Detection analysis method and system of ultrasonic Doppler blood flow detector

Abstract

The invention belongs to the technical field of blood flow detection, and particularly relates to a detection analysis method and system of an ultrasonic Doppler blood flow detector. A pressure sensor and a coupling agent detection terminal are arranged on an ultrasonic probe, so that the contact pressure between the probe and the skin and the thickness of a coupling agent can be collected in real time in the blood flow detection process; meanwhile, image quality parameters are extracted from the blood flow ultrasonic image, the contact pressure of the probe and the use amount of the coupling agent are dynamically adjusted according to the parameters, fine control over the blood flow detection process is achieved, and the stability and high quality of the ultrasonic image are ensured; in addition, the effective blood flow velocity is extracted from the blood flow ultrasonic image on the basis of accurately controlling the contact pressure of the probe and the thickness of the coupling agent and is combined with the physiological indexes to identify the abnormal blood flow velocity, so that the quality of the ultrasonic image is guaranteed, the accuracy of the blood flow detection result can be further evaluated, and the accuracy of the blood flow detection result is improved. And abnormal conditions can be found and identified in time.

Description

Technical Field

[0001] The invention belongs to the technical field of blood flow detection, and in particular relates to a detection and analysis method and system of an ultrasonic Doppler blood flow detector. Background Art

[0002] With the rapid development of the economy, people's living standards have significantly improved, and the dietary structure has gradually shifted towards high-calorie, high-fat and high-sugar foods. At the same time, the shift in modern work patterns has led to more and more people engaging in sedentary occupations, with significantly less physical activity. These changes in lifestyle have invisibly increased the incidence of cardiovascular diseases. As the incidence of cardiovascular diseases continues to rise, blood flow testing, as a basic diagnostic tool, is also being used more and more frequently.

[0003] With its advantages of non-invasiveness, real-time and high precision, ultrasonic Doppler has become a widely used technical means in current blood flow detection. However, despite the excellent performance of this technology in clinical applications, some existing technical solutions still have certain limitations, especially in ensuring image quality and measurement accuracy. For example, China's invention patent publication number CN103330575A proposes a blood flow detection device based on ultrasonic detection. The device integrates an angle sensor on the ultrasonic probe, which can detect the detection angle of the probe and emit ultrasonic waves according to different angles to preliminarily determine the optimal detection angle of human blood vessels. This design aims to improve the clarity of ultrasonic images by optimizing the detection angle, thereby improving the effect of blood flow detection. Although the introduction of the angle sensor does improve the image quality to a certain extent, its impact on the overall image quality is limited. In fact, the quality of ultrasonic images depends not only on the detection angle, but also on the contact pressure between the probe and the skin and the thickness of the coupling agent. Therefore, it is difficult to ensure stable high-quality images by simply relying on angle adjustment, which may affect the accuracy of blood flow velocity measurement and cannot provide reliable support for clinical diagnosis.

[0004] Another Chinese invention patent with publication number CN114848015A discloses a noise-reducing and anti-interference ultrasonic transcranial Doppler blood flow analyzer, which mainly includes a host and a probe, wherein the probe includes an outer cover, an ultrasonic transmitter is fixed at one end of the outer cover, and is electrically connected to the host through a wire, and an elastic and retractable suction mechanism is installed at the other end of the outer cover. During the detection process, the suction mechanism can automatically absorb the coupling agent as the probe moves, ensuring that the contact surface between the probe and the skin is always filled with coupling agent, preventing air from entering, and reducing the attenuation and interference of the ultrasonic signal. However, although this solution performs well in coupling agent management, it ignores the complex effects of physiological indicators (such as blood pressure, heart rate, respiratory rate, etc.) on blood flow rate. The blood flow of the human body is a dynamic process that is comprehensively regulated by multiple physiological factors. These physiological indicators are not only the power source of blood flow, but also directly affect the speed and pattern of blood flow. When these factors are not considered during the detection process, it may lead to underestimation or overestimation of the actual blood flow situation, thereby causing deviations in the measurement results. This deviation not only affects the accuracy of diagnosis, but also may mislead clinical decisions. Summary of the invention

[0005] The purpose of the present invention is to improve the deficiencies in the prior art and to provide a detection and analysis method and system for an ultrasonic Doppler blood flow detector to optimize blood flow detection control and detection result evaluation.

[0006] The purpose of the present invention can be achieved through the following technical solutions: The first aspect of the present invention provides a detection and analysis method of an ultrasonic Doppler blood flow detector, comprising the following steps: S1, selecting an adapter probe based on the patient's measured part, wherein the probe is equipped with a pressure sensor and a coupling agent detection terminal, and at the same time determining the detection angle between the probe and the skin of the measured part.

[0007] S2. Apply coupling agent evenly on the selected adapter probe, and place the probe on the tested part according to the determined detection angle to perform blood flow detection and generate a blood flow ultrasound image.

[0008] S3. During the blood flow detection process at the tested part, the probe contact pressure and coupling agent thickness are collected in real time through the integrated pressure sensor and coupling agent detection terminal, and image quality parameters, including signal-to-noise ratio and resolution, are extracted from the generated blood flow ultrasound image.

[0009] S4. Control the probe contact pressure and coupling agent thickness according to the image quality parameters.

[0010] S5. Real-time detection of the patient's physiological indicators during the blood flow detection process at the tested site.

[0011] S6. Under the control of the probe contact pressure and the coupling agent thickness, the effective blood flow velocity is extracted from the blood flow ultrasound image, and combined with the physiological indexes to identify abnormal blood flow velocity.

