect blood clots based on changes in the electrical signal of the second probe 220, allowing for early intervention and treatment to prevent further aggregation and thrombus formation, effectively reducing the probability of complications and demonstrating strong practicality.

[0031] Of course, in actual production, each detection port 103 can also be equipped with two or more thrombosis monitors 200, which will not be elaborated here, and are all within the scope of protection of this application.

[0032] For example, considering production costs and the outline size requirements of the catheter pump, in one embodiment, only one of the several fluid outlets on the housing 100 is used as a detection port 103, and the detection port 103 corresponds to only one thrombosis monitor 200.

[0033] At this time, the first probe 210 and the second probe 220 are preferably respectively disposed on both sides of the detection port 103 in the length direction of the housing 100. Specifically, the first probe 210 is installed on the housing 100 and located on the side of the detection port 103 facing the far end of the housing 100, while the second probe 220 is installed on the housing 100 and located on the side of the detection port 103 facing the inlet end of the housing 100.

[0034] Of course, in actual production, the positions of the first probe 210 and the second probe 220 can be interchanged without affecting the thrombus monitor 200's detection of blood components at the fluid outlet. This is not a limitation and is within the scope of protection of this application.

[0035] Furthermore, the laser emitting window 211 is used to emit infrared laser light, while the laser receiving window 221 is used to receive infrared laser light. Understandably, optical detection is widely used in industrial and academic research fields for detecting components and changes in those components. Under normal circumstances, blood is 90% water and the remaining 10% consists of proteins and cells, resulting in a relatively low overall density. It primarily absorbs blue-violet light below 600nm and absorbs relatively little infrared laser light in the 600-800nm ​​wavelength range. In contrast, blood clots are aggregates of proteins, red blood cells, and white blood cells, resulting in a higher density. They can absorb a large amount of infrared laser light in the 600-800nm ​​wavelength range, especially when the size of the blood clot is much larger than 800nm. In this case, the effect of the blood clot on infrared laser light in the 600-800nm ​​wavelength range is mainly absorption and back / side scattering. Therefore, this embodiment can use infrared laser with a wavelength of 600-800nm ​​to monitor changes in blood clot composition in real time, which helps medical personnel to detect blood clots in the early stage and intervene in treatment in a timely manner, making it highly practical.

[0036] In one embodiment, the housing 100 has a first groove communicating with the detection port 103 at a position distal to the detection port 103, and the first probe 210 is fixed to the first groove by adhesive. Conversely, the housing 100 has a second groove communicating with the detection port 103 at a position proximal to the detection port 103, and the second probe 220 is fixed to the second groove by adhesive.

[0037] In this embodiment, the first groove can be disposed on the outer wall of the housing 100 to fix the first probe 210 to the outer wall of the housing 100; of course, the first groove can also be disposed on the edge side wall of the detection port 103, thereby embedding the first probe 210 in the side wall of the housing 100. Conversely, the second groove can be disposed on the outer wall of the housing 100 to fix the second probe 220 to the outer wall of the housing 100; or, the second groove can be disposed on the edge side wall of the detection port 103, thereby embedding the second probe 210 in the side wall of the housing 100. No further limitations are imposed here, all of which are within the protection scope of this application.

[0038] Furthermore, in actual production, a first mounting base 104 can be provided on the outer wall of the housing 100. The first mounting base 104 is located on the side of the detection port 103 facing the far end of the housing 100, and the first mounting base 104 is provided with a first fixing hole 1041, in which the first probe 210 passes. Conversely, a second mounting base 105 is provided on the outer wall of the housing 100. The second mounting base 105 is located on the side of the detection port 103 facing the near end of the housing 100, and the second mounting base 105 is provided with a second fixing hole 1051, in which the second probe 220 passes.

