A detection analysis method and system of an ultrasonic Doppler blood flow detector

Abstract

This invention belongs to the field of blood flow detection technology, specifically relating to a detection and analysis method and system for an ultrasonic Doppler blood flow detector. By configuring a pressure sensor and a coupling agent detection terminal on the ultrasonic probe, the contact pressure between the probe and the skin and the coupling agent thickness can be collected in real time during blood flow detection. Simultaneously, image quality parameters are extracted from the blood flow ultrasonic images, and the contact pressure of the probe and the amount of coupling agent used are dynamically adjusted based on these parameters, achieving precise control of the blood flow detection process and ensuring the stability and high quality of the ultrasonic images. In addition, by precisely controlling the probe contact pressure and coupling agent thickness, the effective blood flow velocity is extracted from the blood flow ultrasonic images and combined with physiological indicators to identify abnormal blood flow velocities. This operation not only ensures the quality of the ultrasonic images but also allows for further accuracy evaluation of the blood flow detection results, enabling timely detection and identification of abnormalities.

Description

Technical Field

[0001] This invention belongs to the field of blood flow detection technology, specifically relating to a detection and analysis method and system for an ultrasonic Doppler blood flow detector. Background Technology

[0002] With rapid economic development and a significant improvement in living standards, people's diets are increasingly shifting towards high-calorie, high-fat, and high-sugar foods. Simultaneously, the transformation of modern work patterns has led to more and more people engaging in sedentary occupations, resulting in a marked reduction in physical activity. These lifestyle changes have inadvertently increased the incidence of cardiovascular diseases. As the incidence of cardiovascular diseases continues to rise, blood flow testing, as a fundamental diagnostic tool, is being used more frequently.

[0003] With its advantages of being non-invasive, real-time, and highly accurate, ultrasound Doppler has become a widely used technique for blood flow detection. However, despite its excellent performance in clinical applications, some existing solutions still have limitations, particularly in ensuring image quality and measurement accuracy. For example, Chinese invention patent publication number CN103330575A proposes a blood flow detection device based on ultrasound detection. This device integrates an angle sensor on the ultrasound probe to detect the probe's detection angle and emits ultrasound waves at different angles to preliminarily determine the optimal detection angle for human blood vessels. This design aims to improve the clarity of ultrasound images by optimizing the detection angle, thereby improving the effectiveness of blood flow detection. While the introduction of the angle sensor does improve image quality to some extent, its impact on overall image quality is limited. In fact, the quality of ultrasound 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, simply relying on angle adjustment cannot ensure stable, high-quality images, which may affect the accuracy of blood flow velocity measurement and fail to provide reliable support for clinical diagnosis.

[0004] Another Chinese invention patent, CN114848015A, discloses a noise-reducing and interference-resistant transcranial Doppler ultrasound blood flow analyzer, mainly comprising a main unit and a probe. The probe includes an outer casing with an ultrasonic transmitter fixed at one end and electrically connected to the main unit via a wire. The other end of the casing is equipped with an elastically telescopic suction mechanism. During the detection process, the suction mechanism automatically absorbs coupling agent as the probe moves, ensuring that the contact surface between the probe and the skin is always saturated with coupling agent, preventing air from entering and reducing the attenuation and interference of the ultrasonic signal. However, while this solution performs well in terms of coupling agent management, it neglects the complex influence of physiological indicators (such as blood pressure, heart rate, and respiratory rate) on blood flow velocity. Human blood flow is a dynamic process, comprehensively regulated by multiple physiological factors. These physiological indicators are not only the driving force of blood flow but also directly affect its speed and pattern. Failure to consider these factors during the detection process may lead to an underestimation or overestimation of the actual blood flow, resulting in measurement deviations. Such deviations not only affect the accuracy of diagnosis but may also mislead clinical decisions. Summary of the Invention

[0005] The purpose of this invention is to improve upon the shortcomings of the existing technology and provide a detection and analysis method and system for an ultrasonic Doppler blood flow detector, thereby optimizing blood flow detection control and detection result evaluation.

[0006] The objective of this invention can be achieved through the following technical solution: The first aspect of this invention provides a detection and analysis method for an ultrasound Doppler blood flow detector, comprising the following steps: S1, selecting an appropriate probe based on the patient's test site, wherein the probe is equipped with a pressure sensor and a coupling agent detection terminal, and simultaneously determining the detection angle between the probe and the skin of the test site.