[0012] The second aspect of the present invention proposes a detection and analysis system for an ultrasonic Doppler blood flow detector, comprising the following modules: an ultrasonic probe selection module, for selecting an adapter probe based on the patient's measured part, wherein the probe is integrated with a pressure sensor and a coupling agent thickness detection terminal, and the detection angle between the probe and the skin of the measured part is determined at the same time.

[0013] The blood flow detection implementation module is used to evenly apply coupling agent on the selected adapter probe, and place the probe on the tested part according to the determined detection angle to perform blood flow detection and generate a blood flow ultrasound image.

[0014] The blood flow detection parameter acquisition module is used to collect the probe contact pressure and coupling agent thickness in real time through the integrated pressure sensor and coupling agent detection terminal during the blood flow detection process at the tested part, and to extract image quality parameters from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution.

[0015] The blood flow detection control module is used to control the probe contact pressure and coupling agent thickness according to the image quality parameters.

[0016] Inspection reference library for storing suitable couplant thickness ranges.

[0017] The physiological index detection module is used to detect the patient's physiological indexes in real time during the blood flow detection process of the tested part.

[0018] The abnormal detection, evaluation and identification module is used to extract the effective blood flow velocity from the blood flow ultrasound image under the control of the probe contact pressure and the coupling agent thickness, and combine it with the physiological indexes to identify the abnormal blood flow velocity.

[0019] In combination with all the above-mentioned technical solutions, the positive effects of the present invention are as follows: 1. By configuring a pressure sensor and a coupling agent detection terminal on the ultrasonic probe, the present invention can collect the contact pressure between the probe and the skin and the coupling agent thickness in real time during the blood flow detection process, and extract image quality parameters from the generated blood flow ultrasound image, and dynamically adjust the contact pressure of the probe and the amount of coupling agent used according to these parameters, thereby realizing refined control of the blood flow detection process and ensuring the stability and high quality of the ultrasonic image, which not only improves the accuracy of blood flow velocity measurement, but also reduces the risk of misdiagnosis or missed diagnosis due to image quality problems.

[0020] 2. The present invention monitors the patient's physiological indicators in real time during the blood flow detection process, and extracts the effective blood flow velocity from the blood flow ultrasound image based on the precise control of the probe contact pressure and the thickness of the coupling agent, and combines it with the physiological indicators to identify abnormal blood flow velocity. This operation not only ensures the quality of the ultrasonic image, but also can further evaluate the accuracy of the blood flow detection results, timely discover and identify abnormal situations, significantly improve the accuracy and reliability of blood flow detection, and provide a more solid foundation for clinical diagnosis and treatment. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] The present invention is further described using the accompanying drawings, but the embodiments in the accompanying drawings do not constitute any limitation to the present invention. A person skilled in the art can obtain other drawings based on the following drawings without creative work.

[0022] Figure 1 The present invention is a flowchart of the steps for implementing the method.

[0023] Figure 2 It is a schematic diagram of the Doppler effect in the present invention.

[0024] Figure 3 It is a schematic diagram of the ultrasonic Doppler blood flow probe of the present invention acting on the surface of human skin.

[0025] Figure 4 This is an implementation operation diagram of controlling the probe contact pressure and coupling agent thickness according to the image quality parameters in the present invention.

[0026] Figure 5 It is a schematic diagram of system module connection of the present invention. DETAILED DESCRIPTION

[0027] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0028] Example 1.

[0029] See also Figure 1 As shown, the present invention provides a detection and analysis method of an ultrasonic Doppler blood flow detector, comprising the following steps: S1, selecting an adapter probe based on the patient's tested part, wherein the probe is provided with a pressure sensor and a coupling agent detection terminal, and simultaneously determining the detection angle between the probe and the skin of the tested part.

[0030] It should be pointed out that the selection of adapter probes mentioned above refers to the probe type, which includes high-frequency probes and low-frequency probes. High-frequency probes are suitable for superficial blood vessels to obtain higher resolution. This is because superficial blood vessels are usually located above the subcutaneous fat layer and can be easily displayed clearly by high-frequency probes. Low-frequency probes are suitable for deep blood vessels to ensure sufficient penetration. This is because deep blood vessels are located near the muscle layer or bones, and low-frequency probes may be required to penetrate deeper tissues.

[0031] In the specific implementation of the above steps, the adapter probe is selected based on the patient's tested part in the following process: the patient's historical ultrasound examination records are retrieved from the hospital's electronic medical record system, and the ultrasound examination part is extracted from the records. For example, the ultrasound examination part can be the upper limbs, lower limbs, neck, etc., and then matched with the patient's tested part, and the successfully matched ultrasound examination records are screened out and recorded as similar ultrasound examination records.

[0032] It should be understood that similar ultrasound test records are screened out by matching the patient's tested parts because the blood vessels in different parts have different depths, and similar ultrasound test records can narrow the scope of analysis and improve the efficiency and accuracy of subsequent steps.

[0033] It should be emphasized that when retrieving historical ultrasonic test records, the time span of the retrieval period should be considered to ensure that the time interval between the selected historical ultrasonic test records and the current test is not too long to reduce errors caused by time changes.

[0034] The patient's weight is extracted from the patient's medical information associated with similar ultrasound test records, and the patient's current weight is extracted from the medical information of the current patient's blood flow test.