[0039] In this embodiment, by using a first mounting base 104 and a second mounting base 105 to mount the first probe 210 and the second probe 220, the first probe 210 and the second probe 220 can be more securely fixed to the outer wall of the housing 100, reducing the possibility of the first probe 210 and the second probe 220 detaching from the housing 100 or even being damaged due to blood flow erosion. Furthermore, because the laser emission window 211 is located on the side of the first probe 210 facing the second probe 220, that is, the laser emission window 211 is located on the proximal end face of the first probe 210, the first mounting base 104 will not obstruct the laser emission window 211, thus ensuring a more secure fixation of the first probe 210 without affecting laser detection. In contrast, the laser receiving window 221 is located on the side of the second probe 220 facing the first probe 210, that is, the laser receiving window 221 is located on the far end face of the second probe 220. At this time, the second mounting base 105 will not block the laser receiving window 221. This makes the second probe 220 more securely fixed without affecting laser detection. The structure is reasonable and highly practical.

[0040] Preferably, the first mounting base 104, the second mounting base 105, and the housing 100 are manufactured as a single piece, resulting in higher overall structural strength and less susceptibility to damage. Furthermore, the corners of the first mounting base 104 and the connection between the first mounting base 104 and the housing 100 are rounded to prevent the catheter pump from scratching internal tissues during implantation and withdrawal, reducing secondary injury and the risk of complications. Similarly, the corners of the second mounting base 105 and the connection between the second mounting base 105 and the housing 100 are also rounded to prevent the catheter pump from rubbing against internal tissues during implantation and withdrawal, thus improving the safety of the catheter pump.

[0041] Furthermore, both the first probe 210 and the second probe 220 have a cylindrical structure and the same diameter.

[0042] Specifically, in actual production, it is necessary to prevent the diameters of the first probe 210 and the second probe 220 from being too large, which would make catheter pump implantation difficult and increase patient discomfort, while ensuring that the thrombosis monitor 200 has high detection accuracy so that it can detect blood clots as early as possible. Therefore, in this embodiment, the diameters of both the first probe 210 and the second probe 220 are controlled between 0.5mm and 1mm. While ensuring the detection effect of the thrombosis monitor 200, the radial dimensions of the first probe 210 and the second probe 220 are minimized, making it highly practical.

[0043] Furthermore, the diameter of the first fixing hole 1041 is larger than the outer contour size of the first probe 210, which facilitates the insertion of the first probe 210 into the first fixing hole 1041, making installation convenient and quick. At this time, to ensure that the first probe 210 is securely installed in the first mounting base 104, the first probe 210 can be glued to the first mounting base 104 to prevent axial movement. Conversely, the diameter of the second fixing hole 1051 is larger than the outer contour size of the second probe 220, and the second probe 220 is glued to the second mounting base 105.

[0044] Specifically, during the assembly process, adhesive can be applied to the walls of the first fixing hole 1041 and the second fixing hole 1051. Then, the first probe 210 and the second probe 220 are inserted into the corresponding first fixing hole 1041 and second fixing hole 1051, respectively. Finally, wait for the adhesive to cure to complete the assembly of the first probe 210, the second probe 220, and the housing 100.

[0045] It should be noted that during the insertion of the first probe 210 and the second probe 220, it is necessary to ensure that the laser emitting window 211 and the laser receiving window 221 are not covered by glue, so as not to affect the detection accuracy of the thrombosis monitor 200.

[0046] Specifically, the end of the first probe 210 opposite to the second probe 220 is connected to an optical fiber 300, which is used to connect to the laser generator 500. At the same time, the end of the second probe 220 opposite to the first probe 210 is connected to a conductive cable 400, which is used to connect to the control device.

[0047] In practical applications, a catheter pump is implanted into a heart failure patient to pump blood from the left ventricle into the aorta. At this time, a control device, acting as an external instrument, displays images of the catheter pump within the patient for medical personnel to observe; simultaneously, the control device can also drive the movement of the catheter pump, allowing medical personnel to control its movement in real time based on the images.