[0007] S2. Apply coupling agent evenly to the selected adapter probe, and place the probe at the test site according to the determined detection angle to perform blood flow detection and generate blood flow ultrasound images.

[0008] S3. During the blood flow detection process at the test site, the probe contact pressure and coupling agent thickness are collected in real time through the integrated pressure sensor and coupling agent detection terminal. At the same time, 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 monitoring of the patient's physiological indicators during blood flow detection at the tested site.

[0011] S6. Extract the effective blood flow velocity from the blood flow ultrasound image under the control of probe contact pressure and coupling agent thickness, and combine it with physiological indicators to identify abnormal blood flow velocities.

[0012] A second aspect of the present invention provides a detection and analysis system for an ultrasound Doppler blood flow detector, comprising the following modules: an ultrasound probe selection module, used to select an appropriate probe based on the patient's test site, wherein the probe integrates a pressure sensor and a coupling agent thickness detection terminal, and simultaneously determines the detection angle between the probe and the skin of the test site.

[0013] The blood flow detection implementation module is used to evenly apply coupling agent to the selected adapter probe and place the probe at the test site according to the determined detection angle to generate blood flow ultrasound images.

[0014] The blood flow detection parameter acquisition module is used to collect probe contact pressure and coupling agent thickness in real time during blood flow detection at the test site through an integrated pressure sensor and coupling agent detection terminal. At the same time, it extracts image quality parameters from the generated blood flow ultrasound image, specifically 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 based on image quality parameters.

[0016] A reference library for storing suitable coupling agent thickness ranges.

[0017] The physiological index detection module is used to detect the patient's physiological index in real time during the blood flow detection process at the test site.

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

[0019] Combining all the above technical solutions, the positive effects of this invention are as follows: 1. By configuring a pressure sensor and a coupling agent detection terminal on the ultrasonic probe, this invention can collect the contact pressure between the probe and the skin and the thickness of the coupling agent in real time during blood flow detection. At the same time, it can 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 based on these parameters. This achieves refined control of the blood flow detection process, ensuring the stability and high quality of the ultrasound image. It 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. This invention monitors the patient's physiological indicators in real time during blood flow detection and extracts the effective blood flow velocity from the blood flow ultrasound image based on precise control of probe contact pressure and coupling agent thickness. This extracted velocity is then combined with physiological indicators to identify abnormal blood flow velocities. This operation not only ensures the quality of ultrasound images but also allows for further accuracy assessment of blood flow detection results, timely detection and identification of abnormalities, and significantly improves the accuracy and reliability of blood flow detection, providing a more solid foundation for clinical diagnosis and treatment. Attached Figure Description

[0021] The present invention will be further described with reference to the accompanying drawings, but the embodiments in the drawings do not constitute any limitation on the present invention. For those skilled in the art, other drawings can be obtained based on the following drawings without creative effort.

[0022] Figure 1 This is a flowchart illustrating the implementation steps of the method of the present invention.

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

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

[0025] Figure 4 This is an operational diagram illustrating the control of probe contact pressure and coupling agent thickness based on image quality parameters in this invention.

[0026] Figure 5 This is a schematic diagram of the system module connections of the present invention. Detailed Implementation

[0027] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0028] Example 1.

[0029] See Figure 1 As shown, the present invention provides a detection and analysis method for an ultrasound Doppler blood flow detector, including the following steps: S1, selecting an appropriate probe based on the patient's test site, wherein the probe is equipped with a pressure sensor and a coupling agent detection terminal, and simultaneously determining the detection angle between the probe and the skin of the test site.

[0030] It should be noted that the selection of the appropriate probe mentioned above refers to the type of probe. The types of probes include 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 are 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 bone and may require the use of low-frequency probes to penetrate deeper tissues.

[0031] In the specific implementation of the above steps, the process of selecting an appropriate probe based on the patient's test site is as follows: retrieve the patient's historical ultrasound examination records from the hospital's electronic medical record system, and extract the ultrasound examination site from the records. For example, the ultrasound examination site can be the upper limb, lower limb, neck, etc., and then match it with the patient's test site. Select the ultrasound examination records that match successfully and record them as similar ultrasound examination records.

[0032] It is important to understand that matching and filtering similar ultrasound records based on the patient's test site is because the depth of blood vessels varies in different sites, and similar ultrasound records can narrow down the analysis scope and improve the efficiency and accuracy of subsequent steps.

