Blood flow parameter measurement device, apparatus, and storage medium

Abstract

This application relates to a blood flow parameter measurement device, equipment, and storage medium, belonging to the field of medical devices. The blood flow parameter measurement device includes: a first control module for controlling a rotating mechanism to drive an ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be measured is a perfect circle; an acquisition module for acquiring the diameter of the blood vessel to be measured based on the perfect circle image; a second control module for controlling the rotating mechanism to drive the ultrasonic crystal array to rotate in the opposite direction according to a preset Doppler angle to form the required Doppler angle and enter the Doppler blood flow measurement mode; a third control module for selecting an ultrasonic crystal array within a preset width of the blood vessel to be measured to start detection according to the acquired diameter; and a monitoring module for monitoring the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds a fluctuation threshold. The technical solution of this application improves the accuracy and stability of long-term blood flow monitoring.

Description

Technical Field

[0001] This application relates to the field of medical devices, and in particular to a blood flow parameter measuring device, equipment, and storage medium. Background Technology

[0002] Doppler ultrasound technology is widely used for non-invasive monitoring of hemodynamic parameters, especially in intensive care, cardiovascular assessment, and intraoperative monitoring. Existing blood flow parameter measurement systems typically combine B-mode ultrasound imaging with pulsed wave (PW) or continuous wave (CW) Doppler modes to acquire cross-sectional images of blood vessels to determine the vessel diameter and calculate blood flow velocity based on Doppler frequency shift, thereby deriving parameters such as flow rate or stroke volume.

[0003] However, existing blood flow parameter measurement devices suffer from poor measurement accuracy during long-term monitoring. Specifically, when the relative position of the probe and the blood vessel shifts due to patient movement, the angle between the ultrasound beam and the blood vessel deviates from the ideal state, leading to distortion in the vessel diameter measurement and affecting the reliability of subsequent blood flow parameters.

[0004] The information disclosed in this background section is intended only to enhance the understanding of the overall background of this application and should not be construed as an admission or in any way implying that the information constitutes prior art known to those skilled in the art. Summary of the Invention

[0005] In view of this, this application provides a blood flow parameter measuring device, equipment, and storage medium to solve at least one problem existing in the prior art.

[0006] To achieve the above objectives, the technical solution of this application is implemented as follows:

[0007] In a first aspect, embodiments of this application provide a blood flow parameter measuring device applied to a blood flow parameter measuring system. The system includes the blood flow parameter measuring device and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured. The device includes:

[0008] The first control module is used to control the rotating mechanism to drive the ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be tested is a perfect circle.

[0009] The acquisition module is used to acquire the diameter of the blood vessel to be tested based on the circular image;

[0010] The second control module is used to control the rotating mechanism to drive the ultrasound crystal array to rotate in the opposite direction according to the preset Doppler angle, so as to form the required Doppler angle and enter the Doppler blood flow measurement mode.

[0011] The third control module is used to select an ultrasonic crystal array within a preset width of the blood vessel to be tested based on the obtained tube diameter to start detection.

[0012] The monitoring module is used to monitor the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds the fluctuation threshold.

[0013] In one optional embodiment, the preset width is 1.2D to 2.0D, where D is the pipe diameter obtained by the acquisition module.

[0014] In an alternative embodiment, the apparatus further includes:

[0015] The image processing module is used to calculate the ratio of the major axis to the minor axis of the ultrasound cross-sectional image and feed the ratio back to the first control module to determine whether a perfect circle image has been achieved.

[0016] In an optional implementation, the image processing module is further configured to:

[0017] If the fitting roundness error of the vessel wall contour of the vessel to be tested is less than a preset threshold, the ultrasound cross-sectional image is determined to be a perfect circle; the fitting roundness error is calculated by the least squares method.

[0018] In an optional embodiment, the apparatus further includes a calibration module, the calibration module being used for:

[0019] The first control module will be re-executed under any of the following conditions to perform position calibration:

[0020] The monitoring module detected that the fluctuations in hemodynamic parameters exceeded the fluctuation threshold;

[0021] No valid Doppler signal is received within a continuous period of T seconds, where T ≥ 5.

[0022] In an optional implementation, the first control module is further configured to:

[0023] During the process of driving the ultrasonic crystal array to rotate, incremental rotation is performed with a preset step size, and a cross-sectional image of the blood vessel is acquired at each step until N consecutive frames of images meet the criteria for a perfect circle, where N≥3.

[0024] In an optional embodiment, the second control module is further configured to:

[0025] After entering the Doppler blood flow measurement mode, the angle of the ultrasound crystal array is dynamically fine-tuned to optimize the signal-to-noise ratio of the Doppler spectrum signal.

[0026] In an optional implementation, the third control module is further configured to:

[0027] When selecting an ultrasound crystal array within the preset width, the subset of ultrasound crystal arrays symmetrically distributed on both sides of the blood vessel centerline is preferentially activated.

[0028] In an optional implementation, the acquisition module is further configured to:

[0029] After obtaining the tube diameter, the cross-sectional area of ​​the blood vessel is calculated, and the stroke volume is obtained by combining the measured blood flow velocity integral VTI. The stroke volume is: SV = A * VTI.

[0030] Where SV is stroke volume, A is the cross-sectional area of ​​the blood vessel, and VTI is the blood flow velocity integral.

[0031] Secondly, embodiments of this application provide a computing device applied to a blood flow parameter measurement system. The system includes the blood flow parameter measurement device and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured. The computing device includes: a storage component, a communication bus, and a processing component, wherein:

[0032] The storage component is used to store the operating program of the blood flow parameter measuring device;

[0033] The communication bus is used to enable communication between the storage component and the processing component;

[0034] The processing unit is used to perform the work of each module in any of the blood flow parameter measuring devices described above.