[0048] In one specific embodiment, the laser generator 500 is integrated into the control device to convert white light into infrared laser light with a wavelength of 600-800nm. In this case, the first probe 210 may specifically include a first housing 212, an optical fiber inlet window 213, a first focusing lens 214, and a collimating lens 215. The optical fiber inlet window 213 is located at the distal end of the first housing 212, the laser emission window 211 is located at the proximal end of the first housing 212, and the first focusing lens 214 and collimating lens 215 are installed inside the first housing 212, arranged sequentially from the distal end to the proximal end of the first housing 212. The second probe 220 may specifically include a second housing 222, a second focusing lens 223, a light-shielding plate 224, and a photoelectric conversion element 250. The laser receiving window 221 is located at the far end of the first housing 212. The second focusing lens 223, the light-shielding plate 224, and the photoelectric conversion element 250 are sequentially installed inside the second housing 222 from the far end to the near end, and the photoelectric conversion element 250 is electrically connected to the conductive cable 400. The light-shielding plate 224 is made of an opaque material, and a light-transmitting hole is provided at the center of the light-shielding plate 224. The first focusing lens 214, the collimating lens 215, and the second focusing lens 223 are all convex lenses.

[0049] In this embodiment, the infrared laser generated by the laser generator 500 is transmitted through the optical fiber 300 to the optical fiber inlet window 213, where it is a parallel laser beam. Because the catheter pump needs to be implanted into the human body, its size is generally small. Correspondingly, the cross-sectional size of the optical fiber 400 used in the catheter pump is also small, resulting in a smaller cross-sectional area for the emitted parallel laser beam. Therefore, this embodiment includes a first focusing lens 214 and a collimating lens 215 to amplify the laser beam output from the optical fiber 300, ensuring the accuracy of laser detection.

[0050] Specifically, for ease of description, let the focal length of the first focusing lens 214 be f1, the focal length of the collimating lens 215 be f2, and the distance between the first focusing lens 214 and the collimating lens 215 be controlled to be f1+f2, with the central plane of the first focusing lens 214 and the central plane of the collimating lens 215 strictly parallel. In this way, the optical structure formed by the first focusing lens 214 and the collimating lens 215 ensures that the parallel laser beam at the fiber optic inlet window 213 remains a parallel laser beam after passing through the first focusing lens 214 and the collimating lens 215. Simultaneously, the cross-sectional area of ​​this laser beam is magnified from the area of ​​the fiber optic inlet window 213 (i.e., the cross-sectional area of ​​the fiber optic 300) to the cross-sectional area of ​​the collimating lens 215, thus amplifying the signal. The amplified laser beam is emitted from inside the first probe 210 through the laser emission window 211 to the outside, then passes through the blood flowing out of the detection port 103, and then enters the second probe 220 through the laser receiving window 221, illuminating the second focusing lens 223.

[0051] In this embodiment, the second focusing lens 223 is perpendicular to the laser beam entering the second probe 220, with a focal length of f3. The distance between the light-shielding plate 224 and the second focusing lens 223 is also controlled to be f3, and the central planes of the light-shielding plate 224 and the second focusing lens 223 are strictly parallel. Simultaneously, the center position of the light-shielding hole 2241 on the light-shielding plate 224 coincides with the focal point of the second focusing lens 223. Thus, after passing through the second focusing lens 223, the laser beam entering the second probe 220 at least partially passes through the light-shielding hole 2241 on the light-shielding plate 224 and is received by the photoelectric conversion element 250. The photoelectric conversion element 250 converts the received optical signal into an electrical signal and outputs the converted electrical signal to the control device via the conductive cable 400. The control device can display the strength of this electrical signal, allowing medical personnel to promptly determine whether a blood clot has formed based on changes in the electrical signal, enabling intervention treatment in the early stages of blood clot formation and effectively reducing the probability of thrombosis.

[0052] Specifically, if the parallel laser beam travels from the laser emission window 211 to the laser receiving window 221 without passing through a medium, the laser beam entering the second probe 220 will maintain its parallel nature. Thus, under the action of the second focusing lens 223, all photons of the laser beam can pass through the light-shielding hole 2241 on the light-shielding plate 224 and be received by the photoelectric conversion element 250. At this time, the electrical signal strength generated by the photoelectric conversion element 250 is at its maximum.

