An ultrasonic transmission method and system

Abstract

The specification discloses an ultrasonic emission method, which comprises the following steps: acquiring at least one set of ultrasonic imaging historical data based on a trigger condition; acquiring a historical imaging time based on the at least one set of ultrasonic imaging historical data; judging whether an interframe time and the historical imaging time satisfy a preset condition, the interframe time being an interval time of emitted ultrasonic corresponding to adjacent two frames of images; if yes, updating the interframe time as the historical imaging time; and if no, not updating the interframe time.

Description

[0001] Divisional Statement

[0002] This application is a divisional application of Chinese Patent Application CN202111232861.9 entitled “An ultrasonic emission method and system” filed on October 22, 2021. TECHNICAL FIELD

[0003] The present specification relates to the technical field of ultrasonic waves, in particular to an ultrasonic emission method and system. BACKGROUND

[0004] An ultrasonic image is an internal tissue image obtained by scanning a target object using ultrasonic waves for medical treatment or medical research, and by receiving and processing scan data. Each frame of the ultrasonic image can be obtained based on scan data corresponding to multiple ultrasonic emissions. The inter-frame time is the interval time of the emitted ultrasonic waves corresponding to adjacent two frames of the ultrasonic image. However, as the working time of the ultrasonic emission system increases, its performance changes accordingly, resulting in a mismatch between the current inter-frame time and the ultrasonic system. Specifically, when the inter-frame time is too long, after generating a frame of the ultrasonic image, there will be a long pause time before emitting the ultrasonic wave corresponding to the next frame of the ultrasonic image, thereby causing the ultrasonic image to lag and reducing the generation efficiency of the ultrasonic image; when the inter-frame time is too short, the ultrasonic wave corresponding to the next frame of the ultrasonic image is emitted before the previous frame of the ultrasonic image is obtained, which will cause the information of the previous frame of the ultrasonic image to be missing, resulting in the ultrasonic image lagging.

[0005] Therefore, it is desirable to provide an ultrasonic emission method that can improve the adaptability of the inter-frame time, thereby improving the quality of the ultrasonic image. SUMMARY

[0006] One aspect of the present specification provides an ultrasonic emission method, the method comprising: obtaining at least one set of ultrasonic imaging history data based on a triggering condition; obtaining a historical imaging time based on the at least one set of ultrasonic imaging history data; determining whether the inter-frame time and the historical imaging time satisfy a preset condition, the inter-frame time being an interval time of emitted ultrasonic waves corresponding to adjacent two frames of images; if yes, updating the inter-frame time to the historical imaging time; and if no, not updating the inter-frame time.

[0007] Another aspect of the present specification provides an ultrasonic emission system, characterized in that the system comprises an inter-frame time determination module configured to: obtain at least one set of ultrasonic imaging history data based on a triggering condition; obtain a historical imaging time based on the at least one set of ultrasonic imaging history data; determine whether the inter-frame time and the historical imaging time satisfy a preset condition, the inter-frame time being an interval time of emitted ultrasonic waves corresponding to adjacent two frames of images; if yes, update the inter-frame time to the historical imaging time; and if no, not update the inter-frame time.

[0008] Another aspect of the present specification provides a computer readable storage medium, which stores computer instructions, when the computer reads the computer instructions in the storage medium, the computer executes the ultrasonic wave emission method.

[0009] Some other embodiments of the present specification dynamically adjust the interframe interval based on the ultrasonic imaging history data, so that the interframe time can dynamically change with the change of system performance, thereby obtaining high-quality ultrasonic images. BRIEF DESCRIPTION OF DRAWINGS

[0010] The present specification will be further described in the manner of exemplary embodiments, which will be described in detail through the accompanying drawings. These embodiments are not restrictive, and in these embodiments, the same numbers represent the same structures, in which:

[0011] Figure 1 is a schematic diagram of an application scenario of an ultrasonic wave emission system according to some embodiments of the present specification;

[0012] Figure 2 is an exemplary block diagram of an ultrasonic wave emission system according to some embodiments of the present specification;

[0013] Figure 3 is an exemplary flowchart of an ultrasonic wave emission method according to some embodiments of the present specification;

[0014] Figure 4a is an exemplary schematic diagram of a linear array ultrasonic wave probe transducer according to some embodiments of the present specification;

[0015] Figure 4b is an exemplary schematic diagram of a convex array ultrasonic wave probe transducer according to some embodiments of the present specification;

[0016] Figure 5a is an exemplary schematic diagram of the focal point trajectory of ultrasonic wave emission of a linear array ultrasonic wave probe according to some embodiments of the present specification;

[0017] Figure 5b is an exemplary schematic diagram of the focal point trajectory of ultrasonic wave emission of a convex array ultrasonic wave probe according to some embodiments of the present specification;

[0018] Figure 6 is an exemplary flowchart of a method for determining an interframe time according to some embodiments of the present specification;

[0019] Figure 7 is an exemplary flowchart of an ultrasonic wave pulse data transmission method according to some embodiments of the present specification. DETAILED DESCRIPTION

[0020] In order to more clearly illustrate the technical solutions of the embodiments of the present specification, the drawings needed to be used in the embodiment description will be briefly introduced as follows. Obviously, the drawings in the following description are only some examples or embodiments of the present specification, and for those skilled in the art, the present specification can also be applied to other similar scenarios without creative labor on the basis of these drawings. Unless it is clear from the language environment or otherwise stated, the same reference numbers in the drawings represent the same structures or operations.

[0021] It should be understood that the "system", "device", "unit" and / or "module" used in the present specification is a method for distinguishing different components, elements, parts, sections or assemblies at different levels. However, if other words can achieve the same purpose, the words can be replaced by other expressions.

[0022] As shown in the specification and claims, unless the context clearly indicates otherwise, the words "one", "a", "an", and / or "the" do not refer to the singular, but can also include the plural. Generally speaking, the terms "comprise" and "include" only indicate the inclusion of the steps and elements explicitly identified, and these steps and elements do not constitute an exclusive list, and the method or device can also include other steps or elements.

[0023] Flowcharts are used in the present specification to illustrate the operations performed by the system according to the embodiments of the present specification. It should be understood that the preceding or subsequent operations are not necessarily performed in sequence. On the contrary, each step can be processed in reverse order or simultaneously. At the same time, other operations can also be added to these processes, or one or more steps of the operation can be removed from these processes.

[0024] Figure 1 is a schematic diagram of an application scenario of an ultrasonic emission system according to some embodiments of the present specification.

[0025] The ultrasonic emission system 100 can determine the focal point trajectory of ultrasonic emission by implementing the methods and / or processes disclosed in the present specification, thereby compensating for the energy loss on both sides of the ultrasonic probe and improving the resolution of the edge of the ultrasonic image.

[0026] As Figure 1 shown, the ultrasonic emission system 100 can include an ultrasonic probe 110, a processing device 120, a terminal device 130, a network 140 and a storage device 150.

[0027] The components of the ultrasonic emission system 100 can be connected in one or more various ways. As an example only, as Figure 1As shown, the ultrasound probe 110 can be connected to the processing device 120 through the network 140. As another example, the ultrasound probe 110 can be directly connected to the processing device 120 (as shown by the dashed bidirectional arrow connecting the ultrasound probe 110 and the processing device 120). As a further example, the storage device 150 can be connected to the processing device 120 directly or through the network 140. As a further example, the terminal device 130 can be connected to the processing device 120 directly (as shown by the dashed bidirectional arrow connecting the terminal device 130 and the processing device 120) and / or through the network 140.

[0028] The ultrasound probe 110 can acquire scan data. Specifically, the ultrasound probe 110 can emit ultrasound waves to a target object or a portion thereof and receive reflected ultrasound waves of the target object or the portion thereof. In some embodiments, the ultrasound probe 110 can include, but is not limited to, a convex array probe, a linear array probe, a phased array probe, a high frequency probe, and the like.

[0029] The processing device 120 can process data and / or information obtained from the ultrasound probe 110, the terminal device 130, and / or the storage device 150. For example, the processing device 120 can determine a focal point position corresponding to each of a plurality of ultrasound wave emissions based on a number of times and / or a sequence of the plurality of ultrasound wave emissions to be emitted. As another example, the processing device 120 can update an inter-frame time based on at least one set of ultrasound imaging history data. As a further example, the processing device 120 can compress at least a portion of pulses of the plurality of ultrasound wave emissions to be emitted into one octet of data. In some embodiments, the processing device 120 can include a central processing unit (CPU), a digital signal processor (DSP), a system on chip (SoC), a microcontroller unit (MCU), and the like, and / or any combination thereof. In some embodiments, the processing device 120 can include a computer, a user console, a single server, or a group of servers, and the like. The group of servers can be centralized or distributed. In some embodiments, the processing device 120 can be local or remote. For example, the processing device 120 can access information and / or data stored in the ultrasound probe 110, the terminal device 130, and / or the storage device 150 via the network 140. As another example, the processing device 120 can directly connect to the ultrasound probe 110, the terminal device 130, and / or the storage device 150 to access the stored information and / or data. In some embodiments, the processing device 120 can be implemented on a cloud platform. As an example only, the cloud platform can include a private cloud, a public cloud, a hybrid cloud, a community cloud, a distributed cloud, inter-cloud, multi-cloud, and the like, or any combination thereof. In some embodiments, the processing device 120 or a portion of the processing device 120 can be integrated into the ultrasound probe 110.