[0035] Compare the patient weight corresponding to each similar ultrasound test record with the patient's current weight to evaluate the patient's weight change. The specific evaluation formula is: , where Indicates the patient weight corresponding to the same type of ultrasound test record, It represents the patient's current weight and is compared with the set allowable variation. For example, the allowable variation is 5%, thereby screening out similar ultrasound detection records whose patient weight variation is less than or equal to the allowable variation as reference ultrasound detection records.

[0036] It should be explained that the patient's weight is also taken into account when evaluating the depth of blood vessels based on the selected similar ultrasound test records, because the weight directly affects the thickness of the subcutaneous fat layer, which in turn affects the actual depth of the blood vessels. Specifically: patients with a larger body weight usually have a thicker subcutaneous fat layer, which makes the blood vessels appear deeper; while patients with a lighter body weight have a thinner subcutaneous fat layer and the blood vessels are relatively superficial. Therefore, the blood vessel depth of obese patients is often greater than that of thin patients. In addition, the patient's weight changes dynamically, and the weight in the historical ultrasound test records may be significantly different from the current weight. If the weight in the historical record is significantly different from the current weight, the blood vessel depth evaluated based on the historical record may no longer be accurate. For example, weight gain may cause the subcutaneous fat layer to thicken, making the blood vessels appear deeper; conversely, weight loss may make the blood vessels appear shallower. Therefore, in order to ensure the accuracy of the blood vessel depth assessment and avoid historical data deviations caused by weight changes, it is necessary to conduct a secondary screening of the selected similar ultrasound test records.

[0037] The blood vessel depth is estimated from the ultrasound detection image displayed by the reference ultrasound detection record. Specifically, the blood vessel depth can generally be displayed in the ultrasound detection image.

[0038] The appropriate probe is selected according to the blood vessel depth of the measured part. Specifically, a high-frequency probe is selected when the blood vessel depth is shallow, and a low-frequency probe is selected when the blood vessel depth is deep.

[0039] In an improved implementation of the above steps, when similar ultrasound detection records or reference ultrasound detection records are not screened out, anatomical landmarks are determined near the measured part of the patient, thereby evaluating the blood vessel depth of the measured part.

[0040] It should be added that anatomical landmarks (such as bony structures, muscles, ligaments, etc.) are fixed reference points in the human anatomy. They are universally applicable and stable, and can provide operators with reliable positioning basis. By determining these landmarks, the position and depth of blood vessels can be quickly and accurately found through palpation. The main reason is that most blood vessels follow relatively fixed anatomical paths in the human body, which are usually closely related to anatomical landmarks such as bones, muscles, and ligaments. For example, the brachial artery descends along the medial side of the humerus, and the femoral artery runs along the medial side of the femur. After determining these bony landmarks, the palpation operator can directly perceive the morphology and position of the anatomical landmarks, and then infer the position and depth of the blood vessels. When palpating specifically, the operator can distinguish blood vessels from other tissues based on different tissue textures and elasticity. For example, blood vessels usually have a certain elasticity and pulsation, while bones are hard and muscles are soft and have a certain tension. Through these tactile feedback, the operator can more accurately identify the position and depth of blood vessels.

[0041] The present invention directly relies on anatomical landmarks for positioning in the absence of historical data of ultrasonic detection of the tested part, which can reduce the time of blindly searching for blood vessels and improve detection efficiency.

[0042] The anatomical landmarks determined in the above can be selected according to the different parts of the body to be tested. For example, the anatomical landmarks of the upper limbs are the humerus, radius, ulna, etc. The anatomical landmarks of the lower limbs are the femur, tibia, fibula, etc. The anatomical landmarks of the neck are: trachea, esophagus, cervical vertebrae, etc.

[0043] In another implementation of the above steps, a pressure sensor and a coupling agent detection terminal are integrated on the probe, wherein the pressure sensor is used to collect the contact pressure between the probe and the tested part, and the coupling agent detection terminal is used to collect the coating thickness of the coupling agent. In the example, the coupling agent detection terminal can be an infrared sensor, which specifically uses the reflection characteristics of infrared light to measure the reflection intensity of the coupling agent surface, thereby inferring the thickness of the coupling agent. In another example, the coupling agent detection terminal can be a capacitive sensor, and by arranging multiple capacitive sensors on the probe surface to form a sensor array, the coupling agent thickness distribution of the entire probe area can be monitored in real time.

[0044] It should be added that see Figure 2 As shown in the figure, the principle of ultrasonic Doppler blood flow detection is as follows: the probe transmits ultrasonic waves to the human body at the tested part, the red blood cells in the blood receive the ultrasonic waves and generate a certain amount of ultrasonic waves on the surface of the red blood cells. The ultrasonic probe receives the ultrasonic waves reflected by the blood flow, converts them into electrical signals to obtain blood flow signals, and then uses a frequency / voltage converter to convert the blood flow signals. Finally, the blood flow waveform is displayed on the display screen. The blood flow velocity in the blood vessel can be calculated by measuring the frequency difference between the reflected wave and the transmitted wave. This frequency difference is proportional to the blood flow velocity, but it is also related to the ultrasonic incident angle. When the detection angle between the probe and the skin is too large or too small, it may cause reflection, refraction or attenuation of the ultrasonic signal, affecting the signal quality. For example, if the angle is too large, the ultrasonic wave may be reflected back to the probe more instead of entering the blood vessel; if the angle is too small, the ultrasonic wave may be blocked by bones or other tissues, resulting in signal weakening. Therefore, before blood flow detection, it is necessary to determine the detection angle between the probe and the skin of the tested part. In actual operation, the best detection angle usually depends on the specific detection part and the direction of the blood vessel. See Figure 3 As shown, in general, it is recommended to keep the detection angle between the probe and the skin of the tested area at about 60°. If a more precise detection angle is required, an angle sensor can be integrated on the ultrasonic probe to detect the detection angle of the probe and emit ultrasonic waves according to different angles, and then determine the detection angle by observing the ultrasonic image.

