JP2014097249A - Ultrasound diagnostic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To reduce power consumption.SOLUTION: An ultrasound diagnostic device comprises: multiple conversion parts; multiple interpolation filters; a phasing addition part; and a control part. The conversion parts are respectively arranged for multiple reception channels, sample analog reception signals of corresponding reception channels and convert them into digital signals. The interpolation filters are respectively arranged behind the conversion parts, and output the digital signals after performing interpolation between sample points of the digital signals output by the conversion parts before them. The phasing addition part is arranged behind the interpolation filters and performs phasing addition of the input digital signals. The control part determines whether to perform or avoid interpolation processing using the interpolation filters, in accordance with a frequency band of a transmitted ultrasound, and when performing the interpolation processing, it inputs the digital signals respectively output by the interpolation filters into the phasing addition part; however, when avoiding the interpolation processing, it inputs the digital signals respectively output by the conversion parts into the phasing addition part.

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus.

  Conventionally, in an ultrasonic diagnostic apparatus, an analog reception signal is sampled at a predetermined sampling frequency by an AD converter, and converted into a digital signal. Here, in order to obtain a resolution higher than the limit of a predetermined sampling frequency, interpolation between sample points is performed using an interpolation filter. Such a method is particularly effective when imaging a high-frequency probe or a high frequency. However, although the interpolation filter can improve the accuracy of the phasing addition for forming the reception beam, it has a feature that the power consumption is large compared to other circuits.

Japanese Patent Laid-Open No. 7-181999

  The problem to be solved by the present invention is to provide an ultrasonic diagnostic apparatus capable of reducing power consumption.

  The ultrasonic diagnostic apparatus according to the embodiment includes a plurality of conversion units, a plurality of interpolation filters, a phasing addition unit, and a control unit. The plurality of conversion units are installed for each of the plurality of reception channels, sample the analog reception signals of the corresponding reception channels, and convert them into digital signals. The plurality of interpolation filters are installed at the subsequent stage of each of the plurality of conversion units, and output a digital signal obtained by interpolating between sample points of the digital signal output by the previous conversion unit. The phasing addition unit is installed at the subsequent stage of the plurality of interpolation filters, and performs phasing addition of the input digital signals. The control unit determines whether or not to perform interpolation processing using the plurality of interpolation filters according to the frequency band of the transmission ultrasonic wave, and outputs each of the plurality of interpolation filters when performing the interpolation processing. When a digital signal is input to the phasing adder and the interpolation process is avoided, the digital signals output from the plurality of converters are input to the phasing adder.

FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2A is a diagram (1) for explaining the interpolation filter. FIG. 2B is a diagram (2) for explaining the interpolation filter. FIG. 3 is a block diagram illustrating a configuration example of the receiving unit according to the first embodiment. FIG. 4 is a block diagram illustrating a configuration example of the receiving circuit according to the first embodiment. FIG. 5 is a diagram for explaining processing for shifting from the normal mode to the bypass mode. FIG. 6 is a diagram for explaining processing for shifting from the bypass mode to the normal mode. FIG. 7 is a flowchart (1) for explaining an example of the processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 8 is a flowchart (2) for explaining an example of the processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 9 is a block diagram illustrating a configuration example of a receiving unit according to the second embodiment. FIG. 10 is a diagram for explaining a process of shifting from the normal mode to the bypass mode when performing parallel simultaneous reception in the second embodiment. FIG. 11 is a diagram for explaining a process of shifting from the bypass mode to the normal mode when performing parallel simultaneous reception in the second embodiment.

  Hereinafter, an ultrasonic diagnostic apparatus according to an embodiment will be described with reference to the drawings.

(First embodiment)
FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. As illustrated in FIG. 1, the ultrasonic diagnostic apparatus according to the first embodiment includes an ultrasonic probe 1, a monitor 2, an input device 3, and an apparatus main body 10.

