Anatomical M-mode imaging method and ultrasound equipment

Abstract

The present application relates to the field of ultrasonic imaging technology, and discloses an anatomical M-mode imaging method and an ultrasonic device, which are used to solve the problem in the related art that when the frame rate of the B-mode mode is low, the anatomical M-mode image is very likely to have a mosaic phenomenon. In the present application, in order to improve the quality of anatomical M-mode images and reduce the mosaic phenomenon, a method is provided that can effectively improve the B-image frame rate while ensuring the quality of the B-image. On an ultrasonic device that originally has a low B-image frame rate, the quality of the basic data used for anatomical M-mode imaging can be improved, that is, a high B-image frame rate that ensures image quality can be achieved. As a result, the original B-image data can well express the movement of tissues, and the obtained anatomical M-mode image can improve the image quality and reduce the mosaic phenomenon.

Description

Technical Field

[0001] The present application relates to the technical field of ultrasonic image processing, and in particular to an anatomical M-mode imaging method and ultrasonic equipment. Background Art

[0002] In the ultrasound image display interface, the staff can enable the anatomical M-mode function to obtain the anatomical M-mode image. Anatomical M-mode is similar to conventional M-mode imaging methods. Both use grayscale values ​​to express the signal strength of ultrasound echo signals in time and depth. However, there is an essential difference between anatomical M-mode and conventional M-mode. Conventional M-mode is a real scan line in the ultrasound scan control sequence, while the M line of anatomical M-mode is a one-dimensional expression of B-mode ultrasound (Brightness mode) images.

[0003] B-mode ultrasound, commonly known as B-ultrasound, shows the physical characteristics of organs or tissues through grayscale changes from white to gray and then to black. It is a two-dimensional image (black and white gray image) of brightness modulation mode. B-image is the image obtained by B-ultrasound.

[0004] The anatomical M-mode is affected by the frame rate of the B-mode image. When the frame rate of the B-mode mode is low, mosaic phenomenon is very likely to occur in the anatomical M-mode image, which affects the doctor's judgment and diagnosis of the tissue structure. Summary of the invention

[0005] The embodiments of the present application provide an anatomical M-mode imaging method and an ultrasound device, which are used to solve the problem in the related art that when the frame rate of the B-mode is low, the anatomical M-mode image is very likely to have a mosaic phenomenon.

[0006] In a first aspect, the present application provides an anatomical M-mode imaging method, the method comprising:

[0007] Based on the M line routing speed and image quality requirements, the B-image imaging parameters are adjusted to improve the B-image frame rate, and the B-image of the first frame rate is scanned;

[0008] Performing inter-frame interpolation on the B picture of the first frame rate to obtain a B picture of a second frame rate;

[0009] An anatomical M-mode image is obtained based on the B-image at the second frame rate.

[0010] Optionally, adjusting the B-image imaging parameters based on the M-line routing speed and image quality requirements for the purpose of improving the B-image frame rate, and scanning to obtain the B-image at the first frame rate includes:

[0011] Based on the M line speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning line density; or,

[0012] Based on the M line's routing speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning range; or,

[0013] The scan line density is reduced until the A condition is fully met, and then the scan range is reduced to obtain the B graph of the first frame rate.

[0014] Optionally, before performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate, the method further includes:

[0015] Determine the number of B-image frames to be inserted between two adjacent B-image frames of the B-image of the first frame rate; wherein the number of B-image frames to be inserted is positively correlated with the routing speed of the M line and negatively correlated with the first frame rate;

[0016] The performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0017] Based on the number of frames of the to-be-inserted B-picture, inter-frame interpolation is performed on the B-picture of the first frame rate to obtain a B-picture of the second frame rate.

[0018] Optionally, the number of B-picture frames to be inserted is determined based on the following formula:

[0019]

[0020] N represents the number of B-picture frames to be inserted, M Speed Indicates the routing speed of the M line, Fps new Indicates the first frame rate.

[0021] Optionally, performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0022] For the k-th image and the k+1-th image, a weighted summation method is used to obtain the intermediate image between the k-th image and the k+1-th image, where K is a positive integer.

[0023] Optionally, the sum of the weights of the k images and the weight of the k+1th image is 1, and the method includes:

[0024] The weight of the k-th image is determined based on the following method:

[0025] in:

[0026] A: used to control the inter-frame attenuation curve;

[0027] B: This value is a constant and is used to control the flatness between two frames. The faster the measured part moves, the smaller the B value.

[0028] d: represents the difference between the pixel value of the current frame and the pixel value of the previous frame;

[0029] L: represents the correlation level between two frames;

[0030] c: represents a constant, with a value less than 1.

