Calibration method, apparatus, computing device, and system for doppler ultrasound probe

Abstract

This application relates to a calibration method, apparatus, computing device, and system for a Doppler ultrasound probe, belonging to the field of medical devices. The method includes: controlling a transmitting chip to emit ultrasound pulses towards a simulated human body model; receiving the echo signal returned from the simulated human body model via a receiving chip, and obtaining the propagation time of the echo signal relative to the emission time; determining the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the sound velocity within the simulated human body model, wherein the initial Doppler angle is derived by back-calculation using a one-dimensional depth-time relationship; and storing the determined initial Doppler angle of the chip. The technical solution of this application can improve the accuracy of blood flow velocity measurement.

Description

Technical Field

[0001] This application relates to the field of medical devices, and in particular to a calibration method, apparatus, computing device, and ultrasound monitoring system for a Doppler ultrasound probe. Background Technology

[0002] Ultrasonic Doppler equipment is widely used in clinical settings such as cardiovascular, obstetrics, and peripheral vascular diseases. It measures blood flow velocity through the Doppler effect, providing important information for disease assessment.

[0003] However, existing ultrasonic Doppler devices suffer from significant measurement errors.

[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 the above, this application provides a calibration method, apparatus, computing device, and ultrasonic monitoring system for a Doppler ultrasound probe 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] Firstly, embodiments of this application provide a calibration method for a Doppler ultrasound probe.

[0008] The method is applied to an ultrasonic monitoring system, the ultrasonic monitoring system including an ultrasonic probe, the ultrasonic probe including a transmitting chip and a receiving chip; the method includes:

[0009] The transmitting chip is controlled to emit ultrasonic pulses toward the simulated human body model;

[0010] The receiving chip receives the echo signal returned from the simulated human body model and obtains the propagation time of the echo signal relative to the transmission time.

[0011] Based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to the receiving chip is determined, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship;

[0012] The initial Doppler angle of the determined chip is stored.

[0013] In one optional embodiment, the ultrasound probe includes one transmitting chip and at least two receiving chips, both of which are inclined relative to the bottom surface of the probe's housing; the method includes:

[0014] The transmitting chip is controlled to emit ultrasonic pulses toward the simulated human body model along a single fixed direction, and the simulated human body model is equipped with a reflective target of known depth;

[0015] The receiver chip receives the echo signals returning from the reflecting target along the single fixed direction, and obtains the propagation time of each echo signal relative to the transmission time.

[0016] Based on the propagation time, the known depth of the reflecting target, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to each receiving chip is determined;

[0017] The initial Doppler angles of each crystal element are determined and stored in the memory of the ultrasonic probe.

[0018] In an optional embodiment, determining the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model includes:

[0019] The initial Doppler angle is calculated using the following expression:

[0020] θ = arcsin(H / (c*t / 2));

[0021] Wherein, θ is the initial Doppler angle, H is the known depth of the reflecting target, c is the speed of sound in the simulated human body model, and t is the propagation time of the echo signal.

[0022] In an optional embodiment, the simulated human body model is provided with multiple reflective targets at different depths, and the method further includes:

[0023] The transmission, reception, and calculation steps are repeatedly performed on multiple reflective targets at different depths to obtain the Doppler angle of each crystal at different depths;

[0024] Data fitting is performed on multiple Doppler angles for each crystal to obtain the initial Doppler angle of the crystal.

[0025] In an alternative embodiment, before storing the determined initial Doppler angle of the wafer, the method further includes:

[0026] Determine whether the determined initial Doppler angle is within the preset acceptable range;

[0027] If so, then perform the storage step;

[0028] If not, mark the probe as defective.

[0029] In an alternative embodiment, after storing the determined initial Doppler angle of the wafer, the method further includes:

[0030] The transmitting chip is controlled to emit ultrasound waves toward the blood vessel to be tested, and the receiving chip synchronously receives the Doppler echo signal reflected by the blood flow.

[0031] Based on the initial Doppler angle and the frequency shift information of the Doppler echo signal received by the receiving chip, the actual Doppler angle between the blood vessel to be tested and the ultrasound probe is determined.

[0032] In an alternative embodiment, after determining the actual Doppler angle between the blood vessel to be tested and the ultrasound probe, the method further includes:

[0033] Based on the actual Doppler angle, the blood flow velocity measured by the Doppler effect is corrected to obtain the corrected blood flow velocity.

[0034] In an alternative implementation, the method further includes:

[0035] Based on the amplitude fluctuation range of the Doppler echo signal, determine whether it is necessary to re-execute the step of determining the actual Doppler angle.

[0036] In one optional implementation, the data fitting of multiple Doppler angles for each wafer includes:

[0037] The least squares method is used to perform linear or nonlinear regression on the Doppler angle data points at multiple depths to eliminate random errors from a single measurement and obtain the initial Doppler angle of the wafer.

[0038] In one optional embodiment, the simulated human body model is provided with at least two reflective targets spaced apart in the horizontal direction and of the same depth;

[0039] The method further includes: performing a complete transmission, reception and calculation step for each reflecting target to obtain two independent initial Doppler angles;

[0040] Compare the difference between the two initial Doppler angles. If the difference is less than a preset threshold, the calibration result is confirmed to be valid.

[0041] Secondly, embodiments of this application provide a calibration device for a Doppler ultrasound probe, applied to an ultrasound monitoring system, the ultrasound monitoring system including an ultrasound probe, the ultrasound probe including a transmitting chip and a receiving chip; the device includes:

[0042] The control module is used to control the transmitting chip to emit ultrasonic pulses toward the simulated human body model;

[0043] The acquisition module is used to receive the echo signal returned from the simulated human body model through the receiving chip, and to acquire the propagation time of the echo signal relative to the transmission time.

[0044] The determining module is used to determine the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship;

[0045] The storage module is used to store the initial Doppler angle of the determined wafer.

[0046] Thirdly, embodiments of this application provide an ultrasonic probe, comprising:

[0047] The outer shell is made of a hard or soft material; the outer shell has a receiving cavity and is provided with a storage seat;

[0048] A chip assembly includes one transmitting chip and at least two receiving chips. The chip assembly is located in a storage seat of the accommodating cavity. The chip assembly is positioned such that the transmitting or receiving surfaces of each chip are inclined relative to the bottom surface of the housing through a preset position of the storage seat. The inclination angle is 10° to 60°.

[0049] The memory is used to store the initial Doppler angles of each chip.

[0050] Fourthly, embodiments of this application provide a computing device, the computing device comprising: a storage component, a communication bus, and a processing component, wherein:

[0051] The storage component is used to store the calibration method program for the Doppler ultrasound probe;

[0052] The communication bus is used to enable communication between the storage component and the processing component;

[0053] The processing unit is used to execute a calibration method procedure for the Doppler ultrasound probe to implement the steps of any of the methods described above.