[0035] Thirdly, embodiments of this application provide a computer-readable storage medium applied to a blood flow parameter measurement system. The system includes the blood flow parameter measurement device and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured.

[0036] The computer-readable storage medium stores an executable program, which, when executed by a processor, enables the operation of various modules in any of the blood flow parameter measuring devices described above.

[0037] Fourthly, embodiments of this application provide an ultrasound probe for use in conjunction with any of the blood flow parameter measuring devices described above, including:

[0038] Ultrasonic crystal array;

[0039] A rotating mechanism, whose power output end is connected to the ultrasound crystal array, is used to drive the ultrasound crystal array to rotate, so as to change the angle between the ultrasound crystal array and the blood vessel to be tested.

[0040] The interface unit is used to receive control commands from the blood flow parameter measuring device and transmit ultrasound echo data back.

[0041] In an optional embodiment, the ultrasound probe further includes an angle feedback unit integrated in the rotation mechanism, which is used to detect the actual rotation angle of the ultrasound crystal array and transmit the actual rotation angle back to the blood flow parameter measuring device through the interface unit to form closed-loop angle control.

[0042] Fifthly, embodiments of this application provide a blood flow parameter measurement system, including:

[0043] Any of the blood flow parameter measuring devices described above;

[0044] Any of the ultrasonic probes mentioned above.

[0045] The blood flow parameter measurement device, equipment, and storage medium provided in this application include: a first control module for controlling a rotating mechanism to drive an ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be tested is a perfect circle; an acquisition module for acquiring the diameter of the blood vessel to be tested based on the perfect circle image; a second control module for controlling the rotating mechanism to drive the ultrasonic crystal array to rotate in the opposite direction according to a preset Doppler angle to form the required Doppler angle and enter the Doppler blood flow measurement mode; a third control module for selecting an ultrasonic crystal array within a preset width of the blood vessel to be tested to start detection according to the acquired diameter; and a monitoring module for monitoring the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds a fluctuation threshold. As can be seen, the blood flow parameter measuring device, equipment, and storage medium provided in this application embodiment, by rotating the ultrasonic crystal array, first adjusts it to make the cross-section of the blood vessel a perfect circle to ensure accurate diameter measurement, then rotates it in the opposite direction to form a preset Doppler angle, and according to the obtained diameter, activates the ultrasonic crystal array located within a preset width range of the blood vessel to be measured for detection, thereby focusing on the effective signal area of ​​the blood vessel, improving the signal-to-noise ratio, and reducing the activation of unnecessary crystals. At the same time, in conjunction with the blood flow parameter fluctuation monitoring and calibration mechanism, it effectively improves the geometric accuracy of diameter measurement, reduces the blood flow velocity error caused by Doppler angle deviation, and thus improves the accuracy and stability of long-term blood flow monitoring.

[0046] Additional aspects and advantages of this application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of this application. Attached Figure Description

[0047] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0048] Figure 1 This is a schematic diagram of the blood flow parameter measuring device provided in the embodiments of this application;

[0049] Figure 2 A schematic diagram of a blood vessel cross-section perpendicular to the blood vessel in the blood flow parameter measuring device provided in this application embodiment;

[0050] Figure 3 A schematic diagram of a blood vessel cross-section in the blood flow parameter measuring device provided in this application embodiment, showing the wafer array tilted towards the blood vessel.

[0051] Figure 4 A flowchart illustrating the execution process of the blood flow parameter measurement device provided in this application embodiment;

[0052] Figure 5 This is a schematic diagram of the structure of a computing device provided in an embodiment of this application;

[0053] Figure 6 This is a schematic diagram of the blood flow parameter measurement system provided in the embodiments of this application;

[0054] Figure 7 A detailed structural diagram of the blood flow parameter measurement system provided in the embodiments of this application.

[0055] Explanation of reference numerals in the attached figures:

[0056] 10. Blood flow parameter measuring device; 11. First control module; 12. Acquisition module; 13. Second control module; 14. Third control module; 15. Monitoring module; 50. Computing device; 51. Storage component; 52. Communication bus; 53. Processing component; 54. Input device; 55. Output device; 56. External communication interface. Detailed Implementation

[0057] To make the technical solutions and beneficial effects of this application more obvious and understandable, the technical solutions in the embodiments of this application are clearly and completely described below by listing specific embodiments. Obviously, the embodiments of this application are not exhaustive, and the described embodiments are only some embodiments of this application, not all embodiments.

[0058] The exemplary embodiments disclosed in this application will now be described in more detail with reference to the accompanying drawings, providing a detailed structure and steps to illustrate the technical solution of this application. Note that the drawings are not necessarily drawn to scale, and local features may be enlarged or reduced to more clearly show the details of the local features.

[0059] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application pertains. The terminology used herein is for the purpose of describing particular embodiments only and should not be construed as limiting the technical solutions of this application.

[0060] The following description provides numerous specific details to offer a more thorough understanding of this application. However, it will be apparent to those skilled in the art that this application can be practiced without one or more of these details. To clearly define the inventive concept of this application and avoid confusion with its content, technical features well-known in the art and conventionally understood by those skilled in the art are not elaborated upon. Specifically, this document does not fully list all features of actual embodiments, nor does it provide a detailed description of well-known functions and structures.

[0061] The inventors of this application discovered during the research and development that, when using ultrasonic Doppler technology for long-term blood flow parameter monitoring, the relative position between the probe and the blood vessel is easily shifted due to factors such as slight changes in the patient's body position, breathing, or muscle contraction. This causes the ultrasound beam to be unable to remain perpendicular to the blood vessel cross-section, resulting in distorted diameter measurements. At the same time, the Doppler angle (i.e., the angle between the ultrasound beam and the blood flow direction) is difficult to maintain within the ideal range, causing significant cosine errors in blood flow velocity calculations. Furthermore, traditional systems typically use all ultrasound chips for continuous Doppler transmission and reception, which not only increases unnecessary acoustic energy output but also easily introduces sidelobe interference and noise, reducing the signal-to-noise ratio. These problems are particularly prominent in long-term clinical monitoring scenarios, and existing automatic calibration methods mostly rely on manual intervention by the operator or are based solely on a single image frame, making it difficult to achieve highly robust closed-loop adaptive adjustment.

