JP2019154654A - Ultrasonic imaging device and ultrasonic image processing system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To acquire and measure an image of a predetermined cross section of a subject in a short time and accurately regardless of the skill of the user. SOLUTION: A first processing unit generates images of different cross sections of a subject in chronological order by receiving a received signal output by an ultrasonic probe that has received ultrasonic waves from the subject. The frame determination unit determines whether or not the image generated by the first processing unit is an image of a predetermined target cross section of the subject for each image generated in time series. When the frame determination unit determines that the image generated by the first processing unit is an image of a target cross section, the second processing unit receives the image and at least one of the original received signals from which the image was generated. Perform a predetermined process. [Selection diagram] Fig. 1

Description

  The present invention relates to an ultrasound imaging technique for capturing an image in a subject using ultrasound.

The ultrasound imaging technique is a technique for non-invasively imaging the inside of a subject such as a human body using ultrasound (a sound wave not intended to be heard, generally a sound wave having a high frequency of 20 kHz or higher). It is.
A medical ultrasonic imaging apparatus has a function of imaging or measuring the inside of a human body using an ultrasonic imaging technique. For example, B-mode imaging that displays the reflection intensity of ultrasonic waves inside the human body as a black and white image, Doppler measurement that measures blood flow velocity in the blood vessel using the ultrasonic Doppler effect, and tissue from the acquired B-mode image It has a function to acquire the morphological or dynamic characteristics of a living body by the B mode and measurement application and to present it to a doctor or an engineer, such as tracking the movement of the heart and measuring the contraction / expansion index of the heart. Thereby, medical diagnosis by a doctor can be assisted.

  A user such as a doctor or an engineer who uses a medical ultrasonic imaging apparatus generates the time-series data in real time by the apparatus while holding the ultrasonic probe of the apparatus with one hand and moving it on the body surface of the subject. An ultrasonic image such as a B-mode image or a Doppler measurement image is observed on a monitor, and diagnosis is performed on the spot based on the displayed ultrasonic image or the like. Further, the user stops the movement of the ultrasonic probe at a desired position, and presses the freeze button on the operation panel with the hand opposite to the hand holding the ultrasonic probe, and the display is displayed. The ultrasonic image is stopped (freeze mode), the still image is stored, a predetermined part of the subject is measured on the still image, and imaging conditions are adjusted.

  In Patent Document 1, while the user operates the freeze button to switch to the freeze mode and displays a still image, additional processing is performed on the received data that is the source of the still image, A system that generates and displays an image with higher resolution than a still image is disclosed.

Japanese Patent No. 5814646

  As described above, a medical ultrasonic imaging apparatus observes ultrasonic images displayed on a monitor in real time in a time series while a user grasps an ultrasonic probe with one hand and moves it on the body surface of the subject. Diagnosis is performed on the spot, the ultrasonic probe is stopped at a desired position, and the operation panel is operated with the opposite hand to store necessary images and measurement results. For this reason, the user needs to learn the anatomical knowledge to determine the route to move the ultrasound probe on the body surface and the position to stop, the operation method of the device to perform the necessary measurements, Advanced skills such as knowledge of imaging conditions are required. Specifically, for example, in the case of fetal ultrasonography, the sizes of a plurality of parts such as BPD (child head large lateral diameter), FL (femoral length), and AC (abdominal circumference) are measured. It is necessary to measure on an appropriate cross-sectional image. In the case of echocardiography, short-axis images, long-axis images, and apical four-chamber images, LAD (left atrial diameter), RVD (right atrial diameter), AOD (aortic diameter), IVC (lower) The size of a large number of parts such as the vena cava diameter and IVST (ventricular septal thickness) is measured on an image of a predetermined cross section. Since the position and orientation of the cross section for measuring these items are determined by guidelines such as academic societies, the user knows these many measurement items and the position and orientation of the measurement cross section, and the ultrasonic probe Must be moved to that position and stopped exactly.

  In this way, the user is required to be familiar with anatomical knowledge and operation of the ultrasonic imaging apparatus and setting of imaging conditions, so that examination time, image quality, and examination accuracy depend on user skills. There is a problem of being.

  An object of the present invention is to perform image acquisition and measurement of a predetermined cross section of a subject with high accuracy in a short time regardless of the skill of a user.

  In order to achieve the above object, in the ultrasonic imaging apparatus of the present invention, a reception signal output from an ultrasonic probe that receives ultrasonic waves from a subject is received, and images of different cross-sections of the subject are time-series. A first processing unit to be generated, a frame determination unit for determining whether the image generated by the first processing unit is an image of a predetermined target cross section of the subject for each image generated in time series, When the frame determination unit determines that the image generated by the first processing unit is an image of the target cross section, the frame determination unit performs predetermined processing on at least one of the image and the original reception signal from which the image is generated A second processing unit.

  According to the present invention, it is possible to acquire and measure an image of a predetermined cross section of a subject accurately in a short time regardless of the skill of the user.

1 is a block diagram of an ultrasonic imaging apparatus according to the first embodiment. The flowchart which shows operation | movement of the ultrasonic imaging apparatus of 1st Embodiment. Block diagram of an ultrasonic imaging apparatus according to the second embodiment The flowchart which shows operation | movement of the frame determination part and 2nd process part of 2nd Embodiment. The flowchart which shows detailed operation | movement of the one part step of FIG. (A) And (b) The figure which illustrates the objective cross section of 2nd Embodiment The figure which illustrates operation | movement of the background measurement in the ultrasonic imaging device of 3rd Embodiment The figure which illustrates the setting screen in the ultrasonic imaging device of 3rd Embodiment The figure which illustrates the target section and measurement contents corresponding to the setting screen of FIG. The flowchart which shows a part of operation | movement of the control part of 3rd Embodiment. The figure which illustrates the operation | movement which optimizes the imaging parameter in the ultrasonic imaging device of 4th Embodiment The figure which illustrates the table which a 2nd processing part generates in a 4th embodiment. The flowchart which illustrates the operation | movement of the optimization of the imaging parameter of a 2nd process part in 4th Embodiment. The figure which illustrates the contrast judgment part and resolution judgment part which were set to the picture in a 4th embodiment The flowchart which illustrates the calculation operation of the image quality improvement contribution ratio in the fourth embodiment

  An ultrasonic imaging apparatus according to an embodiment of the present invention will be described.

<< First Embodiment >>
The ultrasonic imaging apparatus according to the first embodiment will be described with reference to FIGS. 1 and 2. FIG. 1 is a block diagram of an ultrasonic imaging apparatus 100 according to the first embodiment. FIG. 2 is a flowchart showing the operation of the ultrasonic imaging apparatus.

  As shown in FIG. 1, the ultrasonic imaging apparatus 100 according to the first embodiment includes a first processing unit 1, a frame determination unit 3, and a second processing unit 2. An ultrasonic probe 4 is connected to the first processing unit 1. The ultrasonic probe 4 irradiates the subject 5 with ultrasonic waves and receives ultrasonic waves such as reflected waves, transmitted waves, and scattered waves returning from the subject 5.