[0054] Fifthly, embodiments of this application provide an ultrasonic monitoring system, comprising:

[0055] The controller includes the calibration device for the Doppler ultrasound probe described above;

[0056] The ultrasonic probe described above.

[0057] The Doppler ultrasound probe calibration method, apparatus, computing device, and ultrasound monitoring system provided in this application include: controlling a transmitting chip to emit ultrasound pulses towards a simulated human body model; receiving echo signals returned from the simulated human body model via a receiving chip and obtaining the propagation time of the echo signals relative to the emission time; determining the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the sound velocity in the simulated human body model, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship; and storing the determined initial Doppler angle of the chip. It can be seen that the Doppler ultrasound probe calibration method, apparatus, computing device, and ultrasound monitoring system in this application, by employing an A-mode calibration method based on a one-dimensional depth-time relationship during the probe manufacturing stage, accurately obtains the initial Doppler angle of each chip, thereby reducing the blood flow velocity measurement error caused by the angle setting deviation and improving the accuracy of blood flow velocity measurement.

[0058] 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

[0059] 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:

[0060] Figure 1 This is a schematic flowchart of the calibration method for the Doppler ultrasound probe provided in Embodiment 1 of this application;

[0061] Figure 2 This is a schematic diagram of the probe structure in the calibration method of the Doppler ultrasound probe provided in Embodiment 1 of this application;

[0062] Figure 3 This is a schematic diagram illustrating the determination of the initial Doppler angle of the wafer in the calibration method of the Doppler ultrasonic probe provided in Embodiment 1 of this application.

[0063] Figure 4 This is a schematic diagram illustrating the determination of the actual Doppler angle between the blood vessel to be tested and the ultrasound probe in the calibration method of the Doppler ultrasound probe provided in Embodiment 1 of this application.

[0064] Figure 5 This is a schematic diagram of the calibration device for the Doppler ultrasound probe provided in Embodiment 2 of this application;

[0065] Figure 6 This is a schematic diagram of the structure of the computing device provided in Embodiment 3 of this application;

[0066] Figure 7This is a schematic diagram of the ultrasonic monitoring system provided in Embodiment 5 of this application.

[0067] Explanation of reference numerals in the attached figures:

[0068] 21. Outer casing; 22. Transmitting chip; 23. Receiving chip; 60. Calibration device; 61. Control module; 62. Acquisition module; 63. Determination module; 64. Storage module; 80. Computing device; 81. Storage component; 82. Communication bus; 83. Processing component; 84. Input device; 85. Output device; 86. External communication interface. Detailed Implementation

[0069] 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.

[0070] The exemplary embodiments disclosed in this application will now be described in more detail with reference to the accompanying drawings, providing detailed structures 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.

[0071] 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.

[0072] 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.

[0073] The inventors of this application discovered during the research and development that in the calibration process of existing Doppler ultrasound probes, a preset theoretical sound beam angle is usually used to calculate blood flow velocity. However, in the actual manufacturing process, due to factors such as wafer mounting angle deviation and shell processing error, the initial Doppler angle of each probe differs from the theoretical design value. This difference directly affects the calculation accuracy of the Doppler angle, which in turn leads to blood flow velocity measurement error.

[0074] This problem is exacerbated, especially for probes that use a rigid triangular stepped structure to fix the wafer. On the one hand, the manufacturing process makes it difficult to ensure that the angle between the wafer and the attached step perfectly matches the theoretical design value. On the other hand, acoustic refraction occurs when ultrasound propagates at the rigid-wafer interface, causing additional deflection of the sound beam direction. The aforementioned manufacturing deviations and acoustic refraction effects superimpose to form a cumulative angular error, significantly amplifying the inaccuracy in calculating the Doppler angle.

[0075] In addition, traditional calibration methods often rely on complex 3D scanning equipment or require multiple measurements from multiple reference targets at different angles, which are cumbersome and costly, making them difficult to implement quickly on the production line.

[0076] Therefore, through further research and development, the inventors proposed the following technical solution.

[0077] Example 1

[0078] This application provides a calibration method for a Doppler ultrasound probe. The method can be implemented by a computer, which can be a computing device configured with a processor. 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.

[0079] The method is applied to an ultrasonic monitoring system, which includes an ultrasonic probe, reference... Figure 2 The ultrasonic probe includes a transmitting chip 22 and a receiving chip 23; reference Figure 1 The method includes:

[0080] Step 101: Control the transmitting chip to emit ultrasonic pulses toward the simulated human body model;

[0081] Step 102: Receive the echo signal returned from the simulated human body model by receiving the receiving chip, and obtain the propagation time of the echo signal relative to the transmission time;

[0082] Step 103: Determine the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model; wherein, the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship.

[0083] Step 104: Store the determined initial Doppler angle of the wafer.

[0084] Unrestricted, the transmitting chip can be a chip in an ultrasonic probe used to generate ultrasonic signals, its function being to transmit ultrasonic pulses to the simulated human body model for sound beam angle calibration. The receiving chip 23 can be a chip in an ultrasonic probe used to receive echo signals, its function being to capture ultrasonic echoes returned from the simulated human body model. The simulated human body model can be a standard phantom simulating the acoustic characteristics of human tissue, its function being to provide a reference environment with known acoustic parameters. The propagation time can be the time interval from the time of ultrasonic pulse emission to the time of echo signal reception, its function being to serve as a basic parameter for calculating the sound beam angle. The one-dimensional depth-time relationship can be based on the physical principle that the depth of ultrasonic waves propagating in a medium is proportional to time, its function being to deduce the actual propagation angle of the sound beam through a simple depth-time conversion.

[0085] The above method of calibrating the sound beam angle by means of propagation time can be used in the ultrasonic probe operating mode, which is the ultrasonic A mode, or simply the A mode calibration method.

[0086] Specifically, in the step of controlling the transmitting chip 22 to transmit ultrasonic pulses to the simulated human body model, a pulse echo mode can be used, and the transmission frequency can be set in the range of 2 MHz to 8 MHz according to the probe specifications. When the receiving chip 23 receives the echo signal, the echo can be amplified and filtered by a preamplifier and a bandpass filter.

[0087] For example, in one specific embodiment, the simulated human body model can be made of a water-based gel material, and the speed of sound can be set to 1540 m / s, consistent with the speed of sound of human soft tissue.

[0088] Furthermore, the simulated human body model can be made of materials with different sound velocities, such as silicone, polyurethane, or aqueous solutions, to adapt to the calibration requirements of different application scenarios. The number of receiving chips 23 can be set to one or more according to the probe design requirements, and each receiving chip 23 independently calculates and stores the sound beam angle.