[0062] Therefore, through further research and development, the inventors proposed the following technical solution.

[0063] Example 1

[0064] This application provides a blood flow parameter measuring device 10, applied to a blood flow parameter measuring system. The system includes the blood flow parameter measuring device 10 and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured. (Reference) Figure 1 The device includes:

[0065] The first control module 11 is used to control the rotating mechanism to drive the ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be tested is a perfect circle.

[0066] The acquisition module 12 is used to acquire the diameter of the blood vessel to be tested based on the circular image;

[0067] The second control module 13 is used to control the rotating mechanism to drive the ultrasound crystal array to rotate in the opposite direction according to the preset Doppler angle, so as to form the required Doppler angle and enter the Doppler blood flow measurement mode.

[0068] The third control module 14 is used to select an ultrasonic crystal array within a preset width of the blood vessel to be tested based on the acquired tube diameter to start detection.

[0069] The monitoring module 15 is used to monitor the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds the fluctuation threshold.

[0070] Without limitation, the first control module 11 may be an embedded control unit or a software logic module. Its function is to adjust the rotating mechanism to rotate the ultrasound crystal array relative to the blood vessel axis until the resulting blood vessel cross-sectional image is a perfect circle. This state corresponds to the ideal cross-section of the ultrasound beam perpendicular to the long axis of the blood vessel, thereby providing geometric accuracy for subsequent tube diameter measurement.

[0071] The acquisition module 12 may be an image analysis unit, used to extract the inner or outer diameter of the blood vessel from a circular image, and then determine the diameter D.

[0072] The second control module 13 can be an angle control logic, which calculates the required rotation amount based on a preset Doppler angle (e.g., 60°) and drives the crystal array to rotate in the opposite direction to that angle to enter the pulsed wave (PW) or continuous wave (CW) blood flow measurement mode.

[0073] The third control module 14 can be a chip gating controller, which dynamically enables a local chip subset covering the blood vessel width based on the acquired tube diameter D, avoiding continuous operation of the entire array.

[0074] The monitoring module 15 can be a parameter tracking unit, used to calculate and monitor hemodynamic parameters (such as stroke volume, peak flow rate, etc.) in real time. When the fluctuation amplitude exceeds a preset threshold, it is determined that probe displacement or signal degradation may have occurred. The above modules work together to improve the measurement deviation caused by geometric inaccuracies in long-term monitoring and enhance the system's adaptive capability.

[0075] Specifically, the ultrasound probe is initially placed on the skin surface, with the crystal array parallel to the skin (rotation angle of 0°). The system first acquires a short-axis view of the blood vessels using B-mode imaging. The first control module 11 gradually fine-tunes the rotation angle until the blood vessel outline in the image is nearly a perfect circle. Figure 2Subsequently, module 12 measures the diameter of the circular image as the pipe diameter D; the second control module 13 then rotates the wafer array in the opposite direction to a preset Doppler angle (e.g., a 30° mechanical angle corresponds to a 60° Doppler angle), for reference. Figure 3 The third control module 14 activates the central crystal region with a width of approximately 1.4D for Doppler sampling; the monitoring module 15 continuously calculates the Velocity Time Integral (VTI) and Stroke Volume (SV). If the SV fluctuation exceeds 15%, the recalibration process is triggered.

[0076] For example, when the pipe diameter D is 5 mm, the third control module 14 can enable the chips within a 7 mm width range (i.e., 1.4D), corresponding to approximately 22 chips (assuming a chip pitch of 0.32 mm), while the remaining chips are in a dormant state.

[0077] Furthermore, the monitoring module 15 can combine Doppler signal strength, spectral broadening and heart rate variability to comprehensively determine whether effective signal loss has occurred, rather than relying solely on fluctuations in a single parameter.

[0078] In some other embodiments of this application, the preset width is 1.2D to 2.0D, where D is the pipe diameter obtained by the acquisition module 12.

[0079] Without limitation, the preset width can be a lateral range covering 1.2 to 2.0 times the diameter of the blood vessel, which ensures complete capture of the blood flow signal within the blood vessel while avoiding over-enabling of peripheral chips to introduce noise; this setting reduces ineffective acoustic energy radiation and improves the spatial focusing of the Doppler signal.

[0080] Specifically, the system can dynamically select the width coefficient based on the clarity of the blood vessel wall. For example, 1.8D is used when the vessel wall is blurry to ensure signal integrity, and 1.2D is used when the image is clear to save energy.

[0081] In other embodiments of this application, the apparatus further includes:

[0082] The image processing module is used to calculate the ratio of the major axis to the minor axis of the ultrasound cross-sectional image and feed the ratio back to the first control module 11 to determine whether a perfect circle image has been achieved.

[0083] Without limitation, the image processing module can be an image analysis algorithm unit, which extracts the blood vessel contour through edge detection or Hough Transform and calculates the ratio of the major axis to the minor axis of its circumscribed ellipse; when the ratio is close to 1 (e.g., less than 1.05), it is determined to be a perfect circle image; this feature improves the objectivity and automation level of perfect circle determination.

[0084] Specifically, the image processing module calculates the axis ratio for each frame and feeds the result back to the first control module 11 in real time, which then decides whether to continue rotating or stop adjusting.

[0085] In other embodiments of this application, the image processing module is further configured to:

[0086] If the fitting roundness error of the vessel wall contour of the vessel to be tested is less than a preset threshold, the ultrasound cross-sectional image is determined to be a perfect circle; the fitting roundness error is calculated by the least squares method.