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

[0034] Extract patient weight from patient visit information associated with similar ultrasound examination records, and extract current patient weight from current patient blood flow examination visit information.

[0035] The patient's weight change is assessed by comparing the patient's weight corresponding to each similar ultrasound examination record with the patient's current weight. The specific assessment formula is as follows: In the formula This indicates the patient's weight corresponding to the same type of ultrasound examination record. The current weight of the patient is displayed and compared with the set allowable change. For example, the allowable change is 5%. This allows screening out similar ultrasound examination records where the patient's weight change is less than or equal to the allowable change as reference ultrasound examination records.

[0036] It's important to explain that patient weight was considered when assessing vascular depth based on similar ultrasound records. This is because weight directly affects the thickness of the subcutaneous fat layer, thus influencing the actual depth of the vessels. Specifically, heavier patients typically have a thicker subcutaneous fat layer, making their vessels appear deeper; conversely, lighter patients have a thinner subcutaneous fat layer, making their vessels appear relatively superficial. Therefore, obese patients often have deeper vessels than lean patients. Furthermore, patient weight is dynamic, and the weight recorded in historical ultrasound records may differ significantly from the current weight. If the historical weight differs greatly from the current weight, the vascular depth assessment based on historical records may no longer be accurate. For example, weight gain may lead to a thicker subcutaneous fat layer, making vessels appear deeper; conversely, weight loss may make vessels appear shallower. Therefore, to ensure the accuracy of vascular depth assessment and avoid historical data bias caused by weight changes, a secondary screening of similar ultrasound records is necessary.

[0037] The depth of blood vessels is assessed from ultrasound images displayed in a reference ultrasound examination record. Specifically, the depth of blood vessels can generally be displayed in ultrasound images.

[0038] Select an appropriate probe based on the depth of the blood vessels in the area being tested. Specifically, select a high-frequency probe when the blood vessels are shallow and a low-frequency probe when the blood vessels are deep.

[0039] In the improved implementation of the above steps, when no similar ultrasound examination records or reference ultrasound examination records are found, anatomical landmarks are identified near the patient's test site to assess the vascular depth at the test site.

[0040] It's important to add that anatomical landmarks (such as bony structures, muscles, and ligaments) are fixed reference points in the human anatomy, possessing universal applicability and stability. They provide reliable positioning information for the operator. By identifying these landmarks, the location and depth of blood vessels can be quickly and accurately found through palpation. This is primarily because most blood vessels in the human body follow relatively fixed anatomical paths, 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, while the femoral artery runs along the medial side of the femur. After identifying these bony landmarks, the palpation operator can directly perceive the shape and position of the anatomical landmarks, thereby inferring the location and depth of the blood vessels. During palpation, the operator can distinguish blood vessels from other tissues based on different tissue textures and elasticities. For example, blood vessels typically have a certain elasticity and pulsation, while bones are hard, and muscles are soft and have a certain tension. Through this tactile feedback, the operator can more accurately identify the location and depth of blood vessels.

[0041] This invention allows for localization directly based on anatomical landmarks when there is no historical ultrasound data of the tested area, which can reduce the time spent blindly searching for blood vessels and improve detection efficiency.

[0042] The anatomical landmarks mentioned above can be selected according to the different sites being measured. For example, the anatomical landmarks for the upper limbs are the humerus, radius, and ulna. The anatomical landmarks for the lower limbs are the femur, tibia, and fibula. The anatomical landmarks for the neck are the trachea, esophagus, and cervical vertebrae.

[0043] In another implementation of the above steps, a pressure sensor and a coupling agent detection terminal are integrated onto the probe. The pressure sensor is used to collect the contact pressure between the probe and the measured area, while the coupling agent detection terminal is used to collect the coating thickness of the coupling agent. In this example, the coupling agent detection terminal can be an infrared sensor, specifically utilizing the reflection characteristics of infrared light to measure the reflection intensity of the coupling agent surface, thereby inferring the coupling agent thickness. Alternatively, the coupling agent detection terminal can be a capacitive sensor. By arranging multiple capacitive sensors on the probe surface to form a sensor array, the coupling agent thickness distribution across the entire probe area can be monitored in real time.