[0053] If the parallel laser beam passes through a flowing, non-uniform medium (such as blood) from the laser emission window 211 to the laser receiving window 221, some photons of the laser beam entering the second probe 220 will be absorbed or scattered, deviating from their original direction and unable to pass through the light-shielding hole 2241 on the light-shielding plate 224. At this time, the electrical signal generated by the photoelectric conversion element 250 will be slightly weakened. Simultaneously, because the medium through which the laser beam passes is flowing and non-uniform, the electrical signal generated by the photoelectric conversion element 250 will not fluctuate significantly over time when the composition of the medium does not change considerably.

[0054] If the parallel laser beam passes through a flowing and non-uniform medium containing many tiny particles (such as blood containing tiny blood clots) from the laser emission window 211 to the laser receiving window 221, the electrical signal generated by the photoelectric conversion element 250 will be significantly weakened because the medium can absorb and reflect the laser beam.

[0055] For example, the control device can directly display the value of the electrical signal generated by the photoelectric conversion element 250. When medical personnel observe a significant decrease in the electrical signal value, it indicates that the thrombosis monitor 200 has detected a blood clot, requiring timely intervention. Alternatively, the control device may not directly display the value of the electrical signal generated by the photoelectric conversion element 250, but instead display a prompt box and / or sound an alarm on the screen when the electrical signal significantly weakens or decreases to a certain value, so that medical personnel are immediately informed. Further details are omitted here, but all of these are within the scope of protection of this application.

[0056] In one specific embodiment, a support column 106 is formed between each pair of adjacent fluid outlets 102. The optical fiber 300 can be fixed on one of the support columns 106 adjacent to the detection port 103 and extends toward the near end of the housing 100. The portion of the optical fiber 300 located on the side of the detection port 103 facing the near end of the housing 100 is arranged side by side with the conductive cable 400.

[0057] In this embodiment, the optical fiber 300 extends towards the proximal end of the housing 100 via a support column 106 adjacent to the detection port 103. This avoids the detection port 103, ensuring unimpeded fluid flow and preventing interference with the thrombosis monitor 200's monitoring. Furthermore, the support column 106 provides support for the optical fiber 300, facilitating its secure fixation. Additionally, in this embodiment, the portion of the optical fiber 300 located on the side of the detection port 103 facing the proximal end of the housing 100 is arranged parallel to the conductive cable 400, resulting in neater and more aesthetically pleasing wiring. This also facilitates the synchronous fixation of the optical fiber 300 and the conductive cable 400, enhancing its practicality.

[0058] In one embodiment, the sidewall of the housing 100 is provided with a through hole 107, and the near end of the housing 100 is provided with an opening communicating with the through hole 107. In this case, the end of the optical fiber 300 away from the first probe 210 and the end of the conductive cable 400 away from the second probe 220 can pass through the through hole 107 into the housing 100 and exit from the housing 100 through the opening.

[0059] Specifically, a second chamber is formed within the housing 100, which houses the motor and its cables. A cable conduit 600 is connected to the distal end of the second chamber, allowing the motor cables to pass through an opening located near the proximal end of the housing 100 and extend into the cable conduit 600. At this time, a perforation 107 connects to the second chamber, allowing the optical fiber 300 and conductive cable 400 to pass through the perforation 107 into the interior of the second chamber, and together with the motor cables within the second chamber, pass through the opening into the cable conduit 600.

[0060] In this embodiment, the cable conduit 600 is sleeved outside the motor cable, optical fiber 300 and conductive cable 400, which can provide good protection for the motor cable, optical fiber 300 and conductive cable 400, and enable the conduit pump to operate stably.