[0030] Terminal device 130 can receive instructions from the user (e.g., ultrasound examination mode) and can also display ultrasound images to the user. Terminal device 130 may include mobile device 131, tablet computer 132, laptop computer 133, etc., or any combination thereof. In some embodiments, terminal device 130 may be part of processing device 120.

[0031] Network 140 may include any suitable network that facilitates the exchange of information and / or data between the ultrasonic transmitting system 100. In some embodiments, one or more components of the ultrasonic transmitting system 100 (e.g., ultrasonic probe 110, processing device 120, storage device 150, terminal device 130) may communicate information and / or data with one or more other components of the ultrasonic transmitting system 100 via network 140. For example, processing device 120 may receive user instructions from a terminal device via the network. As another example, ultrasonic probe 110 may acquire ultrasonic transmission parameters from processing device 120 via network 140. Network 140 may be and / or include public networks (e.g., the Internet), private networks (e.g., local area networks (LANs), wide area networks (WANs)), wired networks (e.g., Ethernet networks), wireless networks (e.g., 802.11 networks, Wi-Fi networks), cellular networks (e.g., LTE networks), Frame Relay networks, virtual private networks (“VPNs”), satellite networks, telephone networks, routers, hubs, switches, server computers, and / or any combination thereof. By way of example only, network 140 may include cable networks, wired networks, fiber optic networks, telecommunications networks, intranets, wireless local area networks (WLANs), metropolitan area networks (MANs), public switched telephone networks (PSTNs), and Bluetooth. TM Network, Purple Bee TM Networks, near field communication (NFC) networks, and any combination thereof. In some embodiments, network 140 may include one or more network access points. For example, network 140 may include wired and / or wireless network access points such as base stations and / or internet exchange points, through which one or more components of the ultrasonic transmitting system 100 may connect to network 140 to exchange data and / or information.

[0032] Storage device 150 can store data, instructions, and / or any other information. In some embodiments, storage device 150 can store data obtained from ultrasonic probe 110, terminal device 130, and / or processing device 120. In some embodiments, storage device 150 can store data and / or instructions, and processing device 120 can execute or use the data and instructions to perform the exemplary methods / systems described herein. In some embodiments, storage device 150 may include mass storage, removable storage, volatile read-write memory, read-only memory (ROM), etc., or any combination thereof. Exemplary mass storage may include disks, optical disks, solid-state drives, etc. Exemplary removable storage may include flash drives, floppy disks, optical disks, memory cards, compact disks, magnetic tapes, etc. Exemplary volatile read-write memory may include random access memory (RAM). Exemplary RAM may include dynamic random access memory (DRAM), double data rate synchronous dynamic random access memory (DDR SDRAM), static random access memory (SRAM), thyristor random access memory (T-RAM), and zero-capacitance random access memory (Z-RAM), etc. Exemplary ROMs may include mask read-only memory (MROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), optical disc read-only memory (CD-ROM), and digital multifunction disk read-only memory, etc. In some embodiments, the storage device 150 may operate on a cloud platform. By way of example only, the cloud platform may include private cloud, public cloud, hybrid cloud, community cloud, distributed cloud, internal cloud, multi-tiered cloud, etc., or any combination thereof.

[0033] In some embodiments, storage device 150 may be connected to network 140 to communicate with one or more other components of ultrasonic transmitting system 100 (e.g., ultrasonic probe 110, processing device 120, storage device 150, terminal device 130). One or more components of ultrasonic transmitting system 100 may access data or instructions stored in storage device 150 via network 140. In some embodiments, storage device 150 may be directly connected to or communicate with one or more other components of ultrasonic transmitting system 100 (e.g., ultrasonic probe 110, processing device 120, storage device 150, terminal device 130). In some embodiments, storage device 150 may be part of processing device 120.

[0034] Figure 2 This is an exemplary block diagram of an ultrasonic transmitting system according to some embodiments of this specification.

[0035] In some embodiments, the ultrasonic transmitting system 100 may include a first relative position determination module 210, a second relative position determination module 220, a focal radius determination module 230, and a focal position determination module 240.

[0036] The first relative position determination module 210 can be used to determine the first relative position corresponding to each ultrasonic wave emission based on the number of emission times and / or the emission sequence of the multiple ultrasonic waves to be emitted, so as to obtain multiple first relative positions corresponding to the multiple ultrasonic wave emission. A detailed description of the first relative position determination module can be found in step 310, and will not be repeated here.

[0037] The second relative position determination module 220 can be used to map the plurality of equally spaced first relative positions to a plurality of non-equally spaced second relative positions corresponding to the multiple ultrasonic wave emissions. In some embodiments, the second relative position determination module can be used to map the plurality of equally spaced first relative positions to the plurality of non-equally spaced second relative positions corresponding to the multiple ultrasonic wave emissions using a non-linear curve. A detailed description of the second relative position determination module can be found in step 320, and will not be repeated here.

[0038] The focal radius determination module 230 can be used to determine the emission distance and focal radius corresponding to each ultrasonic emission based on ultrasonic emission parameters and a second relative position corresponding to each ultrasonic emission. In some embodiments, the ultrasonic emission parameters include the number of transducer channels, the array element width, and the transducer curvature. In some embodiments, the focal radius determination module can be used to determine the emission distance corresponding to each ultrasonic emission based on the number of transducer channels, the array element width, and the second relative position corresponding to each ultrasonic emission; and to determine the focal radius corresponding to each ultrasonic emission based on the emission distance, the second relative position, and the transducer curvature. The focal radius determination module can determine the focal curvature corresponding to each ultrasonic emission based on the emission distance, the second relative position, and the transducer curvature; and determine whether the absolute value of the focal curvature corresponding to each ultrasonic emission is less than a curvature threshold: if so, the reciprocal of the curvature threshold is used as the value of the focal radius, and the direction of the focal radius is determined based on the focal curvature; if not, the reciprocal of the focal curvature is used as the focal radius. For a detailed description of the focal radius determination module, please refer to step 330, which will not be repeated here.

[0039] The focal position determination module 240 can determine the focal position corresponding to each ultrasonic wave emission based on the emission distance and the focal radius corresponding to each ultrasonic wave emission. In some embodiments, the focal position determination module 240 can obtain the radian corresponding to the emission distance of each ultrasonic wave emission based on the emission distance and the transducer curvature; obtain the projected distance of the emission distance on the horizontal and vertical axes based on the radian corresponding to the emission distance of each ultrasonic wave emission; obtain the abscissa of the focal point corresponding to each ultrasonic wave emission based on the projected distance on the horizontal axis, the focal radius, and the transducer curvature; and obtain the ordinate of the focal point corresponding to each ultrasonic wave emission based on the projected distance on the vertical axis, the focal radius, and the transducer curvature. A detailed description of the focal position determination module can be found in step 340, and will not be repeated here.

[0040] Figure 3 This is an exemplary flowchart illustrating an ultrasonic emission method according to some embodiments of this specification.

[0041] Ultrasound imaging is used for medical or medical research purposes. It involves scanning a target object with ultrasound waves to obtain images of its internal tissues by receiving and processing the scan data.

[0042] In some embodiments, the target object can be a human body, organ, organism, object, injured site, tumor, etc. For example, the target object could be one or more diseased tissues in a user's heart.

[0043] Scanning data is obtained by transmitting ultrasonic waves to a target object or a part thereof using an ultrasonic probe, and receiving the reflected ultrasonic signals from the target object or a part thereof.

[0044] In some embodiments, the format of the ultrasound image may include Joint Photographic Experts Group (JPEG) image format, Tagged Image File Format (TIFF) image format, Graphics Interchange Format (GIF) image format, Kodak Flash PiX (FPX) image format, Digital Imaging and Communications in Medicine (DICOM) image format, etc.

[0045] In some embodiments, each frame of ultrasonic image can be acquired based on scan data corresponding to multiple ultrasonic transmissions. Each ultrasonic transmission corresponds to a focal point, which is the intersection of the extended beams of the corresponding ultrasonic waves emitted onto the target object or a portion thereof. It can be understood that the more focal points corresponding to the target object or a portion thereof, i.e., the more ultrasonic beams emitted onto the target object or a portion thereof, the higher the resolution of the ultrasonic image of that target object or portion.