[0087] Without limitation, the fitting roundness error can be the root mean square distance from the blood vessel contour point to the best-fit circle. The smaller the error, the closer the image is to the ideal circle. The least squares method provides a mathematically robust way of fitting circles, which enhances the noise resistance of the circle determination.

[0088] Specifically, the system sets the roundness error threshold to 0.15 mm. When the fitting error is lower than this value and the axis ratio is less than 1.05, the system double-confirms the roundness.

[0089] In other embodiments of this application, the apparatus further includes a calibration module, the calibration module being used for:

[0090] The first control module 11 is re-executed under any of the following conditions to perform position calibration:

[0091] The monitoring module 15 detected that the fluctuation of hemodynamic parameters exceeded the fluctuation threshold;

[0092] No valid Doppler signal is received within a continuous period of T seconds, where T ≥ 5.

[0093] Without limitation, the calibration module can be a status monitoring and reset logic unit, which automatically restarts the entire process of "circle calibration - diameter measurement - angle setting" when it detects abnormal parameters or signal interruption, thereby achieving closed-loop self-calibration; this mechanism significantly improves the robustness of long-term monitoring.

[0094] Specifically, T can be set to 8 seconds, and the fluctuation threshold can be set to twice the standard deviation of stroke volume.

[0095] In other embodiments of this application, the first control module 11 is further configured to:

[0096] During the process of driving the ultrasonic crystal array to rotate, incremental rotation is performed with a preset step size, and a cross-sectional image of the blood vessel is acquired at each step until N consecutive frames of images meet the criteria for a perfect circle, where N≥3.

[0097] Without limitation, the preset step size can be a mechanical rotation increment of 0.5° to 2°, and continuous N-frame verification can eliminate instantaneous image artifact interference and ensure the stability of the perfect circle state; this design reduces the risk of misjudgment.

[0098] Specifically, the step size is set to 1°, N is set to 5 frames, and the system needs to have an axis ratio of <1.05 for 5 consecutive frames to confirm the completion of the circle calibration.

[0099] In other embodiments of this application, the second control module 13 is further configured to:

[0100] After entering the Doppler blood flow measurement mode, the angle of the ultrasound crystal array is dynamically fine-tuned to optimize the signal-to-noise ratio of the Doppler spectrum signal.

[0101] Without limitation, the dynamic fine-tuning can involve slightly oscillating the chip angle within a range of ±3° and evaluating the signal-to-noise ratio (SNR) of the Doppler spectrum in real time, selecting the angle with the highest SNR as the final working angle; this operation further reduces the impact of Doppler angle error on speed calculation.

[0102] Specifically, the system scans in 0.2° steps, collecting the spectrum for 0.5 seconds per step, and selects the angle with the highest average SNR.

[0103] In other embodiments of this application, the third control module 14 is further configured to:

[0104] When selecting an ultrasound crystal array within the preset width, the subset of ultrasound crystal arrays symmetrically distributed on both sides of the blood vessel centerline is preferentially activated.

[0105] Without limitation, the symmetrical distribution can refer to the use of an equal number of cells on the left and right sides with the center of the blood vessel as the axis of symmetry. This method helps to balance the energy distribution of the sound field, reduce directional deviation, and improve the symmetry and repeatability of flow velocity measurement.

[0106] Specifically, if 20 chips are used, 10 are arranged symmetrically on the left and right sides around the center line.

[0107] In other embodiments of this application, the acquisition module 12 is further configured to:

[0108] After obtaining the tube diameter, the cross-sectional area of ​​the blood vessel is calculated, and the stroke volume is obtained by combining the measured blood flow velocity integral VTI. The stroke volume is: SV = A * VTI.

[0109] Where SV is stroke volume, A is the cross-sectional area of ​​the blood vessel, and VTI is the blood flow velocity integral.

[0110] Without limitation, the cross-sectional area A of the blood vessel can be the area of ​​a circle calculated based on the diameter D (A=π(D / 2)²), and VTI is obtained by integrating the velocity-time curve over a cardiac cycle using the Doppler spectrum; SV=A×VTI is a standard formula in hemodynamics used to quantify the amount of blood pumped out in a single heartbeat; this integrated calculation enables the direct output from the raw ultrasound signal to key clinical parameters.

[0111] Specifically, the system updates the SV value every time it is used for trend analysis or alarm determination.

[0112] To better understand the blood flow parameter measuring device 10 provided in this application embodiment, the execution process of the blood flow parameter measuring device 10 provided in this application embodiment will be described below. Figure 4 This is a flowchart illustrating the execution process of the blood flow parameter measuring device 10 provided in this application embodiment, with reference to... Figure 4 As shown, the execution process may include:

[0113] Step 401: Control the rotating mechanism to drive the ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be tested is a perfect circle;

[0114] Step 402: Obtain the diameter of the blood vessel to be tested based on the circular image;

[0115] Step 403: According to the preset Doppler angle, control the rotating mechanism to drive the ultrasound crystal array to rotate in the opposite direction to form the required Doppler angle and enter the Doppler blood flow measurement mode;

[0116] Step 404: Based on the obtained tube diameter, select the ultrasound crystal array within the preset width of the blood vessel to be tested and start the detection;

[0117] Step 405: Monitor the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds the fluctuation threshold.

[0118] The modules included in this embodiment can be implemented using a processor in a computer; alternatively, they can be implemented using logic circuits in a computer. The processor can be a general-purpose processor, such as a CPU; an integrated system, such as a system-on-a-chip (SoC); an embedded control core, such as a microcontroller unit (MCU); a dedicated signal processing unit, such as a digital signal processor (DSP); a graphics rendering core, such as a graphics processing unit (GPU); a programmable logic device, such as an application-specific integrated circuit (ASIC); a field-programmable gate array (FPGA); or other programmable logic devices, discrete gates, transistor logic devices, or discrete hardware components.

