JP2012005787A - Ultrasound diagnostic apparatus and control program for generating image data - Google Patents

Abstract

PROBLEM TO BE SOLVED: To sequentially display long-running time-oriented image data excellent in resolution using a data storage part having normal storage capacity.SOLUTION: An ultrasound diagnostic apparatus includes: a thinning-out condition setting means for setting a thinning-out condition of RAW data; a thinning-out processing means for thinning out the RAW data based on the thinning-out condition; an RAW data storage means for storing the RAW data after the thinning-out processing; an image data generation means for processing the RAW data after the thinning-out processing, which is read from the RAW data storage means, and generating the image data; and a display means for displaying the image data.

Description

  Embodiments of the present invention can easily generate long-time and high-quality image data when generating time-series image data using raw data once stored in a data storage unit having a finite storage capacity. The present invention relates to an ultrasonic diagnostic apparatus and a control program for generating image data.

  The ultrasonic diagnostic apparatus performs ultrasonic transmission / reception in a plurality of directions of a subject using an ultrasonic probe in which a plurality of vibration elements are arranged, and generates image data or time series generated based on the reflected wave obtained at this time Since the data is displayed on the monitor, 2D image data and 3D image data in the body can be observed in real time with a simple operation by simply bringing the tip of the ultrasonic probe into contact with the body surface. Widely used for morphological and functional diagnosis of organs.

  Ultrasound diagnostic methods for obtaining biological information from reflected waves from the tissue or blood cells of a subject have made rapid progress with the development of two major technologies, the ultrasonic pulse reflection method and the ultrasonic Doppler method, and are obtained using the above technology. Image data effective for diagnosis is generated and displayed using the B-mode data and color Doppler data (hereinafter collectively referred to as RAW data).

  When performing functional diagnosis of the heart or the like, time-series RAW data collected from the diagnosis target region of the subject within a predetermined period is temporarily stored in the data storage unit, and the stored RAW data is repeated. In other words, a so-called cine display method is performed in which a moving image within the above-described period is obtained by reading out.

  When chronological RAW data is stored in the above-described data storage unit for the purpose of cine display, it is desirable to store RAW data with excellent spatial resolution, contrast resolution, and time resolution over a long period of time. However, in order to store such RAW data, a high-performance data storage unit having an extremely large storage capacity is required. For this reason, a method of reducing the data capacity of RAW data stored in the data storage unit by thinning out the RAW data before storage is performed, and further, reversible or irreversible compression processing and decompression processing are performed on the RAW data. A method of doing this has also been proposed.

JP 2000-501948 A

  Conventional thinning processing for data compression has been performed based on fixed thinning conditions set in advance regardless of the characteristics of RAW data and the state of each unit provided in the ultrasonic diagnostic apparatus. For this reason, it is impossible to collect RAW data over a long period of time that enables generation of image data having resolutions (spatial resolution, contrast resolution, and temporal resolution) required for diagnosis of the diagnosis target region. there were.

  In addition, the method of decompressing compressed RAW data and reproducing time-sequential RAW data before storage requires a lot of time for the decompression process and is difficult to apply in a clinical setting. Had problems.

  The present embodiment has been made in view of the above-described problems. The purpose of the present embodiment is to generate time-series image data using RAW data that has been stored once. An object of the present invention is to provide an ultrasonic diagnostic apparatus and an image data generation control program capable of easily generating high-quality image data for a long time by performing a thinning process according to the amount of fluctuation of RAW data.

  In order to solve the above problem, an ultrasonic diagnostic apparatus according to claim 1 is an ultrasonic diagnostic apparatus that generates image data based on time-series RAW data collected by ultrasonic transmission / reception with respect to a subject. Thinning condition setting means for setting thinning conditions for RAW data, thinning processing means for performing thinning processing on the RAW data based on the thinning conditions, RAW data storage means for storing RAW data after thinning processing, and the RAW An image data generating unit that processes the RAW data after the thinning process read from the data storage unit to generate image data, and a display unit that displays the image data are provided.

  According to a fourteenth aspect of the present invention, there is provided a control program for generating image data for an ultrasonic diagnostic apparatus that generates image data based on time-series RAW data collected by ultrasonic transmission / reception for a subject. A decimation condition setting function for setting decimation conditions, a decimation process function for decimation processing on the RAW data based on the decimation conditions, and an image data generation function for processing RAW data after decimation processing and generating image data A display function for displaying the image data is executed.

1 is a block diagram showing the overall configuration of an ultrasonic diagnostic apparatus according to a first embodiment. The block diagram which shows the specific structure of the ultrasonic probe with which the ultrasonic diagnostic apparatus of the Example is provided, and a transmission / reception part. The block diagram which shows the specific structure of the received signal processing part with which the ultrasonic diagnosing device of the Example is provided. The block diagram which shows the specific structure of the thinning condition setting part with which the ultrasonic diagnosing device of the Example is provided. The figure which shows the specific example of the various thinning conditions previously stored by the thinning condition storage part of the Example. The figure which shows the RAW data thinned-out by the RAW data thinning-out process part of the Example. The figure for demonstrating the raw data of the thinning time phase reproduced | regenerated by the image data generation part of the Example. The flowchart which shows the image data production | generation procedure in the Example. The figure for demonstrating the thinning-out processing method in the modification of the Example. The block diagram which shows the whole structure of the ultrasonic diagnosing device in a 2nd Example. The block diagram which shows the specific structure of the thinning condition setting part with which the ultrasonic diagnosing device of the Example is provided. The figure for demonstrating the setting method of the systole and the diastole in the Example. The figure which shows the specific example of the thinning conditions currently stored beforehand by the thinning condition storage part of the Example. The flowchart which shows the image data production | generation procedure in the Example. The figure which shows the thinning condition setting method in the modification of a 1st Example and a 2nd Example. The figure which shows the thinning condition setting method in the other modification of a 1st Example and a 2nd Example.

  Embodiments will be described below with reference to the drawings.

  In the ultrasonic diagnostic apparatus of the first embodiment described below, adjacent ones extracted from time-series two-dimensional RAW data (hereinafter referred to as RAW data) collected from the diagnosis target region of the subject. The amount of change is detected by detecting the displacement of the raw data. Then, the time-sequential RAW data is thinned using a thinning condition corresponding to the fluctuation amount (positional deviation), and the RAW data after the thinning process is stored in the RAW data storage unit. Next, interpolation processing using the thinning parameters corresponding to the thinning conditions is performed on the RAW data after the thinning processing read from the RAW data storage unit to reproduce time-series RAW data, and using the reproduced RAW data Generate and display image data.

  In the following embodiment, thinning processing and storage are performed on time-series two-dimensional RAW data collected by an ultrasonic probe in which vibration elements are one-dimensionally arranged, and the RAW data after the thinning processing is used. However, the present invention is not limited to this. For example, time-series three-dimensional RAW data collected by an ultrasonic probe in which vibration elements are two-dimensionally arranged is described. A thinning process may be performed on.