[0046] Therefore, to compensate for the low resolution of the ultrasonic image edges caused by energy loss on both sides of the ultrasonic probe, a focal trajectory with densely packed focal points on both sides can be designed during the emission of ultrasonic waves to the target object. Furthermore, for ultrasonic probes scanning targets located deep within the target area, such as convex array ultrasonic probes, a focal trajectory with densely packed focal points in the center can be designed to improve the ultrasonic image resolution of deep-seated targets.

[0047] like Figure 3 As shown, the ultrasonic wave emission method 300 may include:

[0048] Step 310: Based on the number of times and / or the order of the multiple ultrasonic waves to be emitted, determine the first relative position corresponding to each ultrasonic wave emission, so as to obtain multiple first relative positions corresponding to the multiple ultrasonic wave emissions.

[0049] Specifically, step 310 can be performed by the first relative position determination module 210.

[0050] The multiple ultrasonic waves to be emitted are multiple ultrasonic waves corresponding to each frame of an ultrasonic image. In some embodiments, the multiple ultrasonic waves to be emitted can be in an unfocused emission mode. The unfocused emission mode refers to an emission mode in which the focal point of the ultrasonic wave is not in the imaging area when it is emitted. For example, plane wave emission mode, divergent wave emission mode, wide beam emission mode, etc.

[0051] The number of ultrasound waves to be emitted is the number of ultrasound waves emitted corresponding to each frame of an ultrasound image. For example, if the number of emissions is 10, then each frame of an ultrasound image is generated based on scan data of ultrasound reflections emitted 10 times towards the target object or a part thereof. In some embodiments, the first relative position determination module 210 can determine the number of emissions based on the ultrasound examination mode input by the user (e.g., abdominal examination mode, vascular examination mode, and thyroid examination mode, etc.). For example, the first relative position determination module 210 can determine the number of emissions to be 10 based on the ultrasound examination mode "abdominal examination mode" input by the user. In some embodiments, the first relative position determination module 210 can also directly obtain the number of emissions input by the user.

[0052] The emission sequence of multiple ultrasonic waves to be emitted is determined by the order in which each ultrasonic wave is emitted. The emission order of each ultrasonic wave can be represented by a number. For example, the emission sequence of 10 ultrasonic waves to be emitted could be 0, 1, 2...8, 9, representing the first, second, third...ninth, and tenth ultrasonic waves, respectively.

[0053] The first relative position refers to the relative position of the array element centers on the ultrasonic probe corresponding to the focal point of the ultrasonic waves during emission, when the waves are emitted in the corresponding emission sequence. The relative position refers to the positional distribution within a certain range mapped from the distance (i.e., the emission distance) from the center of the array element corresponding to the emission sequence to the center of the ultrasonic probe. A detailed description of the emission distance can be found in step 330, and will not be repeated here.

[0054] In some embodiments, the first relative position can be represented by a value between [-1, 1] to indicate the positional distribution. For example... Figure 4a As shown, when the ultrasonic probe is a linear array, the focal points corresponding to multiple ultrasonic wave emissions include focal point A for the first emitted ultrasonic wave and focal point B for the second emitted ultrasonic wave. The first relative position of the first emitted ultrasonic wave, i.e., the distance A'O between the array element center A' corresponding to focal point A and the ultrasonic probe center O, is mapped to a value between [-1, 1]. Similarly, the first relative position of the second emitted ultrasonic wave, i.e., the distance B'O between the array element center B' corresponding to focal point B and the ultrasonic probe center O, is mapped to a value between [-1, 1]. For example, when the first relative position is less than 0, it indicates that the focal point of the ultrasonic wave in the corresponding emission sequence is to the left of the ultrasonic probe center; when the first relative position is greater than 0, it indicates that the focal point of the ultrasonic wave in the corresponding emission sequence is to the right of the ultrasonic probe center. Furthermore, the closer the first relative position is to -1 or 1, the closer the focal point of the ultrasonic wave in the corresponding emission sequence is to the edge of the ultrasonic probe; the closer the first relative position is to 0, the closer the focal point of the ultrasonic wave in the corresponding emission sequence is to the center of the ultrasonic probe.

[0055] The first relative position can also reflect the relative position of the energy distribution of each ultrasonic wave in the ultrasonic image frame corresponding to its emission sequence. For example, the closer the first relative position is to -1 or 1, the closer the energy distribution of the ultrasonic wave in the ultrasonic image frame corresponding to its emission sequence is to the edge of the image; the closer the first relative position is to 0, the closer the energy distribution of the ultrasonic wave in the ultrasonic image frame corresponding to its emission sequence is to the center of the image.

[0056] In some embodiments, the first relative position can be determined by formula (1):

[0057] (1)

[0058] Where n represents the number of times the ultrasonic waves to be emitted are emitted, and i represents the order of each ultrasonic wave emission, i≥0. This represents the first relative position corresponding to the i-th emitted ultrasonic wave. .

[0059] As can be seen from formula (1), the multiple first relative positions corresponding to multiple ultrasound waves are... The multiple focal points corresponding to multiple ultrasound waves are equally spaced, with equal intervals between them.

[0060] For example, if the number of times n of the multiple ultrasonic waves to be emitted is 10, then the first relative positions corresponding to the first (i=0), second (i=1), third (i=2), ... ninth (i=8), tenth (i=9) ultrasonic wave emission are -1, -7 / 9, -5 / 9...7 / 9, 1 respectively, and are distributed at equal intervals of 2 / 9.

[0061] It is understandable that, based on the first relative position and the parameters of the ultrasonic probe, the transmission distance corresponding to the center of the equally spaced array elements can be calculated, thereby further calculating the focal positions of the equally spaced array elements. However, the ultrasonic waves emitted based on the equally spaced focal positions cannot resolve the uneven distribution of ultrasonic image resolution caused by scattering from both sides of the ultrasonic probe. Therefore, it is necessary to further obtain the transmission distance corresponding to the center of the non-equally spaced array elements, thereby further calculating the focal positions of the non-equally spaced array elements.

[0062] Step 320: Map the plurality of equally spaced first relative positions to a plurality of non-equally spaced second relative positions corresponding to the multiple ultrasonic wave emissions.

[0063] Specifically, step 320 can be performed by the second relative position determination module 220.

[0064] The second relative position is the relative position of the array element centers on the ultrasonic probe corresponding to the focal point of the ultrasonic wave during emission, when the waves of the corresponding emission sequence are not evenly spaced.

[0065] It is understandable that when multiple ultrasound waves are distributed at equal intervals, the corresponding ultrasound waves are emitted uniformly from the ultrasound probe. However, since the ultrasound energy loss is greater closer to the edge of the ultrasound probe, the resolution of the corresponding ultrasound wave at the corresponding position in the ultrasound image frame (i.e., the edge position of the ultrasound image frame) is lower.

[0066] To compensate for uneven energy loss during multiple ultrasonic wave emissions, the second relative position determination module 220 can map the relative positions of equally spaced focal points to a non-equally spaced distribution. Specifically, the second relative position determination module 220 can set more focal points at locations with greater ultrasonic energy loss, thus making the relative position intervals of multiple focal points smaller.

[0067] In some embodiments, the second relative position determination module 220 can map a plurality of equally spaced first relative positions to a plurality of non-equally spaced second relative positions corresponding to the multiple ultrasonic wave emissions using a non-linear curve.

[0068] In some embodiments, the nonlinear curve can be represented by formula (2):

[0069] (2)

[0070] Where i represents the order in which each ultrasonic wave is emitted. This represents the first relative position corresponding to the i-th emitted ultrasonic wave. This represents the second relative position corresponding to the i-th emitted ultrasonic wave.

[0071] Continuing with the above example, the second relative position determination module 220 can map the first relative positions -1, -7 / 9, -5 / 9, ..., 5 / 9, 7 / 9, 1 corresponding to the 0th, 1st, 2nd, ..., 7th, 8th, and 9th ultrasonic waves to the second relative positions 1, -679 / 729, -545 / 729, ..., 545 / 729, 679 / 729, 1 respectively, with intervals of 50 / 729, 134 / 729, ..., 134 / 729, and 50 / 729.

[0072] As can be seen from formula (2), the closer the second relative position is to -1 or 1 (that is, when the ultrasonic waves of the corresponding emission sequence are emitted, the closer the focus is to the edge of the ultrasonic probe), the smaller the interval between the corresponding second relative positions, and the greater the corresponding focus distribution density; the closer the second relative position is to 0 (that is, when the ultrasonic waves of the corresponding emission sequence are emitted, the closer the focus is to the center of the ultrasonic probe), the greater the interval between the corresponding second relative positions, and the smaller the corresponding focus distribution density.