  The operation of each part of the ultrasonic imaging apparatus 100 will be described with reference to the flowchart of FIG.

  First, the first processing unit 1 receives a reception signal output from the ultrasonic probe 4 that has received an ultrasonic wave from the subject 5, and generates a cross-sectional image of the subject 5 in time series (step 201). ).

  Next, the frame determination unit 3 determines whether the image (frame) generated by the first processing unit 1 is an image of a predetermined target cross section of the subject 5 (step 202). The target cross section is an anatomically predetermined cross section according to a guideline such as an academic society. For example, the frame determination unit 3 may determine whether the image is a target slice image for each image generated by the first processing unit 1 in time series, or 1 for every predetermined number of images (for example, five images). One image may be selected to determine whether the image is a target cross-sectional image.

  When the frame determination unit 3 determines that the image generated by the first processing unit 1 is an image of the target cross section, the second processing unit 2 applies at least one of the image and the reception signal that is the origin of the image. On the other hand, predetermined processing is performed (step 203).

  The predetermined process performed by the second processing unit may be any process. For example, in the image of the target cross section, processing that measures the size, area, etc. of the site of the subject 5 that is predetermined according to the target cross section, or higher than the image of the target cross section generated by the first processing unit 1. The second processing unit 2 can perform a process for generating an image with a resolution and a process for obtaining an imaging condition for improving the image quality (for example, contrast and resolution) of the image of the target cross section.

  The processing of the second processing unit 2 can be performed in parallel with the image generation processing of the first processing unit 1 or can be performed by stopping the image generation processing of the first processing unit 1. When the processing by the second processing unit 1 is performed in parallel with the image generation processing by the first processing unit, the second processing unit displays the time-series images generated by the first processing unit 1 on the display unit 6. 2 can be performed. As a result, the user can continue the operation of moving the ultrasound probe 4 on the surface of the subject 5, so that the user can continue to observe the images generated in time series by the first processing unit 1. The processing by the second processing unit 2 can be executed on the ground, and the processing result can be acquired.

  On the other hand, when the image processing of the first processing unit 1 is stopped and the processing of the second processing unit 2 is performed, the user stops the movement of the ultrasonic probe 3 and observes a still image as desired. A process can be selected, and the second processing unit 2 can execute a process in accordance with a user instruction.

  For example, the frame determination unit 3 extracts the feature amount of the image generated by the first processing unit 1 in order to determine whether the image generated by the first processing unit 1 is an image of the target cross section. Further, it is possible to adopt a configuration in which a predetermined feature amount or a feature amount obtained in advance for an image of the target cross section is compared.

  In the ultrasonic imaging apparatus according to the present embodiment, since the frame determination unit determines whether the generated image is an image of the target cross section, the superimposition of a predetermined cross section of the subject is not dependent on the anatomical knowledge or skill of the user. Acquisition and measurement of a sound wave image can be performed.

  Specifically, for example, while the user is operating the ultrasound probe 4, the user adjusts the target cross section to a preferable imaging condition in the background without performing image adjustment or measurement through button operation or the like. The acquired image can be acquired and necessary measurement can be performed. It is also possible to acquire and measure a still image on a target cross section according to a user instruction instead of the background. Therefore, it is possible to greatly improve the burden on the user's operation and the inspection time.

  In addition, since the first processing unit 1 and the second processing unit 2 can perform image generation and signal processing in parallel at this time, the user always confirms the imaging cross section on the display unit in real time and performs ultrasonic search. The operation of the touch element 4 can be continued.

  Hereinafter, specific embodiments of the ultrasonic imaging apparatus of the present embodiment will be described.

<< Second Embodiment >>
An ultrasonic imaging apparatus according to the second embodiment will be described. In this ultrasonic imaging apparatus, in parallel with the first processing unit 1 performing image generation processing in time series, the second processing unit 2 automatically executes measurement processing based on the frame determination result. At that time, the second processing unit 2 notifies the user of the measurement result by display on the display unit 6 or the like.

  The ultrasonic imaging apparatus of the second embodiment includes a memory 17 in addition to the first processing unit 1, the frame determination unit 3, and the second processing unit similar to the ultrasonic imaging apparatus of FIG. 1 of the first embodiment. It has more. Hereinafter, specific configurations of these units will be described.

<First processing unit 1>
First, the configuration and processing contents of the first processing unit 1 will be described with reference to FIG. As shown in FIG. 3, the first processing unit 1 includes a transmission beamformer 11, a reception unit 12, a reception beamformer 13, a signal processing unit 14, a back-end processing unit 15, a transmission / reception switching unit 18, A control unit 16 that controls the whole, a user interface 19, and a control unit 16 are provided. The configuration and operation of the first processing unit 1 are the same as those of a known ultrasonic imaging apparatus, and will be briefly described below.

  The transmission beamformer 11 generates a transmission signal (electrical signal) according to a predetermined imaging condition that determines a transmission focus received from the user via the user interface 19, and performs an ultrasonic probe via the transmission / reception switching unit 16. Output to each ultrasonic element of the child 4. Each ultrasonic element of the ultrasonic probe 4 converts a transmission signal into an ultrasonic wave and outputs it. Thereby, an ultrasonic beam is transmitted from the ultrasonic probe 4 to the imaging region of the subject 5.

  Next, ultrasonic waves (echoes, scattered waves, etc.) return to the ultrasonic probe 4 from the imaging region that has received the transmission of the ultrasonic beam. Each ultrasonic element of the ultrasonic probe 4 receives this and converts it into a received signal (electric signal). The received signal is sent to the receiving unit 12.

  The receiving unit 12 converts the received voltage of the ultrasonic element into a digital signal having a constant sampling period by analog / digital conversion (ADC). Further, the receiving unit 12 has a data interface, converts a digital signal into a transmission standard for sending to a reception beamformer, and controls timing. As a result, the reception unit 12 converts the reception signal of each ultrasonic element into digital reception channel data and transmits the digital reception channel data to the reception beam former 13 and the memory unit 17.

  The reception beamformer 13 processes the reception channel data to generate imaging data for a plurality of reception focal points set in the imaging region according to the imaging conditions. In general, the reception focal points are densely arranged along one or more lines for each irradiation range of the transmission beam. The arrangement interval (cycle) of the plurality of reception focal points in the line is the same as the reception sampling interval or an interval thinned out several times. Such imaging data generated on one or more lines per transmission is called reception line data.