[0031] Optionally, obtaining an anatomical M-mode image based on the B-image at the second frame rate includes:

[0032] Obtaining pixel coordinates of line M from the B image of the second frame rate;

[0033] Scanning and converting the pixel point coordinates to obtain the coordinates of the rectangular coordinate system of the M line;

[0034] Using the coordinates of the rectangular coordinate system, the anatomical M-mode image of the M line is obtained and displayed.

[0035] In a second aspect, the present application further provides an ultrasound device, including: a processor, a memory, a display unit 130 and a probe;

[0036] A probe for emitting an ultrasonic beam;

[0037] A display unit, used for displaying anatomical M-mode images;

[0038] The memory is configured to store data required for ultrasound images;

[0039] A processor is connected to the probe and the display unit respectively, and is configured to execute:

[0040] Based on the M line routing speed and image quality requirements, the B-image imaging parameters are adjusted to improve the B-image frame rate, and the B-image of the first frame rate is scanned;

[0041] Performing inter-frame interpolation on the B picture of the first frame rate to obtain a B picture of a second frame rate;

[0042] An anatomical M-mode image is obtained based on the B-image at the second frame rate.

[0043] Optionally, the M-line-based routing speed and image quality requirements are implemented to improve the B-image frame rate, adjust the B-image imaging parameters, and scan to obtain a B-image with a first frame rate, and the processor is configured to execute:

[0044] Based on the M line speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning line density; or,

[0045] Based on the M line's routing speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning range; or,

[0046] The scan line density is reduced until the A condition is fully met, and then the scan range is reduced to obtain the B graph of the first frame rate.

[0047] Optionally, before performing the inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate, the processor is further configured to:

[0048] Determine the number of B-image frames to be inserted between two adjacent B-image frames of the B-image of the first frame rate; wherein the number of B-image frames to be inserted is positively correlated with the routing speed of the M line and negatively correlated with the first frame rate;

[0049] The performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0050] Based on the number of frames of the to-be-inserted B-picture, inter-frame interpolation is performed on the B-picture of the first frame rate to obtain a B-picture of the second frame rate.

[0051] Optionally, the number of B-picture frames to be inserted is determined based on the following formula:

[0052]

[0053] N represents the number of B-picture frames to be inserted, M Speed Indicates the routing speed of the M line, Fps new Indicates the first frame rate.

[0054] Optionally, performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0055] For the k-th image and the k+1-th image, a weighted summation method is used to obtain the intermediate image between the k-th image and the k+1-th image, where K is a positive integer.

[0056] Optionally, the sum of the weights of the k images and the weight of the k+1th image is 1, and the method includes:

[0057] The weight of the k-th image is determined based on the following method:

[0058] in:

[0059] A: used to control the inter-frame attenuation curve;

[0060] B: This value is a constant and is used to control the flatness between two frames. The faster the measured part moves, the smaller the B value.

[0061] d: represents the difference between the pixel value of the current frame and the pixel value of the previous frame;

[0062] L: represents the correlation level between two frames;

[0063] c: represents a constant, with a value less than 1.

[0064] Optionally, obtaining an anatomical M-mode image based on the B-image at the second frame rate includes:

[0065] Obtaining pixel coordinates of line M from the B image of the second frame rate;

[0066] Scanning and converting the pixel point coordinates to obtain the coordinates of the rectangular coordinate system of the M line;

[0067] Using the coordinates of the rectangular coordinate system, the anatomical M-mode image of the M line is obtained and displayed.

[0068] In a third aspect, an embodiment of the present application further provides a computer-readable storage medium. When the instructions in the computer-readable storage medium are executed by a processor of an electronic device, the electronic device is enabled to execute any method provided in the first aspect of the present application.

[0069] In a fifth aspect, an embodiment of the present application provides a computer program product, including a computer program, which, when executed by a processor, implements any method provided in the first aspect of the present application.

[0070] The technical solution provided by the embodiments of the present application brings at least the following beneficial effects: In the embodiments of the present application, in order to improve the quality of anatomical M-mode images and reduce the mosaic phenomenon, a method is provided that can effectively improve the B-image frame rate while ensuring the quality of the B-image. On an ultrasound device that originally has a low B-image frame rate, the basic data quality used for anatomical M-mode imaging can be improved, that is, a high B-image frame rate that ensures image quality. As a result, the original B-image data can well express the tissue movement situation, and the obtained anatomical M-mode image can improve the image quality and reduce the mosaic phenomenon.