[0073] Similar to the first relative position, the second relative position can also reflect the relative position of the energy distribution of each emission sequence of ultrasound waves in the ultrasound image frame. For example, the closer the second relative position is to -1 or 1, the closer the energy distribution of the corresponding emission sequence of ultrasound waves in the ultrasound image frame is to the edge of the image; the closer the second relative position is to 0, the closer the energy distribution of the corresponding emission sequence of ultrasound waves in the ultrasound image frame is to the center of the image.

[0074] Some embodiments of this specification map multiple equally spaced first relative positions corresponding to multiple ultrasonic waves to be emitted to multiple non-equally spaced second relative positions using curves. This results in a higher density of relative positions between multiple focal points corresponding to multiple ultrasonic waves on both sides, thereby compensating for the low resolution of ultrasonic image edges caused by energy loss on both sides of the ultrasonic probe.

[0075] Step 330: Based on the ultrasonic emission parameters and the second relative position corresponding to each ultrasonic emission, determine the emission distance and focal radius corresponding to each ultrasonic emission.

[0076] Specifically, step 330 can be performed by the focal radius determination module 230.

[0077] Ultrasonic emission parameters are parameters used to control ultrasonic emission. In some embodiments, ultrasonic emission parameters may include the number of transducer channels, element width, and transducer curvature.

[0078] A transducer is a component of an ultrasonic probe. It converts electrical signals into ultrasonic signals using array elements for transmission towards a target object or a portion thereof. It can also convert reflected ultrasonic signals from a target object or a portion thereof into electrical signals (i.e., scan data) to generate an ultrasonic image. Array elements can be piezoelectric materials, such as barium titanate, lead titanate, lead zirconate titanate, etc. In some embodiments, the transducer may include array elements of multiple frequencies and a corresponding transducer channel (i.e., control circuitry) for each array element. The transducer can generate ultrasonic waves of different frequencies by exciting array elements at different locations with electrical signals through the transducer channels. Specifically, the transducer can send each pulse signal to the corresponding transducer channel, and each transducer channel excites the corresponding array element based on the pulse signal, thereby emitting ultrasonic waves of different or the same frequency at different or the same times. For a more detailed description of pulse signals, please refer to [link to relevant documentation]. Figure 7 The details and related descriptions will not be repeated here.

[0079] The number of transducer channels refers to the number of transducer channels (control circuits). In some embodiments, each transducer channel can excite one array element. For example, if the number of transducer channels is 20, then 20 array elements can be excited.

[0080] The width of an array element is the width of its cross-section. For example... Figure 4a As shown, the transducer element width of the linear array ultrasonic probe (represented by short black lines in the figure) is d1 (e.g., 0.00003 meters). Figure 4b As shown, the width of the transducer element (represented by the short black line segment in the figure) of the convex array ultrasonic probe is d2 (e.g., 0.000452 meters).

[0081] Transducer curvature, the reciprocal of the transducer radius, is a parameter characterizing the degree of curvature of the array of elements within the transducer. A larger transducer curvature indicates a greater degree of curvature in the array of elements (i.e., a more convex transducer) and a smaller transducer radius; conversely, a smaller transducer curvature indicates a less curvature in the array of elements (i.e., a flatter transducer) and a larger transducer radius. For example... Figure 4a As shown, if the transducer elements of a linear array ultrasonic probe are arranged in a straight line, then the transducer curvature of the linear array ultrasonic probe is 0. Figure 4b As shown, if the transducer elements of a convex array ultrasonic probe are arranged in a curved pattern, then the transducer curvature of a linear array ultrasonic probe is greater than 0 (e.g., curvature k=20).

[0082] The transmission distance is the distance between the center of the array element corresponding to the focal point of the ultrasonic wave in the corresponding transmission sequence and the center of the ultrasonic probe.

[0083] like Figure 4a As shown, when the ultrasonic probe is a linear array, the multiple transmission distances corresponding to multiple ultrasonic wave transmissions include line segments A'O and B'O. Here, A'O represents the distance between the array element center A' of the ultrasonic wave corresponding to transmission focus A and the center O of the ultrasonic probe, and B'O represents the distance between the array element center B' of the ultrasonic wave corresponding to transmission focus B and the center O of the ultrasonic probe. Figure 4b As shown, when the ultrasonic probe is a convex array, the multiple transmission distances corresponding to multiple ultrasonic wave transmissions include arc length. and ,in, This represents the distance between the center C' of the ultrasonic wave array element corresponding to the emission focal point C and the center O of the ultrasonic probe. This represents the distance between the center D' of the ultrasonic wave array element corresponding to the emission focus D and the center O of the ultrasonic probe.

[0084] In some embodiments, the focal radius determination module 230 can determine the emission distance corresponding to each ultrasonic emission based on the number of transducer channels, the width of the array element, and the second relative position corresponding to each ultrasonic emission.

[0085] In some embodiments, the focal radius determination module 230 can determine the emission distance corresponding to each ultrasonic wave emission based on formula (3):

[0086] (3)

[0087] Where N represents the number of transducer channels, Indicates the width of the array element. This represents the transmission distance corresponding to the i-th ultrasonic wave.

[0088] Some embodiments of this specification obtain the non-equal interval transmission distance of multiple array element centers corresponding to multiple focal points on the ultrasonic probe based on multiple non-equal interval second relative positions.

[0089] The focal radius is the radius of the closely spaced circle along the focal trajectory, and it reflects the curvature of the focal trajectory. The larger the focal radius, the smaller the curvature of the corresponding focal point along the focal trajectory.

[0090] In some embodiments, the focal radius determination module 230 can determine the focal radius corresponding to each ultrasonic wave emission based on the emission distance corresponding to each ultrasonic wave emission, the second relative position corresponding to each ultrasonic wave emission, and the transducer curvature.

[0091] Specifically, the focal radius determination module 230 can determine the focal curvature corresponding to each ultrasonic wave emission based on the emission distance corresponding to each ultrasonic wave emission, the second relative position corresponding to each ultrasonic wave emission, and the transducer curvature.

[0092] The focal curvature is the reciprocal of the focal radius. In some embodiments, the focal radius determination module 230 can determine the focal curvature corresponding to each ultrasonic wave emission based on formula (4):

[0093] (4)

[0094] Where i represents the order in which each ultrasonic wave is emitted. Let represent the focal curvature corresponding to the i-th emitted ultrasonic wave. Indicates the transducer curvature. Represents the ultrasonic emission constant, the Adjustments can be made based on empirical values, for example It can be -0.04.

[0095] Furthermore, the focal radius determination module 230 can determine whether the focal curvature corresponding to each ultrasonic wave emission is less than the curvature threshold.

[0096] It is understandable that since the transducer curvature k=0 of the linear array ultrasonic probe, the absolute value of the focal curvature corresponding to each ultrasonic emission determined by formula (4) may be small, and the corresponding focal radius may be large, thus causing the corresponding focal position to be outside the range of the linear array ultrasonic probe. The curvature threshold can be the minimum value of the focal curvature corresponding to each ultrasonic emission. For example, the curvature threshold can be 1.

[0097] If the absolute value of the focal curvature corresponding to the current sequence of ultrasonic wave emission is less than the curvature threshold, then the reciprocal of the curvature threshold is used as the value of the focal radius, and the direction of the focal radius is determined based on the focal curvature. For example, the focal curvature corresponding to the first ultrasonic wave emission... If the value is -0.5, then the curvature threshold 1 is used as the value of the corresponding focal curvature, and the reciprocal of the curvature threshold 1 is used as the value of the focal radius, based on the corresponding focal curvature. (For example, -0.5) determines the direction of the focal radius to be negative, i.e., the focal radius. It is -1.

[0098] If the absolute value of the focal curvature corresponding to the current sequence of ultrasonic wave emission is greater than the curvature threshold, then the reciprocal of the focal curvature is used as the focal radius. For example, the focal curvature corresponding to the second ultrasonic wave emission... If the absolute value of -2 is 2, which is greater than the curvature threshold of 1, then the reciprocal of the focal curvature -2, -0.5, is taken as the focal radius. .

[0099] In some embodiments, the focal radius determination module 230 can determine the focal radius corresponding to each ultrasonic wave emission based on formula (5):

[0100] (5)

[0101] Where i represents the order in which each ultrasonic wave is emitted. Let represent the focal radius of the ultrasonic wave emitted in the i-th transmission. Indicates the curvature threshold. Indicates obtaining The symbol.

[0102] Some embodiments of this specification obtain the focal radius based on a second relative position, such that the larger the value of the second relative position, i.e., the farther the second relative position is from the center of the ultrasonic probe, the larger the absolute value of the focal curvature. Furthermore, when the absolute value of the focal curvature is greater than the curvature threshold, the corresponding focal radius value is smaller, and the corresponding focal radius value interval is smaller, so that the horizontal and vertical coordinates of the focal position determined in step 340 based on the focal radius and the transmission distance are further correlated with the second relative position. At the same time, when the absolute value of the focal curvature is less than the curvature threshold (i.e., the transducer is a linear array transducer), the value of the focal radius remains unchanged, so that only the horizontal coordinate of the focal position determined in step 340 based on the transmission distance is further correlated with the second relative position.