  The ultrasonic probe 1 has a plurality of transducers, and the plurality of transducers generate ultrasonic waves based on drive signals supplied from a transmission unit 11 and a reception unit 12 included in the apparatus main body 10 to be described later. The vibrator included in the ultrasonic probe 1 is, for example, a piezoelectric vibrator. The ultrasonic probe 1 receives a reflected wave signal from the subject P and converts it into an electrical signal. The ultrasonic probe 1 includes a matching layer provided in the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like. The ultrasonic probe 1 is detachably connected to the apparatus main body 10.

  When ultrasonic waves are transmitted from the ultrasonic probe 1 to the subject P, the transmitted ultrasonic waves are reflected one after another at the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe is used as a reflected wave signal. 1 is received by a plurality of piezoelectric vibrators. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift.

  For example, a 1D array probe in which a plurality of piezoelectric vibrators are arranged in a row is connected to the apparatus main body 10 as an ultrasonic probe 1 for two-dimensional scanning of the subject P. For example, the 1D array probe as the ultrasonic probe 1 is a sector probe that performs sector scanning, a convex probe that performs offset sector scanning, a linear probe that performs linear scanning, or the like.

  Alternatively, for example, a mechanical 4D probe or a 2D array probe is connected to the apparatus main body 10 as the ultrasonic probe 1 for three-dimensional scanning of the subject P. The mechanical 4D probe is capable of two-dimensional scanning using a plurality of piezoelectric vibrators arranged in a line like a 1D array probe, and swings the plurality of piezoelectric vibrators at a predetermined angle (swing angle). By doing so, three-dimensional scanning is possible. The 2D array probe can be three-dimensionally scanned by a plurality of piezoelectric vibrators arranged in a matrix and can be two-dimensionally scanned by focusing and transmitting ultrasonic waves.

  The input device 3 includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, and the like. The input device 3 accepts various setting requests from the operator of the ultrasonic diagnostic apparatus and transfers the accepted various setting requests to the apparatus main body 10.

  The monitor 2 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus to input various setting requests using the input device 3, and displays ultrasonic image data generated in the apparatus main body 10. It is a display device that displays.

  The apparatus main body 10 is an apparatus that generates ultrasonic image data based on a reflected wave signal received by the ultrasonic probe 1. The apparatus main body 10 shown in FIG. 1 can generate two-dimensional ultrasound image data based on a two-dimensional reflected wave signal, and can generate three-dimensional ultrasound image data based on a three-dimensional reflected wave signal. Device.

  As shown in FIG. 1, the apparatus body 10 includes a transmission unit 11, a reception unit 12, a B mode processing unit 13, a Doppler processing unit 14, an image generation unit 15, an image memory 16, and an internal storage unit 17. And a control unit 18.

  The transmission unit 11 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like, and supplies a drive signal to the ultrasonic probe 1. The pulsar circuit repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency. The delay circuit also sets the delay time for each vibration element used to determine the transmission directivity by focusing the ultrasonic wave generated from the ultrasonic probe 1 into a beam shape for each rate pulse generated by the pulser circuit. Give to. The trigger generation circuit applies a drive signal (drive pulse) to the ultrasonic probe 1 at a timing based on the rate pulse. That is, the transmission unit 11 controls the timing of the drive signal supplied to each vibration element by the delay time corresponding to the distance between the focal point of the living tissue in the subject P and each vibration element. Ultrasound beamformed to a predetermined focal point is transmitted (transmission beamform).

  The reception unit 12 performs various processes on the reflected wave signal received by the ultrasonic probe 1 to generate a reception signal. Each vibration element of the ultrasonic probe 1 receives a reflected wave from the same focus with a time difference corresponding to the distance between the focus and each vibration element. Therefore, in order to control the reception directivity in ultrasonic reception, the receiving unit 12 temporally adjusts each vibration element with a delay time corresponding to the distance between the focal point of the living tissue in the subject P and each vibration element. The phases (time) of the reflected wave signals from the predetermined focal points received differently are added together (phased addition). As a result, the receiving unit 12 generates a single received signal (received beam) in focus (received beamform). Specifically, the receiving unit 12 performs gain correction processing by amplifying the reflected wave signal (analog reception signal) for each reception channel. Then, the receiving unit 12 A / D converts the gain-corrected reflected wave signal into a digital signal. And the receiving part 12 produces | generates a received signal (reflected wave data) by giving and adding the delay time required in order to determine receiving directivity to the digital signal of each receiving channel. Here, the receiving unit 12 according to the present embodiment includes an interpolation filter for each reception channel in order to perform digital signal interpolation processing. The receiving unit 12 according to the present embodiment will be described in detail later. The receiving unit 12 can also perform reception aperture control by an aperture calculation circuit.