  As a processing method for generating the reception line data from the reception channel data, any method may be used. For example, a delay addition method may be used. The delay addition method is a method of adding reception channel signals after delaying reception channel data for each ultrasonic element to adjust the phase. The delay amount of the reception channel data for each ultrasonic element is the ultrasonic element of the time required for the ultrasonic echo reflected by the tissue at the reception focus position in the imaging region to reach each ultrasonic element in the same phase. Each time difference is set in advance to be equal. The amount of delay differs for each reception focus, and the process of delaying and adding each reception channel data is repeated for each reception focus. For this reason, the delay amount given to each reception channel data is changed with time in the sampling period of the reception focus. The generation of imaging data by repeating the delay and addition processes while changing the reception focus over time along the reception line is called dynamic focus. By dynamic focusing, a uniform reception beam (reception line data) having a predetermined beam width is virtually formed from a shallow part to a deep part of the imaging region.

  Next, the signal processing unit 14 performs various signal processing necessary according to the imaging / measurement mode. As the signal processing, for example, bandpass filter processing or lowpass filter processing for removing components other than the target frequency component is performed for the purpose of improving the SN ratio (signal noise ratio) of the reception line data. The amplitude value of the reception line data is converted into IQ data composed of an I component that is a real part and a Q component that is an imaginary part by orthogonal detection processing. As a result, the amplitude component displayed in the B mode and the phase component used in Doppler measurement can be detected.

  Further, the signal processing unit 14 can perform synthetic aperture aperture (STA). Aperture synthesis imaging is one of the B-mode imaging methods, and by synthesizing received signals between a plurality of transmissions, a transmission aperture can be virtually enlarged to obtain a high-resolution image. That is, in aperture synthesis imaging, the signal processing unit 14 coherently synthesizes reception line data at the same position obtained by a plurality of different transmissions. An image of one frame is formed using the received line data after combining.

  The signal processing unit 14 can also obtain a high-resolution image by compound processing. In general, an image composed of received line data that has not been subjected to aperture synthesis is called a low resolution image (LRI). In the compound processing, the signal processing unit 14 incoherently adds the low resolution images respectively generated by N different transmissions to the same reception focal point where the reception areas overlap, thereby obtaining a high resolution image (HRI). Is generated. Since the compound process is an incoherent combining process in which the amplitude value is added at the reception focal point, an effect that the SN ratio increases N times corresponding to the number N of combining is obtained. Therefore, a high SN ratio and high resolution image can be obtained. In addition, in the compound processing, there is a case where addition is performed after a weight (LRI weight) corresponding to the reception focus position is given for the purpose of making the synthesis effect uniform.

  As described above, the signal processing unit 14 performs various signal processing such as filter processing, quadrature detection processing, and compound processing on the reception line data generated by a plurality of transmission beams according to the imaging / measurement mode.

  The back-end processing unit 15 performs image processing and measurement / analysis processing for each imaging / measurement mode using IQ data generated by the signal processing unit 14. Thus, measurement data such as a B-mode image to be displayed on the display unit 6, a Doppler measurement speed spectrum, a color flow image, and an elastic modulus of elastography are generated.

  For example, as the B-mode image processing, the back-end processing unit 15 performs an interpolation process on the imaging data arranged in the reception line direction and the line depth direction, so that an XZ actual image of the imaging section is obtained. Convert to spatial coordinates (scan conversion process).

  Further, for example, in Doppler measurement, the back-end processing unit 15 uses the continuous time-phase IQ data obtained by irradiating the transmission beam in the same direction a plurality of times, and changes the phase components thereof. Calculate and convert the phase rotation amount to the moving speed. Thereby, the back end process part 15 measures velocity components, such as a blood flow.

  The B-mode image data and measurement data for each frame generated by the back-end processing unit 15 are called cine data. The display unit 6 receives a plurality of cine data and displays them as moving images.

  As described above, the first processing unit 1 repeats transmission / reception of ultrasonic waves and processes reception channel data in real time, thereby displaying an ultrasonic tomographic image or an ultrasonic measurement result on the display unit in real time.

<Memory unit 17>
The memory unit 17 receives and stores the reception channel data sampled by the reception unit 12, the reception line data generated by the first processing unit 1, and the cine data generated by the back-end processing unit 15. Unnecessary data is deleted under the control of the second processing control unit 22 of the processing unit 2.

  In the present embodiment, the memory unit 17 is arranged outside the first processing unit 1 and the second processing unit 2, but may be arranged inside the first processing unit 1 or the second processing unit 2. For example, the first processing unit 1 may have a RAM as a memory, and the second processing unit 2 may have an on-chip memory arranged on a processor (for example, a GPU) that configures the RAM.

  The memory unit 17 may be arranged on a memory server. In this case, the first processing unit 1 and the second processing unit 2 access the memory unit 17 on the common memory server.

<Frame determination unit 3>
The frame determination unit 3 sequentially outputs the cine data sequentially output in time series by the first processing unit 1, and determines whether the imaging section of the frame (image) is the target section. In the case of the target cross section, the second processing unit 2 executes the process. If it is not the frame of the target section, the processing in the second processing unit 2 is not executed. It is desirable that the timing at which the frame determination unit 3 reads the cine data stored in the memory unit 17 is immediately after it is stored in the memory unit 17 in order to perform determination in real time. However, when the process of the second processing unit 2 is a process that does not require real-time processing, it may not be immediately after being stored in the memory unit 17. The operation of the frame determination unit 3 will be described in detail later.

<Second processing unit 2>
Next, the second processing unit 2 will be described. The second processing unit 2 includes a second processing control unit 22, a calculation analysis processing unit 20, and an analysis unit 26. In the present embodiment, the calculation analysis processing unit 20 includes a reception beam former 23, a signal processing unit 24, a back-end processing unit 25, and an analysis unit 26. However, the calculation analysis processing unit 20 is configured to perform desired calculation analysis processing. One or more may be arranged.

  The second processing control unit 22 receives the result of the frame determination unit 3 and controls the calculation analysis processing executed by the calculation analysis processing unit 20.

  The calculation analysis processing unit 20 receives at least one of the reception channel data, reception line data, and cine data stored in the memory unit 17 via the second processing control unit 22 and performs calculation analysis processing. The processing by the calculation analysis processing unit 20 is executed in parallel with the processing by the first processing unit 1. Specifically, the calculation analysis processing unit 20 performs reception beam forming processing such as delay addition processing, signal processing such as quadrature detection, aperture synthesis, and compound processing, and various back-end processing such as image generation and velocity measurement. At least one of the processes is performed. Thereby, for example, the reception beamformer 23, the signal processing unit 24, and the back-end processing unit 15 of the calculation analysis processing unit 20 generate a B-mode image with higher image quality than the B-mode image generated by the first processing unit 1. Also, desired data such as LRI data in the middle of B-mode image generation, Doppler velocity data, and the like are generated. For example, the analysis unit 26 calculates the resolution and contrast of the B-mode image generated by the first processing unit 1 or the B-mode image output from the back-end processing unit 25, analyzes LRI data and velocity measurement data, and improves image quality. The second processing control unit 22 performs calculation and analysis of at least one evaluation index such as calculation of an imaging parameter that contributes to the image, and the calculation result and the analysis result together with a high-quality B-mode image generated as necessary. To give feedback.