[0103] Step 340: Determine the focal position corresponding to each ultrasonic wave emission based on the emission distance and the focal radius corresponding to each ultrasonic wave emission.

[0104] Specifically, step 340 can be performed by the focus position determination module 240.

[0105] It can be understood that by determining the focal position corresponding to each ultrasonic wave emission, the focal trajectory of multiple ultrasonic waves to be emitted can be determined.

[0106] In some embodiments, the focus position determination module 240 can obtain the radian corresponding to the emission distance of each ultrasonic wave emission based on the emission distance and transducer curvature corresponding to each ultrasonic wave emission. Specifically, the radian corresponding to the emission distance of each ultrasonic wave emission is the emission distance of each ultrasonic wave emission. The ratio of the transducer's radius of curvature to the distance of each ultrasonic wave emission, i.e., the emission distance corresponding to each ultrasonic wave emission. The product of the transducer curvature k, i.e. .

[0107] Furthermore, the focus position determination module 240 can obtain the projected distances of the emission distance corresponding to each ultrasonic wave emission on the horizontal and vertical axes based on the radian of the emission distance corresponding to each ultrasonic wave emission. Specifically, the focus position determination module 240 can obtain the projected distances of the emission distance corresponding to each ultrasonic wave emission on the horizontal and vertical axes respectively. and

[0108] Furthermore, the focal position determination module 240 can obtain the abscissa of the focal point corresponding to each ultrasonic wave emission based on the projected distance of the emission distance on the horizontal axis, the focal radius, and the transducer curvature corresponding to each ultrasonic wave emission; and obtain the ordinate of the focal point corresponding to each ultrasonic wave emission based on the projected distance of the emission distance on the vertical axis, the focal radius, and the transducer curvature corresponding to each ultrasonic wave emission.

[0109] In some embodiments, the focal position determination module 240 can determine the abscissa and ordinate of the focal point corresponding to each ultrasonic wave emission based on formula (6):

[0110] (6)

[0111] Where i represents the order of each ultrasonic wave emission, the and Let x and y represent the x and y coordinates of the focal point corresponding to the i-th emitted ultrasonic wave, respectively. The focal radius corresponds to the i-th ultrasonic wave emission.

[0112] When the ultrasonic probe is a linear array ultrasonic probe, corresponding to a transducer curvature k=0, the focal trajectory of the multiple ultrasonic waves to be emitted is: As mentioned above, the larger the absolute value of the second relative position corresponding to the ultrasonic wave sequence (i.e., the farther the distance from the center of the ultrasonic probe), the larger the absolute value of the corresponding non-equal interval transmission distance, and the smaller the interval. That is, the larger the absolute value of the horizontal axis, the smaller the interval. When the absolute value of the focal curvature is less than the curvature threshold (i.e., the transducer is a linear array transducer), the value of the focal radius remains unchanged, which is the reciprocal of the curvature threshold, 1 / a. The direction of the focal radius is determined based on the direction of the focal curvature, i.e., the vertical axis is... 1 / a. For example... Figure 5a As shown, the focal points are more concentrated the farther away from the origin on the horizontal axis (X-axis), thus compensating for the greater energy loss as the ultrasonic probe gets closer to the sides. Meanwhile, the absolute value of the focal points on the vertical axis (Z-axis) is close to 0.

[0113] When the ultrasonic probe is a convex array ultrasonic probe, and the corresponding transducer curvature k≠0, the focal trajectory of the multiple ultrasonic waves to be emitted is further related to the emission distance and transducer curvature corresponding to each ultrasonic wave emission.

[0114] like Figure 5b As shown, the focal points on the horizontal axis (X-axis) are more concentrated the farther and closer they are from the origin, thus compensating for the greater energy loss of the ultrasonic probe as it gets closer to the sides, while improving the ultrasonic image resolution of the convex array ultrasonic probe for deep targets; in addition, the absolute value of the focal points on the vertical axis (Z-axis) is smaller the closer they are to the origin on the horizontal axis (X-axis) (i.e., the smaller the second relative position).

[0115] Figure 6 This is an exemplary flowchart illustrating a method for determining inter-frame time according to some embodiments of this specification. Specifically, Figure 6 This can be performed by the inter-frame time determination module.

[0116] As mentioned above, each frame of ultrasonic image can be acquired based on scan data corresponding to multiple ultrasonic wave transmissions. In some embodiments, the process of acquiring each frame of ultrasonic image may include: generating a transmission command, transmitting ultrasonic waves to a target object based on the transmission command, receiving reflected ultrasonic waves (i.e., scan data) from the target object, generating an initial ultrasonic image based on the reflected ultrasonic waves, and processing the initial ultrasonic image to generate a final ultrasonic image. Here, the intra-frame time is the time of ultrasonic wave transmission corresponding to each frame, and the inter-frame time is the interval between ultrasonic wave transmissions corresponding to two adjacent frames, including the time of receiving reflected ultrasonic waves (i.e., scan data) from the target object, the time of generating the initial ultrasonic image based on the reflected ultrasonic waves, the time of processing the initial ultrasonic image to generate the final ultrasonic image, and the time of generating the transmission command for the next frame.

[0117] When the inter-frame time is too long, there will be a significant pause between generating one ultrasonic image and transmitting the next, causing the ultrasonic image to stutter and reducing generation efficiency. Conversely, if the inter-frame time is too short, transmitting the next ultrasonic image before acquiring the previous one will result in missing information from the previous image, also causing stuttering. Therefore, it is necessary to determine an inter-frame time that matches the efficiency of ultrasonic image generation.

[0118] like Figure 6 As shown, the method 600 for determining inter-frame time may include:

[0119] Step 610: Based on the triggering conditions, acquire at least one set of historical ultrasound imaging data.

[0120] Ultrasound imaging history data is data acquired during the generation of ultrasound images. A set of ultrasound imaging history data can be acquired for each frame of ultrasound image generated. In some embodiments, at least one set of ultrasound imaging history data includes at least one of ultrasound propagation time, imaging time, and image processing time.

[0121] Ultrasonic propagation time includes the time it takes to emit ultrasonic waves towards a target object and the time it takes to receive reflected ultrasonic waves from the target object. The time to emit ultrasonic waves towards the target object includes the time to generate a transmission command and the time it takes for the emitted ultrasonic waves to reach the target object. In some embodiments, the transmission command may include parameters such as the pulse, focal trajectory, and gain of the emitted ultrasonic waves. In some embodiments, the time to generate the transmission command can be obtained from the processing device. For example, the time consumed by the CPU of the processing device to execute "generate transmission command" can be calculated via an interface (such as the relevant API in the CUDA time library). In some embodiments, the time it takes for the ultrasonic waves to reach the target object and the time it takes to receive reflected ultrasonic waves from the target object can be obtained based on the ultrasonic probe.

[0122] Imaging time is the time required to generate an initial ultrasonic image based on reflected ultrasonic waves. In some embodiments, imaging time may include beamforming time and image compositing time. Beamforming time is the time required to synthesize reflected ultrasonic waves received by multiple array elements. Image compositing time is the time required to synthesize an initial ultrasonic image based on multiple portions of the image (e.g., multiple scan lines) corresponding to multiple reflected ultrasonic waves. In some embodiments, imaging time can be obtained from the processing device. For example, the time consumed by the processing device's GPU to perform "image compositing" can be calculated via an interface (such as the relevant API in the C language time library).

[0123] Image processing time is the time taken to process the initial ultrasound image and generate the processed ultrasound image. In some embodiments, image processing time may include spatial filtering time, image compression time, and scan conversion time. The spatial filtering time is the time taken to enhance the quality of the initial ultrasound image using filtering. In some embodiments, filtering may include, but is not limited to, at least one or a combination of low-pass filtering (smoothing), high-pass filtering (sharpening), and band-pass filtering. The image compression time is the time taken to reduce the amount of initial ultrasound image data. In some embodiments, image compression methods may include, but are not limited to, at least one or a combination of differential pulse code modulation, hierarchical interpolation, differential pyramiding, multiple autoregressive methods, and discrete cosine transform. The scan conversion time is the time taken to convert the initial ultrasound image into an ultrasound image in the target coordinate system. For example, converting the initial ultrasound image from polar coordinates to rectangular coordinates. In some embodiments, image processing time can be obtained from the processing device. For example, the time consumed by the processing device to perform "spatial filtering" can be statistically analyzed through an interface (such as calling OpenGL-related APIs).

[0124] In some embodiments, the storage device can acquire historical ultrasonic data from the processing device and the ultrasonic probe. Furthermore, the inter-frame time determination module can acquire at least one set of historical ultrasonic data from the storage device based on triggering conditions.