[0071] It is to be understood that the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the present disclosure. BRIEF DESCRIPTION OF THE DRAWINGS

[0072] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the embodiments of the present application will be briefly introduced below. Obviously, the drawings introduced below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0073] Figure 1 A schematic diagram of the framework of an ultrasound device provided in an embodiment of the present application;

[0074] Figure 2 A schematic diagram of the application principle of an ultrasound device according to an embodiment of the present application to implement anatomical M-mode imaging;

[0075] Figure 3 A schematic diagram of a user interface provided in an embodiment of the present application;

[0076] Figure 4 A schematic diagram of another user interface provided by an embodiment of the present application;

[0077] Figure 5 A schematic diagram of a flow chart of an anatomical M-mode imaging method provided in an embodiment of the present application;

[0078] Figure 6 A schematic diagram of a process of inter-frame difference provided in an embodiment of the present application;

[0079] Figure 7 Another schematic diagram of the process of the anatomical M-mode imaging method provided in one embodiment of the present application;

[0080] Figure 8-Figure 9 A comparison diagram provided for an embodiment of the present application. DETAILED DESCRIPTION

[0081] In order to enable ordinary persons in the art to better understand the technical solution of the present application, the technical solution in the embodiments of the present application will be clearly and completely described below in conjunction with the accompanying drawings.

[0082] It should be noted that the terms "first", "second", etc. in the specification and claims of the present application and the above-mentioned drawings are used to distinguish similar objects, and are not necessarily used to describe a specific order or sequence. It should be understood that the data used in this way can be interchanged where appropriate, so that the embodiments of the present application described here can be implemented in an order other than those illustrated or described here. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present application. On the contrary, they are merely examples of devices and methods consistent with some aspects of the present application as detailed in the attached claims.

[0083] Below, some terms in the embodiments of the present application are explained to facilitate understanding by those skilled in the art.

[0084] (1) In the embodiments of the present application, the term "plurality" refers to two or more than two, and other quantifiers are similar.

[0085] (2) "and / or" describes the association relationship of the associated objects, indicating that there can be three relationships. For example, A and / or B can mean: A exists alone, A and B exist at the same time, and B exists alone. The character " / " generally indicates that the associated objects are in an "or" relationship.

[0086] (3) Ultrasound equipment. In the embodiments of the present application, the ultrasound equipment refers to an ultrasound imaging device that supports the B-mode and the anatomical M-mode. The user can select the anatomical M-mode mode through the system menu or the control button in the display interface. In this mode, the ultrasound device can generate and display the anatomical M-mode image based on the B-image. The anatomical M-mode image describes the signal strength of the echo signal at depth over time. For example, the anatomical M-mode image can be used to understand the movement of the myocardium and help doctors diagnose diseases.

[0087] In view of the problem in the related art that when the frame rate of the B-mode is low, the anatomical M-mode image is very likely to have a mosaic phenomenon, which affects the doctor's judgment and diagnosis of the tissue structure, the embodiment of the present application provides an anatomical M-mode imaging method and ultrasound equipment.

[0088] In the related art, multiple pairs of M lines are interpolated to improve the frame rate of anatomical M-type images. For example, if two anatomical M lines are interpolated before scan conversion, the biggest problem is that the B-image frame rate is low and the movement information of the tissue will be missed, so the two lines cannot accurately evaluate the complete tissue movement. In the process of converting from the rectangular coordinate system to the polar coordinate system during the scan conversion process, the polar coordinates obtained are often not integers. Adjacent M lines need to be interpolated during the conversion process. Since the coordinates of the point after scan conversion do not correspond to the coordinates of a point before scan conversion, several points are often required for interpolation. In this way, the interpolation between the two M lines cannot fully describe the motion trajectory. Therefore, there is a certain error in the interpolation between two adjacent M lines, and mosaics are prone to appear. If M-line interpolation is performed only after scan conversion, the accuracy of each point of the M line cannot be guaranteed, and mosaics are prone to appear.

[0089] In an embodiment of the present application, in order to improve the quality of anatomical M-mode images and reduce the mosaic phenomenon, a method is provided that can effectively improve the B-image frame rate while ensuring the quality of the B-image. On an ultrasound device that originally has a low B-image frame rate, the basic data quality used for anatomical M-mode imaging can be improved, that is, a high B-image frame rate that ensures image quality. As a result, the original B-image data can well express the tissue movement situation, and the obtained anatomical M-mode image can improve the image quality and reduce the mosaic phenomenon.

[0090] The ultrasound device and anatomical M-mode imaging method provided in the embodiments of the present application are described below in conjunction with the accompanying drawings.