  The second processing control unit 22 stores at least one or more of the B-mode image with improved image quality received from the calculation analysis processing unit 20, speed data, imaging parameters that contribute to image quality improvement, and the like. Returned to the unit 17 for storage. In a predetermined case such as when the image quality has not reached the desired evaluation value, the second processing control unit 22 changes the processing conditions to the calculation analysis processing unit 20 to further generate a B-mode image. It is also possible to do this.

  In addition, the 2nd process part 2 may be incorporated in the ultrasonic imaging device main body similarly to the 1st process part 1, and may be attached externally. Alternatively, the second processing unit 2 may be arranged on a server different from the main body so as to exchange data with the main body through a network.

  The functions of the first processing unit 1, the frame determination unit 3, and the second processing unit 2 can be realized by software, or part or all of the functions can be realized by hardware. is there. When realized by software, the first processing unit 1, the frame determination unit 3, and the second processing unit are configured by a computer system incorporating a processor such as a CPU (Central Processing Unit) or a GPU (Graphics Processing Unit). The functions of the respective units are realized by reading and executing a program stored in advance in the memory 16. Further, when realized by hardware, the first processing unit 1 and the frame determination unit using a custom IC such as an application specific integrated circuit (ASIC) or a programmable IC such as a field-programmable gate array (FPGA). 3 and the second processing unit 2 are configured, and circuit design may be performed so as to realize the operation.

  Thus, in the present embodiment, the first processing unit 1 and the second processing unit 2 can perform beam forming and signal processing in parallel. In addition, since the frame determination unit 3 determines whether the second processing unit 2 is a frame of a target cross section for which processing such as image adjustment and measurement is performed, the frame determination unit 3 does not depend on the anatomical knowledge or skill of the user, and The frame determination unit 3 can select an image of the determined target cross section and perform measurement or the like.

  In addition, the user continues the operation of the ultrasound probe 4 while observing the image generated by the first processing unit 1 in real time on the display unit 6 and confirming the imaging section, while the frame determination unit 3 For the frame determined to be the target cross section, the second processing unit 2 can automatically perform image adjustment and measurement.

<Examples of Specific Operations of Frame Determination Unit 3 and Second Processing Unit>
An example of operations of the frame determination unit 3 and the second processing unit 2 of the present embodiment will be specifically described. 4 is a flowchart showing operations of the frame determination unit 3 and the second processing unit 2, FIG. 5 is a flowchart showing details of the operation of the frame determination unit 3, and FIG. FIG. 6B is a diagram showing an example in which the target cross section is a predetermined cross section of the heart.

  Examples of the target cross section include a fetal head cross section, an abdominal cross section, and a femoral cross section observed in a fetal echo diagnosis as shown in FIG. 6A, and a heart as shown in FIG. 6B. There are the apical four-chamber section, the apex two-chamber section, the short-axis mitral valve level, etc. observed in the echo diagnosis. The cross section to be observed or measured in the ultrasonic diagnosis is anatomically determined according to academic guidelines.

  The user moves the ultrasonic probe 4 on the surface of the subject 5, and accordingly, the first processing unit 1 generates images (cine data) in real time in time series, and the generated cine data is stored in the memory unit 17. Are stored sequentially.

  In step 401 of FIG. 4, the frame determination unit 3 reads the nth frame of cine data stored in the memory unit 17. Then, it is determined whether or not the read frame n is an image of the target cross section (steps 402 and 403). In order to perform the processing of the second processing unit 2 in real time, it is desirable that the frame determination unit 3 reads out the frame n immediately after it is stored in the memory unit 17 by the first processing unit 1.

  Detailed processing in steps 402 and 403 will be described with reference to FIG. Here, an example in which the frame determination unit 3 performs determination by feature amount analysis will be described. That is, whether or not the frame n is the target cross section is determined based on the degree of coincidence between the feature amount obtained for one or more images prepared in advance for the target cross section X and the feature amount with the frame n. The one or more images prepared in advance may be from the same subject 5 or from different subjects. The feature amount is, for example, an artificially set feature amount such as luminance distribution analysis or edge shape analysis, or an abstract extracted from one or more images of the target cross section X prepared in advance by a machine learning method. Characteristic features are used. A predetermined plurality of feature amounts (for example, luminance distribution, edge shape, abstract feature amount) are analyzed with respect to one or more target cross-sectional images prepared in advance, and a feature amount map is obtained in advance.

  When there are a plurality of target cross sections as shown in FIG. 6A or FIG. 6B, a feature amount map is obtained for each target cross section X, Y, Z.

  The frame determination unit 3 analyzes the plurality of predetermined feature amounts for the frame n and generates a feature amount map (step 501 in FIG. 5). Next, the generated feature map of the frame n is collated with a feature amount map of an image of a target cross section prepared in advance, and a coincidence rate is calculated. A method using a cross-correlation value or the like is used for calculating the coincidence rate (step 502). When the coincidence rate exceeds a preset threshold value, it is determined that the frame n is the target cross section, and when it falls below the threshold value, it is determined that it is not the target cross section (step 403). When there are a plurality of target sections X, Y, and Z, the coincidence rate is calculated for each of the target sections X, Y, and Z, and it is determined whether the frame n is any of the target sections X, Y, and Z. .

  If the frame determination unit 3 determines in step 403 that the frame n is not one of the target cross-sections X, Y, and Z, the process proceeds to step 404 and the channel data, reception line data, and cine data of frame n are transferred from the memory unit 17. Is deleted (step 404). Then, the determinations in steps 401 to 403 are repeated for the next n + 1th frame (step 405). However, in order to enable measurement using a plurality of frames before and after the target cross section, successive frames may be temporarily stored in the memory unit 17 for a certain period.

  If it is determined in step 403 that the frame n is one of the target cross sections X, Y, and Z, the frame determination unit 3 proceeds to step 406 and receives the channel n channel data from the memory unit 17 of the frame n, and receives it. The line data and cine data are stored in the memory unit 17 as they are, and the determination result is output to the second processing control unit 22 of the second processing unit 2.

  When the second processing control unit 22 receives the determination result from the frame determination unit 3, the second processing control unit 22 determines the target cross section that matches the frame n indicated by the determination result, and the execution processing content (program) corresponding to the target cross section is determined by the control unit. 16 (step 407). For example, when the target section X is a fetal head section, the execution process is measurement of a large head diameter (BPD), and when the target section Y is a fetal abdominal section, the execution process is an abdominal circumference (AC). When the target section Z is a thigh section, the execution process is measurement of the femur length (FL). The second processing control unit 22 operates each part of the calculation analysis processing unit 20 to execute measurement by executing a program read in accordance with the target cross sections X, Y, and Z with which the frame n matches (step S1). 408-413). Thereby, the second processing control unit 22 displays the measurement result on the display unit 6 via the first processing unit 1. FIG. 4 shows the execution process only for the target cross sections X and Y for the convenience of illustration.