[0089] The calibration method for the Doppler ultrasound probe in this application reduces the blood flow velocity measurement error caused by the deviation in angle setting by using an A-mode calibration method based on a one-dimensional depth-time relationship during the probe production stage, thereby improving the accuracy of blood flow velocity measurement.

[0090] In other embodiments of this application, the ultrasonic probe includes one transmitting chip 22 and at least two receiving chips 23, wherein both the transmitting chip 22 and the receiving chip 23 are inclined to the bottom surface of the probe housing 21; the method includes:

[0091] The transmitting chip 22 is controlled to emit ultrasonic pulses toward the simulated human body model along a single fixed direction, and the simulated human body model is provided with a reflective target of known depth;

[0092] The receiving chip 23 receives the echo signals returning from the reflecting target along the single fixed direction, and obtains the propagation time of each echo signal relative to the transmission time.

[0093] Based on the propagation time, the known depth of the reflecting target, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to each receiving cell 23 is determined;

[0094] The initial Doppler angles of each crystal element are determined and stored in the memory of the ultrasonic probe.

[0095] Non-limitingly, the at least two receiving chips 23 can be an array of receiving chips 23, the function of which is to achieve multi-channel synchronous reception to improve calibration efficiency. The tilting arrangement can be such that the mounting plane of the chip forms a certain angle with the bottom surface of the probe housing 21, the function of which is to allow the ultrasonic beam to be incident on the target area at a specific angle, reference... Figure 2 .

[0096] The single fixed direction can be the ultrasonic wave emission direction that remains unchanged throughout the calibration process, ensuring the consistency of measurement conditions. The reflective target with known depth can be a pre-set acoustic reflector with a precisely known depth position in a simulated human body model, providing an accurate depth reference. The memory can be a non-volatile memory chip integrated inside the ultrasonic probe, permanently storing the calibrated beam angle parameters.

[0097] Specifically, the tilt angles of the transmitting chip 22 and the receiving chip 23 can be set within the range of 15 degrees to 45 degrees, preferably 25 degrees to 35 degrees. The reflective target can be made of metal wire, bubbles, or a highly reflective material. Each receiving chip 23 independently receives the echo signal, and the accuracy of the measurement is ensured by a time synchronization circuit. The memory can be an electrically erasable programmable read-only memory or a flash memory chip, and the storage capacity is determined according to the number of chips.

[0098] For example, refer to Figure 2 In one specific embodiment, the ultrasonic probe includes a housing 21, within which one transmitting crystal 22 and two receiving crystals 23 are disposed, all of which are mounted at an angle. The transmitting crystal 22 is located in the center, and the receiving crystals 23 are located on either side of the transmitting crystal 22. The transmission or reception trajectories of the three crystals can be parallel or non-parallel, and are not limited thereto.

[0099] Furthermore, in addition to storing the sound beam angle, the memory can also store additional information such as calibration time and calibration equipment number, which facilitates quality traceability.

[0100] In other embodiments of this application, determining the initial Doppler angle corresponding to the receiving chip 23 based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model includes:

[0101] The initial Doppler angle is calculated using the following expression:

[0102] θ=arcsin(H / (c*t / 2)) (1)

[0103] Wherein, θ is the initial Doppler angle, H is the known depth of the reflecting target, c is the speed of sound in the simulated human body model, and t is the propagation time of the echo signal.

[0104] Unrestricted, the expression can be a beam angle calculation formula derived from trigonometric relationships, which accurately calculates the initial Doppler angle using known depth, sound velocity, and time parameters. H represents the known depth of the reflecting target, which can be the vertical distance from the reflecting target to the bottom surface of the probe housing 21, in millimeters or meters. c represents the sound velocity in the simulated human body model, which can be the propagation speed of ultrasound in the simulated human body model medium, in meters per second. t represents the propagation time of the echo signal, which can be the time interval from ultrasound pulse transmission to echo signal reception, in seconds.

[0105] To better understand the calculation process of the initial Doppler angle, the following section combines... Figure 3 Let me introduce it. From Figure 3 It can be seen that:

[0106] The initial Doppler angle of the left-side receiving cell 23 is θ1.

[0107] The receiving beam length of the receiving chip 23, i.e., the trajectory length of the ultrasonic pulse, is:

[0108] L1 = c*t1 / 2 (2)

[0109] Then we can obtain an approximate formula for calculating sinθ1:

[0110] sinθ1=H / L1 (3)

[0111] From (3), we can obtain:

[0112] θ1=arcsin(H / (c*t1 / 2)) (4)

[0113] Similarly, the initial Doppler angle θ2 between the middle transmitting crystal 22 and the right receiving crystal 23 can be obtained. 、 The formula for calculating θ3. In the attached figure, the transmitting chip 22 is represented by T, and the receiving chip 23 is represented by R. By induction, the general formula for calculating the initial Doppler angle of the chips can be obtained, namely expression (1).

[0114] Furthermore, since expression (3) is an approximate calculation, in order to calculate more accurately, it is necessary to subtract the distance between the crystal and the surface of the reflecting target in the actual sound beam trajectory direction (marked as D in the attached figure, including D1, D2, and D3), that is:

[0115] S1=L1-D1 (5)

[0116] Therefore, we can conclude that:

[0117] sinθ1=H / S1 (6)

[0118] θ1=arcsin(H / (c*t1 / 2-D1)) (7)

[0119] Similarly, the initial Doppler angle θ2 between the middle transmitting crystal 22 and the right receiving crystal 23 can be obtained. 、 The formula for calculating θ3. By generalization, we can obtain the general formula for calculating the initial Doppler angle of the crystal:

[0120] θ=arcsin(H / (c*t / 2-D)) (8)

[0121] For example: the depth of the reflected target is H = 50 mm = 0.05 m, the speed of sound of the simulated human body model is c = 1540 m / s, and the measured propagation time is t = 112.6 microseconds = 112.6 × 10^-6 seconds.

[0122] Substitute into expression (1) and calculate:

[0123] θ=arcsin(0.05 / (1540*112.6×10^-6 / 2))=arcsin(0.05 / 0.087164)=arcsin(0.5736)=35 degrees.

[0124] Substituting into expression (8), we get D = 2 millimeters = 0.002 meters:

[0125] θ=arcsin(0.05 / (1540*112.6×10^-6 / 2-0.002))=arcsin(0.05 / 0.08507=arcsin(0.588)=36 degrees.