[0091] See also Figure 1 , which is a structural block diagram of the ultrasonic device provided in an embodiment of the present application.

[0092] It should be understood that Figure 1 The ultrasound device 100 shown is only one example, and the ultrasound device 100 may have more Figure 1The more or less components shown in the figure can be combined with two or more components, or can have different component configurations. The various components shown in the figure can be implemented in hardware, software, or a combination of hardware and software including one or more signal processing and / or application specific integrated circuits.

[0093] Figure 1 Schematically shows a hardware configuration block diagram of the ultrasound apparatus 100 according to an exemplary embodiment.

[0094] like Figure 1 As shown, the ultrasound device 100 may include, for example: a processor 110, a memory 120, a display unit 130 and a probe 140; wherein,

[0095] A probe 140, used for emitting an ultrasonic beam;

[0096] A display unit 130, for displaying anatomical M-mode images;

[0097] The memory 120 is configured to store data required for ultrasound images, which may include software programs, application interface data, etc.;

[0098] The processor 110 is connected to the probe 140 and the display unit 130 respectively, and is configured to execute:

[0099] Based on the M line routing speed and image quality requirements, the B-image imaging parameters are adjusted to improve the B-image frame rate, and the B-image of the first frame rate is scanned;

[0100] Performing inter-frame interpolation on the B picture of the first frame rate to obtain a B picture of a second frame rate;

[0101] An anatomical M-mode image is obtained based on the B-image at the second frame rate.

[0102] Optionally, the M-line-based routing speed and image quality requirements are implemented to improve the B-image frame rate, adjust the B-image imaging parameters, and scan to obtain a B-image with a first frame rate, and the processor is configured to execute:

[0103] Based on the M line speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning line density; or,

[0104] Based on the M line's routing speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning range; or,

[0105] The scan line density is reduced until the A condition is fully met, and then the scan range is reduced to obtain the B graph of the first frame rate.

[0106] Optionally, before performing the inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate, the processor is further configured to:

[0107] Determine the number of B-image frames to be inserted between two adjacent B-image frames of the B-image of the first frame rate; wherein the number of B-image frames to be inserted is positively correlated with the routing speed of the M line and negatively correlated with the first frame rate;

[0108] The performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0109] Based on the number of frames of the to-be-inserted B-picture, inter-frame interpolation is performed on the B-picture of the first frame rate to obtain a B-picture of the second frame rate.

[0110] Optionally, the number of B-picture frames to be inserted is determined based on the following formula:

[0111]

[0112] N represents the number of B-picture frames to be inserted, M Speed Indicates the routing speed of the M line, Fps new Indicates the first frame rate.

[0113] Optionally, performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes:

[0114] For the k-th image and the k+1-th image, a weighted summation method is used to obtain the intermediate image between the k-th image and the k+1-th image, where K is a positive integer.

[0115] Optionally, the sum of the weights of the k images and the weight of the k+1th image is 1, and the method includes:

[0116] The weight of the k-th image is determined based on the following method:

[0117] in:

[0118] A: used to control the inter-frame attenuation curve;

[0119] B: This value is a constant and is used to control the flatness between two frames. The faster the measured part moves, the smaller the B value.

[0120] d: represents the difference between the pixel value of the current frame and the pixel value of the previous frame;

[0121] L: represents the correlation level between two frames;

[0122] c: represents a constant, with a value less than 1.

[0123] Optionally, obtaining an anatomical M-mode image based on the B-image at the second frame rate includes:

[0124] Obtaining pixel coordinates of line M from the B image of the second frame rate;

[0125] Scanning and converting the pixel point coordinates to obtain the coordinates of the rectangular coordinate system of the M line;

[0126] Using the coordinates of the rectangular coordinate system, the anatomical M-mode image of the M line is obtained and displayed.

[0127] Figure 2 Schematic diagram of the application principle according to an embodiment of the present application. Figure 1 The partial modules or functional components of the ultrasonic device shown are implemented, and only the main components will be described below, while other components, such as memory, controller, control circuit, etc., will not be described here in detail.

[0128] like Figure 2 As shown, the application environment may include a user interface 210 , a display unit 220 for displaying the user interface, and a processor 230 .

[0129] The display unit 220 may include a display panel 221 and a backlight assembly 222. The display panel 221 is configured to display an ultrasound image, the backlight assembly 222 is located behind the display panel 221, and the backlight assembly 222 may include a plurality of backlight partitions (not shown in the figure), each of which may emit light to illuminate the display panel 221.