  When the calculation analysis process corresponding to the target section is completed, the second processing control unit 22 deletes the data stored for the frame n from the memory unit 17 (step 410). However, in order to enable measurement using a plurality of frames before and after the target cross section, successive frames may be temporarily stored in the memory unit 17 for a certain period.

  Then, in order to perform processing for the next frame, the process returns to step 401 (step 415).

  As described above, in the present embodiment, since the first processing unit 1 and the second processing unit 2 can perform beam forming and signal processing in parallel, the user always observes and confirms the imaging section on the display unit 6 in real time. Thus, the operation of the ultrasonic probe 4 can be continued.

  In addition, since the frame determination unit 3 determines whether the second processing unit 2 is a frame of a target cross section for which processing such as image adjustment and measurement is performed, the frame determination unit 3 does not depend on the anatomical knowledge or skill of the user, and The frame determination unit 3 can select an image of the determined target cross section and perform measurement or the like. Therefore, the user does not need to operate the freeze button, and can measure accurately in a short time even when he / she wants to measure a plurality of measurement items like a fetal medical examination.

  In general ultrasonic diagnostic apparatuses, since imaging is performed at about 20 to 60 fps, the data amount of the reception channel data is a maximum of about 8 GB / s, and all the reception channels being imaged. In order to store data, the memory unit 17 requires a large memory capacity. In the present embodiment, since the frame determination unit 3 and the second processing control unit 22 delete data of a frame that is not the target cross section in Step 404 and Step 410, a large memory capacity is not necessary for the memory unit 17, and the memory capacity is not large. A small and small device can be provided.

  In addition, after the calculation analysis processing of the second processing unit 2 was completed, data was held in the memory unit 17 up to a preset memory capacity threshold, and the user confirmed the measurement result and satisfied the measurement result. In some cases, the second process control unit 22 may erase all data in the memory unit 17 in response to the user feedback. When the user requests correction of the measurement result, the image processed by the second processing unit 2 is changed by reproducing the stored data, the gain of the image is adjusted, the M mode or the pulse Doppler. Manual correction may be added to the processing contents of the second processing unit such as the measurement points.

  With these configurations, data for each frame that is continuously stored can be managed so as to be stored only for the time required for processing, and the calculation analysis processing of the second processing unit can be executed with a limited memory capacity.

<< Third Embodiment >>
An ultrasonic imaging apparatus according to the third embodiment will be described with reference to FIGS. FIG. 7 is a diagram illustrating the background measurement operation in the ultrasonic imaging apparatus of the present embodiment, and FIG. 8 shows the types of the ultrasonic probe 4 of the present embodiment, the region to be imaged, and the types of inspection items. FIG. 9 is a diagram illustrating a setting screen for setting, FIG. 9 is a diagram illustrating a target cross section corresponding to an inspection item and measurement contents, and FIG. 10 is a flow illustrating a part of the operation of the control unit 16.

  The ultrasonic imaging apparatus of the third embodiment has the same configuration as the ultrasonic diagnostic apparatuses of the first and second embodiments, and the second processing unit 2 and the imaging processing of the first processing unit 1 are the same. In parallel, the measurement process is automatically executed based on the determination result of the frame determination unit 3. The third embodiment is different from the first and second embodiments in that the execution status of the measurement process is transmitted to the user through the user interface at that time. Thereby, execution of predetermined measurement by the user is supported.

  As described above, the predetermined measurement is, for example, a morphological measurement in which fetal echo diagnosis measures the length of the fetus head and limbs, and a cardiac contraction / expansion function in echo echo diagnosis. There are M mode for measuring the displacement of the heart wall in order to diagnose the above, and Doppler measurement for measuring the blood flow velocity in the heart and blood vessels by utilizing the Doppler effect of ultrasonic waves. In these, the basic observation cross section, measurement items, and measurement positions necessary for diagnosis are stipulated in the guidelines and the like, and the user needs to perform measurement according to the stipulations.

  In general, in the ultrasonic examination, a user who is a doctor or an engineer moves the ultrasonic probe 4 and observes a cross section displayed on the display unit 6 in real time, and a position where an image of an observation cross section necessary for diagnosis is drawn. Until the ultrasonic probe 4 is accurately moved. When an image of a desired cross section is drawn, while maintaining the position of the ultrasound probe 4 with one hand, the user interface 19 is monitored and operated with the other hand, and the image is adjusted, stored, and measured. . This operation is repeated many times. For this reason, users are required to have advanced skills such as anatomical knowledge and experience, and depending on the user's skills, it takes a long time for inspection, the optimal section is not drawn, and sufficient image quality adjustment is not performed. The inspection time, image quality, and inspection accuracy are affected.

  As described in the first and second embodiments, in the ultrasonic apparatus of the present embodiment, as shown in FIG. 7, the first processing unit 1 is operated while the ultrasonic probe 4 is operated by the user. Performs transmission and reception for B-mode imaging as the default mode. The B-mode image generated by the first processing unit 1 is displayed on the display unit 6. On the other hand, in the second processing unit 2, as described in detail in the second embodiment, frame determination and measurement processing are performed.

  In the third embodiment, the target cross-section in which the frame determination unit 3 performs frame determination and the content of the measurement process performed by the second processing unit 2 are shown in FIG. 10 before the user starts the inspection in step 201 in FIG. As shown in the flow, the setting can be made by selecting the type of the ultrasound probe 4, the region to be imaged, and the type of the inspection item via the user interface 19 on the display screen of the display unit 6. it can.

  First, for example, as illustrated in FIG. 8, the control unit 16 displays a screen indicating the type of the ultrasound probe 4, the region to be imaged, and the type of the inspection item on the display unit 6. As shown in FIG. 10, when the user selects these via the user interface 19, the control unit 16 accepts this (Step 101), refers to the diagnostic workflow stored in the built-in memory based on the selection result, A target cross section and measurement contents are set (step 102). For example, if the user selects, for example, the convex ultrasound probe 4 as the type of the ultrasound probe 4, selects the obstetrics and gynecology department as the imaging target, and selects the fetal screening 01 as the examination item, Based on the selection result of the user, the control unit 16 refers to a table stored in a built-in memory and sets a target cross section and measurement contents as shown in FIG. Specifically, CRL (head heel length) is set in examination item 1, fetal sagittal section is set as the target section, and hip linear distance measurement from the head is set as the measurement content to be performed on this target section. Is done. Similarly, for the inspection items 2 and 3, a target cross section and measurement contents as shown in FIG. 9 are set. In this manner, the target sections are set in order, and when the frame determination unit 3 that has captured the target section determines, predetermined measurement is executed by the second processing unit 2.