  Further, thinning processing (frame thinning) is performed on the time-series RAW data collected in the abdominal region of the subject, and based on the raw data after the thinning processing once stored in the RAW data storage unit. Although the case of reproducing RAW data in the thinning time phase will be described, the diagnosis target area may be an area other than the abdominal area, and the thinning process is not limited to frame thinning.

(Device configuration)
The configuration and functions of the ultrasonic diagnostic apparatus according to this embodiment will be described with reference to FIGS. FIG. 1 is a block diagram showing an overall configuration of the ultrasonic diagnostic apparatus, and FIG. 2 is a block diagram showing a specific configuration of an ultrasonic probe and a transmission / reception unit included in the ultrasonic diagnostic apparatus. 3 and 4 are block diagrams showing specific configurations of a reception signal processing unit and a thinning condition setting unit included in the ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic apparatus 100 of the present embodiment shown in FIG. 1 transmits an ultrasonic pulse (transmission ultrasonic wave) to a diagnosis target region of a subject and receives an ultrasonic reflected wave (reception ultrasonic wave) obtained from the diagnosis target region. An ultrasonic probe 2 having a plurality of vibration elements for converting sound waves) into electrical signals (reception signals) and a drive signal for transmitting ultrasonic pulses in a predetermined direction of the diagnosis target region to the vibration elements described above. A transmission / reception unit 3 for phasing and adding (adding and synthesizing the signals with the same phase) and a two-dimensional B mode by processing the received signals after phasing addition Received signal processing unit 4 that generates data and color Doppler data (hereinafter collectively referred to as RAW data), and RAW data collected in time series at a predetermined time or a predetermined cycle. Selected time A decimation condition setting unit 5 that detects a positional shift between RAW data using two RAW data adjacent in the direction (frame direction), and sets a decimation condition for the RAW data based on the detection result; and a received signal processing unit RAW data decimation processing unit 6 that performs decimation processing on the RAW data supplied from 4 based on the decimation conditions set in the decimation condition setting unit 5, and a time series in which a part thereof has been deleted by the above decimation processing A RAW data storage unit 7 is provided for storing RAW data (hereinafter referred to as RAW data after thinning processing) by adding a thinning pattern number which is identification information of a thinning condition.

  The ultrasonic diagnostic apparatus 100 also includes a thinning parameter storage unit 8 in which various thinning parameters including the thinning parameters corresponding to the above-described thinning conditions are stored in advance, and a RAW after thinning processing read from the RAW data storage unit 7. Time series RAW data is reproduced by interpolating data based on the thinning parameters corresponding to the thinning conditions read from the thinning parameter storage unit 8, and time series image data is obtained based on the reproduced RAW data. An image data generation unit 9 for generating the image data, a display unit 10 for displaying the obtained image data, a scanning control unit 11 for controlling the ultrasonic scanning (ultrasound transmission / reception direction) with respect to the diagnosis target region, and a subject. An input unit 12 for inputting information, setting RAW data collection conditions, image data generation conditions, and the like; And a system controller 13 for centrally controlling the door.

  Hereinafter, the configuration and function of each unit included in the ultrasonic diagnostic apparatus 100 of the present embodiment will be described in more detail.

  As shown in FIG. 2, the ultrasonic probe 2 of FIG. 1 has N vibrating elements 21 arranged one-dimensionally at the tip thereof, and each of the vibrating elements 21 is connected via an N-channel multicore cable. The input / output terminal 3 is connected to the input / output terminal.

  The vibration element 21 is an electroacoustic transducer, which converts an electric pulse (drive signal) into an ultrasonic pulse (transmitted ultrasonic wave) at the time of transmission, and converts an ultrasonic reflected wave (received ultrasonic wave) into an electric reception signal at the time of reception. It has a function to convert. The ultrasonic probe 2 corresponds to any one of sector scanning / linear scanning / convex scanning, etc., and doctors and examiners can arbitrarily select according to the purpose of diagnosis and the diagnostic part. In the present embodiment, a case will be described in which a sector scanning ultrasonic probe 2 in which N vibration elements 21 are one-dimensionally arranged is used.

  Next, as shown in FIG. 2, the transmission / reception unit 3 transmits a drive signal for radiating transmission ultrasonic waves to the subject to the N vibration elements 21 provided in the ultrasonic probe 2. And a receiving unit 32 that performs phasing addition of the N-channel received signals obtained from the vibration element 21.

  The transmission unit 31 includes a rate pulse generator 311, a transmission delay circuit 312, and a drive circuit 313, and the rate pulse generator 311 is a control that is supplied from the system control unit 13 with a rate pulse that determines a repetition period of transmission ultrasonic waves. Generate based on the signal.

  The transmission delay circuit 312 is composed of an N-channel delay circuit, and a delay time (focusing delay time) for focusing the transmission ultrasonic wave to a predetermined depth and a predetermined transmission / reception in order to form a narrow beam width in transmission. A delay time (deflection delay time) for emitting transmission ultrasonic waves in the direction θp is given to the rate pulse. On the other hand, the drive circuit 313 including the N channel generates a drive pulse for driving the N vibration elements 21 built in the ultrasonic probe 2 based on the rate pulse.

  Next, the receiving unit 32 includes a preamplifier 321 composed of N channels, an A / D converter 322, a reception delay circuit 323, and an adder 324. The preamplifier 321 amplifies a minute reception signal converted into an electric signal by the vibration element 21 and supplied via a multicore cable to secure a sufficient S / N. The reception signal amplified by the preamplifier 321 is A The digital signal is converted by the / D converter 322.

  The reception delay circuit 323 is for deflection for setting a focusing delay time for focusing the ultrasonic reflected wave reflected at a predetermined depth of the subject and a strong reception directivity for a predetermined transmission / reception direction θp. The delay time is given to the reception signal supplied from the A / D converter 322, and the adder 324 adds and synthesizes the above-described reception signal composed of the N channels output from the reception delay circuit 323. In other words, the reception signal obtained from the predetermined direction by the reception delay circuit 323 and the adder 324 is phased and added.

  Next, the received signal processing unit 4 of FIG. 1 processes a received signal output from the adder 324 of the receiving unit 32 to generate B mode data as shown in FIG. A Doppler signal detector 42 for detecting the Doppler signal by quadrature detection of the received signal, and a color Doppler data generator 43 for generating color Doppler data reflecting blood flow information in the blood vessel based on the detected Doppler signal. And a data storage unit 44 for storing B-mode data and color Doppler data.

  The B-mode data generation unit 41 is an envelope detector that detects the received signal after the phasing addition supplied from the reception unit 32 in the two-dimensional scan (first two-dimensional scan) with respect to the diagnosis target region of the subject. 411 and a logarithmic converter 412 that generates B-mode data by logarithmically converting the received signal after envelope detection. However, the envelope detector 411 and the logarithmic converter 412 may be configured by changing the order.

  On the other hand, the Doppler signal detection unit 42 includes a π / 2 phase shifter 421, mixers 422-1 and 422-2, and LPFs (low-pass filters) 423-1 and 423-2, and performs two-dimensional scanning on the diagnosis target region. In (second two-dimensional scanning), the received signal supplied from the receiving unit 32 is detected by quadrature phase detection to detect a Doppler signal.