[0119] Example 2

[0120] This application provides a computing device 50 applied to a blood flow parameter measurement system. The system includes a blood flow parameter measurement device 10 and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured. (Reference) Figure 5 The computing device 50 includes: a storage unit 51, a communication bus 52, and a processing unit 53, wherein:

[0121] The storage component 51 is used to store the operating program of the blood flow parameter measuring device 10;

[0122] The communication bus 52 is used to realize the connection and communication between the storage component 51 and the processing component 53.

[0123] The processing unit 53 is used to perform the work of each module in the blood flow parameter measuring device 10 described in Embodiment 1.

[0124] The type or structure of the storage component 51 can be found in the storage medium section below, and will not be repeated here.

[0125] The processing unit 53 can be a general-purpose processor, such as a CPU; an integrated system, such as a system-on-a-chip (SoC); an embedded control core, such as a microcontroller unit (MCU); a dedicated signal processing unit, such as a digital signal processor (DSP); a graphics rendering core, such as a graphics processing unit (GPU); a programmable logic device, such as an application-specific integrated circuit (ASIC); a field-programmable gate array (FPGA); or other programmable logic devices, discrete gates, transistor logic devices, or discrete hardware components.

[0126] In some embodiments, the computing device 50 may further include an input device 54, an output device 55, and an external communication interface 56, which are interconnected via a bus system and / or other forms of connection mechanisms (not shown).

[0127] In some embodiments, the input device 54 may include, for example, a keyboard, mouse, microphone, etc. The output device 55 may output various information to the outside, including a display, speaker, printer, projector, and communication network and its connected remote output devices, etc. The external communication interface 56 may be wired, such as a standard serial port (RS232), a General-Purpose Interface Bus (GPIB) interface, an Ethernet interface, or a Universal Serial Bus (USB) interface, or it may be wireless, such as wireless network communication technology (WiFi), Bluetooth, etc.

[0128] The descriptions of the above device embodiments are similar to those of the above apparatus embodiments, and have similar beneficial effects. For technical details not disclosed in the embodiments of this application, please refer to the descriptions of the apparatus embodiments in this application for understanding.

[0129] Example 3

[0130] This application provides a computer-readable storage medium for use in a blood flow parameter measurement system. The system includes a blood flow parameter measurement device 10 and an ultrasound probe. The ultrasound probe includes a rotating mechanism and an ultrasound crystal array. The rotating mechanism can drive the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured.

[0131] The computer-readable storage medium stores an executable program, which, when executed by a processor, enables the operation of each module in the blood flow parameter measuring device 10 described in Embodiment 1.

[0132] Exemplary examples show that a computer-readable storage medium may be any combination of one or more readable media. A readable medium may be a readable signal medium or a readable storage medium. A computer-readable storage medium is a tangible device capable of holding and storing instructions for use by an instruction execution device. A readable storage medium may, for example, include, but is not limited to, electrical, magnetic, optical, electromagnetic, infrared, or semiconductor systems, apparatuses, or devices, or any combination thereof. More specific examples of readable storage media (a non-exhaustive list) include: portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), flash memory, compact disc read-only memory (CD-ROM), digital versatile discs (DVDs), memory sticks, floppy disks, mechanical encoding devices, such as punch cards or recessed protrusions storing instructions thereon, and any suitable combinations thereof.

[0133] The RAM includes: Static Random Access Memory (SRAM), Synchronous Static Random Access Memory (SSRAM), Dynamic Random Access Memory (DRAM), Synchronous Dynamic Random Access Memory (SDRAM), Double Data Rate Synchronous Dynamic Random Access Memory (DDRSDRAM), Enhanced Synchronous Dynamic Random Access Memory (ESDRAM), SyncLink Dynamic Random Access Memory (SLDRAM), and Direct Rambus Random Access Memory (DRRAM).

[0134] The ROM includes: Programmable Read-Only Memory (PROM), Erasable Programmable Read-Only Memory (EPROM), and Electrically Erasable Programmable Read-Only Memory (EEPROM).

[0135] The description of the computer-readable storage medium embodiments above is similar to the description of the device embodiments above, and has similar beneficial effects. For technical details not disclosed in the embodiments of this application, please refer to the description of the device embodiments in this application for understanding.

[0136] Example 4

[0137] This application provides an ultrasound probe for use in conjunction with the blood flow parameter measuring device 10 described in Embodiment 1. The ultrasound probe includes:

[0138] Ultrasonic crystal array;

[0139] A rotating mechanism, whose power output end is connected to the ultrasound crystal array, is used to drive the ultrasound crystal array to rotate, so as to change the angle between the ultrasound crystal array and the blood vessel to be tested.

[0140] The interface unit is used to receive control commands from the blood flow parameter measuring device 10 and transmit ultrasound echo data back.

[0141] Without limitation, the ultrasonic crystal array may include 32 to 128 piezoelectric crystals with an operating frequency range of 1 MHz to 12 MHz; the rotating mechanism may be a micro stepper motor or a piezoelectric motor; and the interface unit may be a high-speed serial interface that supports bidirectional command and data transmission.

[0142] In some other embodiments of this application, the ultrasound probe further includes an angle feedback unit integrated in the rotation mechanism, which is used to detect the actual rotation angle of the ultrasound crystal array and transmit the actual rotation angle back to the blood flow parameter measuring device 10 through the interface unit to form closed-loop angle control.

[0143] Without limitation, the angle feedback unit can be an encoder or a Hall sensor, which provides real-time feedback of the actual angle, enabling the control system to compensate for mechanical lag or slippage and improve angle positioning accuracy.

[0144] Example 5

[0145] This application provides a blood flow parameter measurement system, referencing... Figure 6 The blood flow parameter measurement system includes:

[0146] The blood flow parameter measuring device 10 described in Example 1;

[0147] The ultrasonic probe described in Example 4.