  In the third embodiment, as shown in FIG. 7, the second processing control unit 22 of the second processing unit 2 has an alert function that informs the user of an alert regarding the implementation status of the measurement process. Specifically, a display notifying the user that “BPD measurement is in progress” is displayed on the display unit 6 at the start of the large head diameter (BPD) measurement process in step 411, or from a speaker (not shown). Output audio. In addition, when the large head diameter (BPD) measurement process in step 413 is completed, a message such as “BPD measurement has been completed. Next, operate the ultrasound probe 4 to the AC cross section.” Is displayed and voiced. Output. Thereby, a measurement condition can be communicated to the user.

  Further, when the series of measurements set in the control unit 16 is completed, the second processing control unit 22 “all measurements have been completed. Please terminate the operation of the ultrasound probe.” Etc., and a report of imaging / measurement results can be output.

  In addition, when the target cross section is not drawn for a certain time or longer in the frame determination unit 3, the second processing control unit 22 sends an alert notifying the drawing failure such as “the long-axis cross section of the carotid artery is not drawn”. It is also possible to give suggestions regarding the operation of the ultrasound probe 4 to the user by displaying on the display unit 6.

  Furthermore, when the measurement content set in the control unit 16 is a measurement that needs to hold the ultrasonic probe 4 while stopping for a certain period of time or to instruct the subject 5 to hold the breath temporarily. The second processing control unit 22 can also issue an alert for quickly giving an instruction to the user by a method such as generating a stop sound from a speaker (not shown) in steps 408 and 411. Further, instead of the second processing control unit 22, the frame determination unit 3 may directly output these instructions from a speaker or the like.

  Further, when the measurement is started in the second processing unit 2, as described in the second embodiment, in addition to the configuration using the stored data of the corresponding frame stored in the memory unit 17, it is set in advance. The transmission / reception conditions (for example, transmission intensity, transmission waveform, transmission scan sequence, and filter setting of the reception unit) are transferred from the second processing control unit 22 of the second processing unit 2 to the control unit 16 of the first processing unit 1. It is possible to set and re-acquire one or more of channel data, line data, and cine data.

  According to these embodiments, the user (doctor or engineer) simply moves the ultrasonic probe 4 in order according to the operation procedure defined in the guideline, and during that time, the acquisition of the basic cross section and all the measurements necessary for the inspection are performed. It can be performed in the background without burdens such as button operation of the user interface 19, and inspection in a short time becomes possible.

  In addition, when the frame determination unit determines the target cross section and the target cross section is not obtained, an alert is issued to the user, whereby measurement at an angle suitable for the inspection can be performed without depending on the user.

<< Fourth Embodiment >>
An ultrasonic imaging apparatus according to the fourth embodiment will be described with reference to FIGS. FIG. 11 is a diagram for explaining the operation for optimizing the imaging parameters in the ultrasonic imaging apparatus of the present embodiment.

  The ultrasonic imaging apparatus of the fourth embodiment has the same configuration as the ultrasonic diagnostic apparatuses of the first and second embodiments. However, as shown in FIG. When the determination is made, as a calculation analysis process of the second processing unit 2, an optimization analysis of imaging parameters is performed, and the obtained optimal parameter is fed back to the first processing unit 1.

  In general, in ultrasonic imaging, image degradation such as a decrease in contrast, a decrease in resolution, a decrease in frame rate, and the generation of virtual images occurs due to the imaging conditions and the presence or absence of movement of the imaging target. It is desirable to adjust the imaging conditions according to the tissue characteristics / movement) and the imaging purpose (diagnostic item, measurement item). However, since there are multiple imaging parameters (transmission / reception conditions) that need to be adjusted for each of a plurality of transmission processes and a plurality of reception processes, the user must set appropriate parameter values for obtaining a good image. Is not easy.

  Specifically, the imaging parameters that can be set by the user include, for example, the transmission beam focus depth, transmission / reception scan line density, imaging mode selection such as DAS (delayed addition) imaging / aperture synthesis, imaging range (angle of view) ) And dynamic gain. In addition to parameters and modes that can be directly set by the user, there are many imaging parameters that are preset in the apparatus. For example, the receiving unit 12 has a filter coefficient for determining a sampling frequency and a band pass frequency, a channel apodization weight value, a reception beamformer has a sound velocity value used for calculating a delay value, the number of received lines in aperture synthetic imaging, the number of LRI composites, There are weight values assigned to LRI. Some of these parameters are set in a plurality of processing processes, and the image quality is different between a case where the parameter is changed in a certain processing process and a case where the parameter is changed in another processing process. For this reason, it is not easy to set an appropriate parameter value in an appropriate processing process.

In the present embodiment, as in the first embodiment, the control unit 16 first causes the first processing unit 1 to perform imaging using the initial setting parameters (step 201 in FIG. 2).
When the frame determination unit 3 determines that the frame is the target cross section (step 202), the second processing control unit 22 of the second processing unit 2 sets the optimum parameter for improving the image quality of the captured frame. The calculation analysis processing unit 20 is caused to execute a calculation analysis process for calculating the optimal parameter value. The second processing control unit 22 feeds back the calculated optimum parameter to the control unit 16 of the first processing unit 1 (step 203). As a result, the first processing unit 1 switches from imaging using the initial setting value to imaging using the optimal parameter, and the display unit 6 displays a B-mode image with improved image quality compared to the initial image. .

  As described above, the basic cross section is set as the target cross section, and when the frame of the basic cross section is determined by the frame determination unit 3, the optimum imaging parameter is calculated by the second processing unit 2. Thus, while the basic cross section is displayed on the display unit 6, the optimum parameter is feedback-set, and a B-mode image with improved image quality can be displayed.

  Alternatively, when the ultrasonic probe 4 is operated by the user and the imaging cross section changes by a certain distance or more, the second processing unit 2 calculates and sets the optimal imaging parameter in the first processing unit 1. It is also possible to do. In this case, the second processing unit 2 is configured to perform parameter optimization every time it is determined that the position of the imaging cross section determined by the frame determination unit 3 has changed by a certain distance or more from a predetermined cross section. The amount of movement of the imaging cross section can be detected by, for example, performing a process of calculating the cross-correlation of images between frames and calculating the amount of movement from the position of the peak value of the cross-correlation value.

  Since the parameter optimization processing of the second processing unit 2 is performed in parallel with the B-mode imaging of the first processing unit 1, even when the time required for parameter optimization spans imaging of a plurality of frames, real time by the display unit 6 The image display is not interrupted.

  A specific example of the parameter optimization process performed by the second processing unit 2 will be described with reference to FIGS. 12 and 13. FIG. 12 is a table generated by the second processing unit 2. This table shows an evaluation index (image quality improvement evaluation index) for image quality when the imaging parameters are changed in a plurality of imaging processes. FIG. 13 is a flowchart showing the operation of the parameter optimization process of the second processing unit 2.

