Method for lung ultrasound scanning

Abstract

The invention discloses a method for lung ultrasonic scanning, lung ultrasonic scanning comprises a first scanning mode with a first scanning depth, a second scanning mode with a second scanning depth and a threshold scanning depth, the first scanning depth is smaller than the threshold scanning depth, and the second scanning depth is larger than the threshold scanning depth. The method comprises the following steps: setting scanning depth; if the scanning depth is smaller than the threshold scanning depth, starting a first scanning mode; if the scanning depth is larger than the threshold scanning depth, a second scanning mode is started, and the probe transmitting frequency of the first scanning mode is larger than the probe transmitting frequency of the second scanning mode.

Description

Technical Field

[0001] The present application relates to the technical field of medical equipment, and in particular to a method for lung ultrasound scanning. Background Art

[0002] In the prior art, imaging examination of the lungs is generally performed through X-ray or CT (computed tomography) scanning. The problems with the above two types of scanning are that they cause a certain amount of radiation to the human body, are costly, cannot perform real-time scanning, and cannot be used at the bedside.

[0003] Lung ultrasound, as an emerging bedside imaging diagnostic technology, has the advantages of being non-invasive, easy to operate, accurate and reliable, highly repeatable, and easy to observe dynamically. It can reduce the movement and radiation exposure of critically ill patients, and can provide timely and effective information on lung morphological changes. It has important clinical significance for the early diagnosis, dynamic evaluation, and follow-up of a variety of lung diseases.

[0004] Although lung ultrasound has many advantages over X-ray or CT, its disadvantages are poor image quality, and the doctor needs to have certain experience in image printing and reading. In addition, when using it, different scanning parameters need to be set for different scans. Summary of the invention

[0005] The purpose of the present application is to overcome the deficiencies in the prior art and to provide a method for lung ultrasound scanning that is easy to operate.

[0006] To achieve the above technical objectives, the present application provides a method for lung ultrasound scanning, wherein the lung ultrasound scanning includes a first scanning mode with a first scanning depth, a second scanning mode with a second scanning depth, and a threshold scanning depth, wherein the first scanning depth is less than the threshold scanning depth, and the second scanning depth is greater than the threshold scanning depth, including:

[0007] Set the scanning depth;

[0008] If the scanning depth is less than the threshold scanning depth, the first scanning mode is started;

[0009] If the scanning depth is greater than the threshold scanning depth, the second scanning mode is started, and the probe transmission frequency of the first scanning mode is greater than the probe transmission frequency of the second scanning mode.

[0010] Further, after starting the second scanning mode, a lung ultrasound image is acquired;

[0011] Automatically identify the pleural line on lung ultrasound images;

[0012] The part below the pleural line was taken as the region of interest for B-line identification;

[0013] Automatically identify B-lines from the region of interest.

[0014] Furthermore, the number of B lines and the distance between two adjacent B lines are automatically calculated.

[0015] Furthermore, the lung ultrasound image is line data, the B line extends in the vertical direction, and the B line is identified by:

[0016] Calculate the average value of each column of pixels in the vertical direction from left to right in the area of ​​interest;

[0017] The horizontal direction of the region of interest from left to right is taken as the horizontal axis, and the vertical direction is taken as the vertical axis. The average values ​​of the pixels are connected into a curve, and the coordinates of the peak are extracted as the preliminary screening position of the B line.

[0018] Furthermore, the peak of the curve is calculated according to a threshold method.

[0019] Furthermore, B lines are identified in the region of interest by AI, and unidentified B lines are added and misidentified B lines are deleted by editing.

[0020] Furthermore, the probe transmission frequency of the first scanning mode is 8 MHz, and the probe transmission frequency of the second scanning mode is 2 MHz.

[0021] Furthermore, the first scanning mode is used for scanning the pleural line, and the second scanning mode is used for scanning the B line.

[0022] Furthermore, in the first scanning mode, multiple frames of lung ultrasound images containing the pleural line are acquired, the optical flow between two adjacent frames of lung ultrasound images is calculated, and the pleural sliding at the pleural interface is determined based on the optical flow.