[0045] S2. Apply coupling agent evenly on the selected adapter probe, and place the probe on the tested part according to the determined detection angle, thereby performing blood flow detection on the tested part to form a blood flow ultrasound image.

[0046] It is important to know that the reason for evenly applying coupling agent on the probe is that air is a very poor sound wave transmission medium, and the propagation speed of ultrasound in air is much lower than that in tissue. If there is an air layer between the probe and the skin, ultrasound will be strongly reflected and refracted at the interface between air and tissue, causing most of the energy to be reflected back to the probe and unable to effectively enter the human tissue, thus affecting the test results. The coupling agent is a liquid or gel with good acoustic impedance matching characteristics that can fill the tiny gap between the probe and the skin and eliminate the interference of the air layer. By evenly applying the coupling agent, it can ensure that ultrasound can smoothly pass through the interface between the probe and the skin and enter the human tissue, thereby improving the transmission efficiency of the signal. In addition, the coupling agent has a lubricating effect and can form a protective film between the probe and the skin, reducing the friction between the probe and the skin, preventing the probe surface from being worn, and extending the service life of the probe.

[0047] S3. During the blood flow detection process at the tested part, the probe contact pressure and coupling agent thickness are collected in real time through the integrated pressure sensor and coupling agent detection terminal, and image quality parameters, including signal-to-noise ratio and resolution, are extracted from the generated blood flow ultrasound image.

[0048] It should be understood that the signal-to-noise ratio and resolution are selected as the image quality parameters of blood flow ultrasound images because the signal-to-noise ratio reflects the noise level of the image and the resolution reflects the detail clarity of the image. When the probe contact pressure is inappropriate or the coupling agent thickness is inappropriate, it may cause reflection, refraction or attenuation of the ultrasonic signal, which may introduce additional noise and reduce the resolution and signal-to-noise ratio of the image. Therefore, when the probe contact pressure and the coupling agent thickness are inappropriate, it will directly affect the noise level and clarity of the ultrasound image.

[0049] S4. See Figure 4 As shown, the probe contact pressure and coupling agent thickness are controlled according to the image quality parameters, and the specific implementation is as follows: (1) The signal-to-noise ratio and resolution are extracted from the image quality parameters according to the acquisition interval setting of the image quality parameters, and compared with the set standard image quality parameters.

[0050] The above-mentioned qualified image quality parameters can be obtained from the instructions for use of the ultrasound equipment according to its specifications and models.

[0051] (21) If the signal-to-noise ratio extracted at a certain moment is lower than the qualified signal-to-noise ratio but the resolution reaches the qualified resolution, it means that the blood flow ultrasound image at that moment has more noise and a stronger background signal, but the boundaries of blood vessels and other structures are relatively clear. It is very likely that the air gap is large due to the excessive thinness of the coupling agent, and the ultrasonic wave is reflected and scattered during the transmission process, resulting in air artifacts and increasing the background noise. At this time, the appropriate coupling agent thickness range is extracted from the detection reference library, and the coupling agent thickness collected at that moment is compared with the lower limit coupling agent thickness in the appropriate coupling agent thickness range. If the coupling agent thickness does not reach the lower limit coupling agent thickness, execute (31), otherwise execute (51).

[0052] The above mentioned suitable coupling agent thickness range can be obtained from the instruction manual of the ultrasonic equipment, because most ultrasonic equipment manufacturers will provide a recommended coupling agent thickness range based on their probe design and operating frequency.

[0053] (31) A control prompt is issued that the coupling agent is too thin, and the signal-to-noise ratio and coupling agent thickness of the blood flow ultrasound image are continuously collected during the coupling agent addition process. If the coupling agent thickness is within the appropriate coupling agent thickness range at a certain moment and the signal-to-noise ratio of the blood flow ultrasound image reaches the standard signal-to-noise ratio, then (41) is executed. If the coupling agent thickness reaches the upper limit coupling agent thickness at a certain moment but the signal-to-noise ratio of the blood flow ultrasound image still does not reach the standard signal-to-noise ratio, the coupling agent addition has reached the upper limit at this time, and continued addition will cause the coupling agent to be too thick. Therefore, coupling agent cannot be added at this time. Contact pressure control can be used to assist, specifically by increasing the probe contact pressure to reduce the air gap and ensure the effective transmission of ultrasound waves, and then (51) is executed.

[0054] (41) Issue a control prompt to stop adding coupling agent.

[0055] (51) A control prompt to increase the probe contact pressure is issued to control the probe contact pressure.

[0056] (22) If the signal-to-noise ratio extracted at a certain moment reaches the target signal-to-noise ratio but the resolution is lower than the target resolution, it means that the background noise of the blood flow ultrasound image at that moment is less, but the boundaries of blood vessels and other structures are blurred, and small details cannot be clearly displayed. It is very likely that the ultrasonic penetration is weakened due to the excessive thickness of the coupling agent, which affects the resolution of the image. At this time, the appropriate coupling agent thickness range is extracted from the detection reference library, and the coupling agent thickness collected at that moment is compared with the upper limit coupling agent thickness in the appropriate coupling agent thickness range. If the coupling agent thickness reaches the upper limit coupling agent thickness, execute (32), otherwise execute (52).