  First, the second processing unit 2 determines a plurality of predetermined processes A, B, C,... (For example, transmission beam forming (transmission of the transmission beam former 11) of the first processing unit 1 in order to obtain an optimum imaging parameter. Signal generation process, reception beam forming process of the reception beam former 13, signal processing process of the signal processing unit 14, and parameters α, β, γ... Used in each process (focus depth, scan line density, DAS ( For the combination of delay addition and imaging mode selection such as imaging / aperture synthesis, the image quality improvement evaluation index when the parameter value is changed is calculated (steps 131 and 132). Thereby, a table showing the image quality improvement evaluation index is generated as shown in FIG. 12 (step 133). By referring to the table of FIG. 12, parameters that have a particularly high image quality improvement effect are fed back to the first processing unit 1 (steps 134 to 137). This will be described in detail below.

  First, in step 131, the second processing unit 2 reads channel data, reception line data, or cine data stored in the memory unit 17 in order to obtain an image quality improvement evaluation index of parameters in each process, and sets parameter values in advance. The B-mode image is generated by the reception beamformer 23 and the signal processing unit 24 of the signal analysis processing unit 20 while changing within a predetermined range. In step 132, the analysis unit 26 evaluates the image quality of the obtained image, thereby calculating an image quality improvement evaluation index for the parameter.

  When the second processing unit 2 obtains the effect of improving the image quality of the parameters in the process of performing the transmission beam forming or the processing process before the generation of the reception channel data, the second processing unit 2 sends the control unit 16 of the first processing unit to each process. A parameter value is instructed, and transmission / reception is performed from the first processing unit 1 via the control unit 16. Thereby, the second processing unit 2 causes the first processing unit 1 to re-acquire one or more data among the channel data, the reception line data, and the cine data. Then, the second processing unit 2 generates a B-mode image of the re-acquired data using the reception beam former 23 and the signal processing unit 24 of the signal analysis processing unit 20 (step 131). Further, the image quality improvement evaluation index of the parameter is calculated by evaluating the image quality of the obtained image by the analysis unit 26 (step 132).

  Note that, as the image quality improvement evaluation index, the analysis unit 26 of the second processing unit 2 calculates two of the image quality improvement contribution rate and the frame rate holding determination here.

The image quality improvement contribution rate means the degree of image improvement when comparing the initial image of the corresponding frame with, for example, the image when the parameter α of the processing process A is changed from the initial value α ₀ to α _1. . On the other hand, in the frame rate holding determination, the time required for transmission / reception in the first processing unit 1 after changing the parameter α of the processing process A from the initial value α ₀ to α ₁ is obtained, and the same frame as the initial frame rate is obtained. It is to determine whether the rate is maintained or the frame rate is lowered. The calculation method of the image quality improvement contribution rate and the determination method of the frame rate retention will be described in detail later.

  The second processing unit 2 changes each parameter as described above, obtains the image quality improvement contribution rate and the frame rate holding determination as the image quality improvement evaluation index, and generates the table of FIG. 12 (step 133).

  Next, the second processing unit 2 reads whether or not the user has set the frame rate priority mode via the user interface 19, and determines whether or not the user has set the frame rate priority mode (step S1). 134). When the frame rate priority mode is set, the process proceeds to step 135, and a combination of a process and a parameter whose frame rate holding determination result is “frame rate holding possible” is selected from the table of FIG. Among them, a combination having a high image quality improvement contribution rate (parameter γ of the processing process B in FIG. 12) is selected. On the other hand, when the frame rate priority mode is off (the image quality is prioritized over the frame rate), the process proceeds to step 136 and the combination of the processing process and the parameter having the highest image quality improvement contribution rate (the parameter α of the processing process A in FIG. 12). ) Is selected.

  Then, the second processing unit 2 outputs the selected processing process and the parameter value (the parameter value of step 131) to the control unit 16 of the first processing unit 1 and instructs it to be applied to imaging (step 137). ). Thereby, the first processing unit 1 performs imaging by applying the set parameter value to the processing process.

  The frame rate priority mode described above may be configured to be arbitrarily set by the user as described above, or the second process depending on the region or organ of the target cross section of the frame determined by the frame determination unit 3. The second processing control unit 22 of the unit 2 may set the frame rate priority mode. For example, when the target organ including the target cross section is the heart, a high frame rate is desirable. Therefore, the second processing control unit 22 of the second processing unit 2 turns on the frame rate priority mode and sets the target organ. When is a liver, the frame rate priority mode is turned off because a high frame rate is not necessarily required.

  As described above, in this embodiment, by using the two evaluation indexes of the image quality improvement contribution rate and the frame rate holding determination, it is possible to achieve both the necessary frame rate and the improvement of the image quality.

  Here, the calculation method of the image quality improvement contribution rate and the frame rate will be specifically described. These calculations are performed by the analysis unit 26 of the second processing unit 2. First, a specific example of a method for calculating the image quality improvement contribution rate will be described with reference to FIGS. FIG. 14 is a diagram for explaining an evaluation part of an image, and FIG. 15 is a flowchart showing an operation for calculating an image quality improvement contribution rate.

  In the present embodiment, the image quality improvement contribution rate is calculated using one or more of a plurality of image evaluation indexes such as image contrast and resolution.

  As shown in FIG. 14, the analysis unit 26 sets an image evaluation part for the frame (initial image) of the target section and the image generated by changing the imaging parameter value in step 131 (step 151). For example, as contrast determination parts, two parts, a relatively high-luminance part (a part displayed in white) and a comparatively low-luminance part (a part displayed in black) in the image, are extracted and set. Further, as a resolution (sharpness) evaluation part, a part where a relatively high-luminance and fine structure is depicted is extracted and set. For example, a fine blood vessel cross section, a wall structure, a lime portion, and the like are suitable.

  Next, the analysis unit 26 calculates the difference between the average values (unit decibels (dB)) of the brightness of each of the pair of contrast determination portions as a contrast index. In addition, the analysis unit 26 obtains a luminance profile that crosses the extracted resolution evaluation site (structure), and the distance from the position indicating the luminance value peak in the luminance profile to the position where the luminance value decreases by a certain luminance value (the structure body). (Width) is obtained and used as an index of resolution (step 152). In the present embodiment, since it is only necessary to calculate the relative improvement degree with respect to the initial image quality, the width of the structure calculated by such a method is defined as resolution (sharpness).

  The analysis unit 26 calculates the ratio of the contrast or resolution of the image after the imaging parameter change with respect to the initial image as the image quality improvement contribution rate (step 153).

  Next, a frame rate calculation method by the analysis unit 26 will be described.

  In general, the frame rate of an ultrasonic wave is controlled by two of the propagation time required for the ultrasonic wave to reciprocate in the living body and the processing time in a processing process such as a reception beam former or a signal processing unit.