[0023] Furthermore, the pleural interface is identified in the following manner: by combining Hough transform and brightness threshold, the lines on two adjacent frames of ultrasound images are processed to identify bright lines on the ultrasound image.

[0024] The method for lung ultrasound scanning of the present application compares the set scanning depth with the threshold scanning depth to automatically select a suitable scanning mode, thereby reducing the complexity of the scanning operation. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 This is a flow chart for lung ultrasound scanning in the present application.

[0026] Figure 2 Ultrasound image of the lungs.

[0027] Figure 3 is a curve connecting the average values ​​of each column of pixels. DETAILED DESCRIPTION

[0028] In order to make the above-mentioned purposes, features and advantages of the present application more obvious and easy to understand, the specific implementation methods of the present application are described in detail below in conjunction with the accompanying drawings. In the following description, many specific details are set forth to facilitate a full understanding of the present application. However, the present application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar improvements without violating the connotation of the present application, so the present application is not limited by the specific embodiments disclosed below.

[0029] In order to simplify the drawings, only the parts related to the present invention are schematically shown in each figure, and they do not represent the actual structure of the product. In addition, in order to simplify the drawings and facilitate understanding, in some figures, only one of the parts with the same structure or function is schematically drawn or marked. In this article, "one" not only means "only one", but also means "more than one".

[0030] It should be further understood that the term “and / or” used in the specification and appended claims refers to any combination and all possible combinations of one or more of the associated listed items, and includes these combinations.

[0031] In this document, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection, or it can be indirectly connected through an intermediate medium, or it can be the internal communication of two components. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0032] In addition, in the description of the present application, the terms "first", "second", etc. are only used to distinguish the description and cannot be understood as indicating or implying relative importance.

[0033] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the specific implementation methods of the present invention will be described below with reference to the accompanying drawings. Obviously, the accompanying drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings and other implementation methods can be obtained based on these drawings without creative work.

[0034] See also Figure 1As shown, the present application provides a method for lung ultrasound scanning. Lung ultrasound scanning includes a first scanning mode with a first scanning depth, a second scanning mode with a second scanning depth, and a threshold scanning depth, wherein the first scanning depth is less than the threshold scanning depth, and the second scanning depth is greater than the threshold scanning depth. The threshold scanning depth is the default scanning depth in the system, which is generally 10 cm. The threshold scanning depth can be adjusted as needed. The first scanning mode and the second scanning mode are used to scan different parts of the lungs. Since the pleural line is closer to the surface of the human skin than the B line, the first scanning mode is used for scanning the pleural line, and the second scanning mode is used for scanning the B line. The scanning method comprises the following steps:

[0035] Set the scanning depth. The scanning depth is the scanning depth set by the doctor based on his / her experience during the scan.

[0036] If the scanning depth is less than the threshold scanning depth, the first scanning mode is started. If the scanning depth is set to 5 cm, since the scanning depth is less than the threshold scanning depth, the first scanning mode is started. In the first scanning mode, the transmitting frequency of the probe is 8 MHz. The first scanning mode is used for scanning the pleural line, and the second scanning mode is used for scanning the B line.

[0037] If the scanning depth is greater than the threshold scanning depth, the second scanning mode is started. If the scanning depth is set to 12 cm, the second scanning mode is started because the scanning depth is greater than the threshold scanning depth. In the second scanning mode, the transmitting frequency of the probe is 2 MHz. The transmitting frequency of the probe in the first scanning mode is greater than the transmitting frequency of the probe in the second scanning mode. When the transmitting frequency of the probe increases, the penetration depth of ultrasound decreases, and the image quality obtained becomes better; when the transmitting frequency of the probe decreases, the penetration depth of ultrasound increases, and the image quality obtained becomes worse.

[0038] After the second scanning mode is activated, a lung ultrasound image is acquired. In the second scanning mode, the pleural line and the B line can be identified due to the deeper scanning depth.

[0039] Automatically identify the pleural line on the lung ultrasound image. The identification of the pleural line can be automatically identified by an algorithm. Preferably, the pleural line is automatically identified by an artificial intelligence method. The identified pleural line can be colored or labeled to prompt the user.