[0126] In other embodiments of this application, the simulated human body model is provided with multiple reflective targets at different depths, and the method further includes:

[0127] The transmission, reception, and calculation steps are repeatedly performed on multiple reflective targets at different depths to obtain the Doppler angle of each crystal at different depths;

[0128] Data fitting is performed on multiple Doppler angles for each crystal to obtain the initial Doppler angle of the crystal.

[0129] Without limitation, the multiple reflective targets at different depths can be multiple reflectors distributed along the depth direction in a simulated human body model, serving to provide multi-point calibration data to improve calibration accuracy. The repeated execution can involve performing a complete calibration process for each reflective target separately, aiming to acquire sound beam angle data at different depths. The data fitting can employ mathematical methods to perform curve fitting or averaging on multiple measurement data, eliminating random errors and obtaining more reliable sound beam angle values.

[0130] Specifically, multiple reflecting targets can be positioned at different depths, such as 10 mm, 30 mm, 50 mm, and 70 mm. For each reflecting target at each depth, a complete process is executed sequentially: transmitting an ultrasonic pulse, receiving the echo signal, calculating the propagation time, and determining the sound beam angle. Data fitting can be performed using methods such as arithmetic mean, weighted average, or least squares.

[0131] Furthermore, the data fitting can consider depth weighting, assigning different weight coefficients to measurement data at different depths. The fitting method can employ advanced algorithms such as linear regression, polynomial fitting, or spline interpolation. The fitting results can be statistically analyzed, such as calculating standard deviation and confidence intervals, to evaluate calibration accuracy.

[0132] In other embodiments of this application, before storing the determined initial Doppler angle of the wafer, the method further includes:

[0133] Determine whether the determined initial Doppler angle is within the preset acceptable range;

[0134] If yes, then perform the storage step; otherwise, mark the probe as defective.

[0135] Without limitation, the preset acceptable range can be the allowable deviation range of the acoustic beam angle determined according to the probe design specifications and manufacturing process, and its function is to screen out qualified products that meet quality standards. The judgment can be a comparison between the calculated initial Doppler angle and the preset range, and its function is to achieve automated quality control. Marking as unqualified products can be a process of identifying and isolating probes that exceed the allowable range, and its function is to prevent unqualified products from entering the market.

[0136] Specifically, the preset acceptable range can be determined based on ±5 degrees of the theoretical design angle. For example, if the design angle is 35 degrees, the allowable range is 30 to 40 degrees. The judgment process can be automatically completed by the calibration system's control software, triggering an alarm when the range is exceeded. Non-conforming products can be marked using software marking, physical labels, or database records.

[0137] Furthermore, the preset acceptable range can be set with different allowable deviations based on different wafer positions. The judgment criteria can include multiple dimensions, such as angular deviation, consistency between multiple wafers, and stability of repeated measurements. Defective products can be reworked or scrapped; rework requires recalibration.

[0138] In other embodiments of this application, after storing the determined initial Doppler angle of the wafer, the method further includes:

[0139] The transmitting chip 22 is controlled to emit ultrasound waves toward the blood vessel to be tested, and the receiving chip 23 synchronously receives the Doppler echo signal reflected by the blood flow.

[0140] Based on the initial Doppler angle and the frequency shift information of the Doppler echo signal received by the receiving chip 23, the actual Doppler angle between the blood vessel to be tested and the ultrasound probe is determined.

[0141] Without limitation, the blood vessel to be tested can be any human blood vessel for which blood flow velocity measurement is required, serving as the target object for Doppler ultrasound detection. The Doppler echo signal can be an ultrasound signal reflected back from red blood cells with a frequency shift, carrying blood flow velocity information. The frequency shift information can be the change in frequency of the Doppler echo signal relative to the transmitted signal, serving as a fundamental parameter for calculating blood flow velocity. The actual Doppler angle can be the angle between the ultrasound beam and the blood flow direction, a key parameter for calculating Doppler blood flow velocity.

[0142] Specifically, when transmitting ultrasound waves to the blood vessel being tested, continuous wave or pulsed wave Doppler modes can be used. When receiving the Doppler echo signal, orthogonal demodulation technology can be used to extract frequency shift information. To determine the actual Doppler angle, a comprehensive calculation can be performed considering the probe placement angle, the blood vessel orientation, and the initial Doppler angle.

[0143] To better understand the calculation process of the actual Doppler angle, the following section combines... Figure 4 Let's begin with an introduction. Before explaining the calculation process, let's define the following:

[0144] θ1: The initial Doppler angle of the left receiving cell 23;

[0145] θ2: The initial Doppler angle of the intermediate emitting crystal 22;

[0146] θ2: The initial Doppler angle of the receiving cell 23 on the right side;

[0147] φ: The angle between the blood vessel and the probe surface;

[0148] f0: Transmission frequency;

[0149] Δf left: Doppler frequency shift of the left receiving cell 23;

[0150] Δf right: Doppler frequency shift of the receiving cell 23 on the right side;

[0151] V: Blood flow velocity;

[0152] Vm1: Blood flow velocity measured by the left-side receiving chip 23;

[0153] Vm2: Blood flow velocity of the right-side receiving chip 23.

[0154] Based on the calibrated angle, the measured blood flow velocities Vm1 and Vm2

[0155] Doppler frequency shift Δf left of the receiving chip 23 on the left

[0156]

[0157] Since c » Vm1 cosθ1, therefore

[0158]

[0159] Right now:

[0160]

[0161] Real blood flow velocity :

[0162]

[0163] From the actual blood flow velocity V and the measured velocity Vm2 of the left-side receiving cell 23, we can obtain:

[0164]

[0165] Right now:

[0166]

[0167] Similarly, the Doppler frequency shift Δf of the receiving cell 23 on the right is:

[0168]

[0169] Right now:

[0170]

[0171] The actual blood flow velocity V:

[0172]

[0173] From the actual blood flow velocity V and the measured velocity Vm2 of the receiving cell 23 on the right, we can obtain:

[0174]

[0175] By combining Vm1 and Vm2, we can obtain:

[0176]

[0177] Let R = Vm1 / Vm2, then we get:

[0178]

[0179] Sum to product:

[0180]

[0181] make

[0182]

[0183] so:

[0184]

[0185] Expanding, we get:

[0186]

[0187] Dividing both the numerator and denominator by cosφ, we get:

[0188]

[0189] After sorting, we get:

[0190]

[0191] Will

[0192]

[0193] Substituting, the final φ is:

[0194]

[0195] By calculating φ, the actual Doppler angle can be obtained, i.e.:

[0196] The actual Doppler angle = θ - φ

[0197] Therefore, the actual blood flow velocity :

[0198]

[0199] or

[0200]

[0201] The corrected speed is:

[0202]

[0203] In other embodiments of this application, after determining the actual Doppler angle between the blood vessel to be tested and the ultrasound probe, the method further includes:

[0204] Based on the actual Doppler angle, the blood flow velocity measured by the Doppler effect is corrected to obtain the corrected blood flow velocity.