[0061] Furthermore, an impeller is provided in the first chamber, which is connected to a motor drive, and a first docking part 110 is provided at the opening 101 of the first chamber for docking with the tubing body. When the catheter pump is implanted into the human body, the motor drives the impeller to rotate. Under the continuous rotation of the impeller, blood enters the first chamber through the tubing body and the opening 101 on the first chamber, and then is pumped out through the fluid outlet 102 into the aorta.

[0062] For example, the impeller is located on the central axis of the first chamber, and the impeller, motor, first docking part 110 and pipe body are coaxially assembled, which can make the fluid pumping capacity of the duct pump better.

[0063] In one embodiment, the outer wall of the housing 100 is provided with a first mounting groove 108, suitable for mounting the optical fiber 300. The first mounting groove 108 is at least partially located on one of the two support pillars 106 adjacent to the detection port 103, and the support pillar 106 with the first mounting groove 108 provides a better support point for fixing the optical fiber 300, making the fixing of the optical fiber 300 more secure. In this embodiment, the outer wall of the housing 100 is also provided with a second mounting groove 109, suitable for mounting the optical fiber 300 and the conductive cable 400.

[0064] In this embodiment, the first mounting slot 108 not only fixes the optical fiber 300 but also restricts its arrangement, thus achieving better cable routing. Similarly, the second mounting slot 109 also restricts the arrangement of the optical fiber 300 and the conductive cable 400, thereby achieving better cable routing.

[0065] Furthermore, the arrangement of the first mounting slot 108 and the second mounting slot 109 can reduce the portion of the optical fiber 300 and the conductive cable 400 protruding from the housing 100, thereby reducing the overall radial dimension of the catheter pump, which in turn improves the passage of the catheter pump during surgery, avoids scratching the inside of the human body during implantation and withdrawal, and improves the safety of the catheter pump.

[0066] In this embodiment, the first mounting groove 108 is preferably a groove with a semi-circular cross-section to fit the outline of the optical fiber 300; in contrast, the second mounting groove 109 is preferably a groove with a semi-elliptical cross-section to fit the outline of the optical fiber 300 and the conductive cable 400.

[0067] For example, the opening size of the first mounting groove 108 is larger than the outer diameter of the optical fiber 300, which is more conducive to the installation of the optical fiber 300 in the first mounting groove 108, making installation convenient and quick. In this case, to ensure that the optical fiber 300 is securely installed in the first mounting groove 108, the optical fiber 300 can be fixed to the first mounting groove 108 with adhesive to prevent axial movement. Specifically, the cross-sectional radius of the first mounting groove 108 is slightly larger than the cross-sectional radius of the optical fiber 300, and the first mounting groove 108 is filled with adhesive. After the adhesive cures, the optical fiber 300 is adhered to the first mounting groove 108 without displacement.

[0068] Conversely, the opening size of the second mounting groove 109 is larger than the sum of the outer diameters of the optical fiber 300 and the conductive cable 400, and the optical fiber 300 and the conductive cable 400 are fixed to the second mounting groove 109 by adhesive. Specifically, the cross-sectional radius of the second mounting groove 109 is slightly larger than the sum of the cross-sectional radii of the optical fiber 300 and the conductive cable 400, and the second mounting groove 109 is filled with adhesive. After the adhesive cures, the optical fiber 300 and the conductive cable 400 are adhered to the second mounting groove 109 without displacement.

[0069] To expedite assembly, in actual production, the optical fiber 300 and conductive cable 400 should first be glued together, followed by the first probe 210 and the second probe 220. Finally, the components with adhesive are placed in a temperature-controlled chamber for curing, thus integrating the first probe 210, the second probe 220, the optical fiber 300, and the conductive cable 400 onto the housing 100.

[0070] In the above embodiments, the conductive cable 400 and the optical fiber 300 are arranged side by side on the side of the detection port 103 facing the near end of the housing 100. However, in actual production, the conductive cable 400 and the optical fiber 300 on the side of the detection port 103 facing the near end of the housing 100 can also be arranged at intervals, that is, there is a certain distance between them. In this case, the housing 100 is provided with two through holes 107 for the conductive cable 400 and the optical fiber 300 to pass through respectively; similarly, the housing 100 is provided with two independent mounting slots to fix the conductive cable 400 and the optical fiber 300 respectively. There are no restrictions on this, and all are within the protection scope of this application.