[0125] Triggering conditions are the conditions for acquiring historical ultrasound imaging data. In some embodiments, triggering conditions may include activating the ultrasound transmission system, changing system parameters, and the time interval reaching a preset value.

[0126] "Activating the ultrasonic transmitting system" refers to the first time the ultrasonic transmitting system is turned on and entered after it was last turned off. In some embodiments, at least one set of ultrasonic imaging history data can be ultrasonic imaging history data from the last activation to the last deactivation of the ultrasonic transmitting system. For example, if a total of 5 ultrasonic scans were performed between the last activation and deactivation of the ultrasonic transmitting system, and each scan generated 50 ultrasonic images, then the inter-frame time determination module can retrieve 50 sets of ultrasonic imaging history data from the storage device based on the trigger condition "activating the ultrasonic transmitting system".

[0127] A system parameter change refers to a change in the value of a specific parameter that meets preset requirements. For example, a system parameter change may be a change in the ultrasound examination mode, such as changing from an abdominal examination mode to a vascular examination mode. Another example is a system parameter change where the value of a specific parameter exceeds a threshold, such as a change in the number of ultrasound transmissions per frame exceeding 10%. Yet another example is a system parameter change where the number of changed feature parameters reaches a threshold, such as when the number of changed feature parameters exceeds 10. In some embodiments, at least one set of ultrasound imaging history data may be ultrasound imaging history data from the previous system parameter change to the current system parameter change. For example, when the ultrasound examination mode changes from an abdominal examination mode to a vascular examination mode, at least one set of ultrasound imaging history data may include ultrasound imaging history data stored during the abdominal examination mode.

[0128] The time interval reaching the preset value means that the time interval between the current moment and the last time at least one set of historical ultrasound data was acquired is equal to the preset duration. For example, if the preset duration is 24 hours, and the last time at least one set of historical ultrasound data was acquired was 8:00 AM on January 1, 2021, then the current moment is 8:00 AM on January 2, 2021, and the time interval is 24 hours, thus meeting the trigger condition. In some embodiments, at least one set of historical ultrasound imaging data can be historical ultrasound imaging data within the time interval. Continuing the above example, the inter-frame time determination module can, based on "the current moment is 8:00 AM on January 2, 2021," acquire historical ultrasound imaging data from the storage device within the time interval from 8:00 AM on January 1, 2021 to 8:00 AM on January 2, 2021.

[0129] Step 620: Based on the at least one set of historical ultrasound imaging data, obtain the historical imaging time.

[0130] Historical imaging time is the time required to generate a single frame of historical ultrasound image.

[0131] Specifically, the inter-frame time determination module can obtain the imaging time corresponding to each frame of historical ultrasound image based on each set of historical ultrasound imaging data.

[0132] In some embodiments, the imaging time corresponding to each frame of historical ultrasound image can be the sum of the time consumed in each step during the generation of each frame of historical ultrasound image, for example, the sum of ultrasound propagation time, imaging time, and image processing time during the generation of each frame of historical ultrasound image. For example, at least one set of historical ultrasound imaging data includes 50 sets of historical ultrasound imaging data acquired during the generation of 50 frames of ultrasound images, wherein the imaging time corresponding to the first frame of historical ultrasound image includes the sum of the ultrasound propagation time of 0.1s, the imaging time of 10s, and the image processing time of 20s during the generation of the first frame of historical ultrasound image, totaling 30.1s.

[0133] In some embodiments, the imaging time corresponding to each frame of historical ultrasound image can also be the weighted sum of the time consumed in each step during the generation of each frame of historical ultrasound image. The weight corresponding to the time consumed in each step can be determined based on the predicted growth rate of the time consumed in that step. For example, the weights corresponding to ultrasound propagation time, imaging time, and image processing time can be 1, 1.1, and 1.2, respectively, then the imaging time corresponding to the first frame of historical ultrasound image is 0.1×1 + 10×1.1 + 20×1.2 = 35.1 s.

[0134] Furthermore, the inter-frame time determination module can obtain the historical imaging time based on the imaging time corresponding to each frame of historical ultrasonic image.

[0135] In some embodiments, the historical imaging time can be the average of the imaging times of at least one frame of historical ultrasound image corresponding to at least one set of historical ultrasound imaging data. Continuing the example above, the imaging times corresponding to the 1st frame of historical ultrasound image, the 2nd frame of historical ultrasound image, the 3rd frame of historical ultrasound image, ..., the 50th frame of historical ultrasound image are 35.1s, 34.9s, 35s, ..., 34s ​​respectively. Therefore, the historical imaging time can be (35.1 + 34.9 + 35 + ... 34) / 50 = 35s.

[0136] Some embodiments in this specification directly use the average imaging time of multiple historical ultrasound images as the historical imaging time, which can improve computational efficiency. The term "50 frames" as used in this specification is only for describing specific exemplary embodiments and does not limit the scope of this specification.

[0137] In some embodiments, the inter-frame time determination module can further assign weights to the imaging time of at least one historical ultrasound image based on time. For example, the inter-frame time determination module can assign linearly increasing weights with a sum of 1 to 50 ultrasound images arranged in chronological order: 0, 0.0008, 0.0016, ..., 0.0384, 0.0392, 0.04, respectively. Then the historical imaging time can be 35.1×0 + 34.9×0.0008 + 35×0.0016 + ... + 34×0.04 = 35s.

[0138] Some embodiments in this specification assign weights to the corresponding imaging times based on the generation order of each historical ultrasound image frame. The closer the historical ultrasound image is to the current moment, the higher the weight of the corresponding imaging time, so that the value of the historical imaging time is closer to the time required to generate a current ultrasound image frame.

[0139] Step 630: Determine whether the inter-frame time and the historical imaging time meet the preset conditions.

[0140] As mentioned earlier, the inter-frame time is the interval between the emitted ultrasound waves corresponding to two adjacent frames of images. It includes the time to receive the reflected ultrasound waves (i.e., scan data) corresponding to the previous frame image from the target object, the time to generate the initial ultrasound image of the previous frame based on the reflected ultrasound waves, the time to process the initial ultrasound image to generate the final ultrasound image of the previous frame, and the time to generate the transmission command for the next frame image.

[0141] The preset condition is the condition for updating the inter-frame time. In some embodiments, the preset condition may be that the difference between the historical imaging time and the inter-frame time exceeds a time threshold. For example, the difference between the historical imaging time and the inter-frame time exceeds a time threshold of 1 second. In some embodiments, the preset condition may also be that the ratio of the difference between the historical imaging time and the inter-frame time exceeds a percentage threshold. For example, the ratio of the difference between the historical imaging time and the inter-frame time exceeds a percentage threshold of 20%.

[0142] Furthermore, if the inter-frame time and the historical imaging time meet preset conditions, the inter-frame time is updated to the historical imaging time. For example, if the current inter-frame time is 3 seconds and the historical imaging time is 2 seconds, the difference between the historical imaging time and the inter-frame time is (3-2) / 3×100%=33.3%, which exceeds the percentage threshold of 20%, then the inter-frame time is updated to 2 seconds. If the inter-frame time and the historical imaging time do not meet the preset conditions, the inter-frame time is not updated. For example, if the current inter-frame time is 3 seconds and the historical imaging time is 2.5 seconds, the difference between the historical imaging time and the inter-frame time is (3-2.5) / 3×100%=16.7%, which is less than the percentage threshold of 20%, then the inter-frame time is not updated, meaning the inter-frame time remains 3 seconds.

[0143] Some embodiments in this specification adjust the inter-frame time by comparing the inter-frame time with the historical imaging time. Specifically, when the difference between the inter-frame time and the historical imaging time is large, that is, when the current inter-frame time and the current system adaptability are poor, the adjustment is made; otherwise, no adjustment is made. This allows the inter-frame time to change dynamically with the changes in system performance, thereby obtaining high-quality ultrasound images.

[0144] Figure 7 This is an exemplary flowchart illustrating an ultrasonic pulse data transmission method according to some embodiments of this specification. Specifically, Figure 7 This can be performed by the transmission module.

[0145] As previously mentioned, the transducer of an ultrasonic probe can use electrical signals to excite array elements at different positions through the transducer channel, thereby generating ultrasonic waves of different frequencies. The magnitude and direction of the electrical signal can determine the corresponding ultrasonic wave frequency and magnitude. Each set of electrical signals can consist of multiple pulses. In some embodiments, the multiple pulses corresponding to the multiple ultrasonic waves to be emitted can be determined by the processing device 120 based on user instructions obtained from the terminal device 130. For example, the user inputs an ultrasonic examination mode "abdominal examination mode" through the terminal device 130, and the processing device 120 can determine the multiple pulses corresponding to the multiple ultrasonic waves to be emitted based on the "abdominal examination mode".