  The color Doppler data generation unit 43 includes a Doppler signal storage unit 431 that temporarily stores the Doppler signal detected by the Doppler signal detection unit 42, and a signal component (clutter component) resulting from the movement of a living tissue or the like included in the Doppler signal. Obtained from the MTI filter 432 for extracting a signal component (blood flow component) caused by blood flow and an autocorrelation operation on the extracted signal component resulting from the blood flow. An autocorrelation calculation unit 433 that generates color Doppler data using the characteristic values (for example, blood flow velocity value, variance value, and power value) is provided. The B-mode data generated by the B-mode data generation unit 41 and the color Doppler data generated by the color Doppler data generation unit 43 are sequentially stored in the data storage unit 44 in correspondence with the ultrasonic transmission / reception direction θp and are two-dimensionally stored. RAW data (two-dimensional B-mode RAW data and two-dimensional color Doppler RAW data) is generated.

  Next, a specific configuration of the thinning condition setting unit 5 shown in FIG. 1 will be described with reference to FIG. As shown in FIG. 4, the thinning condition setting unit 5 includes an adjacent RAW data storage unit 51, a positional deviation detection unit 52, a threshold storage unit 53, a thinning condition storage unit 54, and a thinning condition selection unit 55, and stores adjacent RAW data storage. The unit 51 includes two pieces of RAW data adjacent to each other in the time direction (first RAW data and first RAW data) extracted from the RAW data supplied in time series from the data storage unit 44 of the received signal processing 4 in a predetermined cycle. 2 RAW data) is stored.

  The positional deviation detection unit 52 reads the first RAW data and the second RAW data stored in the adjacent RAW data storage unit 51, and sets a predetermined region of interest for the first RAW data, for example. The difference square sum or absolute difference of the data elements of the RAW data existing in the region of interest and the values (element values) of the data elements of the second RAW data corresponding to each of these data elements By calculating the sum of values, a positional deviation of the RAW data due to a change in the diagnosis target region or the like is detected.

The element value of M data elements existing in the region of interest of the first RAW data is S1m (m = 1 to M), and the data element of the second RAW data corresponding to each of the data elements Assuming that the element value included in S2m (m = 1 to M), the above-mentioned difference square sum (A1) and difference absolute value sum (A2) are calculated based on the following equation (1).

  On the other hand, the threshold value storage unit 53 stores a plurality of threshold values (for example, B1, B2, and B3 (B1) set in advance for the positional deviation Bx between RAW data based on the above-mentioned difference square sum A1 or difference absolute value sum A2. <B2 <B3)) is stored, and in the thinning condition storage unit 54, various thinning conditions corresponding to the relationship between the positional deviation Bx and the threshold values B1 to B3 are stored in advance as thinning pattern numbers.

  As data thinning methods for RAW data, time direction (frame direction) thinning (frame thinning) for time-sequential RAW data, bit thinning (bit thinning) of data elements of RAW data, data in the transmission / reception direction There are element thinning (data element thinning) and transmission / reception beam thinning (beam thinning) in a direction substantially orthogonal to the transmission / reception direction. In the diagnosis of the circulatory region where high temporal resolution is required, usually one of bit thinning / data thinning / beam thinning or a plurality of methods selected from these methods is applied, and high spatial resolution and contrast are applied. Frame thinning is applied in diagnosis of an abdominal region or the like that requires resolution.

  FIG. 5 shows a specific example of the thinning conditions stored in the thinning condition storage unit 54. For example, the positional deviation Bx between RAW data corresponds to B2 ≦ Bx <B3 and Bx <B2. Thinning pattern numbers “Bt-1” and “Bt-2” are added to the thinning conditions of “bit thinning (1/2)” and “bit thinning (1/4)”, and B2 ≦ Bx <B3, B1 ≦ Thinning pattern numbers “De-1” to “De-3” with respect to the thinning conditions of “data element thinning (1/2)” to “data element thinning (1/4)” corresponding to Bx <B2 and Bx <B1. "Is added.

  Similarly, the thinning pattern number “Bm−1” is set for the beam thinning (1/2) to beam thinning (1/4) thinning conditions corresponding to B2 ≦ Bx <B3, B1 ≦ Bx <B2, and Bx <B1. ”To“ Bm−3 ”are added to the frame decimation conditions corresponding to B2 ≦ Bx <B3, B1 ≦ Bx <B2 and Bx <B1 (1/2) to frame decimation (1/4). Thinning pattern numbers “Fr-1” to “Fr-3” are added. Note that (1 / K) shown in parentheses in the thinning-out condition means a thinning-out condition such that the number of raw data or the number of bits constituting the raw data in the thinning-out direction is 1 / K. is doing.

  Returning to FIG. 4, the thinning-out condition selection unit 55 determines the position between the diagnosis target region information of the subject supplied from the input unit 12 via the system control unit 13 and the position between the RAW data supplied from the misalignment detection unit 52. A thinning condition for the RAW data is set by selecting a suitable thinning condition from various thinning conditions stored in the thinning condition storage section 54 based on the threshold value supplied from the deviation and threshold storage section 53.

  For example, the diagnosis target region information supplied from the input unit 12 is “abdominal region”, and the positional deviation Bx supplied from the positional deviation detection unit 52 is B1 with respect to the thresholds B1 to B3 supplied from the threshold storage unit 53. When the relation of ≦ Bx <B2 is satisfied, the thinning-out condition selection unit 55 selects “frame thinning-out (1/3)” from various thinning-out conditions stored in the thinning-out condition storage unit 54, thereby generating the RAW data. A thinning condition suitable for the thinning process is set. The set decimation condition “frame decimation (1/3)” is supplied to the RAW data decimation processing unit 6 together with the decimation pattern number “Fr-2” as the accompanying information.

  Next, the RAW data decimation processing unit 6 shown in FIG. 1 receives the above-described decimation condition set in the decimation condition setting unit 5 and the decimation pattern number added to this decimation condition. The decimating condition is applied to the RAW data sequentially supplied from the received signal processing unit 4 to perform the decimating process. The RAW data after the decimating process has the decimated pattern number as supplementary information. Saved in.

  For example, when the RAW data decimation processing unit 6 performs decimation processing based on the decimation condition “frame decimation (1/3)” supplied from the decimation condition setting unit 5, as shown in FIG. RAW data F1 and F4 thinned out to 1/3 with respect to the frame direction (time direction) by thinning-out processing “frame thinning (1/3)” with respect to the time-series RAW data generated in FIG. , F7, F10,... Are stored in the RAW data storage unit 7 with the thinning pattern number “Fr-2” as supplementary information.

  If the positional deviation Bx of the RAW data detected by the positional deviation detection unit 52 of the thinning condition setting unit 5 is larger than the threshold B3, the RAW data thinning processing unit 6 that receives these pieces of information via the thinning condition selection unit 55. The RAW data supplied in time series from the data storage unit 44 of the received signal processing unit 4 is stored in the RAW data storage unit 7 as it is. That is, when Bx> B3, the thinning process for the RAW data is not performed.