[0057] (32) A control prompt is issued that the coupling agent is too thick, and the resolution and coupling agent thickness of the blood flow ultrasound image are continued to be collected during the coupling agent reduction process. If the coupling agent thickness is within the appropriate coupling agent thickness range at a certain moment and the resolution of the blood flow ultrasound image reaches the standard resolution, then execute (42). If the coupling agent thickness reaches the lower limit coupling agent thickness at a certain moment but the resolution of the blood flow ultrasound image still does not reach the standard resolution, the reduction of the coupling agent has reached the lower limit at this time, and further reduction will cause the coupling agent to be too thin. Therefore, the amount of coupling agent cannot be reduced at this time, but it can be assisted by contact pressure control, specifically by reducing the pressure of the probe, ensuring the penetration of ultrasound, and improving the resolution of the image, and then execute (52).

[0058] (42) A control prompt is issued to stop reducing the coupling agent.

[0059] (52) A control prompt to reduce the probe contact pressure is issued to perform probe contact pressure control.

[0060] It should be understood that when the quality of blood flow ultrasound images does not meet the standards and the thickness of the coupling agent and the contact pressure of the probe need to be controlled, the thickness of the coupling agent should be controlled first. The reason is that the coupling agent is the medium for the transmission of ultrasound from the probe to the skin and tissue, and its thickness directly affects the transmission effect of ultrasound. If the coupling agent is too thin or too thick, the image quality will be reduced. Therefore, the thickness of the coupling agent is a basic condition that affects the image quality and needs to be controlled first. If the coupling agent is too thin, the air gap will be larger, the background noise will increase, and the signal-to-noise ratio will be reduced; if the coupling agent is too thick, the penetration of ultrasound will be weakened, resulting in image distortion and reduced image resolution. The contact pressure of the probe mainly affects the contact between the probe and the skin, which in turn affects the transmission effect of ultrasound. Appropriate probe pressure can reduce the air gap and improve the signal-to-noise ratio; but if the pressure is too high, it may compress the blood vessels or over-compress the coupling agent, affecting the resolution of the image. Therefore, although the control of probe pressure is important, its influence range is relatively small and depends on the basic condition of the thickness of the coupling agent. Therefore, before adjusting the probe pressure, it is necessary to ensure that the thickness of the coupling agent is already in an appropriate range. Only when the thickness of the coupling agent is appropriate can the adjustment of the probe pressure be fully effective. If the couplant thickness is not appropriate, image quality may not be significantly improved even if the transducer pressure is adjusted.

[0061] In the improved implementation of the above scheme, if the signal-to-noise ratio extracted at a certain moment does not reach the standard signal-to-noise ratio and the resolution is lower than the standard resolution, the coupling agent thickness collected at that moment is compared with the appropriate coupling agent thickness range. If the collected coupling agent thickness is within the appropriate coupling agent thickness range, the ultrasonic wave is controlled to increase the gain, otherwise the coupling agent thickness is controlled.

[0062] It should be understood that if the coupling agent thickness is already within the appropriate range but the signal-to-noise ratio and resolution are still low, it may be due to insufficient signal strength or high background noise. At this time, the received echo signal strength can be increased by increasing the gain, thereby improving the signal-to-noise ratio. In ultrasonic testing, gain refers to the degree of amplification of the received ultrasonic signal strength. The main function of the gain is to adjust the system's amplification of the received weak ultrasonic signal so that these signals can be displayed more clearly in the image or data. In addition, when increasing the gain, the gain needs to be increased gradually. Do not adjust the gain too high at one time, but increase it gradually. Observe the changes in the image after each increase to ensure that the increase in gain does not introduce too much noise or artifacts.

[0063] As the probe contact pressure control mentioned in the above scheme, the specific implementation is as follows: when performing the probe contact pressure control, a probe contact pressure time series before the contact pressure control is constructed, and the time series reflects the change of the probe contact pressure over time, and the probe contact pressure time series is used to calculate the standard deviation, wherein the standard deviation reflects the degree of fluctuation of the contact pressure before it is not controlled, and then the single allowable pressure control change is determined in combination with the standard deviation, and the specific determination formula is: , where represents the standard deviation of the probe contact pressure time series, Represents the adjustment factor.

[0064] It should be added that the single allowable pressure control change refers to the maximum allowable change each time the probe pressure is adjusted. The single allowable pressure control change analysis is performed to avoid excessive pressure fluctuations during contact pressure control that have a negative impact on image quality.

[0065] It is further necessary to add that the adjustment coefficient is actually the adjustment of the standard deviation of the contact pressure, and its value range can be from 0 to 1, which is determined by the sensitivity of the ultrasound device. For highly sensitive ultrasound devices, they are very sensitive to pressure changes, and even small pressure fluctuations may cause significant changes in image quality. For such devices, it is recommended to choose a smaller adjustment coefficient. On the contrary, some low-end or old ultrasound devices are less sensitive to pressure changes, and large pressure changes may not immediately affect image quality. Therefore, for such devices, a larger adjustment coefficient can be selected.

[0066] The pressure value before contact pressure control is extracted from the probe contact pressure time series. This pressure value reflects the current probe contact pressure level. The first required pressure control value is calculated in combination with the single allowable pressure control change. The calculation formula for the first required pressure control value is: , where Indicates the current demand pressure control value, Indicates the pressure value before contact pressure control.

[0067] It should be pointed out that when increasing the probe contact pressure, the calculation formula for the first required pressure control value is: When the probe contact pressure is reduced, the first required pressure control value is calculated as follows: .