[0130] The processor 230 may be configured to control the brightness of the backlight source of each backlight partition in the backlight assembly 222 , and control the probe to transmit a wide beam and receive an echo signal.

[0131] The processor 230 may include a focusing processing unit 231, a beamforming unit 232, and a spectrum generating unit 233. The focusing processing unit 231 may be configured to perform focusing processing on the current frame ultrasound image, and the focusing processing includes: taking the ultrasound puncture needle in the current frame ultrasound image as the focusing position of the wide beam, emitting a wide beam to the target detection area according to the emission coefficient of the ultrasound puncture needle; and receiving the echo signal fed back by the ultrasound puncture needle body. The beamforming unit 232 is configured to perform beamforming on the echo signal fed back by the same ultrasound puncture needle after completing the focusing processing on the ultrasound puncture needle in the target detection area to obtain scanning information. The spectrum generating unit 233 is configured to perform Doppler imaging based on the scanning information of each ultrasound puncture needle.

[0132] In the embodiment of the present application, in order to obtain an anatomical M-mode image, the user can set the number and trajectory of M lines through the operation interface of the ultrasound device. In principle, any number of M lines can be set, and usually 1-3 lines can meet the medical diagnosis requirements. In the embodiment of the present application, the quality of anatomical M-mode imaging is improved based on the situation of increasing the frame rate of the B-image. There is no restriction on the shape of the M line, so in the example Figure 3 In the operation interface shown, the user can set an M line of any shape. The shape of the M line is determined by the set M line track points, such as Figure 3 As shown, users can set the track points on the M line (such as Figure 3 The white circles in the figure represent the number of trajectory points) and adjust the positions of the trajectory points to obtain the M line of the desired trajectory.

[0133] In addition, the user can also select the M line speed in the operation interface. The line speed is used to describe the moving speed of the M spectrum line, such as the speed of moving on the time axis.

[0134] The routing speed can be divided into several gears, such as Figure 4 As shown, the routing speed includes low gear, medium gear and high gear, and the higher the gear, the higher the routing speed. The higher the routing speed, the higher the corresponding required B-image frame rate, in order to better describe the movement trajectory of the tissue. It should be noted that all user interfaces in the embodiments of the present application are only used to illustrate the embodiments of the present application and are not used to limit them.

[0135] like Figure 5 As shown, in the embodiment of the present application, in step 501, based on the routing speed of the M line and the image quality requirements, the B-image imaging parameters are adjusted for the purpose of improving the B-image frame rate, and the B-image of the first frame rate is obtained by scanning.

[0136] The first frame rate is higher than the frame rate before adjusting the B-image imaging parameters, and the first frame rate is often lower than the frame rate that matches the wiring speed.

[0137] In the present application, by optimizing the B-image imaging parameters, the B-image frame rate is improved while ensuring the image quality requirements. The B-image of the first frame rate is obtained through actual scanning and can accurately express the movement of the tissue.

[0138] Since the frame rate can be increased if the number of scan lines in each B-image frame is reduced, the frame rate can be increased by reducing the number of scan lines in each B-image frame. In addition, the number of scan lines required in a frame also depends on the scanning range. Therefore, during implementation, the optimized B-image imaging parameters may include line density and / or scanning range, wherein a reasonable reduction in line density can ensure image quality and improve the B-image frame rate. Therefore, the implementation method of improving the B-image frame rate based on optimizing the B-image program parameters includes:

[0139] (1) Improving the frame rate of the B-picture by reducing the scan line density can be implemented as follows: based on the line speed of the M-line and the image quality requirement, the scan line density is reduced to obtain the B-picture of the first frame rate. It can be implemented as follows: determining the lower limit of the scan line density that meets the image quality requirement based on the line speed of the M-line, and then improving the frame rate of the B-picture by continuously reducing the scan line density and ensuring that the reduced scan line density is greater than the lower limit of the scan line density.

[0140] The expression method of scanning line density can be shown as formula (1):

[0141]

[0142] In formula (1), D represents the scan line density, Fps new represents the first frame rate, represents the scanning detection time of each scanning line, and R represents the scanning range.

[0143] The first frame rate is related to the routing speed. Due to the limitation of the device's own capabilities, the first frame rate is often lower than the frame rate matched by the routing speed. During implementation, in order to ensure image quality, the scan line density lower limit can be configured. When the scan line density is determined to be lower than the scan line density lower limit based on the first frame rate, the scan line density lower limit can be used as the final scan line density, and then inter-frame interpolation can be used to increase the frame rate.