  Next, in the thinning parameter storage unit 8 in FIG. 1, the thinning parameters corresponding to the various thinning conditions (see FIG. 5) stored in the thinning condition storage unit 54 in the thinning condition setting unit 5 are the same. Is stored in advance as incidental information.

  On the other hand, the image data generation unit 9 reads the RAW data after the thinning process stored in the RAW data storage unit 7 and the thinning pattern number added to these RAW data, and is stored in the thinning parameter storage unit 8. A thinning parameter to which the same thinning pattern number as the thinning pattern number is added is read out from the various thinning parameters. Then, the RAW data after the thinning process is arranged in a predetermined time phase based on the thinning parameter, and further, the RAW in the time phase (thinning time phase) thinned out by performing the interpolation process using these RAW data. Play the data.

  FIG. 7 shows the raw data F1, F4, F7, F10,..., Which have been read out from the raw data storage unit 7, and the raw data F2 reproduced by the interpolation processing using these raw data. F3, F5, F6,... In this case, the RAW data F1, F4, F7, F10,... After the decimation processing are arranged in the time phases t1, t4, t7, t10 based on the decimation parameters supplied from the decimation parameter storage unit 8, and these RAW data in the thinning-out time phases t2, t3, t5, t6,... Are reproduced by the interpolation process using the RAW data.

  In addition, the image data generation unit 9 regenerates the data elements in each of the raw data after the thinning process read from the raw data storage unit 7 and the raw data reproduced by the above-described interpolation process in accordance with the actual ultrasonic transmission / reception direction. Arrangement is performed, and filter processing for the distance direction, azimuth direction, and frame direction (see FIG. 7) is performed as necessary to generate time-series image data.

  Next, the display unit 10 includes a display data generation unit, a conversion processing unit, and a monitor (not shown). The display data generation unit converts the above-described image data generated by the image data generation unit 9 into a predetermined display format, and adds additional information such as subject information and RAW data collection conditions to display the display data. Generate. On the other hand, the conversion processing unit performs conversion processing such as D / A conversion and television format conversion on the display data generated by the display data generation unit, and displays the display data on the monitor.

  The scanning control unit 11 performs first two-dimensional scanning and color Doppler data for the purpose of collecting B-mode data in the diagnosis target region based on RAW data collection conditions supplied from the input unit 12 via the system control unit 13. The scanning direction of the second two-dimensional scanning for the purpose of collecting the data and the transmission delay time and reception delay time necessary for these scanning are set.

  The input unit 12 is an interface including input devices such as a display panel, a keyboard, various switches, a selection button, and a mouse. The input unit 12 inputs subject information including diagnosis target region information, sets RAW data collection conditions, and generates image data. Conditions and image data display conditions are set, and various command signals are input.

  The system control unit 13 includes a CPU and a storage circuit (not shown), and the above-described various information input or set by the input unit 12 is stored in the storage circuit. The CPU comprehensively controls each unit of the ultrasonic diagnostic apparatus 100 based on the input information and setting information described above, and performs thinning processing and thinning processing on RAW data collected in time series from the diagnosis target region. RAW data storage, reproduction of RAW data in a thinning time phase using RAW data after thinning processing, RAW data after thinning processing and time-series image data based on reproduced RAW data in thinning time phase Generate etc.

(Image data generation procedure)
Next, the image data generation procedure in this embodiment will be described with reference to the flowchart of FIG. Prior to the generation of image data, the operator of the ultrasonic diagnostic apparatus 100 inputs object information including diagnosis target region information, sets RAW data collection conditions, sets image data generation conditions, and image data display conditions in the input unit 12. Further, a RAW data collection start command is input in a state where the ultrasonic probe 2 is placed at a predetermined position of the subject. Then, by supplying the command signal to the system control unit 13, time-series RAW data collection is performed on the diagnosis target region (abdominal region) of the subject (step S1 in FIG. 8).

  At this time, the rate pulse generator 311 of the transmission unit 31 shown in FIG. 2 divides the reference signal supplied from the system control unit 13 to generate a rate pulse and supplies it to the transmission delay circuit 312. The transmission delay circuit 312 transmits the ultrasonic wave in the first transmission / reception direction θ1 and the focusing delay time for converging the ultrasonic wave to a predetermined depth based on the scanning control signal supplied from the scanning control unit 11. Is applied to the rate pulse, and this rate pulse is supplied to the N-channel drive circuit 313. Next, the drive circuit 313 supplies a drive signal generated based on the rate pulse supplied from the transmission delay circuit 312 to the vibration element 21 of the ultrasonic probe 2 to radiate transmission ultrasonic waves into the subject.

  A part of the radiated transmission ultrasonic wave is reflected by an organ boundary surface or tissue of a subject having different acoustic impedance, received by the vibration element 21, and converted into an N-channel electrical reception signal. Next, the received signal is amplified by the preamplifier 321 of the receiving unit 32 and then converted into a digital signal by the A / D converter 322. Further, the N-channel reception delay circuit 323 further receives a signal exceeding a predetermined depth. After the delay time for focusing for converging the sound wave and the delay time for deflection for setting a strong reception directivity with respect to the received ultrasonic wave from the transmission / reception direction θ1, the adder 324 performs phasing addition.

  Then, the envelope detector 411 and the logarithmic converter 412 of the reception signal processing unit 4 to which the reception signal after the phasing addition is supplied perform envelope detection and logarithmic conversion on the reception signal to obtain B-mode data. The generated B-mode data is stored in the data storage unit 44.

  When the generation and storage of the B-mode data in the transmission / reception direction θ1 is completed, the scanning control unit 11 controls the delay time in the transmission delay circuit 312 of the transmission unit 31 and the reception delay circuit 323 of the reception unit 32 in the θ direction. Two-dimensional scanning is performed by transmitting and receiving ultrasonic waves in the same procedure for each of the transmission / reception directions θp (θp = θ1 + (p−1) Δθ, (p = 2 to P)) sequentially updated by Δθ. The B-mode data obtained at this time is also stored in the data storage unit 44 in correspondence with the transmission / reception direction.

  Further, the scanning control unit 11 performs ultrasonic transmission / reception (first transmission) for the purpose of collecting B-mode data in the transmission / reception direction θp (p = 1 to P) based on the instruction signal supplied from the system control unit 13. The ultrasonic transmission / reception (second two-dimensional scanning) for the purpose of collecting color Doppler data is performed substantially in parallel with the two-dimensional scanning.

  That is, the scanning control unit 11 first controls the transmission delay time in the transmission delay circuit 312 of the transmission unit 31 and the reception delay time in the reception delay circuit 323 of the reception unit 32 to perform ultrasonic transmission / reception in the transmission / reception direction θ1 a predetermined number of times ( The received signal obtained from the receiving unit 32 in each ultrasonic transmission / reception is supplied to the Doppler signal detecting unit 42 of the received signal processing unit 4. Next, this Doppler signal is detected by the Doppler signal detector 42 to detect the Doppler signal, and this Doppler signal is temporarily stored in the Doppler signal storage circuit 431 of the color Doppler data generator 43.