[0146] Furthermore, the processing device 120 transmits the corresponding pulse to the ultrasonic probe 110, so that the ultrasonic probe 110 generates ultrasonic waves based on the pulse. It is understood that the efficiency of pulse transmission from the processing device 120 to the ultrasonic probe 110 can affect the efficiency of ultrasonic imaging; therefore, an efficient ultrasonic pulse transmission method is required.

[0147] like Figure 7 As shown, the method 700 may include:

[0148] Step 710: Divide at least a portion of the pulses of the multiple ultrasonic waves to be emitted into a transmission group.

[0149] The multiple ultrasonic waves to be emitted can be based on an electrical signal consisting of multiple pulses. Each pulse can represent at least one of the following electrical signal values ​​per unit time: "positive," "negative," and "zero," respectively indicating "excitation of array elements with positive pressure," "excitation of array elements with negative pressure," and "no excitation of array elements," causing the array elements to vibrate differently, thereby generating ultrasonic waves of different frequencies and magnitudes. In some embodiments, the numbers "0," "1," and "2" can be used to represent "positive," "negative," and "zero," respectively. Exemplarily, the multiple pulses can include 100 pulses such as 1, 0, 2, 2, 1, 1, 2, 0, 0, 1…

[0150] Transmission groups are the basic transmission method for transmitting pulses to an ultrasonic probe.

[0151] In some embodiments, each transmission group (or pulse group) may include a fixed number of pulses, that is, each pulse group may include the same number of pulses. For example, the transmission module may divide every N pulses from a plurality of pulses into a transmission group, that is, each transmission group may include N pulses, where N≥1.

[0152] In some embodiments, the transmission module can determine the number of pulses in each pulse group based on the total number of pulses. For example, if the total number of pulses is 99, then N can be 3, and the transmission module can divide the 99 pulses into 33 transmission groups. As another example, if the total number of pulses is 100, then N can be 5, and the transmission module can divide the 100 pulses into 20 transmission groups; or N can be 4, and the transmission module can divide the 100 pulses into 25 transmission groups.

[0153] In some embodiments, the transmission module may also determine the number of pulses contained in each pulse group based on transmission efficiency. A detailed description of determining the number of pulses contained in each pulse group based on transmission efficiency can be found in step 720, and will not be repeated here.

[0154] In some embodiments, each transmission group (or pulse group) may also include a different number of pulses. For example, the transmission module may determine that each transmission group contains N pulses based on transmission efficiency, that is, divide every N pulses out of a plurality of pulses into one transmission group, and divide the remaining pulses into one or more transmission groups. For example, if the total number of pulses is 98, and the transmission module determines N to be 4 based on transmission efficiency, the transmission module may divide the 98 pulses into 24 transmission groups containing 4 pulses and 1 transmission group containing 2 pulses, or 23 transmission groups containing 4 pulses and 2 transmission groups containing 3 pulses.

[0155] Step 720: Compress the transmission group into compressed data and transmit the compressed data.

[0156] Compression is a mechanism that reduces the amount of data using specific algorithms. Compressed data is the transmitted data after compression. The size of compressed data is smaller than the size of the transmitted data.

[0157] In some embodiments, the transmission module can compress a transmission group into a single value (i.e., compress data). As mentioned earlier, each pulse in each transmission group can correspond to at least one of "positive value," "negative value," and "zero value," meaning each pulse may be one of three states. Therefore, N pulses may have 3... N One of the states (i.e., each transmission group may be one of the states).

[0158] In some embodiments, the transmission module can be 3 N The value represents the 3 corresponding to each transmission group. N Any one of the following states. For example, if N=4, then 3... 4 Each value (e.g., 1~81) represents one of the 81 states corresponding to each transmission group. For example, 1 can correspond to the transmission group pulse (0, 0, 0, 0), 2 can correspond to the transmission group pulse (0, 0, 0, 1), 3 can correspond to the transmission group pulse (0, 0, 1, 0), ..., and 81 can correspond to the transmission group pulse (2, 2, 2, 2).

[0159] In some embodiments, each pulse group may further include C state values, and correspondingly, the transmission module can use 3 N +C values ​​represent the 3 corresponding to each transmission group N Any of the +C states. In some embodiments, each state value may represent parameters such as transducer T / R switching, control gain change, and recording system errors.

[0160] In some embodiments, the compressed data corresponding to each transmission group can be determined by formula (7):

[0161] (7)

[0162] in, , ... , Each of the three states corresponding to the N pulses in the transmission group can be represented by a value in {0, 1, 2}; c represents one of the C state values; and x represents the compressed data corresponding to the transmission group.

[0163] For example, N=4, C=2, and c takes the value 0 or 1, representing the transducer switching to T mode and R mode respectively. Then, 100 pulses can be divided into: (1, 0, 2, 2), (1, 1, 2, 0), (0, 1…., and each pulse group can be compressed into 3… 4 + One of the two compressed data sets, the compressed data obtained by compressing the first transmission group (1, 0, 2, 2) is: x1= =27×1+9×0+3×2+1×2+0=35; The compressed data obtained from compressing the second transmission group (1, 1, 2, 0) is: x2= =27×1+9×1+3×2+1×0+1=43;….

[0164] In another example, N=5, C=4, and c takes values ​​of 1, 2, 3, and 4, representing (transducer switches to T mode, system has no error), (transducer switches to T mode, system has error), (transducer switches to R mode, system has no error), and (transducer switches to R mode, system has error), respectively. Then, 100 pulses can be divided into: (1, 0, 2, 2, 1), (1, 2, 0, 0, 1)..., and each pulse group can be compressed into 3... 5 + One of the four compressed data sets. The compressed data obtained by compressing the first transmission group (1, 0, 2, 2, 1) is: x1= =81×1+27×0+9×2+3×2+1×1+4=110; The compressed data obtained from compressing the second transmission group (1, 2, 0, 0, 1) is: x2= =81×1+27×2+9×0+3×0+1×1+3=119;….

[0165] In some embodiments, the transmission module can be based on 3 corresponding to each transmission group. N +C states determine the size of the compressed data. Specifically, each byte can represent two states, and the transmission module is based on... Rounding up gives 3. N +C states correspond to the size of the compressed data.

[0166] For example, if N=4 and C=2, then the size of the compressed data corresponding to each transmission group is... Rounded up, that is, 7 bits. For example, if N=5 and C=4, then the size of the compressed data corresponding to each transmission group is... Round up to the nearest 8 bits.

[0167] As mentioned earlier, the transmission module can also determine the number of pulses in each pulse group based on transmission efficiency. For example, if the transmission efficiency is highest when the compressed data size is 8 bits, the transmission module can determine that each pulse group contains 5 pulses.

[0168] Furthermore, the transmission module can transmit compressed data corresponding to multiple transmission groups to the ultrasonic probe 110 via network 140. For example, the transmission module can transmit compressed data 110, 119, ... corresponding to transmission groups (1, 0, 2, 2, 1), (1, 2, 0, 0, 1), ... to the ultrasonic probe 110.

[0169] Step 730: Decode the received compressed data to obtain the at least partial pulse.

[0170] Decoding is the process of restoring the compressed data received by the ultrasonic probe to the corresponding transmission group. Specifically, the transmission module can decode the received compressed data based on the received compressed data and the compression method. In some embodiments, the transmission group corresponding to each compressed data can be determined by formula (8):

[0171] (8)

[0172] in, This represents the value corresponding to the pulse state in the transmission group. The values ​​are {0, 1, 2}, k is [0, N-1], and N is the number of pulses in each transmission group.

[0173] For example, compressed data x1=110 based on N=5, C=4, can obtain the value corresponding to the pulse state in the transmission group. That is, obtain the corresponding transmission group (1, 0, 2, 2, 1).

[0174] Furthermore, the transmission module can acquire at least a portion of the pulses based on multiple transmission groups.

[0175] The beneficial effects that the embodiments of this specification may bring include, but are not limited to: (1) mapping multiple first relative positions with equal intervals corresponding to multiple ultrasonic waves to multiple second relative positions with non-equal intervals based on curves, and designing the focal trajectory of ultrasonic waves with dense focal points on both sides based on the multiple second relative positions with non-equal intervals and the curvature of the transducer, which can compensate for the low resolution of ultrasonic image edges caused by energy loss on both sides of the ultrasonic probe, and at the same time design the focal trajectory of ultrasonic waves with dense focal points in the middle for convex array ultrasonic probes to improve the resolution of ultrasonic images of target objects at depth; (2) dynamically adjusting the inter-frame interval based on ultrasonic imaging historical data, so that the inter-frame time can change dynamically with the change of system performance, thereby obtaining high-quality ultrasonic images; (3) dividing the pulse into transmission groups for compression and transmission based on transmission efficiency, which can improve transmission efficiency based on different bandwidths, thereby improving the efficiency of ultrasonic imaging. It should be noted that different embodiments may produce different beneficial effects. In different embodiments, the beneficial effects that may be produced can be any one or a combination of the above, or any other possible beneficial effects.