[0040] The portion below the pleural line is used as the region of interest for B-line identification. The B-line is generally located below the pleural line. Using the portion below the pleural line as the region of interest for B-line identification can reduce the amount of calculation when identifying the B-line.

[0041] Automatically identify B-lines from the region of interest.

[0042] The number of B lines and the distance between two adjacent B lines are automatically calculated. The number of B lines and the distance between two adjacent B lines can be automatically calculated by an algorithm.

[0043] See also Figure 2 as well as Figure 3 As shown in FIG. 1 , the lung ultrasound image is line data, and the B line extends in the vertical direction. Figure 2 In the figure, the lung ultrasound image includes a pleural line 211 and a B-line area 212. The B-line 111 can be identified by an automatic identification method. If there is an unidentified B-line, the B-line 112 can be added by manual addition. If the B-line 112 is added, the B-line 112 can be moved in the ultrasound image area to move to the area where the B-line exists. If the automatically identified B-line is misidentified, the misidentified B-line can be deleted by editing. The B-line is identified by the following method:

[0044] Calculate the average value of each column of pixels from left to right in the region of interest. Figure 3 As shown in the figure, the x-axis is the width direction from left to right along the ultrasound image, and the y-axis is the brightness value of the pixel. For the sake of simplicity, only the average value of three columns of pixels is schematically drawn in this coordinate area. In actual calculations, it is necessary to calculate the average value of multiple columns of pixels, and mark the average value of each column of pixels on the xy coordinates, connect them into a curve through the fitting method, and find the peak position in the curve.

[0045] The horizontal direction of the region of interest from left to right is the horizontal axis, and the vertical direction is the vertical axis. The average values ​​of the pixels are connected into a curve, and the coordinates of the peaks are extracted as the preliminary screening positions of line B. In this figure, peak 311 is the preliminary screening position of line B. In actual use, there may be multiple peaks.

[0046] The peak of the curve is calculated according to the threshold method.

[0047] B lines are identified in the region of interest by AI, and unidentified B lines are added and misidentified B lines are deleted by editing. The addition and deletion of B lines have been described above and will not be repeated here.

[0048] In the first scanning mode, multiple frames of lung ultrasound images containing the pleural line are acquired, the optical flow between two adjacent frames of lung ultrasound images is calculated, and the pleural sliding at the pleural interface is determined based on the optical flow. In this embodiment, the correspondence between the pixels in the image sequence between two adjacent frames of ultrasound images is used to calculate the pleural sliding. In specific use, after knowing the pleural line, the change of pixels in the area above the pleural line and the change of pixels in the area below the pleural line over time are determined. If the change of pixels in the area above the pleural line over time is small, and the change of pixels in the area below the pleural line over time is large, it can be determined to be normal.

[0049] The pleural interface is identified in the following manner: lines on two adjacent frames of ultrasound images are processed by combining Hough transform and brightness threshold to identify bright lines on the ultrasound image.

[0050] The present application also discloses an ultrasound scanning system, which can be used for ultrasound scanning of the lungs. The ultrasound scanning system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processing unit, and a display unit. When in use, the ultrasound probe is coated with sound-conducting glue and then placed on the scanned part, such as the lungs. The transmitting circuit controls the ultrasound probe to transmit ultrasound waves, which enter the human body through the sound-conducting glue. When the ultrasound waves pass through the human body, part of the signal is reflected, and the transmitted signal is received by the ultrasound probe, and the acoustic signal is converted into an electrical signal. The processing unit processes the electrical signal to produce an ultrasound image. The generated ultrasound image is displayed on the display unit for the doctor to read.