  When the storage of the Doppler signal obtained by the predetermined number of times (L times) of ultrasonic transmission / reception with respect to the transmission / reception direction θ <b> 1 is completed, the system control unit 13 selects the predetermined Doppler signal stored in the Doppler signal storage circuit 431. L pieces of Doppler signals corresponding to the position (depth) are sequentially read out and supplied to the MTI filter 432. Then, the MTI filter 432 filters the supplied Doppler signal to extract a Doppler component caused by the blood flow, and supplies it to the autocorrelation calculator 433.

  The autocorrelation calculator 433 performs autocorrelation calculation using the Doppler signal supplied from the MTI filter 432, and further calculates blood flow information based on the calculation result. Such calculation is also performed for other positions (depths), and the calculated blood flow information (color Doppler data) in the transmission / reception direction θ1 is stored in the data storage unit 44.

  Further, the scanning control unit 11 controls the delay time in the transmission delay circuit 312 and the reception delay circuit 323, and similarly for each of the transmission / reception directions θp (θp = θ1 + (p−1) Δθ (p = 2 to P)). The two-dimensional scanning is performed by transmitting and receiving ultrasonic waves in accordance with the above procedure, and color Doppler data obtained in each transmission / reception direction is also stored in the data storage unit 44 in correspondence with the transmission / reception direction. That is, the data storage unit 44 generates RAW data based on the B mode data and the color Doppler data. Then, by repeating ultrasonic transmission / reception with respect to the transmission / reception direction θp (θp = θ1 + (p−1) Δθ (p = 1 to P)), time-series RAW data is sequentially generated and obtained. These raw data are supplied to the thinning condition setting unit 5 and the raw data thinning processing unit 6 (step S2 in FIG. 8).

  On the other hand, two pieces of RAW data adjacent in the time direction extracted from the RAW data supplied in time series from the data storage unit 44 of the received signal processing 4 in a predetermined period are adjacent RAW data of the thinning condition setting unit 5. It is stored in the storage unit 51. Then, the positional deviation detection unit 52 of the thinning-out condition setting unit 5 reads out two pieces of RAW data stored in the adjacent RAW data storage unit 51, and the difference square sum or the difference absolute value of the element values of the data elements of these RAW data By calculating the sum, a positional deviation of the RAW data due to the variation of the diagnosis target region is detected (step S3 in FIG. 8).

  Next, the thinning-out condition selection unit 55 between the thinning-out condition setting unit 5 and the diagnosis target region information (abdominal region) supplied from the input unit 12 via the system control unit 13 and the RAW data supplied from the misalignment detection unit 52 The RAW data is thinned out by selecting a suitable thinning condition from various thinning conditions stored in the thinning condition storage section 54 based on the positional deviation of the data and the threshold value supplied from the threshold storage section 53. Conditions are set (step S4 in FIG. 8).

  When the setting of the thinning condition by the thinning condition setting unit 5 is completed, the RAW data thinning processing unit 6 uses the thinning condition set in the thinning condition setting unit 5 and the thinning pattern number added to the thinning condition. The decimation process is performed by applying the above decimation condition to the time-series RAW data received and supplied from the received signal processing unit 4 (step S5 in FIG. 8). The RAW data after the thinning process is stored in the RAW data storage unit 7 with the thinning pattern number as supplementary information (step S6 in FIG. 8).

  On the other hand, the image data generation unit 9 reads the RAW data after the thinning process stored in the RAW data storage unit 7 and the thinning pattern number added to these RAW data, and is stored in the thinning parameter storage unit 8. A thinning parameter to which the same thinning pattern number as the thinning pattern number is added is read out from the various thinning parameters. Then, the RAW data after the decimation process is arranged at a predetermined position (time phase) based on the decimation parameter, and further deleted by the decimation process of the RAW data decimation processing unit 6 by the interpolation process using these RAW data. The thinned-out RAW data is reproduced (step S7 in FIG. 8).

  Further, the image data generation unit 9 sets the data elements in each of the RAW data after the thinning process read from the RAW data storage unit 7 and the RAW data at the thinning time phase reproduced by the above-described interpolation process in the actual ultrasonic transmission / reception direction. After rearranging them in correspondence, filter processing is performed with respect to the distance direction, the azimuth direction, and the frame direction to generate time-series image data (step S8 in FIG. 8). Then, the obtained image data is displayed on the monitor of the display unit 10 (step S9 in FIG. 8).

  In this case, the display unit 10 repeatedly displays image data (cine display) by repeatedly reading out the RAW data stored in the RAW data storage unit 7 for a predetermined period.

  In the above-described embodiment, the case where the frame direction thinning process (frame thinning) is performed on the RAW data collected from the abdominal region of the subject has been described. However, image data having high time resolution is required. For circulatory region RAW data, bit thinning, data element thinning, or beam thinning is preferred.

  FIG. 9 is a diagram for explaining data element thinning and beam thinning for RAW data. FIG. 9A shows data element thinning in which data elements in the distance direction (transmission / reception direction) of RAW data are thinned to 1/3. FIG. 9B shows beam thinning (1/2) in which the transmission / reception number (number of beams) in the azimuth direction orthogonal to the distance direction is halved.

  In this case, the image data generation unit 9 uses the RAW data (FIG. 9A or 9B) after the thinning processing stored in the RAW data storage unit 7 and the thinning added to these RAW data. A pattern number “De-2” or “Bm-1” is read out, and a thinning parameter to which the same thinning pattern number as the thinning pattern number is added from among various thinning parameters stored in the thinning parameter storage unit 8 read out. Based on the thinning parameters, the data elements after the thinning process are arranged at predetermined positions, and further, the data elements deleted by the thinning process are reproduced by the interpolation process using these data elements.

  Further, the image data generation unit 9 rearranges the data elements after the thinning process and the data elements newly reproduced using these data elements in correspondence with the actual ultrasonic transmission / reception direction, and then the distance direction and the azimuth direction. Is subjected to filter processing to generate image data.

  According to the first embodiment described above, when time-series image data is generated using RAW data once stored in the RAW data storage unit, the time-series RAW data before the storage is generated. By performing the thinning process according to the amount of fluctuation, it is possible to easily generate high-quality image data for a long time.

  In particular, the measurement of the fluctuation amount is performed based on the positional deviation of the RAW data adjacent in the time direction extracted from the time-series RAW data, so that highly accurate measurement can be performed in a short time. . In addition, since the displacement can be measured repeatedly at a predetermined cycle, even when the fluctuation amount changes with time, the thinning condition is always updated according to the magnitude, so that the optimum thinning is always performed. Processing can be performed.

  Furthermore, it is possible to reproduce the RAW data of the time phase (thinning time phase) deleted by the thinning process by the interpolation process using the raw data after the thinning process, and accordingly, time-series RAW data before the thinning process. Can be obtained.

  On the other hand, since the thinning process for the RAW data is performed according to the thinning conditions set based on the above-described positional deviation and the diagnosis target region of the subject, image data having resolution necessary for diagnosis of the diagnosis target region is obtained. RAW data that can be generated can be stored for a long time.