  The propagation time of the ultrasonic wave is obtained from the number of beam transmissions required for one frame (N), the maximum imaging depth (d), and the sound speed (c) of the living body as shown in Equation (1).

τ = N × 2d / c (1)
Where τ: propagation time required for one frame, N: number of beam transmissions of one frame, d: maximum imaging depth, and c: sound speed of a living body.

  The processing time can be calculated by a method in which a proportional constant for each parameter value is measured in advance or calculated from the amount of calculation. For example, in general, the processing time of the reception beam former 13 is proportional to the number of reception lines, and the proportionality constant is determined by the arithmetic performance of the first processing unit 1 (number of processing clocks, number of parallel processes, data transfer speed) and the like.

  Therefore, the analysis unit 26 calculates the propagation time after the change of the imaging parameter according to the equation (1), and calculates the processing time after the change of the imaging parameter using a proportional constant obtained in advance for each imaging parameter. Thus, it can be determined whether or not the frame rate can be maintained.

  In the fourth embodiment described above, during the imaging process of the first processing unit 1, the second processing unit 2 performs optimization analysis of imaging parameters in parallel with it and feeds back the optimal parameters to the first processing unit 1. can do. Therefore, it is possible to display an image improved by an optimum parameter for each imaging target and to secure a necessary frame rate without adjusting the image by a button operation or the like by the user.

  In the first to fourth embodiments described above, the example in which one ultrasonic imaging apparatus is configured by the first processing unit 1, the memory unit 17, the frame determination unit 3, and the second processing unit 2 has been described. An existing ultrasonic imaging device may be used as the one processing unit 1 and an ultrasonic image processing system including the frame determination unit 3 and the second processing unit 2 may be connected to the existing ultrasonic imaging device. In this case, the memory unit 17 may use a memory built in an existing ultrasonic imaging apparatus, or the memory unit 17 may be arranged in the ultrasonic image processing system. Further, the ultrasonic image processing system and the existing ultrasonic imaging apparatus may be connected via a network.

DESCRIPTION OF SYMBOLS 1 ... 1st process part, 2 ... 2nd process part, 3 ... Frame determination part, 4 ... Ultrasonic probe, 5 ... Subject, 11 ... Transmission beam former, 12 ... Reception part, 13 ... Reception beam for 14 ... signal processing unit, 15 ... back end unit, 16 ... control unit, 17 ... memory unit, 18 ... transmission / reception switching unit, 19 ... user interface, 20 ... calculation analysis processing unit, 22 ... second processing control unit, 23: Receive beamformer, 24: Signal processing unit, 25: Back-end processing unit, 26: Analysis unit.

Claims (11)

A first processing unit that receives a reception signal output by an ultrasonic probe that has received ultrasonic waves from a subject, and generates a cross-sectional image of the subject in time series;
A frame determination unit for determining whether the image generated by the first processing unit is an image of a predetermined target cross section of the subject;
When the frame determination unit determines that the image generated by the first processing unit is an image of the target cross section, a predetermined value is applied to at least one of the image and the original reception signal from which the image is generated. An ultrasonic imaging apparatus, comprising: a second processing unit that performs the above process.   2. The ultrasonic imaging apparatus according to claim 1, wherein the second processing unit processes an image of the target cross section and measures a shape of a predetermined part of the subject on the target cross section. A characteristic ultrasonic imaging apparatus.   2. The ultrasonic imaging apparatus according to claim 1, wherein the second processing unit processes the image of the target cross section to obtain an imaging condition for improving an image quality of the image of the target cross section. Ultrasonic imaging device.   The ultrasonic imaging apparatus according to claim 1, wherein the frame determination unit extracts a feature amount of the image generated by the first processing unit, and obtains in advance one or more images of the target cross section. An ultrasonic imaging apparatus that determines whether the image generated by the first processing unit is an image of the target cross section by comparing with a feature amount that has been placed.   The ultrasonic imaging apparatus according to claim 1, further comprising a memory that stores images generated in time series by the first processing unit, wherein the frame determination unit is an image generated by the first processing unit. If the image is not an image of the target section, the image is erased from the memory. 2. The ultrasonic imaging apparatus according to claim 1, wherein the first processing unit is an image of a cross section of the subject at a current position of the ultrasonic probe that is moved by the user on the subject. Produces
The frame determination unit is preset with a plurality of the target cross sections,
When the frame determination unit determines that the image generated by the first processing unit is an image of one of the target cross sections, the second processing unit moves the ultrasonic search to another target cross section. An ultrasonic imaging apparatus that causes a display or audio output unit connected to execute display or audio output that prompts a user to move a touch element. 2. The ultrasonic imaging apparatus according to claim 1, wherein the first processing unit is an image of a cross section of the subject at a current position of the ultrasonic probe that is moved by the user on the subject. Is generated and displayed on the connected display in real time,
The frame determination unit is preset with a plurality of the target cross sections,
When the frame determination unit determines that the image generated by the first processing unit is an image of one of the target cross sections, the second processing unit performs predetermined measurement on the determined image of the target cross section. During the processing, the first processing unit generates an image of a cross section of the subject at the current position of the ultrasonic probe that the user is moving on the subject, and the display unit An ultrasonic imaging apparatus characterized by continuing the operation of displaying the image in real time. The ultrasonic imaging apparatus according to claim 1, wherein the type of the ultrasonic probe, a user interface that receives a region to be imaged in the subject, the type of the ultrasonic probe, and the imaging target For each combination of parts, further comprising a memory unit that pre-stores a table indicating the target cross section and the content of the predetermined processing of the second processing unit, and a control unit,
The control unit includes the type of the ultrasound probe received by the user interface, the target cross section corresponding to the region to be imaged in the subject, and the content of the predetermined process, the frame determination unit, An ultrasonic imaging apparatus that is set in each of the second processing units.   4. The ultrasonic imaging apparatus according to claim 3, wherein the second processing unit obtains an image quality evaluation value by processing an image of the target cross section generated by the first processing unit, and a plurality of types of the imaging. Images with different conditions are generated using data output from the first processing unit, image quality evaluation values are obtained for the respective images, and the image quality evaluation value of the image of the target cross section generated by the first processing unit is obtained. An ultrasonic imaging apparatus characterized in that an imaging condition with the largest improvement in image quality evaluation value is set in the first processing unit.   10. The ultrasonic imaging apparatus according to claim 9, wherein the second processing unit calculates a frame rate when the imaging condition is changed, and the imaging condition is such that the frame rate of the first processing unit can be maintained. Among them, an imaging condition having the largest image quality evaluation value is set in the first processing unit. A frame determination unit that sequentially reads out the images from a memory in which a plurality of time-series ultrasonic images are stored, and determines whether the image is a predetermined target cross section of the subject;
When the frame determination unit determines that the image is an image of the target section, a processing unit that performs a predetermined process on at least one of the image and the original reception signal from which the image is generated An ultrasonic image processing system comprising:

Images