[0044] It should be added that, see [link / reference] Figure 2 As shown, the principle of ultrasonic Doppler blood flow detection is as follows: The probe emits ultrasonic waves into the body at the test site. Red blood cells in the blood receive the ultrasonic waves and generate a certain amount of ultrasonic waves on their surface. The ultrasonic probe receives the ultrasonic waves reflected back by the blood flow, converts them into electrical signals to obtain blood flow signals, and then uses a frequency / voltage converter to transform the blood flow signals. Finally, the blood flow waveform is displayed on the screen. By measuring the frequency difference between the reflected wave and the emitted wave, the blood flow velocity in the blood vessel can be calculated. This frequency difference is proportional to the blood flow velocity, but it is also related to the ultrasonic wave 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, more ultrasonic waves may be reflected back to the probe instead of entering the blood vessel; if the angle is too small, the ultrasonic waves may be blocked by bones or other tissues, resulting in signal weakening. Therefore, it is necessary to determine the detection angle between the probe and the skin at the test site before blood flow detection. In practice, the optimal detection angle usually depends on the specific test site and the direction of the blood vessels. See also Figure 3 As shown, it is generally recommended to keep the detection angle between the probe and the skin of the test site at about 60°. If a more precise detection angle is required, an angle sensor can be integrated into the ultrasonic probe to detect the detection angle of the probe and emit ultrasonic waves according to different angles. The detection angle can then be determined by observing the ultrasonic image.

[0045] S2. Apply coupling agent evenly to the selected adapter probe and place the probe at the test site according to the determined detection angle to perform blood flow detection at the test site and form a blood flow ultrasound image.

[0046] It's important to understand that the reason for evenly applying coupling agent to the probe is that air is a very poor medium for sound wave transmission; the speed of ultrasound in air is much lower than its speed of propagation in tissue. If an air layer exists between the probe and the skin, the ultrasound waves will be strongly reflected and refracted at the air-tissue interface, causing most of the energy to be reflected back to the probe and unable to effectively enter the human tissue, thus affecting the detection results. Coupling agent, a liquid or gel with good acoustic impedance matching properties, can fill the tiny gaps between the probe and the skin, eliminating interference from the air layer. By evenly applying the coupling agent, it is ensured that the ultrasound waves can smoothly pass through the probe-skin interface and enter the human tissue, thereby improving signal transmission efficiency. In addition, the coupling agent has a lubricating effect, forming a protective film between the probe and the skin, reducing friction between the probe and the skin, preventing probe surface wear, and extending the probe's lifespan.

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

[0048] It is important to understand that signal-to-noise ratio (SNR) and resolution are chosen as image quality parameters for blood flow ultrasound images because SNR reflects the noise level of the image, and resolution reflects the clarity of the image details. When the probe contact pressure is improper or the coupling agent thickness is inappropriate, it may cause the ultrasound signal to be reflected, refracted, or attenuated, which may introduce additional noise and reduce the image resolution and SNR. Therefore, when the probe contact pressure and coupling agent thickness are inappropriate, it will directly affect the noise level and clarity of the ultrasound image.

[0049] S4, see also Figure 4 As shown, the probe contact pressure and coupling agent thickness are controlled according to the image quality parameters. 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 of the image quality parameters, and compared with the set compliant image quality parameters.

[0050] The above-mentioned image quality parameters can be obtained from the user manual of the ultrasound equipment according to its specifications and model.

[0051] (21) If the signal-to-noise ratio extracted at a certain moment is lower than the target signal-to-noise ratio but the resolution reaches the target resolution, it indicates that the blood flow ultrasound image at that moment has a lot of noise and a strong background signal, but the boundaries of blood vessels and other structures are relatively clear. This is most likely due to the large air gap caused by the thin coupling agent, which causes the ultrasound waves to be reflected and scattered during transmission, resulting in air artifacts and increasing the background noise. At this time, a suitable 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 suitable coupling agent thickness range. If the coupling agent thickness does not reach the lower limit coupling agent thickness, then (31) is executed; otherwise, (51) is executed.

[0052] The appropriate coupling agent thickness range mentioned above can be obtained from the instruction manual of the ultrasound equipment, as most ultrasound equipment manufacturers provide recommended coupling agent thickness ranges based on their probe design and operating frequency.

[0053] (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 and the signal-to-noise ratio of the blood flow ultrasound image reaches the standard signal-to-noise ratio at a certain moment, then execute (41). If the coupling agent thickness reaches the upper limit coupling agent thickness but the signal-to-noise ratio of the blood flow ultrasound image still does not reach the standard signal-to-noise ratio at a certain moment, the addition of coupling agent has reached the upper limit. Continuing to add coupling agent will cause the coupling agent to be too thick. Therefore, coupling agent cannot be added at this time. It can be assisted by contact pressure control. Specifically, increase the probe contact pressure to reduce the air gap and ensure the effective transmission of ultrasound waves. Execute (51).