  In addition, since the RAW data reproduction process in the thinning time phase is performed based on the thinning parameters set in advance corresponding to the thinning conditions, the image data can be generated in a short time and easily. Accordingly, real-time display of image data is possible by instantaneously reading out the raw data after thinning correction once stored in the raw data storage unit, and the raw data after thinning correction stored in the raw data storage unit for a predetermined time. By repeatedly reading out later, cine display of image data over a long period of time becomes possible. In particular, the quality of the RAW data after the thinning process stored in the RAW data storage unit can be confirmed by real-time display of the image data.

  Next, a second embodiment will be described. In the ultrasonic diagnostic apparatus according to the second embodiment, the time series collected from the diagnosis target region of the subject in the systole and diastole set based on the ECG waveform (electrocardiogram waveform) detected from the subject. Thin two-dimensional RAW data (hereinafter referred to as RAW data) is thinned using a thinning condition set in advance for each period, and the raw data after the thinning is stored in the RAW data storage unit . Next, interpolation processing based on the thinning parameters corresponding to the thinning conditions is performed on the raw data after the thinning processing read from the RAW data storage unit to reproduce time-series RAW data, and an image is generated using the reproduced raw data. Generate and display data.

  In this embodiment as well, thinning processing and storage are performed on time-series two-dimensional RAW data collected using the ultrasonic probe 2 in which the vibration elements are one-dimensionally arranged, and RAW data after the thinning processing is performed. However, the present invention is not limited to this. For example, time-series image data collected using an ultrasonic probe in which two-dimensionally arranged vibration elements are used. Thinning processing and storage may be performed on the three-dimensional RAW data, and time-series image data may be generated using the three-dimensional raw data after the thinning processing.

(Device configuration)
The configuration of the ultrasonic diagnostic apparatus according to this embodiment will be described with reference to FIGS. In the block diagram of FIG. 10 showing the overall configuration of the ultrasonic diagnostic apparatus, units having the same configuration and function as the units of the ultrasonic diagnostic apparatus 100 shown in FIG. Description is omitted.

  The ultrasonic diagnostic apparatus 200 of the present embodiment shown in FIG. 10 transmits an ultrasonic pulse (transmission ultrasonic wave) to a diagnosis target region of a subject and receives an ultrasonic reflected wave (reception ultrasonic wave) obtained from the diagnosis target region. An ultrasonic probe 2 having a plurality of vibration elements for converting sound waves) into electrical signals (reception signals) and a drive signal for transmitting ultrasonic pulses in a predetermined direction of the diagnosis target region to the vibration elements described above. A transmission / reception unit 3 for phasing and adding (adding and synthesizing the signals with the same phase) and a two-dimensional B mode by processing the received signals after phasing addition A reception signal processing unit 4 for generating data and color Doppler data (RAW data), a thinning condition setting unit 15 for setting a thinning condition for RAW data based on an ECG waveform detected from a subject, a reception signal processing A RAW data decimation processing unit 6a that performs decimation processing on the RAW data supplied from the processing unit 4 based on the decimation conditions set in the decimation condition setting unit 15, and a decimation process in which a part thereof is deleted by the above decimation processing A RAW data storage unit 7a is provided that stores the RAW data after adding a thinning pattern number, which is identification information of the thinning conditions.

  The ultrasonic diagnostic apparatus 200 also includes a thinning parameter storage unit 8a in which various thinning parameters including thinning parameters corresponding to the above-described thinning conditions are stored in advance, and a RAW after thinning processing read from the RAW data storage unit 7. Time series raw data is reproduced by interpolating data based on the thinning parameters corresponding to the thinning pattern numbers read from the thinning parameter storage unit 8a, and time series images are obtained based on the reproduced raw data. An image data generation unit 9a that generates data, a display unit 10 that displays the obtained image data, a scanning control unit 11 that controls ultrasonic scanning (ultrasonic transmission / reception direction) with respect to the diagnosis target region, An input unit 12 for inputting specimen information, setting RAW data collection conditions, and image data generation conditions; A system control unit 13 which collectively controls the respective units described above, and includes an ECG measuring unit 14 which measures the ECG waveform of the subject.

  The ECG measurement unit 14 has a plurality of measurement electrodes mounted on the body surface of the subject for the purpose of detecting the ECG waveform, and amplification for amplifying the ECG waveform detected by these measurement electrodes to a predetermined amplitude. A circuit and an A / D converter (both not shown) for converting the amplified ECG waveform into a digital signal are provided.

  On the other hand, the thinning condition setting unit 15 includes an R wave detection unit 151, a systolic / diastolic setting unit 152, a thinning condition storage unit 153, and a thinning condition selection unit 154, as shown in FIG. The R wave is detected by detecting the maximum value of the ECG waveform after A / D conversion supplied from the ECG measurement unit 14.

  The systolic / diastolic setting unit 152 measures a heartbeat cycle based on the R wave detected by the R wave detection unit 151, and sets the systole and the diastole by dividing the heartbeat cycle by a predetermined ratio. . FIG. 12 shows the period [t1] by dividing the R wave of the ECG waveform Ec detected by the R wave detector 151, the heartbeat period T0 measured by the generation period of the R wave, and the heartbeat period T0 at a predetermined ratio. The systolic period Ts set in -t2] and the diastolic period Td set in period [t2-t3] are shown.

  In the thinning condition storage unit 153, various thinning conditions set for the systole and the diastole are stored in advance as thinning pattern numbers as supplementary information. FIG. 13 shows a specific example of the thinning condition stored in the thinning condition storage unit 153. For example, a thinning pattern number “Fr” is used for the thinning condition of “frame thinning (1/2)” for the systole. -S "is added, and the thinning pattern number" Fr-d "is added to the" frame thinning (1/4) "thinning condition for the expansion period.

  Then, the thinning condition selection unit 154 sets the thinning condition used for the thinning process for the RAW data by selecting the thinning condition for the systole and diastole from the various thinning conditions stored in the thinning condition storage unit 153. To do.

  Returning to FIG. 10, the RAW data thinning-out processing unit 6a is configured to set the thinning-out condition “frame thinning out (1/2)” in the systole set in the thinning-out condition setting unit 15 and the thinning out condition “frame thinning out (1/4)” ) ”And the thinning pattern numbers“ Fr-s ”and“ Fr-d ”added to the thinning conditions. Next, the thinning-out condition “frame thinning out (1/2)” is thinned out from the raw data of the systolic period [t1-t2] supplied from the data storage unit 44 of the received signal processing unit 4, and the expansion period [t2 The thinning-out condition “frame thinning (1/4)” is thinned out on the RAW data at −t3]. The thinned pattern number “Fr-s” is assigned to the RAW data in the period [t1-t2] subjected to the thinning process, and the thinned pattern number “Fr-d” is assigned to the RAW data in the period [t2-t3]. In addition, it is stored in the RAW data storage unit 7a.