[0068] The probe contact pressure is controlled according to the initial required pressure control value, and the image quality parameters of the blood flow ultrasound image are recollected after the control, and compared with the qualified image quality parameters. If the image quality parameters of the blood flow ultrasound image still do not meet the qualified image quality parameters after the initial contact pressure control, the probe contact pressure is controlled again on the basis of the initial contact pressure control until the image quality parameters of the blood flow ultrasound image after the contact pressure control meet the qualified image quality parameters.

[0069] When the probe contact pressure is controlled, the present invention determines the single allowable pressure change by analyzing the probe contact pressure time series before the contact pressure control, thereby realizing the gradual adjustment of the contact pressure. This step-by-step control method ensures that the amplitude of each pressure adjustment is moderate, avoiding unnecessary pressure or damage to the patient. Through multiple fine-tuning, the image quality parameters that meet the standards are gradually approached, and the quality of the ultrasound image can be optimized more stably.

[0070] S5. During the blood flow detection process at the tested site, the patient's physiological indicators are detected in real time, including blood pressure, heart rate, left ventricular load (SPTI), myocardial perfusion (DPTI), cardiac index (SEVR), central pressure (SBP2) and augmentation index (AI), etc. These physiological indicators can be recorded synchronously through other monitoring equipment (such as ECG monitor, sphygmomanometer, pulse oximeter, etc.).

[0071] S6. Under the control of the probe contact pressure and the coupling agent thickness, the effective blood flow velocity is extracted from the blood flow ultrasound image, and combined with the physiological indexes to identify abnormal blood flow velocity.

[0072] Preferably, the effective blood flow velocity is extracted as follows: the image quality parameters of the blood flow ultrasound image are compared with the standard image quality parameters in real time during the process of controlling the coupling agent thickness and the probe contact pressure; if the image quality parameters of the blood flow ultrasound image at a certain moment meet the standard image quality parameters, the blood flow velocity is read from the blood flow ultrasound image at that moment as the effective blood flow velocity.

[0073] Further preferably, the abnormal blood flow velocity is identified in combination with the physiological index by referring to the following process: the reading time of the effective blood flow velocity is recorded as the effective detection time, and then the physiological index of the effective detection time is extracted.

[0074] In a coordinate system constructed with the detection time as the horizontal axis and the blood flow velocity as the vertical axis, the effective blood flow velocity at the effective detection time is fitted to form a blood flow velocity variation curve.

[0075] It should be noted that during the fitting process, the fitting model should be selected according to the distribution characteristics of the data points, such as linear regression, polynomial fitting, spline interpolation, etc.

[0076] Similarly, the physiological index change curve is formed by fitting the physiological index at the effective detection time in a coordinate system constructed with the detection time as the horizontal axis and the physiological index as the vertical axis.

[0077] The inflection points of the blood flow velocity change curve and the physiological index change curve are captured respectively, thereby dividing the change curve into a change segment and a non-change segment, wherein the change segment refers to a curve segment where the curve changes, and the non-change segment refers to a curve segment where the curve remains stable.

[0078] The changing segments divided by the blood flow velocity change curve and the changing segments and non-changing segments divided by the physiological index change curve are evaluated for correlation. If it is judged that there is no correlation between a changing segment or a non-changing segment in the blood flow velocity change curve, the blood flow velocity data in the corresponding segment is regarded as abnormal blood flow velocity.

[0079] Specifically, the correlation judgment is as follows: when a changing segment appears in the blood flow velocity change curve, the time period corresponding to the changing segment is captured, and whether the same time period is a changing segment is obtained from the physiological indicator change curve. If the same time period is not a changing segment in any physiological indicator change curve, it is judged that there is no correlation.

[0080] Of course, the correlation judgment also includes the judgment of the non-changing segment. The specific judgment is: when a non-changing segment appears in the blood flow velocity change curve, the time period corresponding to the non-changing segment is captured, and whether the same time period is a non-changing segment is obtained from the physiological indicator change curve. If there is no non-changing segment in the same time period in any physiological indicator change curve, it is judged that there is no correlation.

[0081] It is important to understand that changes in blood flow velocity are usually closely related to changes in physiological indicators under normal circumstances. For example, increased blood pressure will cause an increase in blood flow velocity, and an increase in heart rate will also cause changes in blood flow velocity. Therefore, when the blood flow velocity changes, at least one physiological indicator should also change accordingly; conversely, when the blood flow velocity is stable, at least one physiological indicator should also remain stable. If the blood flow velocity changes within a certain period of time, but no physiological indicator changes, or when the blood flow velocity is stable, no physiological indicator remains stable, this indicates that there is no reasonable correlation between the change in blood flow velocity and the change in physiological indicators, which is usually unreasonable and may indicate abnormal blood flow velocity.

[0082] It should be emphasized that when using correlation judgment to identify abnormal blood flow velocity, it is necessary to ensure the accuracy of physiological index detection to avoid the impact of physiological index detection errors on correlation judgment.

[0083] The present invention can identify those blood flow velocity data that are inconsistent with the changes in physiological indicators by using the correlation judgment method, and mark them as potential abnormal blood flow velocity. These data may be caused by instrument errors, improper operation or other external factors, and need to be further verified or eliminated, thereby enhancing the accuracy and reliability of blood flow detection data and providing a more reliable basis for clinical diagnosis.