[0071] This application also provides a duct pump, including an impeller, a motor driving the impeller to rotate, and the duct pump assembly provided in any of the above embodiments. A second chamber is further formed within the housing 100, and the first and second chambers are arranged sequentially from the distal end to the proximal end along the length of the housing 100. The impeller is located in the first chamber, and the motor is located in the second chamber. Driven by the motor, the impeller draws fluid through the opening 101 of the first chamber into the interior of the first chamber, and then discharges the fluid through the fluid outlet 102.

[0072] Specifically, when the catheter pump is implanted into the human body, the motor drives the impeller to rotate. Under the continuous rotation of the impeller, blood enters the first chamber through the opening 101 on the first chamber, and then is pumped out through the fluid outlet 102 into the aorta.

[0073] For example, the impeller is located on the central axis of the first chamber, and the impeller, motor, first docking part 110 and pipe body are coaxially assembled, which can make the fluid pumping capacity of the duct pump better.

[0074] This application also provides a ventricular assist device, including a cable conduit 600 and the conduit pump provided in all the above embodiments. In this case, the distal end of the housing 100 is provided with a first docking portion 110, which is adapted to dock with the conduit body; the proximal end of the housing 100 is provided with a second docking portion 111, which is adapted to dock with the cable conduit 600.

[0075] In this embodiment, both the optical fiber 300 and the conductive cable 400 pass through the through-hole 107 in the housing 100 into the second chamber, and then, together with the motor cable in the second chamber, pass through an opening near the end of the housing 100 and into the cable conduit 600. At this point, the cable conduit 600 provides good protection for the motor cable, optical fiber 300, and conductive cable 400, enabling the conduit pump to operate stably.

[0076] Specifically, the first docking part 110 has a tubular structure and can be inserted into the tube body as a tube, and fixedly connected to the tube body by adhesive or laser welding.

[0077] Furthermore, this application provides a thrombosis detection system, including a control device and the ventricular assist device provided in all the above embodiments. The control device, as an external device, is used to display images of the catheter pump within the patient's body for observation by medical personnel; simultaneously, the control device can also drive the catheter pump to move, allowing medical personnel to control the pump's movement in real time based on the images.

[0078] Specifically, the control device includes a device body and a laser generator 500. The laser generator 500 is connected to the first probe 210 via an optical fiber 300 and is used to convert white light into infrared laser light with a wavelength of 600-800nm. This infrared laser light is transmitted to the first probe 210 via the optical fiber 300. The second probe 220 is equipped with a photoelectric conversion element 250, which is used to convert the received optical signal into an electrical signal and output the converted electrical signal to the device body via a conductive cable 400. The change in the electrical signal can determine whether a blood clot has appeared, which facilitates timely intervention by medical personnel to prevent the blood clot from further agglomerating and forming a thrombus, effectively reducing the probability of complications and demonstrating strong practicality.

[0079] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail or recorded in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0080] It should be noted that the above embodiments can be freely combined as needed. The above are merely preferred embodiments of this application. It should be pointed out that for those skilled in the art, several improvements and modifications can be made without departing from the principles of this application, and these improvements and modifications should also be considered within the scope of protection of this application.

Claims

1. A conduit pump assembly, characterized in that, include: A housing having an opening in the first chamber, and a plurality of fluid outlets circumferentially formed on the sidewall of the first chamber; wherein at least one of the plurality of fluid outlets is a detection port; A thrombosis monitor is provided, corresponding to each of the detection ports, and each of the thrombosis monitors includes a first probe and a second probe. The first probe and the second probe are both installed on the side wall of the housing and located around the detection port. The first probe has a laser emitting window, and the second probe has a laser receiving window. The laser emitting window and the laser receiving window are arranged opposite to each other to form a laser detection segment at the detection port, which is used to monitor the changes in the solid composition of the fluid flowing through the laser detection segment.