  On the other hand, the image data generation unit 9a is attached to the RAW data of the systole [t1-t2] and the diastolic period [t2-t3] stored in the RAW data storage unit 7a, and the RAW data. A thinning parameter in which thinning pattern numbers “Fr-s” and “Fr-d” are read and a thinning pattern number identical to the thinning pattern number is added from various thinning parameters stored in the thinning parameter storage unit 8a. Is read. Then, based on the thinning parameters, the RAW data is arranged in a predetermined time phase, and further, interpolation processing using these RAW data is performed to reproduce the RAW data in the thinning time phase.

  Further, the image data generation unit 9a rearranges the raw data after the thinning process read from the raw data storage unit 7a and the data elements of the raw data reproduced by the above-described interpolation process in accordance with the actual ultrasonic transmission / reception direction. Then, filter processing for the distance direction, the azimuth direction, and the frame direction is performed to generate time-series image data.

(Image data generation procedure)
Next, the image data generation procedure in this embodiment will be described with reference to the flowchart of FIG. Prior to the generation of the image data, the operator of the ultrasonic diagnostic apparatus 200 attaches the electrode of the ECG measurement unit 14 to a predetermined position on the surface of the subject body. Next, input of subject information, input of RAW data collection conditions, image data generation conditions and image data display conditions, placement of the ultrasound probe 2 with respect to the subject, etc. are input after the input unit 12 is input. Input in part 12. Then, by supplying this command signal to the system control unit 13, time-series RAW data collection is performed on the diagnosis target region of the subject (step S11 in FIG. 14). Upon receiving this command signal, the system control unit 13 controls the transmission / reception unit 3, the reception signal processing unit 4, and the scanning control unit 11, and generates time-series RAW data by the same procedure as in step S2 of FIG. (Step S12 in FIG. 14).

  On the other hand, the R wave detection unit 151 of the thinning condition setting unit 15 detects the R wave by detecting the maximum value of the ECG waveform after A / D conversion supplied from the ECG measurement unit 14, and the systolic / diastolic phase. The setting unit 152 sets the systole and the diastole by dividing the heartbeat cycle measured based on the R wave at a predetermined ratio (step S13 in FIG. 14). Then, the thinning condition selection unit 154 selects, for example, from the various thinning conditions stored in the thinning condition storage unit 153, the thinning condition “frame thinning (1/2)” for the systole and the thinning condition “frame” for the diastole. By selecting the “thinning (1/4)” and the thinning pattern numbers “Fr-s” and “Fr-d” which are the accompanying information, the thinning condition in the thinning processing of the RAW data is set (step S14 in FIG. 14). .

  Next, the RAW data thinning-out processing unit 6a determines that the systolic thinning condition “frame thinning (1/2)” and the diastole thinning condition “frame thinning (1/4)” set in the thinning condition setting unit 15. The thinning pattern numbers “Fr-s” and “Fr-d” added to these thinning conditions are received. Next, the thinning-out condition “frame thinning out (1/2)” is thinned out from the raw data of the systolic period [t1-t2] supplied from the data storage unit 44 of the received signal processing unit 4, and the expansion period [t2 The thinning-out condition “frame thinning (1/4)” is thinned out on the RAW data at −t3] (step S15 in FIG. 14).

  The thinned pattern number “Fr-s” is used for the RAW data in the systole [t1-t2] subjected to the thinning process, and the thinned pattern number “Fr-d” is used for the RAW data in the diastole [t2-t3]. Are added and stored in the RAW data storage unit 7a (step S16 in FIG. 14).

  Next, the image data generation unit 9a adds the RAW data in the systole [t1-t2] and the RAW data in the diastole [t2-t3] stored in the RAW data storage unit 7a and these RAW data. The thinning pattern numbers “Fr-s” and “Fr-d” are read out, and the thinning pattern number that is the same as the thinning pattern number is added from the various thinning parameters stored in the thinning parameter storage unit 8a. Read parameters. Then, based on the thinning parameters, the RAW data is arranged in a predetermined time phase, and further, interpolation processing using these RAW data is performed to reproduce the RAW data in the thinning time phase (step S17 in FIG. 14). .

  Further, the image data generation unit 9a rearranges the raw data after the thinning process read from the raw data storage unit 7a and the data elements of the raw data reproduced by the above-described interpolation process in accordance with the actual ultrasonic transmission / reception direction. Then, filter processing for the distance direction, the azimuth direction, and the frame direction is performed to generate time-series image data in the heartbeat period T0 (step S18 in FIG. 14). Then, the obtained image data is displayed on the monitor of the display unit 10 (step S19 in FIG. 14).

  According to the second embodiment described above, when generating chronological image data using RAW data once stored in the RAW data storage unit, the heartbeat is compared with the chronological RAW data before storage. By performing the thinning process according to the systole and diastole, it is possible to easily generate high-quality image data for a long time.

  In particular, it is possible to reproduce the RAW data of the time phase (thinning time phase) deleted by the thinning process by the interpolation process using the raw data after the thinning process, and therefore the time-series RAW data before the thinning process. Can be obtained.

  On the other hand, since the thinning process for the RAW data is performed based on a thinning condition set in advance corresponding to the systole or diastole, the RAW data enables generation of image data having a resolution necessary for diagnosis. Can be stored for a long time.

  In addition, since the RAW data reproduction process in the thinning time phase is performed based on the thinning parameters set in advance corresponding to the thinning conditions, the image data can be generated in a short time and easily. Accordingly, real-time display of image data is possible by instantaneously reading out the raw data after thinning correction once stored in the raw data storage unit, and the raw data after thinning correction stored in the raw data storage unit for a predetermined time. By repeatedly reading out later, cine display of image data over a long period of time becomes possible.

  Although several embodiments of the present invention have been described above, these embodiments are presented as examples and are not intended to limit the scope of the invention. That is, these embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. In addition, these examples and modifications thereof are included in the invention described in the claims and equivalents thereof, as well as included in the scope and gist of the invention.

  For example, in the above-described embodiment, thinning processing and storage are performed on time-series two-dimensional RAW data collected by the ultrasonic probe 2 in which the vibration elements are one-dimensionally arranged, and the RAW data after the thinning processing is stored. Although the case of generating time-series image data using the above-described method has been described, thinning-out processing may be performed on time-series three-dimensional RAW data collected by an ultrasonic probe in which vibration elements are two-dimensionally arranged. In addition, when performing bit thinning or data element thinning, thinning processing is performed on one-dimensional RAW data directly supplied from the B-mode data generation unit 41 or the color Doppler data generation unit 43 of the reception signal processing unit 4. You may do.

  Further, the RAW data collected from the subject is subjected to thinning processing (frame thinning) in the frame direction, and the thinning time phase is based on the RAW data after the thinning processing once stored in the RAW data storage unit 7 (7a). In the above description, the RAW data is reproduced, but the thinning process is not limited to frame thinning. For example, bit thinning, data element thinning, or beam thinning may be performed on RAW data obtained in the abdominal region, or frame thinning may be performed on RAW data obtained in the circulatory region.