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

[0055] (51) Issue a control prompt to increase the probe contact pressure to control the probe contact pressure.

[0056] (22) If the signal-to-noise ratio extracted at a certain moment reaches the standard signal-to-noise ratio but the resolution is lower than the standard 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. This is likely due to the weakening of ultrasound penetration caused by excessive coupling agent thickness, which affects the resolution of the image. At this time, a suitable 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 suitable coupling agent thickness range. If the coupling agent thickness reaches the upper limit coupling agent thickness, then execute (32); otherwise execute (52).

[0057] (32) Issue a control prompt that the coupling agent is too thick, and continue 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 and the resolution of the blood flow ultrasound image reaches the standard resolution at a certain moment, 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, then the reduction of coupling agent has reached the lower limit. Continuing to reduce it will cause the coupling agent to be too thin. Therefore, the amount of coupling agent cannot be reduced at this time. It can be assisted by contact pressure control. Specifically, reduce the pressure of the probe to ensure the penetration of ultrasound and improve the resolution of the image. Execute (52).

[0058] (42) Issue a control prompt to stop reducing the coupling agent.

[0059] (52) Issue a control prompt to reduce probe contact pressure to control probe contact pressure.

[0060] It's important to understand that when blood flow ultrasound image quality is substandard and control of the coupling agent thickness and probe contact pressure is necessary, prioritizing coupling agent thickness is crucial. This is because the coupling agent acts as the medium for transmitting ultrasound waves from the probe to the skin and tissue, and its thickness directly affects the transmission efficiency. Both excessively thin and excessively thick coupling agents can lead to decreased image quality. Therefore, coupling agent thickness is a fundamental factor affecting image quality and must be prioritized. Too thin a coupling agent results in a larger air gap, increasing background noise and reducing the signal-to-noise ratio; too thick a coupling agent weakens the penetration of ultrasound waves, causing image distortion and reducing image resolution. Probe contact pressure primarily affects the contact between the probe and the skin, thus influencing ultrasound transmission. Appropriate probe pressure can reduce air gaps and improve the signal-to-noise ratio; however, excessive pressure may compress blood vessels or over-compress the coupling agent, affecting image resolution. Therefore, while probe pressure control is important, its impact is relatively small and depends on the initial coupling agent thickness. Thus, before adjusting the probe pressure, it's essential to ensure the coupling agent thickness is within an appropriate range. Only when the coupling agent thickness is suitable can adjusting the probe pressure be effective. If the coupling agent thickness is not appropriate, even if the probe pressure is adjusted, the image quality may not be significantly improved.

[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's important to understand that if the coupling agent thickness is already within a suitable range but the signal-to-noise ratio and resolution are still low, it may be due to insufficient signal strength or high background noise. In this case, increasing the gain can improve the received echo signal strength, thereby improving the signal-to-noise ratio. In ultrasonic testing, gain refers to the degree to which the received ultrasonic signal intensity is amplified. The main function of gain is to adjust the amplification factor of the system for weak received ultrasonic signals, so that these signals can be displayed more clearly in the image or data. Furthermore, when increasing the gain, it should be done gradually, rather than increasing it too high all at once. Observe the image changes after each increase to ensure that the increase in gain does not introduce excessive noise or artifacts.

[0063] The probe contact pressure control mentioned in the above scheme is implemented as follows: When performing probe contact pressure control, a time series of the probe contact pressure before control is constructed. This time series reflects the change of the probe contact pressure over time. The standard deviation is calculated using this time series, where the standard deviation reflects the degree of fluctuation in the contact pressure before control. Then, the allowable pressure control change per instance is determined based on the standard deviation, using the following formula: In the formula This represents the standard deviation of the probe contact pressure time series. This represents the adjustment factor.

[0064] It should be added that the single allowable pressure control change refers to the maximum allowable change in pressure each time the probe pressure is adjusted. The purpose of analyzing the single allowable pressure control change is to avoid excessive pressure fluctuations that could negatively impact image quality when contacting the pressure control.