2. The conduit pump assembly according to claim 1, characterized in that, The laser emitting window is used to emit infrared laser light, and the laser receiving window is used to receive the infrared laser light.

3. The conduit pump assembly according to claim 1 or 2, characterized in that, The outer wall of the housing is provided with a first mounting base, which is located on the side of the detection port facing the distal end of the housing. The first mounting base has a first fixing hole, through which the first probe passes. The outer wall of the housing is provided with a second mounting base, which is located on the side of the detection port facing the near end of the housing, and the second mounting base is provided with a second fixing hole, through which the second probe passes.

4. The duct pump assembly according to claim 3, characterized in that, The diameter of the first fixing hole is larger than the outer contour size of the first probe, and the first probe is fixed to the first mounting base by adhesive. The diameter of the second fixing hole is larger than the outer contour size of the second probe, and the second probe is fixed to the second mounting base by adhesive.

5. The duct pump assembly according to claim 3, characterized in that, The first probe is connected to an optical fiber at the end opposite to the second probe, and the optical fiber is used to connect to a laser generator; and the second probe is connected to a conductive cable at the end opposite to the first probe, and the conductive cable is used to connect to a control device; A support pillar is formed between each pair of adjacent fluid outlets. The optical fiber is fixed to a support pillar adjacent to the detection port and extends toward the near end of the housing. The optical fiber is located on the side of the detection port facing the near end of the housing and is arranged side by side with the conductive cable.

6. The conduit pump assembly according to claim 5, characterized in that, The first probe includes a first housing, a first focusing lens, and a collimating lens; The first outer casing has a fiber optic inlet window at its distal end for connecting to the fiber optic cable, and the laser emission window is located at the proximal end of the first outer casing; and Both the first focusing lens and the collimating lens are disposed inside the first housing, with the first focusing lens positioned close to the fiber optic inlet window and the collimating lens positioned close to the laser emission window; The first focusing lens and the collimating lens are used to magnify the cross-sectional area of ​​the laser beam that enters the interior of the first housing through the fiber optic guide window.

7. The conduit pump assembly according to claim 5, characterized in that, The side wall of the housing is provided with a perforation, and the near end of the housing is provided with an opening communicating with the perforation; The end of the optical fiber furthest from the first probe and the end of the conductive cable furthest from the second probe pass through the perforation inside the housing and exit through the opening inside the housing.

8. The duct pump assembly according to claim 5, characterized in that, The outer wall of the housing is provided with a first mounting groove, which is suitable for mounting the optical fiber, and the first mounting groove is at least partially located on a support adjacent to the detection port; and the size of the opening of the first mounting groove is larger than the outer diameter of the optical fiber, and the optical fiber is fixed to the first mounting groove by adhesive. The outer wall of the housing is provided with a second mounting groove, which is suitable for mounting the optical fiber and the conductive cable. The size of the second mounting groove is larger than the sum of the outer diameter of the optical fiber and the outer diameter of the conductive cable. The optical fiber and the conductive cable are fixed to the second mounting groove by adhesive.

9. A duct pump, characterized in that, include: An impeller, a motor for driving the impeller to rotate, and a duct pump assembly according to any one of claims 1-8; A second chamber is formed inside the shell, and the first chamber and the second chamber are arranged sequentially from the distal end to the proximal end along the length of the shell. The impeller is located in the first chamber, and the motor is located in the second chamber. Driven by the motor, the impeller draws fluid into the first chamber through the opening and then discharges the fluid through the fluid outlet.

10. A ventricular assist device, characterized in that, include: Cable conduit and the conduit pump of claim 9; The housing has a first docking portion at its distal end, suitable for docking with the pipe body; the housing has a second docking portion at its proximal end, suitable for docking with the cable conduit.

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