[0205] Without limitation, the blood flow velocity measured by the Doppler effect can be a blood flow velocity value initially calculated based on frequency shift information, which serves to provide raw measurement data. The correction can be an angular correction of the raw blood flow velocity using the actual Doppler angle, which eliminates velocity measurement deviations caused by angular errors. The corrected blood flow velocity can be an accurate blood flow velocity value after angle correction, which provides reliable data for clinical diagnosis.

[0206] In other embodiments of this application, the method further includes:

[0207] Based on the amplitude fluctuation range of the Doppler echo signal, determine whether it is necessary to re-execute the step of determining the actual Doppler angle.

[0208] Without limitation, the signal amplitude fluctuation range can be the amplitude variation range of the Doppler echo signal over a time series, and its function is to evaluate the stability and reliability of the measurement data. The judgment can be a comparison of the signal amplitude fluctuation range with a preset threshold, and its function is to achieve adaptive measurement quality control. The re-execution can be to repeat the Doppler angle calculation process when the judgment result indicates that it is necessary, and its function is to improve the accuracy of the measurement results.

[0209] Specifically, the signal amplitude fluctuation range can be calculated based on the standard deviation or peak-to-peak value of the signal amplitude. Excessive fluctuation is considered when the standard deviation exceeds 10% of the average or the peak-to-peak value exceeds 20% of the average. This judgment process can be monitored and automatically triggered in real time by the signal processing software. Preset thresholds can be adaptively adjusted according to different blood vessel types and measurement conditions.

[0210] For example, in one specific embodiment, the system detects that the standard deviation of the Doppler echo signal amplitude within a 1-second time window is 15% of the average value, which exceeds the preset 10% threshold. It determines that the signal amplitude fluctuation is too large and automatically prompts the operator to adjust the probe position and redetermine the Doppler angle.

[0211] Furthermore, the calculation of the signal amplitude fluctuation range can employ a sliding window algorithm to monitor signal stability in real time. The evaluation of the fluctuation range can be combined with frequency domain analysis, such as multi-dimensional indicators like spectral width changes. Judgment thresholds can be set with multiple levels of standards according to different application scenarios, such as warning thresholds and stop thresholds.

[0212] In other embodiments of this application, the data fitting of multiple Doppler angles for each wafer includes:

[0213] The least squares method is used to perform linear or nonlinear regression on the initial Doppler angle data points at multiple depths to eliminate random errors from a single measurement and obtain the initial Doppler angle of the wafer.

[0214] Without limitation, the least squares method can be a mathematical optimization method that finds the best function match for the data by minimizing the sum of squared errors, thereby providing the optimal fitting result. The linear regression can be a fitting method that assumes a linear relationship between the beam angle and depth, simplifying calculations and being applicable to small-range depth variations. The nonlinear regression can be a fitting method that considers the possibility of a nonlinear relationship between the beam angle and depth, improving fitting accuracy. The random error can be an unpredictable error caused by factors such as measurement noise and environmental interference; its purpose is to reduce its impact through multiple measurements and fittings.

[0215] Furthermore, the data fitting can employ weighted least squares, assigning different weights to measurement data at different depths.

[0216] In other embodiments of this application, the simulated human body model includes at least two horizontally spaced reflective targets of the same depth; the method further includes:

[0217] Perform a complete transmission, reception, and calculation process for each reflecting target to obtain two independent initial Doppler angles.

[0218] Compare the difference between the two initial Doppler angles. If the difference is less than a preset threshold, the calibration result is confirmed to be valid.

[0219] Without limitation, the at least two horizontally spaced reflecting targets can be multiple reflectors in the same depth plane but with different lateral positions, serving to provide verification data for lateral consistency. The two independent initial Doppler angles can be beam angle datasets calculated based on different reflecting targets, used for lateral consistency verification. The difference can be the degree of deviation between the two sets of beam angle data, used to quantitatively evaluate the lateral consistency of the calibration results. The preset threshold can be an angle deviation judgment standard set according to accuracy requirements, used to achieve automated quality verification.

[0220] Specifically, the two reflective targets can be spaced 10 mm to 50 mm apart in the horizontal direction. The difference comparison can be based on the absolute value or relative error of the angular deviation. The preset threshold can be set to an angular deviation of no more than 1 degree or a relative error of no more than 3%.

[0221] Furthermore, the difference comparison can employ statistical methods, such as calculating the correlation coefficient between the two sets of data or performing analysis of variance. The number of reflective targets can be increased to three or more to improve the reliability of the verification. The difference threshold can be set with different standards according to probes of different accuracy levels.

[0222] Example 2

[0223] This application provides a calibration device (hereinafter referred to as calibration device 60) for a Doppler ultrasound probe, applied to an ultrasound monitoring system. The ultrasound monitoring system includes an ultrasound probe, which includes a transmitting chip 22 and a receiving chip 23. (Reference) Figure 5 The calibration device 60 includes:

[0224] Control module 61 is used to control the transmitting chip 22 to transmit ultrasonic pulses to the simulated human body model;

[0225] The acquisition module 62 is used to receive the echo signal returned from the simulated human body model through the receiving chip 23, and to acquire the propagation time of the echo signal relative to the transmission time.

[0226] The determining module 63 is used to determine the initial Doppler angle corresponding to the receiving chip 23 based on the propagation time, the simulated human body model, and the sound speed in the simulated human body model, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship;

[0227] Storage module 64 is used to store the determined initial Doppler angle of the wafer.

[0228] In other embodiments of this application, the ultrasonic probe includes one transmitting chip 22 and at least two receiving chips 23, both the transmitting chip 22 and the receiving chip 23 being inclined to the bottom surface of the probe housing 21; the control module 61 is used for:

[0229] The transmitting chip 22 is controlled to emit ultrasonic pulses toward the simulated human body model along a single fixed direction, and the simulated human body model is provided with a reflective target of known depth;

[0230] The receiving chip 23 receives the echo signals returning from the reflecting target along the single fixed direction, and obtains the propagation time of each echo signal relative to the transmission time.

[0231] Based on the propagation time, the known depth of the reflecting target, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to each receiving cell 23 is determined;

[0232] The initial Doppler angles of each crystal element are determined and stored in the memory of the ultrasonic probe.