[0144] (2) Improving the frame rate of the B-image by reducing the scanning range can be implemented as follows: based on the routing speed of the M line and the image quality requirements, the scanning range is reduced to obtain a B-image of the first frame rate.

[0145] For example, under the premise of ensuring that the lesion can be scanned for medical diagnosis, the frame rate of the B image can be improved by adjusting the scanning range. For example, the original scanning range is the first area, which includes a lot of tissues that do not need to be observed, and the lesion occupies a small part of the area. Therefore, the scanning range can be reduced to include the second area, including the lesion area and a small amount of tissue around it. As a result, the scanning range is reduced and the frame rate can be improved.

[0146] The scanning range can be expressed as shown in formula (2):

[0147]

[0148] In formula (2), D represents the scan line density, Fps new represents the first frame rate, represents the scanning detection time of each scanning line, and R represents the scanning range.

[0149] During implementation, the user may select a smaller scanning range according to his / her own needs before entering the anatomical M-mode.

[0150] (3) Improving the B-image frame rate by reducing the scanning density and scanning range, which can be implemented as follows: first reducing the scanning line density to a certain extent, for example, when it is reduced to the lower limit of the scanning line density, and then reducing the scanning range to improve the B-image frame rate.

[0151] After the B-image imaging parameters are optimized to improve the B-image frame rate, in order to further improve the B-image frame rate, in the embodiment of the present application, inter-frame interpolation can be performed on the B-image of the first frame rate to obtain a B-image of the second frame rate in step 502. Thus, the tissue motion trajectory between two adjacent B-image frames can be obtained through inter-frame interpolation.

[0152] During implementation, in order to ensure the interpolated image effect, the number of B-picture frames to be inserted between two adjacent B-picture frames of the first frame rate can be determined first, and then, based on the number of B-picture frames to be inserted, inter-frame interpolation is performed on the B-picture of the first frame rate to obtain the B-picture of the second frame rate.

[0153] In order to ensure the image quality of the B-picture, in the embodiment of the present application, the number of B-picture frames to be inserted is positively correlated with the line speed of the M-line and negatively correlated with the first frame rate.

[0154] For example, the number of B-picture frames to be inserted can be determined according to formula (3):

[0155]

[0156] N represents the number of B-picture frames to be inserted, M Speed Indicates the routing speed of the M line, Fps new Indicates the first frame rate.

[0157] In formula (3), the routing speed is taken as a reference so that the frame rate matches the routing speed as much as possible.

[0158] You can also directly use the numerator as the difference, which means how many frames need to be inserted per unit time.

[0159] Therefore, based on the first frame rate and the M line routing speed, the number of B-picture frames that need to be inserted between two adjacent B-picture frames can be reasonably determined to avoid inserting too many B-pictures, which leads to a waste of processing resources, and to avoid inserting too few B-pictures, which leads to a lack of organized motion trajectories. The method of formula (3) can well balance the number of inserted B-pictures and obtain the appropriate number of B-picture frames to be inserted.

[0160] When performing inter-frame interpolation, a weighted summation method can be used to obtain an intermediate image between the kth image and the k+1th image, where K is a positive integer. The interpolation expression can be expressed as shown in formula (4):

[0161] I (n) =αI (k) +(1-α)I(k+1) (4)

[0162] in:

[0163] I k represents the image data of the Kth B image, I (k+1) Represents the image data of the k+1th B-image;

[0164] n: represents the nth frame inserted between two frames; a possible implementation is as follows Figure 6 As shown in FIG. 1 , it is assumed that A1 and A2 are scanned B images, that is, images in the B image of the first frame rate. Assuming that three images in the order of B1, B2, and B3 need to be inserted between A1 and A2, then the B1 image is based on A1 and A2 as I k and I (k+1) Get, B2 image, based on B1 image and A2 image as I k and I (k+1) Obtain, and so on, the B3 image is based on the B2 and A2 images as I k and I (k+1) Of course, in other embodiments, the weights of the two images can be adjusted to obtain the intermediate frame B image using the two images.

[0165] α: Frame weight coefficient, used to control the weighting of the current frame and the previous frame.

[0166] Therefore, the weighted summation method is convenient for calculation, can save processing resources and obtain an intermediate frame B image that meets the requirements.

[0167] In addition, in order to further improve the image quality of the interpolated intermediate frame B image, the embodiment of the present application determines the weight of the k-th image based on the following formula (5) when performing interpolation:

[0168] Where 0≤d≤255 (5)

[0169] In formula (5):

[0170] A: used to control the attenuation curve between B frames; the larger the value of A, the faster the entire curve decays. Conversely, the smaller the value, the slower the decay. The setting of A value is related to the part. If the part moves faster, A needs a larger value. The setting of A value can be obtained based on experimental tests.