[0176] The basic concepts have been described above. Obviously, for those skilled in the art, the detailed disclosure above is merely illustrative and does not constitute a limitation of this specification. Although not explicitly stated herein, those skilled in the art may make various modifications, improvements, and corrections to this specification. Such modifications, improvements, and corrections are suggested in this specification and therefore remain within the spirit and scope of the exemplary embodiments described herein.

[0177] Furthermore, this specification uses specific terms to describe embodiments thereof. For example, "an embodiment," "one embodiment," and / or "some embodiments" refer to a particular feature, structure, or characteristic associated with at least one embodiment of this specification. Therefore, it should be emphasized and noted that references to "an embodiment," "one embodiment," or "an alternative embodiment" in different locations throughout this specification do not necessarily refer to the same embodiment. Moreover, certain features, structures, or characteristics in one or more embodiments of this specification can be appropriately combined.

[0178] Furthermore, those skilled in the art will understand that various aspects of this specification can be described and illustrated in several patentable ways or situations, including any new and useful combination of processes, machines, products, or substances, or any new and useful improvements thereof. Accordingly, various aspects of this specification can be implemented entirely by hardware, entirely by software (including firmware, resident software, microcode, etc.), or by a combination of hardware and software. All of the above hardware or software may be referred to as a “data block,” “module,” “engine,” “unit,” “component,” or “system.” Furthermore, various aspects of this specification may be represented as a computer product located on one or more computer-readable media, including computer-readable program code.

[0179] Computer storage media may contain a propagated data signal containing computer program code, for example, on baseband or as part of a carrier wave. This propagated signal may take various forms, including electromagnetic, optical, and suitable combinations thereof. Computer storage media can be any computer-readable medium other than a computer-readable storage medium, which can be connected to an instruction execution system, apparatus, or device to enable communication, propagation, or transmission of a program for use. The program code located on the computer storage medium can be propagated through any suitable medium, including radio, cable, fiber optic cable, RF, or similar media, or any combination of the above media.

[0180] The computer program code required for the operation of each part of this manual can be written in any one or more programming languages, including object-oriented programming languages ​​such as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C++, C#, VB.NET, Python, etc.; conventional procedural programming languages ​​such as C, Visual Basic, Fortran2003, Perl, COBOL2002, PHP, ABAP; dynamic programming languages ​​such as Python, Ruby, and Groovy; or other programming languages. This program code can run entirely on the user's computer, or as a standalone software package on the user's computer, or partially on the user's computer and partially on a remote computer, or entirely on a remote computer or processing device. In the latter case, the remote computer can be connected to the user's computer through any network, such as a local area network (LAN) or wide area network (WAN), or connected to an external computer (e.g., via the Internet), or in a cloud computing environment, or used as a service such as Software as a Service (SaaS).

[0181] Furthermore, unless expressly stated in the claims, the order of processing elements and sequences, the use of numbers and letters, or other names described in this specification are not intended to limit the order of the processes and methods described herein. Although various examples have been discussed in the foregoing disclosure of some embodiments of the invention that are currently considered useful, it should be understood that such details are for illustrative purposes only, and the appended claims are not limited to the disclosed embodiments; rather, the claims are intended to cover all modifications and equivalent combinations that conform to the spirit and scope of the embodiments described herein. For example, while the system components described above can be implemented by hardware devices, they can also be implemented solely by software solutions, such as installing the described system on existing processing devices or mobile devices.

[0182] Similarly, it should be noted that, in order to simplify the description disclosed herein and thus aid in the understanding of one or more embodiments of the invention, the foregoing description of embodiments in this specification may sometimes combine multiple features into a single embodiment, drawing, or description thereof. However, this method of disclosure does not imply that the subject matter of this specification requires more features than those mentioned in the claims. In fact, the embodiments contain fewer features than all the features of a single embodiment disclosed above.

[0183] In some embodiments, numbers describing the quantity of components and attributes are used. It should be understood that such numbers used in the description of embodiments are modified in some examples with the terms "approximately," "approximately," or "generally." Unless otherwise stated, "approximately," "approximately," or "generally" indicates that the numbers are allowed to vary by ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximate values, which may be changed depending on the characteristics required by individual embodiments. In some embodiments, numerical parameters should take into account specified significant digits and employ a general method of digit reservation. Although the numerical ranges and parameters used to confirm their breadth of range in some embodiments of this specification are approximate values, in specific embodiments, such values ​​are set as precisely as feasible.

[0184] For each patent, patent application, patent application publication, and other material such as articles, books, specifications, publications, and documents referenced in this specification, the entire contents of which are incorporated herein by reference. This excludes historical application documents that are inconsistent with or conflict with the content of this specification, as well as documents that limit the broadest scope of the claims in this specification (currently or subsequently appended to this specification). It should be noted that in the event of any inconsistency or conflict between the descriptions, definitions, and / or terminology used in the supplementary materials to this specification and the content of this specification, the descriptions, definitions, and / or terminology used in this specification shall prevail.

[0185] Finally, it should be understood that the embodiments described in this specification are merely illustrative of the principles of the embodiments described herein. Other variations may also fall within the scope of this specification. Therefore, alternative configurations of the embodiments described herein are intended to be illustrative rather than limiting, and should be considered consistent with the teachings of this specification. Accordingly, the embodiments described herein are not limited to those explicitly introduced and described herein.

Claims

1. A method for transmitting ultrasonic waves, characterized in that, The method includes: Based on the triggering conditions, acquire at least one set of historical ultrasound imaging data; Based on the at least one set of historical ultrasound imaging data, the historical imaging time is obtained; the historical imaging time is the time required to generate a frame of historical ultrasound image. Determine whether the inter-frame time and the historical imaging time meet preset conditions. The inter-frame time is the interval between the emitted ultrasound corresponding to two adjacent frames. The preset conditions are that the difference between the historical imaging time and the inter-frame time exceeds a time threshold, or the ratio of the difference between the historical imaging time and the inter-frame time exceeds a percentage threshold. If so, the inter-frame time is updated to the historical imaging time; If not, the inter-frame time will not be updated.

2. The method as described in claim 1, characterized in that, The triggering conditions include at least one of the following: activating the ultrasonic transmitting system, changing system parameters, and the time interval reaching a preset value.

3. The method as described in claim 2, characterized in that, The system parameter change is a change in the value of a specific parameter that meets preset requirements; the preset requirements include at least one of the following: a change in the ultrasound examination mode, a change in the value of the specific parameter exceeding a threshold, and a number of changed feature parameters reaching a threshold.

4. The method as described in claim 1, characterized in that, The at least one set of historical ultrasound imaging data includes ultrasound propagation time, imaging time, and image processing time. The historical imaging time is the sum or weighted sum of the ultrasound propagation time, imaging time, and image processing time during the generation of each frame of historical ultrasound image.

5. The method as described in claim 4, characterized in that, The ultrasonic propagation time includes the time for generating the transmission command, which includes at least the focal trajectory of the ultrasonic wave transmission.

6. The method as described in claim 1, characterized in that, The step of obtaining the historical imaging time based on the at least one set of historical ultrasound imaging data includes: Based on each set of ultrasound imaging historical data in the at least one set of ultrasound imaging historical data, obtain the imaging time corresponding to each frame of historical ultrasound image. The historical imaging time is obtained based on the imaging time corresponding to each frame of the historical ultrasound image.

7. An ultrasonic transmitting system, characterized in that, The system includes an inter-frame time determination module, used for: Based on the triggering conditions, acquire at least one set of historical ultrasound imaging data; Based on the at least one set of historical ultrasound imaging data, the historical imaging time is obtained; the historical imaging time is the time required to generate a frame of historical ultrasound image. Determine whether the inter-frame time and the historical imaging time meet preset conditions. The inter-frame time is the interval between the emitted ultrasound corresponding to two adjacent frames. The preset conditions are that the difference between the historical imaging time and the inter-frame time exceeds a time threshold, or the ratio of the difference between the historical imaging time and the inter-frame time exceeds a percentage threshold. If so, the inter-frame time is updated to the historical imaging time; If not, the inter-frame time will not be updated.

8. The system as described in claim 7, characterized in that, The inter-frame time determination module is further used for: Based on each set of ultrasound imaging historical data in the at least one set of ultrasound imaging historical data, obtain the imaging time corresponding to each frame of historical ultrasound image. The historical imaging time is obtained based on the imaging time corresponding to each frame of the historical ultrasound image.

9. A computer-readable storage medium storing computer instructions, wherein when a computer reads the computer instructions, the computer executes the ultrasonic emission method as described in any one of claims 1-6.

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