[0233] Non-limitingly, the at least two receiving chips 23 can be an array of receiving chips 23, the function of which is to achieve multi-channel synchronous reception to improve calibration efficiency. The tilting arrangement can be such that the mounting plane of the chip forms a certain angle with the bottom surface of the probe housing 21, the function of which is to allow the ultrasonic beam to be incident on the target area at a specific angle, reference... Figure 2 .

[0234] The single fixed direction can be the ultrasonic wave emission direction that remains unchanged throughout the calibration process, ensuring the consistency of measurement conditions. The reflective target with known depth can be a pre-set acoustic reflector with a precisely known depth position in a simulated human body model, providing an accurate depth reference. The memory can be a non-volatile memory chip integrated inside the ultrasonic probe, permanently storing the calibrated beam angle parameters.

[0235] Specifically, the tilt angles of the transmitting chip 22 and the receiving chip 23 can be set within the range of 15 degrees to 45 degrees, preferably 25 degrees to 35 degrees. The reflective target can be made of metal wire, bubbles, or a highly reflective material. Each receiving chip 23 independently receives the echo signal, and the accuracy of the measurement is ensured by a time synchronization circuit. The memory can be an electrically erasable programmable read-only memory or a flash memory chip, and the storage capacity is determined according to the number of chips.

[0236] For example, refer to Figure 2 In one specific embodiment, the ultrasonic probe includes one transmitting crystal 22 and two receiving crystals 23, all of which are mounted at a 35-degree angle. The transmitting crystal 22 is located in the middle, and the receiving crystals 23 are located on either side of the transmitting crystal 22. The transmission or reception trajectories of the three crystals can be parallel or non-parallel, and are not limited thereto.

[0237] Furthermore, in addition to storing the sound beam angle, the memory can also store additional information such as calibration time and calibration equipment number, which facilitates quality traceability.

[0238] In other embodiments of this application, the determining module 63 is further configured to:

[0239] The initial Doppler angle is calculated using the following expression:

[0240] The expression is the same as expression (1), and will not be repeated here.

[0241] To better understand the calculation process of the initial Doppler angle, you can combine... Figure 3 For an introduction, please refer to the relevant content in Example 1.

[0242] In other embodiments of this application, the determining module 63 is further configured to:

[0243] The transmission, reception, and calculation steps are repeatedly performed on multiple reflective targets at different depths to obtain the Doppler angle of each crystal at different depths;

[0244] Data fitting is performed on multiple Doppler angles for each crystal to obtain the initial Doppler angle of the crystal.

[0245] Without limitation, the multiple reflective targets at different depths can be multiple reflectors distributed along the depth direction in a simulated human body model, serving to provide multi-point calibration data to improve calibration accuracy. The repeated execution can involve performing a complete calibration process for each reflective target separately, aiming to acquire sound beam angle data at different depths. The data fitting can employ mathematical methods to perform curve fitting or averaging on multiple measurement data, eliminating random errors and obtaining more reliable sound beam angle values.

[0246] Specifically, multiple reflecting targets can be positioned at different depths, such as 10 mm, 30 mm, 50 mm, and 70 mm. For each reflecting target at each depth, a complete process is executed sequentially: transmitting an ultrasonic pulse, receiving the echo signal, calculating the propagation time, and determining the sound beam angle. Data fitting can be performed using methods such as arithmetic mean, weighted average, or least squares.

[0247] Furthermore, the data fitting can consider depth weighting, assigning different weight coefficients to measurement data at different depths. The fitting method can employ advanced algorithms such as linear regression, polynomial fitting, or spline interpolation. The fitting results can be statistically analyzed, such as calculating standard deviation and confidence intervals, to evaluate calibration accuracy.

[0248] In other embodiments of this application, the storage module 64 is further configured to:

[0249] Determine whether the determined initial Doppler angle is within the preset acceptable range;

[0250] If yes, then perform the storage step; otherwise, mark the probe as defective.

[0251] Without limitation, the preset acceptable range can be the allowable deviation range of the acoustic beam angle determined according to the probe design specifications and manufacturing process, and its function is to screen out qualified products that meet quality standards. The judgment can be a comparison between the calculated initial Doppler angle and the preset range, and its function is to achieve automated quality control. Marking as unqualified products can be a process of identifying and isolating probes that exceed the allowable range, and its function is to prevent unqualified products from entering the market.

[0252] Specifically, the preset acceptable range can be determined based on ±5 degrees of the theoretical design angle. For example, if the design angle is 35 degrees, the allowable range is 30 to 40 degrees. The judgment process can be automatically completed by the calibration system's control software, triggering an alarm when the range is exceeded. Non-conforming products can be marked using software marking, physical labels, or database records.

[0253] Furthermore, the preset acceptable range can be set with different allowable deviations based on different wafer positions. The judgment criteria can include multiple dimensions, such as angular deviation, consistency between multiple wafers, and stability of repeated measurements. Defective products can be reworked or scrapped; rework requires recalibration.

[0254] In other embodiments of this application, the determining module 63 is further configured to:

[0255] The transmitting chip 22 is controlled to emit ultrasound waves toward the blood vessel to be tested, and the receiving chip 23 synchronously receives the Doppler echo signal reflected by the blood flow.

[0256] Based on the initial Doppler angle and the frequency shift information of the Doppler echo signal received by the receiving chip 23, the actual Doppler angle between the blood vessel to be tested and the ultrasound probe is determined.

[0257] Without limitation, the blood vessel to be tested can be any human blood vessel for which blood flow velocity measurement is required, serving as the target object for Doppler ultrasound detection. The Doppler echo signal can be an ultrasound signal reflected back from red blood cells with a frequency shift, carrying blood flow velocity information. The frequency shift information can be the change in frequency of the Doppler echo signal relative to the transmitted signal, serving as a fundamental parameter for calculating blood flow velocity. The actual Doppler angle can be the angle between the ultrasound beam and the blood flow direction, a key parameter for calculating Doppler blood flow velocity.

[0258] Specifically, when transmitting ultrasound waves to the blood vessel being tested, continuous wave or pulsed wave Doppler modes can be used. When receiving the Doppler echo signal, orthogonal demodulation technology can be used to extract frequency shift information. To determine the actual Doppler angle, a comprehensive calculation can be performed considering the probe placement angle, the blood vessel orientation, and the initial Doppler angle.

[0259] To better understand the calculation process of the actual Doppler angle, you can combine... Figure 4 For an introduction, please refer to the relevant content in Example 1.

[0260] 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.

[0261] The descriptions of the apparatus embodiments above are similar to those of the method 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 method embodiments in this application for understanding.