[0065] It's important to further clarify that the adjustment factor essentially adjusts the standard deviation of the contact pressure. Its value can range from 0 to 1, depending on the sensitivity of the ultrasound equipment. High-sensitivity ultrasound equipment is extremely sensitive to pressure changes; even small pressure fluctuations can lead to significant changes in image quality. For such equipment, a smaller adjustment factor is recommended. Conversely, some lower-end or older ultrasound equipment is less sensitive to pressure changes, and large pressure variations may not immediately affect image quality. Therefore, for these types of equipment, a larger adjustment factor can be chosen.

[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 initial required pressure control value is calculated by combining this value with the allowable pressure control change for a single test. The formula for calculating the initial required pressure control value is as follows: In the formula This indicates the current demand pressure control value. This indicates the pressure value before contact pressure control.

[0067] It should be noted that when increasing the probe contact pressure, the initial required pressure control value is calculated using the following formula: When controlling the reduction of probe contact pressure, the initial required pressure control value is calculated using the following formula: .

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

[0069] This invention, when controlling probe contact pressure, analyzes the time series of probe contact pressure before control to determine the allowable pressure change per instance, thereby achieving gradual adjustment of the contact pressure. This gradual control method ensures that each pressure adjustment is moderate, avoiding unnecessary pressure or damage to the patient. Through multiple fine-tuning steps, the system gradually approaches the target image quality parameters, allowing for more stable optimization of ultrasound image quality.

[0070] S5. During the blood flow detection at the test site, the patient's physiological indicators are monitored in real time. These physiological indicators include blood pressure, heart rate, left ventricular load (SPTI), myocardial perfusion (DPTI), cardiac index (SEVR), central pressure (SBP2), and enhancement index (AI). These physiological indicators can be recorded synchronously by other monitoring devices (such as electrocardiogram monitors, blood pressure monitors, pulse oximeters, etc.).

[0071] S6. Extract the effective blood flow velocity from the blood flow ultrasound image under the control of probe contact pressure and coupling agent thickness, and combine it with physiological indicators to identify abnormal blood flow velocities.

[0072] Preferably, the effective blood flow velocity is extracted as follows: during the process of controlling the coupling agent thickness and 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, then the blood flow velocity is read from the blood flow ultrasound image at that moment as the effective blood flow velocity.

[0073] More preferably, the identification of abnormal blood flow velocity in combination with physiological indicators is carried out as follows: the time when the effective blood flow velocity is read is recorded as the effective detection time, and then the physiological indicators of the effective detection time are extracted.

[0074] Within a coordinate system constructed with the detection time as the horizontal axis and 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.

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

[0076] Similarly, within a coordinate system constructed with the detection time as the horizontal axis and the physiological indicators as the vertical axis, physiological indicator change curves are formed by fitting physiological indicators for the effective detection time.

[0077] Inflection points were captured for the blood flow velocity change curve and the physiological index change curve, and the change curve was divided into variable segment and non-variable segment. The variable segment is the curve segment where the curve changes, and the non-variable segment is the curve segment where the curve remains stable.

[0078] The variable segments of the blood flow velocity change curve and the variable and non-variable segments of the physiological index change curve are correlated and evaluated. If it is determined that there is no correlation between a variable segment or a non-variable 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 assessment is as follows: when a variable segment appears in the blood flow velocity change curve, the time period corresponding to the variable segment is captured, and whether the same time period is a variable segment is obtained from the physiological indicator change curve. If no physiological indicator change curve has a variable segment for the same time period, then the correlation is judged to be non-correlation.

[0080] Of course, the correlation assessment also includes the assessment of the invariable segment. Specifically, the assessment is as follows: when an invariable segment appears in the blood flow velocity change curve, capture the time period corresponding to the invariable segment, and obtain whether the same time period is an invariable segment from the physiological indicator change curve. If there is no invariable segment in the same time period in any physiological indicator change curve, then the assessment is that there is no correlation.

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

[0082] It is important to emphasize that when using correlation assessment to identify abnormal blood flow velocities, it is necessary to ensure the accuracy of physiological indicator detection to avoid the impact of physiological indicator detection errors on the correlation assessment.

[0083] This invention utilizes a correlation evaluation method to identify blood flow velocity data that are inconsistent with changes in physiological indicators and marks them as potentially abnormal blood flow velocities. These data may be caused by instrument errors, improper operation, or other external factors, requiring further verification or exclusion. This enhances the accuracy and reliability of blood flow detection data, 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, used to select an appropriate probe based on the patient's test site, wherein the probe integrates a pressure sensor and a coupling agent thickness detection terminal, and simultaneously determines the detection angle between the probe and the skin of the test site.