[0084] Example 2

[0085] Reference Figure 5 As shown, the present invention proposes a detection and analysis method system for an ultrasonic Doppler blood flow detector, comprising the following modules: an ultrasonic probe selection module, for selecting an adapter probe based on the patient's measured part, wherein the probe is integrated with a pressure sensor and a coupling agent thickness detection terminal, and the detection angle between the probe and the skin of the measured part is determined at the same time.

[0086] The blood flow detection implementation module is connected to the ultrasonic probe selection module, and is used to evenly apply the coupling agent on the selected adapter probe, and place the probe on the tested part according to the determined detection angle to perform blood flow detection and generate a blood flow ultrasonic image.

[0087] The blood flow detection parameter acquisition module is connected to the blood flow detection implementation module, and is used to collect the probe contact pressure and coupling agent thickness in real time through the integrated pressure sensor and coupling agent detection terminal during the blood flow detection process at the tested part, and to extract image quality parameters from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution.

[0088] The blood flow detection control module is connected to the blood flow detection parameter acquisition module and is used to control the probe contact pressure and coupling agent thickness according to the image quality parameters.

[0089] The detection reference library is connected to the blood flow detection control module and is used to store the appropriate coupling agent thickness range.

[0090] The physiological index detection module is used to detect the patient's physiological indexes in real time during the blood flow detection process of the tested part.

[0091] The abnormal detection, evaluation and identification module is connected to the blood flow detection control module and the physiological index detection module respectively, and is used to extract the effective blood flow velocity from the blood flow ultrasound image under the control of the probe contact pressure and the coupling agent thickness, and combine it with the physiological index to identify the abnormal blood flow velocity.

[0092] The above contents are merely examples and explanations of the structure of the present invention. The technicians in this technical field may make various modifications or additions to the specific embodiments described or replace them in a similar manner. As long as they do not deviate from the structure of the invention or exceed the scope defined by the present invention, they should all fall within the protection scope of the present invention.

Claims

1. A detection and analysis method of an ultrasonic Doppler blood flow detector, characterized in that: The following steps are involved: S1. Select an adapter probe based on the patient's tested part, where a pressure sensor and a coupling agent detection terminal are configured on the probe, and a detection angle between the probe and the skin of the tested part is determined; S2. Apply coupling agent evenly on the selected adapter probe, and place the probe at the tested part according to the determined detection angle to perform blood flow detection and generate a blood flow ultrasound image; S3, in the process of blood flow detection at the tested part, the probe contact pressure and coupling agent thickness are collected in real time through the integrated pressure sensor and coupling agent detection terminal, and image quality parameters are extracted from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution; S4, controlling the probe contact pressure and coupling agent thickness according to the image quality parameters; S5. Real-time detection of the patient's physiological indicators during the blood flow detection process at the tested site; S6. Under the control of the probe contact pressure and the coupling agent thickness, the effective blood flow velocity is extracted from the blood flow ultrasound image, and combined with the physiological indexes to identify abnormal blood flow velocity.

2. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 1, characterized in that: The process of selecting the adapter probe is as follows: Retrieving the patient's historical ultrasound test records from the hospital's electronic medical record system, extracting the ultrasound test site from the records, and then matching it with the patient's tested site, and selecting the successfully matched ultrasound test records from them and recording them as similar ultrasound test records; Extract the patient's weight from the patient's medical records associated with similar ultrasound test records, and extract the patient's current weight from the patient's medical records of blood flow tests; Compare the patient weight corresponding to each similar ultrasound test record with the patient's current weight to evaluate the patient's weight change, and compare it with the set allowable change, thereby screening out similar ultrasound test records whose patient weight change is less than or equal to the allowable change as reference ultrasound test records; The vessel depth is assessed from the ultrasound images displayed on the reference ultrasound recording; Select the appropriate probe according to the blood vessel depth of the measured area.

3. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 2, characterized in that: The selection of the adapter probe also includes the following process: When similar ultrasound test records or reference ultrasound test records are not screened out, anatomical landmarks are identified near the test site of the patient, thereby evaluating the blood vessel depth of the test site; Select the appropriate probe according to the blood vessel depth of the measured area.

4. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 1, characterized in that: The control of the probe contact pressure and the coupling agent thickness is as follows: (1) Extracting the signal-to-noise ratio and resolution from the image quality parameters according to the acquisition interval setting of the image quality parameters, and comparing them with the set target image quality parameters; (21) If the signal-to-noise ratio extracted at a certain moment is lower than the qualified signal-to-noise ratio but the resolution reaches the qualified resolution, the appropriate coupling agent thickness range is extracted from the detection reference library, and the coupling agent thickness collected at this moment is compared with the lower limit coupling agent thickness in the appropriate coupling agent thickness range. If the coupling agent thickness does not reach the lower limit coupling agent thickness, execute (31), otherwise execute (51): (31) Issue a control prompt that the coupling agent is too thin, and continue to collect the signal-to-noise ratio and coupling agent thickness of the blood flow ultrasound image during the coupling agent addition process. If the coupling agent thickness is within the appropriate coupling agent thickness range at a certain moment and the signal-to-noise ratio of the blood flow ultrasound image reaches the standard signal-to-noise ratio, execute (41); if the coupling agent thickness reaches the upper limit coupling agent thickness at a certain moment but the signal-to-noise ratio of the blood flow ultrasound image still does not reach the standard signal-to-noise ratio, execute (51); (41) Sending a control prompt to stop adding coupling agent; (51) A control prompt to increase the probe contact pressure is issued to control the probe contact pressure.

5. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 4, characterized in that: The control of the probe contact pressure and the coupling agent thickness also includes the following process: (22) If the signal-to-noise ratio extracted at a certain moment reaches the target signal-to-noise ratio but the resolution is lower than the target resolution, then the appropriate coupling agent thickness range is extracted from the detection reference library, and the coupling agent thickness collected at that moment is compared with the upper limit coupling agent thickness in the appropriate coupling agent thickness range. If the coupling agent thickness reaches the upper limit coupling agent thickness, then execute (32), otherwise execute (52): (32) issuing a control prompt that the coupling agent is too thick, and continuing to collect the resolution and coupling agent thickness of the blood flow ultrasound image during the coupling agent reduction process. If the coupling agent thickness is within the appropriate coupling agent thickness range at a certain moment and the resolution of the blood flow ultrasound image reaches the standard resolution, execute (42); if the coupling agent thickness reaches the lower limit coupling agent thickness at a certain moment but the resolution of the blood flow ultrasound image still does not reach the standard resolution, execute (52); (42) issuing a control prompt to stop reducing coupling agent; (52) A control prompt to reduce the probe contact pressure is issued to perform probe contact pressure control.

6. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 4, characterized in that: The control of the probe contact pressure and the coupling agent thickness further includes the following process: If the signal-to-noise ratio extracted at a certain moment does not reach the standard signal-to-noise ratio and the resolution is lower than the standard resolution, the coupling agent thickness collected at that moment is compared with the appropriate coupling agent thickness range. If the collected coupling agent thickness is within the appropriate coupling agent thickness range, the ultrasonic wave is controlled to increase the gain, otherwise the coupling agent thickness is controlled.

7. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 5, characterized in that: The probe contact pressure control is implemented as follows: When performing probe contact pressure control, the probe contact pressure time series before contact pressure control is constructed, and the probe contact pressure time series is used to calculate the standard deviation, and then the single allowable pressure control change is determined in combination with the standard deviation. The specific determination formula is: , where represents the standard deviation of the probe contact pressure time series, represents the adjustment factor; The pressure value before contact pressure control is extracted from the probe contact pressure time series, and the first required pressure control value is calculated in combination with the single allowable pressure control change. The calculation formula for the first required pressure control value is: , where Indicates the current demand pressure control value, Indicates the pressure value before contact pressure control; The probe contact pressure is controlled according to the initial required pressure control value, and the image quality parameters of the blood flow ultrasound image are recollected after the control, and compared with the qualified image quality parameters. If the image quality parameters of the blood flow ultrasound image still do not meet the qualified image quality parameters after the initial contact pressure control, the probe contact pressure is controlled again on the basis of the initial contact pressure control until the image quality parameters of the blood flow ultrasound image after the contact pressure control meet the qualified image quality parameters.

8. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 1, characterized in that: The effective blood flow velocity is extracted as follows: During the process of controlling the coupling agent thickness and the probe contact pressure, the image quality parameters of the blood flow ultrasound image are compared with the standard image quality parameters in real time. If the image quality parameters of the blood flow ultrasound image at a certain moment meet the standard image quality parameters, the blood flow velocity is read from the blood flow ultrasound image at that moment as the effective blood flow velocity.

9. The detection and analysis method of an ultrasonic Doppler blood flow detector as claimed in claim 1, characterized in that: The identification of abnormal blood flow velocity in combination with physiological indicators is as follows: The reading time of the effective blood flow velocity is recorded as the effective detection time, and then the physiological index of the effective detection time is extracted; In a coordinate system constructed with the detection time as the horizontal axis and the blood flow velocity as the vertical axis, a blood flow velocity variation curve is formed by fitting the effective blood flow velocity at the effective detection time; Similarly, a physiological index change curve is formed by fitting the physiological index at the effective detection time in a coordinate system constructed with the detection time as the horizontal axis and the physiological index as the vertical axis; Capturing the inflection points of the blood flow velocity change curve and the physiological index change curve respectively, thereby dividing the change curve into a change segment and a non-change segment; The changing segments divided by the blood flow velocity change curve and the changing segments and non-changing segments divided by the physiological index change curve are evaluated for correlation. If it is judged that there is no correlation between a changing segment or a non-changing segment in the blood flow velocity change curve, the blood flow velocity data in the corresponding segment is regarded as abnormal blood flow velocity.

10. A detection and analysis system for an ultrasonic Doppler blood flow detector, characterized in that: Includes the following modules: Ultrasonic probe selection module, used to select an adapter probe based on the patient's tested part, where the probe is integrated with a pressure sensor and a coupling agent thickness detection terminal, and at the same time determines the detection angle between the probe and the skin of the tested part; The blood flow detection implementation module is used to evenly apply the coupling agent on the selected adapter probe, and place the probe on the tested part according to the determined detection angle to perform blood flow detection and generate a blood flow ultrasound image; A blood flow detection parameter acquisition module is used to collect the probe contact pressure and coupling agent thickness in real time through the integrated pressure sensor and coupling agent detection terminal during the blood flow detection process at the tested part, and to extract image quality parameters from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution; A blood flow detection control module, used for controlling the probe contact pressure and coupling agent thickness according to image quality parameters; Inspection reference library, used to store the appropriate couplant thickness range; A physiological index detection module is used to detect the patient's physiological indexes in real time during the blood flow detection process at the tested part; The abnormal detection, evaluation and identification module is used to extract the effective blood flow velocity from the blood flow ultrasound image under the control of the probe contact pressure and the coupling agent thickness, and combine it with the physiological indexes to identify the abnormal blood flow velocity.

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