[0262] Example 3

[0263] This application provides an ultrasonic probe, for reference... Figure 2 The ultrasonic probe includes:

[0264] The outer casing 21 is made of a hard or soft material; the outer casing has a receiving cavity and is provided with a storage seat;

[0265] The chip assembly includes one transmitting chip 22 and at least two receiving chips 23. The chip assembly is located in the storage seat of the accommodating cavity. The chip assembly is positioned so that the transmitting or receiving surfaces of each chip are inclined relative to the bottom surface of the outer casing 21 through a preset position of the storage seat. The inclination angle is 10° to 60°.

[0266] The memory is used to store the initial Doppler angles of each chip.

[0267] Unrestricted, the outer casing 21 can provide physical protection for the internal components and is designed with a specific geometry (such as a triangle). The casing can be made of a rigid material, a soft material, or a combination of both. For example, the bottom surface of the casing that contacts the skin can be made of a soft material, while other parts can be made of a rigid material. In this way, on the one hand, the rigid material provides better protection, and on the other hand, the soft material on the bottom surface is more patient-friendly, as it can act as an acoustic lens for the ultrasound waves, improving the quality of the detection.

[0268] The preset position of the holder is used to fix the wafer assembly and give it a preset tilt angle. The preset tilt angle can be 10° to 60°.

[0269] The chip assembly, the acoustic core of the ultrasound probe, is encapsulated inside the housing 21. Specifically, the chip assembly includes a central transmitting chip 22 and at least two receiving chips 23 symmetrically distributed on either side of it. All chips are tilted relative to the bottom surface of the housing 21 (i.e., the plane in contact with human skin).

[0270] This tilt setting is key to achieving Doppler blood flow detection. By tilting the crystal at a specific angle, the transmitted and received ultrasound beams are directed onto the blood vessel at a non-perpendicular angle, generating a Doppler frequency shift signal that can be used for velocity calculation. Depending on different clinical applications, this tilt angle can be selected in a wide range from 10° to 60°, with the most commonly used clinical range being 45° to 75°.

[0271] Besides storing standard production serial numbers or model information, the memory primarily stores the initial Doppler angles of each chip. These initial Doppler angles are measured individually during probe manufacturing using a mode A calibration procedure. This calibration process effectively compensates for minor chip mounting deviations caused by manufacturing limitations, as well as beam deflection caused by ultrasonic refraction at the hard-shell-chip interface. Therefore, the angle data stored in the chip is a unique, corrected "true" angle for each probe, rather than a theoretical design value. Specifically, the memory can be an EEPROM or a Flash chip.

[0272] In summary, the ultrasound probe of this embodiment combines a multi-chip array with a specific tilt angle with a memory storing individualized calibration parameters, providing a high-precision hardware foundation for the subsequent ultrasound monitoring system. When the probe is connected to the ultrasound monitoring system, the controller can first read the initial Doppler angle from this memory as a reliable reference for all subsequent blood flow velocity calculations and secondary Doppler angle calibrations, thereby improving the overall accuracy and consistency of the measurement.

[0273] Example 4

[0274] This application provides a computing device 80, with reference to... Figure 6 The computing device 80 includes: a storage unit 81, a communication bus 82, and a processing unit 83, wherein:

[0275] The storage component 81 is used to store the calibration method program for the Doppler ultrasound probe;

[0276] The communication bus 82 is used to realize the connection and communication between the storage component 81 and the processing component 83;

[0277] The processing unit 83 is used to execute a calibration method procedure for the Doppler ultrasound probe to achieve the steps of the method described in Embodiment 1.

[0278] The type or structure of the storage component 81 can be found in the storage medium section below, and will not be repeated here.

[0279] The processing unit 83 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.

[0280] In some embodiments, the computing device 80 may further include an input device 84, an output device 85, and an external communication interface 86, which are interconnected via a bus system and / or other forms of connection mechanisms (not shown).

[0281] In some embodiments, input device 84 may include, for example, a keyboard, mouse, microphone, etc. Output device 85 may output various information to the outside, including displays, speakers, printers, projectors, and communication networks and their connected remote output devices, etc. External communication interface 86 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 WiFi or Bluetooth.

[0282] The description of the above-described embodiments of the computing device 80 is similar to that of the above-described method embodiments, and has similar beneficial effects. For technical details not disclosed in the embodiments of this application, please refer to the description of the method embodiments in this application for understanding.

[0283] Example 5

[0284] This application provides a computer-readable storage medium storing an executable program, which, when executed by a processor, implements the steps of the method described in Embodiment 1.

[0285] 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.

[0286] 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).

[0287] The ROM includes: Programmable Read-Only Memory (PROM), Erasable Programmable Read-Only Memory (EPROM), and Electrically Erasable Programmable Read-Only Memory (EEPROM).

[0288] The description of the computer-readable storage medium embodiments above is similar to the description of the method 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 method embodiments in this application for understanding.

[0289] Example 6

[0290] This application provides an ultrasonic monitoring system, as shown in the following embodiments. Figure 7 The ultrasonic monitoring system includes:

[0291] The controller includes the calibration device 60 for the Doppler ultrasound probe described in Embodiment 2;

[0292] The ultrasonic probe described in Example 3.

[0293] Without limitation, the controller is the brain of the entire system, integrating a "Doppler ultrasound probe calibration device" as described in detail in Embodiment 2. The core function of this calibration device 60 is to perform a complete, high-precision angle calibration process. Specifically, it is capable of:

[0294] During the probe manufacturing stage, the initial Doppler angle data of each crystal obtained through A-mode calibration is read and processed.

[0295] During clinical use, it receives multiple signals (including transmitted signals and at least two received signals) from the ultrasound probe in real time.

[0296] Based on the basic angle information stored in the probe chip and combined with the received signal characteristics, the actual Doppler angle between the blood vessel and the sound beam is dynamically calculated and corrected.

[0297] Finally, the calibrated precise angle is used to calculate blood flow velocity, thereby outputting highly accurate hemodynamic parameters.

[0298] The ultrasonic probe employs the specific structure described in Example 3. Its key features include a rigid housing 21 with a triangular stepped structure. Three ultrasonic crystals (a central transmitting crystal 22 and two lateral receiving crystals 23) are fixed to this step in a parallel or non-parallel manner, forming a preset fixed angle (e.g., preferably 30°) with the surface of the rigid housing. This probe design not only simplifies the manufacturing process but also provides the necessary hardware foundation for realizing the aforementioned high-precision calibration method.

[0299] System Workflow Summary: When the operator places the ultrasound probe on the patient's skin for testing, the probe sends the individualized calibration parameters (i.e., the actual angles of each crystal element) recorded in its built-in storage chip to the controller. The calibration device within the controller then activates, using the real-time ultrasound signal returned by the probe to execute a secondary calibration algorithm. This eliminates the cumulative errors caused by probe manufacturing tolerances and acoustic refraction, ultimately ensuring the reliability of blood flow velocity measurement results. This system tightly integrates a dedicated probe with an intelligent calibration algorithm, achieving an integrated solution from hardware to software.