[0086] The blood flow detection implementation module is connected to the ultrasound probe selection module. It is used to evenly apply coupling agent to the selected adapter probe and place the probe at the test site according to the determined detection angle to perform blood flow detection and generate blood flow ultrasound images.

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

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

[0089] The detection reference library, connected to the blood flow detection control module, is used to store suitable coupling agent thickness ranges.

[0090] The physiological index detection module is used to detect the patient's physiological index in real time during the blood flow detection process at the test site.

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

[0092] The above description is merely an example and illustration of the structure of the present invention. Those skilled in the art can make various modifications or additions to the specific embodiments described, or use similar methods to replace them, 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 using an ultrasonic Doppler blood flow detector, characterized in that, Includes the following steps: S1. Select an appropriate probe based on the patient's test site, wherein the probe is equipped with a pressure sensor and a coupling agent detection terminal, and at the same time determine the detection angle between the probe and the skin of the test site; S2. Apply coupling agent evenly to the selected adapter probe, and place the probe at the test site according to the determined detection angle to perform blood flow detection and generate blood flow ultrasound images. S3. During the blood flow detection process at the test site, the probe contact pressure and coupling agent thickness are collected in real time through the integrated pressure sensor and coupling agent detection terminal. At the same time, image quality parameters are extracted from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution. S4. Control the probe contact pressure and coupling agent thickness according to the image quality parameters. That is, extract the signal-to-noise ratio and resolution from the image quality parameters according to the acquisition interval of the image quality parameters, and compare them with the set compliant image quality parameters to determine whether the coupling agent thickness should be increased or decreased, or whether the probe contact pressure should be increased or decreased. S5. Real-time monitoring of the patient's physiological indicators during blood flow detection at the tested site; S6. Under the control of probe contact pressure and coupling agent thickness, extract the effective blood flow velocity from the blood flow ultrasound image, record the reading time of the effective blood flow velocity as the effective detection time and extract the physiological index at that time, fit to form blood flow velocity change curve and physiological index change curve, capture the inflection point of the curve and perform correlation evaluation to identify abnormal blood flow velocity. The effective blood flow velocity is extracted as follows: During the process of controlling the coupling agent thickness and 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. The identification of abnormal blood flow velocities in conjunction with physiological indicators is described in the following process: The effective blood flow velocity reading time is recorded as the effective detection time, and then the physiological indicators of the effective detection time are extracted. Within a coordinate system constructed with the detection time as the horizontal axis and 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, within a coordinate system constructed with the detection time as the horizontal axis and the physiological index as the vertical axis, the physiological index change curve is formed by fitting the physiological index at the effective detection time. Inflection points were captured for the blood flow velocity change curve and the physiological index change curve, thereby dividing the change curve into a variable segment and a non-variable segment; The variable segments of the blood flow velocity change curve and the variable and non-variable segments of the physiological index change curve are correlated and evaluated. If it is determined that there is no correlation between a variable segment or a non-variable segment in the blood flow velocity change curve, the blood flow velocity data in the corresponding segment is regarded as abnormal blood flow velocity.

2. The detection and analysis method of an ultrasonic Doppler blood flow detector as described in claim 1, characterized in that: The process for selecting a compatible probe is as follows: The patient's historical ultrasound examination records are retrieved from the hospital's electronic medical record system. The ultrasound examination sites are extracted from the records and then matched with the patient's examined sites. Successfully matched ultrasound examination records are then selected and recorded as similar ultrasound examination records. Extract patient weight from patient visit information associated with similar ultrasound examination records, and extract current patient weight from current patient blood flow examination visit information; The patient's weight is compared with the patient's current weight for each similar ultrasound examination record to assess the degree of weight change, and then compared with the set allowable degree of change. In this way, similar ultrasound examination records with a patient's weight change less than or equal to the allowable degree of change are selected as reference ultrasound examination records. Assess vascular depth from ultrasound images displayed in a reference ultrasound record; Select an appropriate probe based on the depth of the blood vessels in the area being tested.

3. The detection and analysis method of an ultrasonic Doppler blood flow detector as described in claim 2, characterized in that: The selection of the adapter probe also includes the following process: When no similar ultrasound examination records or reference ultrasound examination records are found, anatomical landmarks are identified near the patient's test site to assess the vascular depth at the test site. Select an appropriate probe based on the depth of the blood vessels in the area being tested.