[0171] B: is a constant used to control the flatness between two frames. The flatness between two frames refers to the speed of change of the transition between the two frames. If the movement is fast, the next frame image needs to change more compared with the previous frame, so the value of B needs to be set to a small value, otherwise a larger value needs to be set. In other words, the faster the movement speed of the measured part, the smaller the B value, and the B value is related to the measured part, and the B value of different parts can be determined based on experiments;

[0172] d: represents the difference between the pixel value of the current frame and the pixel value of the previous frame;

[0173] L: represents the correlation level between two frames. The correlation level can be understood as the frame-related gear. Different parts are set to different gears. The gear is an integer and can be selected from 0 to M. The higher the gear, the higher the coefficient α will be.

[0174] C represents a constant, which has a value less than 1 and is usually 0.5.

[0175] The scheme for determining weights provided in the embodiment of the present application is equivalent to citing the concept of frame correlation and including the concept of motion, so that the determined weights are more reasonable and the interpolated inter-frame images are more realistic.

[0176] After performing inter-frame interpolation to obtain a B-image at a second frame rate, an anatomical M-mode image may be obtained based on the B-image at the second frame rate in step 503 .

[0177] For each M line, the following steps can be implemented:

[0178] In step SC1, the pixel coordinates of the M line can be obtained from the B image of the second frame rate; the pixel coordinates at this time are the pixel points in the B image, so their values ​​are values ​​of the polar coordinate system.

[0179] In step SC2, the pixel point coordinates are scan-converted to obtain the coordinates of the M line in a rectangular coordinate system;

[0180] In step SC3, the anatomical M-mode image of the M line is obtained and displayed using the coordinates of the rectangular coordinate system.

[0181] In addition, in the embodiment of the present application, the temporal resolution and / or spatial resolution of the anatomical M-mode image can be further improved by interpolating the M lines based on the B image.

[0182] like Figure 7 FIG. 1 is a schematic diagram of an exemplary process of the anatomical M-mode imaging method in an embodiment of the present application, comprising the following steps:

[0183] In step 701, the scanning line density is first reduced, and then the scanning range is reduced, and scanning is performed to obtain a B image at a first frame rate.

[0184] In step 702, based on the B-pictures of the first frame rate and the routing speed of the M-line, the number of B-picture frames to be inserted between two adjacent B-picture frames, ie, the number of B-picture frames to be inserted, is determined.

[0185] In step 703, the weight between two adjacent B-picture frames is determined, and then a B-picture is inserted between the two adjacent B-picture frames by weighted summation to obtain a B-picture of the second frame rate.

[0186] In step 704, the pixel coordinates of the M line are obtained from the B image of the second frame rate.

[0187] In step 705, the pixel point coordinates are scanned and converted to obtain the coordinates of the M line in a rectangular coordinate system.

[0188] In step 706, the anatomical M-mode image of the M line is obtained and displayed using the coordinates of the rectangular coordinate system.

[0189] like Figure 8 The above is to use the interface M-type image obtained before the embodiment of the present application, from Figure 8 It can be seen that the image is blurry and the mosaic phenomenon affects the image quality. Fig. 9 The effect diagram after adopting the solution provided by the embodiment of the present application is shown. Fig. 9 The middle M line is clearer and the mosaic phenomenon is significantly reduced.

[0190] Although the operations of the method of the present application are described in a specific order in the drawings, this does not require or imply that the operations must be performed in this specific order, or that all the operations shown must be performed to achieve the desired results. Additionally or alternatively, some steps may be omitted, multiple steps may be combined into one step, and / or one step may be decomposed into multiple steps.

[0191] Those skilled in the art will appreciate that the embodiments of the present application may be provided as methods, systems, or computer program products. Therefore, the present application may adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment in combination with software and hardware. Moreover, the present application may adopt the form of a computer program product implemented in one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) that include computer-usable program code.

[0192] The present application is described with reference to the flowcharts and / or block diagrams of the methods, devices (systems), and computer program products according to the embodiments of the present application. It should be understood that each process and / or box in the flowchart and / or block diagram, as well as the combination of the processes and / or boxes in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable image scaling device to produce a machine, so that the instructions executed by the processor of the computer or other programmable image scaling device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0193] These computer program instructions may also be stored in a computer readable memory capable of directing a computer or other programmable image scaling device to operate in a specific manner, so that the instructions stored in the computer readable memory produce an article of manufacture including an instruction device, the instruction device being implemented in the process Figure 1 A process or multiple processes and / or boxes Figure 1 A function specified in one or more boxes.