[0300] The description of the ultrasonic monitoring system embodiments above is similar to the description of the method 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 method embodiments in this application for understanding.

[0301] 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.

[0302] 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.

[0303] 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.

[0304] 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."

[0305] 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, “a plurality” may be two or more.

[0306] In some embodiments, the terms “at least one,” “one or more,” “multiple,” etc., can be used interchangeably.

[0307] 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.

[0308] 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.

[0309] 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.

[0310] 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.

[0311] 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.

[0312] 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.

[0313] 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.

[0314] 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.

[0315] 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.

[0316] 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.

[0317] 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.

[0318] 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.

[0319] 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 calibration method for a Doppler ultrasound probe, characterized in that, The method is applied to an ultrasonic monitoring system, the ultrasonic monitoring system including an ultrasonic probe, the ultrasonic probe including a transmitting chip and a receiving chip; the method includes: The transmitting chip is controlled to emit ultrasonic pulses toward the simulated human body model; The receiving chip receives the echo signal returned from the simulated human body model and obtains the propagation time of the echo signal relative to the transmission time. Based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to the receiving chip is determined, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship; The initial Doppler angle of the determined chip is stored.

2. The calibration method for a Doppler ultrasound probe according to claim 1, characterized in that, The ultrasonic probe includes one transmitting chip and at least two receiving chips, both of which are inclined relative to the bottom surface of the probe's housing; the method includes: The transmitting chip is controlled to emit ultrasonic pulses toward the simulated human body model along a single fixed direction, and the simulated human body model is equipped with a reflective target of known depth; The receiver chip receives the echo signals returning from the reflecting target along the single fixed direction, and obtains the propagation time of each echo signal relative to the transmission time. Based on the propagation time, the known depth of the reflecting target, and the speed of sound in the simulated human body model, the initial Doppler angle corresponding to each receiving chip is determined; The initial Doppler angles of each crystal element are determined and stored in the memory of the ultrasonic probe.

3. The calibration method for a Doppler ultrasound probe as described in claim 2, characterized in that, The step of determining the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model includes: The initial Doppler angle is calculated using the following expression: θ = arcsin(H / (c*t / 2)); Wherein, θ is the initial Doppler angle, H is the known depth of the reflecting target, c is the speed of sound in the simulated human body model, and t is the propagation time of the echo signal.

4. The calibration method for a Doppler ultrasound probe as described in claim 2, characterized in that, The simulated human body model contains multiple reflective targets at different depths, and the method further includes: The transmission, reception, and calculation steps are repeatedly performed on multiple reflective targets at different depths to obtain the Doppler angle of each crystal at different depths; Data fitting is performed on multiple Doppler angles for each crystal to obtain the initial Doppler angle of the crystal.

5. The calibration method for a Doppler ultrasound probe as described in claim 1 or 2, characterized in that, Before storing the determined initial Doppler angle of the wafer, the method further includes: Determine whether the determined initial Doppler angle is within the preset acceptable range; If so, then perform the storage step; If not, mark the probe as defective.

6. The calibration method for a Doppler ultrasound probe as described in claim 1 or 2, characterized in that, After storing the determined initial Doppler angle of the wafer, the method further includes: The transmitting chip is controlled to emit ultrasound waves toward the blood vessel to be tested, and the receiving chip synchronously receives the Doppler echo signal reflected by the blood flow. Based on the initial Doppler angle and the frequency shift information of the Doppler echo signal received by the receiving chip, the actual Doppler angle between the blood vessel to be tested and the ultrasound probe is determined.

7. The calibration method for a Doppler ultrasound probe as described in claim 6, characterized in that, After determining the actual Doppler angle between the blood vessel to be tested and the ultrasound probe, the method further includes: Based on the actual Doppler angle, the blood flow velocity measured by the Doppler effect is corrected to obtain the corrected blood flow velocity.

8. The calibration method for a Doppler ultrasound probe as described in claim 7, characterized in that, The method further includes: Based on the amplitude fluctuation range of the Doppler echo signal, determine whether it is necessary to re-execute the step of determining the actual Doppler angle.

9. The calibration method for a Doppler ultrasound probe as described in claim 4, characterized in that, The data fitting of multiple Doppler angles for each crystal includes: The least squares method is used to perform linear or nonlinear regression on the Doppler angle data points at multiple depths to eliminate random errors from a single measurement and obtain the initial Doppler angle of the wafer.

10. The calibration method for a Doppler ultrasound probe as described in claim 1 or 2, characterized in that, The simulated human body model contains at least two reflective targets that are spaced apart horizontally and have the same depth. The method further includes: performing a complete transmission, reception and calculation step for each reflecting target to obtain two independent initial Doppler angles; Compare the difference between the two initial Doppler angles. If the difference is less than a preset threshold, the calibration result is confirmed to be valid.

11. A calibration device for a Doppler ultrasonic probe, characterized in that, The device is applied to an ultrasonic monitoring system, which includes an ultrasonic probe, the ultrasonic probe including a transmitting chip and a receiving chip; the device includes: The control module is used to control the transmitting chip to emit ultrasonic pulses toward the simulated human body model; The acquisition module is used to receive the echo signal returned from the simulated human body model through the receiving chip, and to acquire the propagation time of the echo signal relative to the transmission time. The determining module is used to determine the initial Doppler angle corresponding to the receiving chip based on the propagation time, the simulated human body model, and the speed of sound in the simulated human body model, wherein the initial Doppler angle is derived by back-calculation through a one-dimensional depth-time relationship; The storage module is used to store the initial Doppler angle of the determined wafer.

12. An ultrasonic probe, characterized in that, include: The outer shell is made of a hard or soft material; the outer shell has a receiving cavity and is provided with a storage seat; A chip assembly includes one transmitting chip and at least two receiving chips. The chip assembly is located in a storage seat of the accommodating cavity. The chip assembly is positioned such that the transmitting or receiving surfaces of each chip are inclined relative to the bottom surface of the housing through a preset position of the storage seat. The inclination angle is 10° to 60°. The memory is used to store the initial Doppler angles of each chip.

13. A computing device, 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 calibration method program for the Doppler ultrasound probe; The communication bus is used to enable communication between the storage component and the processing component; The processing unit is used to execute a calibration method procedure for a Doppler ultrasound probe to implement the steps of the method as described in any one of claims 1 to 10.

14. An ultrasonic monitoring system, characterized in that, include: The controller includes the calibration device for the Doppler ultrasound probe as described in claim 11; The ultrasonic probe according to claim 12.

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