4. The detection and analysis method of an ultrasonic Doppler blood flow detector as described in claim 1, characterized in that: The process for controlling the probe contact pressure and coupling agent thickness is as follows: (21) If the signal-to-noise ratio extracted at a certain moment is lower than the standard signal-to-noise ratio but the resolution reaches the standard resolution, then extract the appropriate coupling agent thickness range from the detection reference library, and compare the coupling agent thickness collected at that moment 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, then 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 and the signal-to-noise ratio of the blood flow ultrasound image reaches the standard signal-to-noise ratio at a certain moment, then 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, then execute (51). (41) Issue a control prompt to stop adding coupling agent; (51) Issue a control prompt to increase the probe contact pressure to control the probe contact pressure.

5. The detection and analysis method of an ultrasonic Doppler blood flow detector as described in claim 4, characterized in that: The control of probe contact pressure and coupling agent thickness also includes the following process: (22) If the signal-to-noise ratio extracted at a certain moment reaches the standard signal-to-noise ratio but the resolution is lower than the standard resolution, then a suitable 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 suitable coupling agent thickness range. If the coupling agent thickness reaches the upper limit coupling agent thickness, then (32) is executed; otherwise, (52) is executed. (32) Issue a control prompt that the coupling agent is too thick, and continue 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 and the resolution of the blood flow ultrasound image reaches the standard resolution at a certain moment, 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, then execute (52). (42) Issue a control prompt to stop reducing the coupling agent; (52) Issue a control prompt to reduce probe contact pressure to control probe contact pressure.

6. The detection and analysis method of an ultrasonic Doppler blood flow detector as described in claim 4, characterized in that: The control of probe contact pressure and 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 described in claim 5, characterized in that: The probe contact pressure control is implemented as follows: When performing probe contact pressure control, a probe contact pressure time series is constructed before contact pressure control. The standard deviation is then calculated using the probe contact pressure time series, and the allowable pressure control variation for a single operation is determined based on the standard deviation. The specific formula is as follows: In the formula This represents the standard deviation of the probe contact pressure time series. Indicates the adjustment factor; The pressure value before contact pressure control is extracted from the probe contact pressure time series, and the initial required pressure control value is calculated by combining it with the single allowable pressure control change. The formula for calculating the initial required pressure control value is as follows: In the formula This indicates the current demand pressure control value. This indicates the pressure value before contact pressure control; The probe contact pressure is controlled according to the initial required pressure control value. After control, the image quality parameters of the blood flow ultrasound image are re-acquired and compared with the qualified image quality parameters. If the image quality parameters of the blood flow ultrasound image after the initial contact pressure control still do not meet the qualified image quality parameters, the probe contact pressure control is performed again on the basis of the initial contact pressure control until the image quality parameters of the blood flow ultrasound image after contact pressure control meet the qualified image quality parameters.

8. A detection and analysis system for an ultrasonic Doppler blood flow detector, used to perform the steps in the detection and analysis method of an ultrasonic Doppler blood flow detector as described in any one of claims 1-7, characterized in that, Includes the following modules: The ultrasound probe selection module is used to select an appropriate probe based on the patient's test site. The probe integrates a pressure sensor and a coupling agent thickness detection terminal, and simultaneously determines the detection angle between the probe and the skin of the test site. The blood flow detection implementation module is used to evenly apply coupling agent to the selected adapter probe and place the probe at the test site according to the determined detection angle to perform blood flow detection and generate blood flow ultrasound images. The blood flow detection parameter acquisition module is used to collect probe contact pressure and coupling agent thickness in real time during blood flow detection at the test site through an integrated pressure sensor and coupling agent detection terminal. At the same time, it extracts image quality parameters from the generated blood flow ultrasound image, including signal-to-noise ratio and resolution. The blood flow detection control module is used to control the probe contact pressure and coupling agent thickness based on image quality parameters; A reference library for storing suitable coupling agent thickness ranges; The physiological index detection module is used to detect the patient's physiological index in real time during the blood flow detection process at the test site; The abnormality detection, assessment, and identification module is used to extract the effective blood flow velocity from blood flow ultrasound images under the control of probe contact pressure and coupling agent thickness, and to combine it with physiological indicators to identify abnormal blood flow velocities.

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