[0148] Without limitation, the system can automate the entire process from automatic blood vessel positioning, precise tube diameter measurement, Doppler angle setting to low-power blood flow monitoring, and is suitable for intensive care, operating room or home long-term monitoring scenarios.

[0149] In some other embodiments of this application, the center frequency of the ultrasound crystal array is preferably 5.6 MHz or 7.5 MHz, and broadband technology is used to improve axial resolution; the probe is a short-axis imaging probe, and the angle adjustment range between it and the skin is -40 degrees to +40 degrees; in Doppler measurement mode, the ultrasound crystal array is preferably rotated to a 30-degree angle with the skin, so that the ultrasound beam forms a 60-degree Doppler angle with the blood flow direction, which achieves a good balance between velocity sensitivity and cosine error.

[0150] Without limitation, the above parameter combination can optimize the imaging and blood flow detection performance of deep blood vessels (such as the carotid artery and femoral artery); broadband technology allows the use of shorter pulses to improve temporal resolution; 60-degree Doppler angle is a commonly used compromise value in clinical practice, which avoids the absence of Doppler frequency shift at 0 degrees and also avoids the amplification error caused by the steep change of the cosine function when it is close to 90 degrees.

[0151] Specifically, refer to Figure 7 The blood flow parameter measurement system specifically includes:

[0152] Ultrasonic probe, including a rotating mechanism.

[0153] The color Doppler ultrasound module is electrically connected to the ultrasound probe and corresponds to the acquisition module 12 in Embodiment 1.

[0154] The wafer rotation control board is electrically connected to the ultrasonic probe and corresponds to the first control module 11 and the second control module 13 in Embodiment 1.

[0155] The CPU, namely the processor of the blood flow parameter measuring device 10 in Embodiment 1, is communicatively connected to the color Doppler ultrasound module and the wafer rotation control board.

[0156] Runtime memory is used to temporarily store intermediate data processed by the CPU.

[0157] Hard disk storage is used to store data processed by the CPU.

[0158] The display screen is used to show the detected data and the processed data.

[0159] The keyboard or keys are input components that serve as the channel for user commands.

[0160] A touchscreen, as the name suggests, can replace a keyboard, buttons, and display screen, serving both as a display and an input component.

[0161] A speaker is used to play device alerts or voice messages.

[0162] An audio amplifier is used to amplify the weak signals in the playback instructions output by the CPU so that the speakers can play with sufficient volume.

[0163] Here, the color Doppler ultrasound module refers to the signal processing circuit or software module that performs B / CF imaging and outputs color blood flow images. The CPU, or Central Processing Unit, is the core computing unit of the blood flow parameter measurement device, executing algorithms for imaging, computation, and monitoring. RAM (Random Access Memory) is used to cache raw ultrasound data, intermediate image frames, and algorithm variables. Hard disk storage (HDD) refers to flash memory (such as eMMC) or solid-state storage, used for long-term storage of patient records, calibration parameters, and system logs. The keyboard or buttons are physical input devices used to start measurements, switch modes, etc. The touchscreen integrates display and input functions, improving human-computer interaction efficiency. The speaker outputs audio feedback, such as measurement completion prompts and abnormal alarm sounds. The audio amplifier amplifies the low-power audio signal generated by the CPU to the level required to drive the speaker.

[0164] The descriptions of the system embodiments above are similar to those of the device embodiments above, and have similar beneficial effects. For technical details not disclosed in the embodiments of this application, please refer to the descriptions of the device embodiments in this application for understanding.

[0165] It should be noted that the various embodiments or implementation methods in this document can be described in a progressive manner, with each embodiment focusing on the differences from other embodiments. Similar or identical parts between embodiments can be referred to mutually. It should be understood that in the various embodiments of this application, the embodiment numbers are merely for descriptive purposes and do not represent the superiority or inferiority of the embodiments.

[0166] Understandably, without conflict, the technical features in the technical solutions described in each embodiment can be arbitrarily combined to form new embodiments. For example, each structure in each embodiment can be implemented as an independent embodiment, and the structures can be arbitrarily combined; some or all of the structures in different embodiments can be arbitrarily combined. Each step in each embodiment can be implemented as an independent embodiment, and the steps can be arbitrarily combined; the order of the steps can be arbitrarily interchanged; some or all of the steps in different embodiments can be arbitrarily combined. Furthermore, regarding the table in the embodiments, each element, each row, or each column in the table can be implemented as an independent embodiment.

[0167] In this document, when the terms "embodiment," "implementation," or "example" are used, it means that the specific features described in connection with these implementations or examples are included in at least one implementation, embodiment, or example of this application. It should be noted that the illustrative expressions of the above terms do not necessarily refer to the same implementation, embodiment, or example. Furthermore, the specific features described, such as structures or steps, can be appropriately combined in any one or more implementations, embodiments, or examples.

[0168] In some embodiments, prefixes such as "first" and "second" are used merely to distinguish different descriptive objects and do not impose restrictions on the position, order, priority, or value of the descriptive objects. The description of the descriptive objects is given in the context of the embodiments, and the use of prefixes does not constitute unnecessary restrictions. For example, the numerical value of a descriptive object is not limited by ordinal numbers and can be one or more. Taking "first device" as an example, the numerical value of "device" can be one or more. Furthermore, objects modified by different prefixes can be the same or different. For example, if the descriptive object is "device," then "first device" and "second device" can be the same device or different devices, and their types can be the same or different. Describing "first" does not necessarily imply the existence of "second," and discussing "second" does not necessarily imply the existence of "first."

[0169] In some embodiments, unless otherwise stated, elements expressed in the singular, such as “a,” “the,” “the,” “the,” “the,” “the,” etc., may mean “one and only one,” or “one or more,” “at least one,” etc. In some embodiments, “multiple” means two or more.