[0051] When performing an ultrasound scan of the lungs, if the doctor only wants to see the patient's pleural line, he or she will set a scanning depth, such as 5 cm, based on his or her experience. The system will automatically determine the relationship between the scanning depth and the threshold scanning depth. In this ultrasound scanning system, the threshold scanning depth is 10 cm. Since 5 cm is less than 10 cm, the ultrasound scanning system starts the first scanning mode, at which time the ultrasound probe transmits at a higher frequency, so that better image quality can be obtained. If the scanning depth is set to 12 cm, since 12 cm is greater than 10 cm, the ultrasound scanning system starts the second scanning mode, at which time the ultrasound probe transmits at a lower frequency, so that a deeper depth can be obtained. The first scanning mode and the second scanning mode are pre-set modes of the system, with corresponding pre-adjusted parameters such as the probe transmission frequency and TGC. The advantage of this setting is that for people who are not familiar with ultrasound equipment, they only need to set a scanning depth to achieve ultrasound scanning of the lungs, which provides greater convenience to users and reduces the difficulty of use. At the same time, users only need to set one parameter to achieve ultrasound scanning of the lungs. If the threshold scanning depth is 10 cm and the set scanning depth is 9 cm, the system pops up a window and recommends the user to use the first scanning mode. If the user selects "Yes", the first scanning mode is activated. If the user selects "No", the second scanning mode is activated. Similarly, if the set scanning depth is 11 cm, the system pops up an exit and recommends the user to use the second scanning mode. If the user selects "Yes", the second scanning mode is activated. If the user selects "No", the first scanning mode is activated. Through the above settings, the user's operation complexity and operation time are reduced.

[0052] Although the first scanning mode, the second scanning mode and the threshold scanning depth are the default values ​​set by the system, the scanning doctor can also set the above values ​​according to different usage habits to meet his or her usage habits.

[0053] The above embodiments only express several implementation methods of the present application, and the descriptions thereof are relatively specific and detailed, but they cannot be understood as limiting the scope of the patent application. It should be pointed out that, for a person of ordinary skill in the art, several variations and improvements can be made without departing from the concept of the present application, and these all belong to the protection scope of the present application. Therefore, the protection scope of the patent application shall be subject to the attached claims.

Claims

1. A method for lung ultrasound scanning, the lung ultrasound scanning comprising a first scanning mode with a first scanning depth, a second scanning mode with a second scanning depth, and a threshold scanning depth, wherein: The first scanning depth is less than a threshold scanning depth, and the second scanning depth is greater than the threshold scanning depth, and is characterized by comprising: Set the scanning depth; If the scanning depth is less than the threshold scanning depth, the first scanning mode is started; If the scanning depth is greater than the threshold scanning depth, the second scanning mode is started, and the probe transmission frequency of the first scanning mode is greater than the probe transmission frequency of the second scanning mode.

2. The method according to claim 1, characterized in that After starting the second scanning mode, a lung ultrasound image is acquired; Automatically identify the pleural line on lung ultrasound images; The part below the pleural line was taken as the region of interest for B-line identification; B-lines are automatically identified from the region of interest.

3. The method according to claim 2, characterized in that Automatically calculate the number of B lines and the distance between two adjacent B lines.

4. The method according to claim 2, characterized in that: The lung ultrasound image is line data, and the B line extends in the vertical direction. The B line is identified by: Calculate the average value of each column of pixels in the vertical direction from left to right in the area of ​​interest; The horizontal direction of the region of interest from left to right is taken as the horizontal axis, and the vertical direction is taken as the vertical axis. The average values ​​of the pixels are connected into a curve, and the coordinates of the peak are extracted as the preliminary screening position of the B line.

5. The method according to claim 4, characterized in that The peak of the curve is calculated according to the threshold method.

6. The method according to claim 4, characterized in that B lines are identified in the region of interest through AI, and unidentified B lines are added and misidentified B lines are deleted through editing.

7. The method according to claim 1, characterized in that The probe transmission frequency of the first scanning mode is 8 MHz, and the probe transmission frequency of the second scanning mode is 2 MHz.

8. The method according to claim 1, characterized in that The first scanning mode is used for scanning the pleural line, and the second scanning mode is used for scanning the B line.

9. The method according to claim 1, characterized in that: In the first scanning mode, multiple frames of lung ultrasound images containing the pleural line are acquired, the optical flow between two adjacent frames of lung ultrasound images is calculated, and the pleural sliding at the pleural interface is determined based on the optical flow.

10. The method according to claim 9, characterized in that The pleural interface is identified in the following manner: lines on two adjacent frames of ultrasound images are processed by combining Hough transform and brightness threshold to identify bright lines on the ultrasound image.

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