  In the above-described embodiment, the RAW data at the thinning time phase is reproduced using the RAW data after the thinning process stored in the RAW data storage unit 7 (7a), and the RAW data after the thinning process and the reproduced RAW data are reproduced. Although the case of generating time-series image data based on the data has been described, the image data may be generated using only the RAW data after the thinning process stored in the RAW data storage unit 7 (7a). According to this method, it is possible to further reduce the time required to generate image data using the RAW data after the thinning process. When image data is generated using RAW data that has been thinned out of frames, data reading from the RAW data storage unit 7 (7a) is performed in accordance with a trigger pulse corresponding to the time phase of the RAW data.

  Furthermore, in the above-described embodiment, the case where the thinning condition is set based on the positional deviation of the adjacent RAW data and the ECG waveform systole / diastolic period has been described, but the display unit 10 has the elapsed time from the reference time. A thinning condition suitable for the thinning process of the RAW data may be set based on the size of the monitor and the priority of the shooting mode supplied from the input unit 12.

  For example, when ultrasonic imaging is performed on a subject to which a contrast medium is administered as in the CHI (Contrast Harmonic Imaging) method, a thinning condition setting unit (not shown) having a time measurement function is contrasted as shown in FIG. The elapsed time from the time of administration of the agent (reference time) to is measured, and a “no frame decimation” decimation condition is set for the RAW data collected in the period [t0-t1], and the period [t1- A thinning condition of “frame thinning (1/2)” is set for the RAW data collected at t2. Further, “frame decimation (1/3)”, “frame decimation (1/4)” for the RAW data collected in each of the period [t2-t3], the period [t3-t4],. ... Set thinning conditions. By setting such a thinning condition, it is possible to obtain high-quality image data immediately after contrast medium administration that requires particularly detailed observation.

  When a plurality of monitors having different sizes are used in the display unit 10, the thinning condition setting unit that has received the monitor size information via the system control unit 13 is obtained from the subject. A thinning condition for thinning out data elements in the distance direction or thinning out beams in the azimuth direction corresponding to the monitor size may be set for sequential RAW data.

  Further, when a plurality of shooting modes are performed simultaneously as in the B mode and the color Doppler mode in the first embodiment described above, the priority of the shooting modes supplied from the input unit 12 (for example, see FIG. 16). Therefore, a thinning condition suitable for thinning processing of RAW data may be set. In this case, a thinning condition without thinning or a low thinning rate is set for a shooting mode with a high priority, and a thinning condition with a high thinning rate is set for a shooting mode with a low priority.

  Note that the functions of the thinning condition setting unit and the raw data thinning processing unit in the above-described embodiment can be executed by a software program installed in a general-purpose CPU.

DESCRIPTION OF SYMBOLS 2 ... Ultrasonic probe 3 ... Transmission / reception part 31 ... Transmission part 32 ... Reception part 4 ... Reception signal processing part 5 ... Thinning-out condition setting part 51 ... Adjacent RAW data storage part 52 ... Misalignment detection part 53 ... Threshold storage part 54 ... Thinning-out Condition storage 55 ... Thinning condition selection unit 6, 6a ... Raw data thinning processing unit 7, 7a ... Raw data storage unit 8, 8a ... Thinning parameter storage unit 9, 9a ... Image data generation unit 10 ... Display unit 11 ... Scanning control Unit 12: Input unit 13: System control unit 15: Thinning condition setting unit 151 ... R wave detection unit 152 ... Systolic / diastolic phase setting unit 153 ... Thinning condition storage unit 154 ... Thinning condition selection unit 100, 200 ... Ultrasonic diagnosis apparatus

Claims (14)

In an ultrasonic diagnostic apparatus that generates image data based on time-series RAW data collected by ultrasonic transmission / reception with respect to a subject,
Thinning condition setting means for setting thinning conditions for the RAW data;
Decimation processing means for performing decimation processing on the RAW data based on the decimation condition;
RAW data storage means for storing RAW data after the thinning process;
Image data generation means for processing the RAW data after the thinning process read from the RAW data storage means to generate image data;
An ultrasonic diagnostic apparatus comprising: display means for displaying the image data.   2. The ultrasonic wave according to claim 1, wherein the thinning condition setting means sets the thinning condition based on a positional shift of RAW data adjacent in the time direction selected from the time-series RAW data. Diagnostic device.   The decimation condition setting means includes a position deviation detection means for detecting a position deviation of the RAW data, and a decimation condition suitable for the time-sequential RAW data decimation processing from among various decimation conditions set in advance. The ultrasonic diagnostic apparatus according to claim 2, further comprising a thinning condition selection unit that selects based on the deviation.   The ultrasonic diagnostic apparatus according to claim 1, wherein the thinning condition setting unit sets the thinning condition for the RAW data based on an ECG waveform of the subject.   The thinning condition setting means corresponds to the systolic period and the diastole out of various preset thinning conditions, and a systolic period / diastolic period setting means for setting a systolic period and a diastole based on the ECG waveform. The ultrasonic diagnostic apparatus according to claim 4, further comprising a thinning condition selection unit that selects a thinning condition.   Priority setting means for setting the priority of the shooting mode is provided, and when a plurality of shooting modes are executed, the thinning condition setting means is configured to thin out the time-series RAW data collected in each shooting mode. The ultrasonic diagnostic apparatus according to claim 1, wherein: is set based on a priority of the imaging mode.   The ultrasonic diagnostic apparatus according to claim 1, wherein the thinning condition setting unit sets the thinning condition for the RAW data based on a size of a monitor provided in the display unit.   The thinning condition setting means includes time measuring means for measuring an elapsed time from a reference time, and sets the thinning condition for the RAW data based on the elapsed time measured by the time measuring means. Item 2. The ultrasonic diagnostic apparatus according to Item 1.   2. The ultrasonic wave according to claim 1, wherein the thinning processing unit performs at least one of frame thinning, bit thinning, data element thinning, and beam thinning on the time-series RAW data based on the thinning condition. Diagnostic device.   The image data generation means processes the RAW data after the thinning process read from the RAW data storage means, reproduces the RAW data thinned out in the thinning process, and reproduces the reproduced RAW data and the thinning process The ultrasonic diagnostic apparatus according to claim 1, wherein the chronological image data is generated using subsequent RAW data.   The ultrasonic diagnostic apparatus according to claim 10, wherein the image data generation unit reproduces the RAW data by an interpolation process using the RAW data after the thinning process read from the RAW data storage unit.   A thinning parameter storage unit storing various thinning parameters is provided, and the image data generation unit reproduces the RAW data using a thinning parameter corresponding to the thinning condition selected from the various thinning parameters. The ultrasonic diagnostic apparatus according to claim 10.   The ultrasonic diagnostic apparatus according to claim 1, wherein the display unit displays the time-series image data of the predetermined period generated by the image data generation unit as a cine display. For an ultrasonic diagnostic apparatus that generates image data based on time-series RAW data collected by ultrasonic transmission / reception for a subject,
A thinning condition setting function for setting a thinning condition for the RAW data;
A decimation processing function for performing decimation processing on the RAW data based on the decimation condition;
An image data generation function for processing the raw data after the thinning process to generate image data;
An image data generation control program for executing a display function for displaying the image data.

Images