[0170] In some embodiments, the terms “at least one,” “one or more,” “multiple,” etc., can be used interchangeably.

[0171] In some embodiments, the notation "at least one of A and B", "A and / or B", "A in one case, B in another", "A in one case, B in another", etc., may include the following technical solutions depending on the situation: in some embodiments, A (A is executed regardless of B); in some embodiments, B (B is executed regardless of A); in some embodiments, execution is selected from A and B (A and B are selectively executed); in some embodiments, both A and B are executed. The same applies when there are more branches such as A, B, C, etc.

[0172] In some embodiments, the notation "A or B" may include the following technical solutions, depending on the situation: in some embodiments, A (execution of A regardless of B); in some embodiments, B (execution of B regardless of A); in some embodiments, selective execution from A and B (A and B are selectively executed). The same applies when there are more branches such as A, B, and C.

[0173] In some embodiments, unless otherwise expressly defined, the terms "installation," "connection," "linking," "fixing," "setting," etc., should be interpreted broadly. For example, "connection" can be a fixed connection, a detachable connection, or an integral part; it can be a mechanical connection, an electrical connection, or a communication connection; it can be a direct connection or an indirect connection through an intermediate medium; it can also refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this embodiment according to the specific circumstances.

[0174] In some embodiments, specific operational steps, such as flowcharts, are provided. However, it should be noted that these operational steps may be added or removed based on conventional or non-creative effort. The order of steps listed in the embodiments is only one of many possible orders and does not represent the only order. When executed in actual devices, systems, or server products, the steps can be executed either in the order shown in the embodiments or the accompanying drawings, or in parallel in a parallel processor or multi-threaded processing environment.

[0175] The embodiments of this application may be methods, apparatus (systems), and / or computer-readable storage media. The computer-readable storage medium may carry an executable program for causing a processor to implement various aspects of this application. The executable program may be program code written in any combination of one or more programming languages ​​for executing the embodiments of this application. Programming languages ​​include object-oriented programming languages ​​such as Java and C++, as well as conventional procedural programming languages ​​or other programming languages ​​such as "C". The program code may be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer may be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or may be connected to an external computer. The network may be a wired network or a wireless network.

[0176] In some embodiments, electronic circuits, such as programmable logic circuits, field-programmable gate arrays (FPGAs), or programmable logic arrays (PLAs), are personalized by utilizing state information of an executable program. These electronic circuits can execute executable programs to implement various aspects of this application.

[0177] The executable program described herein can be downloaded from a computer-readable storage medium to various computing / processing devices, or downloaded via a network to an external computer or external storage device. The network may include copper cables, fiber optic cables, wireless transmission, routers, firewalls, switches, gateway computers, and / or edge servers. A network adapter card or network interface in each computing / processing device receives the executable program from the network and forwards it for storage on a computer-readable storage medium within the respective computing / processing device.

[0178] Various aspects of this application are described herein with reference to flowchart illustrations and / or block diagrams of methods, apparatus (systems), and / or computer-readable storage media according to embodiments of this application. It should be understood that each block of the flowchart illustrations and / or block diagrams, and combinations of blocks in the flowchart illustrations and / or block diagrams, can be implemented by an executable program.

[0179] These executable programs can be provided to a processor of a general-purpose computer, a special-purpose computer, or other programmable data processing apparatus to produce a machine such that, when executed by the processor of the computer or other programmable data processing apparatus, they create means for implementing the functions / actions specified in one or more blocks of the flowchart and / or block diagram. These executable programs can also be stored in a computer-readable storage medium containing instructions that cause a computer, programmable data processing apparatus, and / or other device to operate in a particular manner. Thus, the computer-readable storage medium storing the instructions comprises an article of manufacture including instructions that implement aspects of the functions / actions specified in one or more blocks of the flowchart and / or block diagram. The executable programs can also be loaded onto a computer, other programmable data processing apparatus, or other device to cause a series of operational steps to be performed on the computer, other programmable data processing apparatus, or other device to produce a computer-implemented process, such that the instructions, which execute on the computer, other programmable data processing apparatus, or other device, implement the functions / actions specified in one or more blocks of the flowchart and / or block diagram. In some embodiments, the disclosed apparatus and methods can be implemented in a variety of other ways. The described device embodiments are for illustrative purposes only. For example, the module division represents only one logical functional division method. In actual implementation, multiple modules or components may be combined or integrated into another system, or certain features may be ignored or specific operations may not be performed. The coupling, direct coupling, or communication connection between the components can be achieved indirectly through interfaces, devices, or modules. The connection form can be electrical, mechanical, or other types.

[0180] In some embodiments, the modules described as separate components may or may not be physically separate; the components shown as modules may or may not be physical modules; these modules may or may not be concentrated in one place or distributed across multiple network modules. In practical applications, some or all of the modules can be selected to achieve the objectives of this embodiment, depending on the requirements.

[0181] In some embodiments, the integration of functional modules is flexible and diverse: they can all be integrated into one processing module, each can be an independent module, or two or more functional modules can be integrated into one module. These integrated modules can be implemented in pure hardware or in a combination of hardware and software functional modules.

[0182] In some embodiments, all or part of the steps of the above method embodiments can be implemented by hardware related to program instructions. The relevant program can be stored in a computer-readable storage medium, such as ROM, RAM, magnetic disk, or optical disk, and implements the steps of the above method embodiments when executed. If the integrated modules of this application are implemented as software functional modules and sold or used as independent products, they can also be stored in a computer-readable storage medium. Therefore, the technical solutions of the embodiments of this application, in essence or contributing to the prior art, can be embodied in the form of a software product. This computer software product is stored in a storage medium and contains several instructions for causing an electronic device (such as a personal computer, server, or network device) to execute all or part of the steps of the methods described in the various embodiments of this application. Therefore, the embodiments of this application are not limited to any specific hardware and software combination.