[0194] These computer program instructions may also be loaded onto a computer or other programmable device so that a series of operational steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for executing on the computer or other programmable device to implement the process. Figure 1 A process or multiple processes and / or boxes Figure 1 The steps for the functions specified in one or more boxes.

[0195] Although the preferred embodiments of the present application have been described, those skilled in the art may make additional changes and modifications to these embodiments once they have learned the basic creative concept. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments and all changes and modifications falling within the scope of the present application.

[0196] Obviously, those skilled in the art can make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalents, the present application is also intended to include these modifications and variations.

Claims

1. An anatomical M-mode imaging method, characterized in that: The method comprises: Based on the M line routing speed and image quality requirements, the B-image imaging parameters are adjusted to improve the B-image frame rate, and the B-image of the first frame rate is scanned; Determine the number of B-image frames to be inserted between two adjacent B-image frames of the B-image of the first frame rate; wherein the number of B-image frames to be inserted is positively correlated with the routing speed of the M line and negatively correlated with the first frame rate; Based on the number of frames of the B picture to be inserted, interpolating the B picture of the first frame rate to obtain a B picture of a second frame rate; An anatomical M-mode image is obtained based on the B-image at the second frame rate.

2. The method according to claim 1, characterized in that The method of adjusting the B-image imaging parameters based on the M-line routing speed and image quality requirements for the purpose of improving the B-image frame rate, and scanning to obtain the B-image at the first frame rate includes: Based on the M line speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning line density; or, Based on the M line's routing speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning range; or, The scan line density is reduced until the A condition is fully met, and then the scan range is reduced to obtain the B graph of the first frame rate.

3. The method according to claim 1, characterized in that The number of B-picture frames to be inserted is determined based on the following formula: N represents the number of B-picture frames to be inserted, M Speed Indicates the routing speed of the M line, Fps new Indicates the first frame rate.

4. The method according to claim 1, characterized in that: The performing inter-frame interpolation on the B picture of the first frame rate to obtain the B picture of the second frame rate includes: For the k-th image and the k+1-th image, a weighted summation method is used to obtain the intermediate image between the k-th image and the k+1-th image, where K is a positive integer.

5. The method according to claim 4, characterized in that The sum of the weights of the k images and the weight of the k+1th image is 1, and the method comprises: The weight of the k-th image is determined based on the following method: in: A: used to control the inter-frame attenuation curve; B: This value is a constant and is used to control the flatness between two frames. The faster the measured part moves, the smaller the B value. d: represents the difference between the pixel value of the current frame and the pixel value of the previous frame; L: represents the correlation level between two frames; c: represents a constant, with a value less than 1.

6. The method according to any one of claims 1 to 5, characterized in that: The step of obtaining an anatomical M-mode image based on the B-image at the second frame rate comprises: Obtaining pixel coordinates of line M from the B image of the second frame rate; Scanning and converting the pixel point coordinates to obtain the coordinates of the rectangular coordinate system of the M line; Using the coordinates of the rectangular coordinate system, the anatomical M-mode image of the M line is obtained and displayed.

7. An ultrasonic device, characterized in that: include: Processor, memory, display unit 130 and probe; A probe for emitting an ultrasonic beam; A display unit, used for displaying anatomical M-mode images; The memory is configured to store data required for ultrasound images; A processor is connected to the probe and the display unit respectively, and is configured to execute: Based on the M line routing speed and image quality requirements, the B-image imaging parameters are adjusted to improve the B-image frame rate, and the B-image of the first frame rate is scanned; Determine the number of B-image frames to be inserted between two adjacent B-image frames of the B-image of the first frame rate; wherein the number of B-image frames to be inserted is positively correlated with the routing speed of the M line and negatively correlated with the first frame rate; Based on the number of frames of the B picture to be inserted, inter-frame interpolation is performed on the B picture of the first frame rate to obtain a B picture of a second frame rate; An anatomical M-mode image is obtained based on the B-image at the second frame rate.

8. The ultrasonic device according to claim 7, characterized in that The M-line-based routing speed and image quality requirements are implemented to improve the B-image frame rate, adjust the B-image imaging parameters, and scan to obtain a B-image with a first frame rate. The processor is configured to execute: Based on the M line speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning line density; or, Based on the M line's routing speed and image quality requirements, the B image of the first frame rate is obtained by reducing the scanning range; or, The scan line density is reduced until the A condition is fully met, and then the scan range is reduced to obtain the B graph of the first frame rate.

Images