[0183] It should be understood that the above embodiments are merely illustrative of several implementation methods of this application and do not limit the scope of protection of this patent application. The above embodiments are all exemplary and are not intended to encompass all possible implementation methods included in the technical solutions of this application. Various modifications and changes can be made to the above embodiments without departing from the scope of this application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without inventive effort are within the scope of protection of this application.

Claims

1. A blood flow parameter measuring device, applied to a blood flow parameter measuring system, the system comprising the blood flow parameter measuring device and an ultrasound probe, the ultrasound probe comprising a rotating mechanism and an ultrasound crystal array, the rotating mechanism capable of driving the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured; characterized in that, The device includes: The first control module is used to control the rotating mechanism to drive the ultrasonic crystal array to rotate until the ultrasonic cross-sectional image of the blood vessel to be tested is a perfect circle. The acquisition module is used to acquire the diameter of the blood vessel to be tested based on the circular image; The second control module is used to control the rotating mechanism to drive the ultrasound crystal array to rotate in the opposite direction according to the preset Doppler angle, so as to form the required Doppler angle and enter the Doppler blood flow measurement mode. The third control module is used to select an ultrasonic crystal array within a preset width of the blood vessel to be tested based on the obtained tube diameter to start detection. The monitoring module is used to monitor the hemodynamic parameters of the target object until the fluctuation of the hemodynamic parameters exceeds the fluctuation threshold.

2. The blood flow parameter measuring device according to claim 1, characterized in that, The preset width is 1.2D to 2.0D, where D is the pipe diameter obtained by the acquisition module.

3. The blood flow parameter measuring device according to claim 1, characterized in that, The device further includes: The image processing module is used to calculate the ratio of the major axis to the minor axis of the ultrasound cross-sectional image and feed the ratio back to the first control module to determine whether a perfect circle image has been achieved.

4. The blood flow parameter measuring device according to claim 3, characterized in that, The image processing module is also used for: If the fitting roundness error of the vessel wall contour of the vessel to be tested is less than a preset threshold, the ultrasound cross-sectional image is determined to be a perfect circle; the fitting roundness error is calculated by the least squares method.

5. The blood flow parameter measuring device according to claim 1, characterized in that, The device further includes a calibration module, the calibration module being used for: The first control module will be re-executed under any of the following conditions to perform position calibration: The monitoring module detected that the fluctuations in hemodynamic parameters exceeded the fluctuation threshold; No valid Doppler signal is received within a continuous period of T seconds, where T ≥ 5.

6. The blood flow parameter measuring device according to claim 1, characterized in that, The first control module is also used for: During the process of driving the ultrasonic crystal array to rotate, incremental rotation is performed with a preset step size, and a cross-sectional image of the blood vessel is acquired at each step until N consecutive frames of images meet the criteria for a perfect circle, where N≥3.

7. The blood flow parameter measuring device according to claim 1, characterized in that, The second control module is also used for: After entering the Doppler blood flow measurement mode, the angle of the ultrasound crystal array is dynamically fine-tuned to optimize the signal-to-noise ratio of the Doppler spectrum signal.

8. The blood flow parameter measuring device according to claim 1, characterized in that, The third control module is also used for: When selecting an ultrasound crystal array within the preset width, the subset of ultrasound crystal arrays symmetrically distributed on both sides of the blood vessel centerline is preferentially activated.

9. The blood flow parameter measuring device according to any one of claims 1-8, characterized in that, The acquisition module is also used for: After obtaining the tube diameter, the cross-sectional area of ​​the blood vessel is calculated, and the stroke volume is obtained by combining the measured blood flow velocity integral VTI. The stroke volume is: SV = A * VTI. Where SV is stroke volume, A is the cross-sectional area of ​​the blood vessel, and VTI is the blood flow velocity integral.

10. A computing device applied to a blood flow parameter measurement system, the system comprising the blood flow parameter measurement device and an ultrasound probe, the ultrasound probe comprising a rotating mechanism and an ultrasound crystal array, the rotating mechanism capable of driving the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured; characterized in that, The computing device includes: a storage component, a communication bus, and a processing component, wherein: The storage component is used to store the operating program of the blood flow parameter measuring device; The communication bus is used to enable communication between the storage component and the processing component; The processing unit is used to perform the operation of each module in the blood flow parameter measuring device according to any one of claims 1-9.

11. A computer-readable storage medium applied to a blood flow parameter measurement system, the system comprising the blood flow parameter measurement device and an ultrasound probe, the ultrasound probe comprising a rotating mechanism and an ultrasound crystal array, the rotating mechanism capable of driving the ultrasound crystal array to rotate, thereby changing the angle between the ultrasound crystal array and the blood vessel to be measured; characterized in that: The computer-readable storage medium stores an executable program, which, when executed by a processor, enables the operation of each module in the blood flow parameter measuring device according to any one of claims 1-9.

12. An ultrasonic probe for use in conjunction with a blood flow parameter measuring device as described in any one of claims 1-9, characterized in that, include: Ultrasonic crystal array; A rotating mechanism, whose power output end is connected to the ultrasound crystal array, is used to drive the ultrasound crystal array to rotate, so as to change the angle between the ultrasound crystal array and the blood vessel to be tested. The interface unit is used to receive control commands from the blood flow parameter measuring device and transmit ultrasound echo data back.

13. The ultrasonic probe according to claim 12, characterized in that, The ultrasound probe also includes an angle feedback unit, which is integrated into the rotation mechanism. The angle feedback unit is used to detect the actual rotation angle of the ultrasound crystal array and transmit the actual rotation angle back to the blood flow parameter measuring device through the interface unit to form closed-loop angle control.

14. A blood flow parameter measurement system, characterized in that, include: The blood flow parameter measuring device according to any one of claims 1-9; The ultrasonic probe according to any one of claims 12-13.

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