  The B-mode processing unit 13 and the Doppler processing unit 14 are signal processing units that perform various types of signal processing on the reflected wave data generated from the reflected wave signal by the receiving unit 12. The B-mode processing unit 13 receives the reflected wave data from the receiving unit 12, performs logarithmic amplification, envelope detection processing, and the like, and generates data (B-mode data) in which the signal intensity is expressed by brightness. . In addition, the Doppler processing unit 14 performs frequency analysis on velocity information from the reflected wave data received from the receiving unit 12, and extracts data (Doppler data) obtained by extracting moving body information such as velocity, dispersion, and power due to the Doppler effect at multiple points. Generate. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast agent.

  Note that the B-mode processing unit 13 and the Doppler processing unit 14 illustrated in FIG. 1 can process both two-dimensional reflected wave data and three-dimensional reflected wave data. That is, the B-mode processing unit 13 generates two-dimensional B-mode data from the two-dimensional reflected wave data, and generates three-dimensional B-mode data from the three-dimensional reflected wave data. The Doppler processing unit 14 generates two-dimensional Doppler data from the two-dimensional reflected wave data, and generates three-dimensional Doppler data from the three-dimensional reflected wave data.

  The image generation unit 15 generates ultrasonic image data from the data generated by the B mode processing unit 13 and the Doppler processing unit 14. That is, the image generation unit 15 generates two-dimensional B-mode image data in which the intensity of the reflected wave is expressed by luminance from the two-dimensional B-mode data generated by the B-mode processing unit 13. The image generation unit 15 also generates two-dimensional Doppler image data representing moving body information from the two-dimensional Doppler data generated by the Doppler processing unit 14. The two-dimensional Doppler image data is velocity image data, distributed image data, power image data, or image data obtained by combining these.

  Here, the image generation unit 15 generally converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format represented by a television or the like, and displays ultrasonic waves for display. Generate image data. Specifically, the image generation unit 15 generates ultrasonic image data for display by performing coordinate conversion according to the ultrasonic scanning mode of the ultrasonic probe 1. In addition to the scan conversion, the image generation unit 15 performs various image processing, such as image processing (smoothing processing) for regenerating an average luminance image using a plurality of image frames after scan conversion, Image processing (edge enhancement processing) using a differential filter is performed in the image. The image generation unit 15 synthesizes auxiliary information (character information of various parameters, scales, body marks, etc.) with the ultrasonic image data.

  That is, the B mode data and the Doppler data are ultrasonic image data before the scan conversion process, and the data generated by the image generation unit 15 is display ultrasonic image data after the scan conversion process. The B-mode data and the Doppler data are also called raw data (Raw Data). The image generation unit 15 obtains “two-dimensional B mode” that is two-dimensional ultrasonic image data for display from “two-dimensional B-mode data or two-dimensional Doppler data” that is two-dimensional ultrasonic image data before scan conversion processing. Image data and 2D Doppler image data "are generated.

  Further, the image generation unit 15 generates three-dimensional B-mode image data by performing coordinate conversion on the three-dimensional B-mode data. The image generation unit 15 generates three-dimensional color Doppler image data by performing coordinate conversion on the three-dimensional Doppler data. In other words, the image generation unit 15 generates “three-dimensional B-mode image data or three-dimensional color Doppler image data” as “volume data that is three-dimensional ultrasound image data”. Furthermore, the image generation unit 15 performs various rendering processes on the volume data in order to generate various two-dimensional image data for displaying the volume data on the monitor 30.

  The image memory 16 is a memory for storing image data for display generated by the image generation unit 15. The image memory 16 can also store data generated by the B-mode processing unit 13 and the Doppler processing unit 14. The B-mode data and Doppler data stored in the image memory 16 can be called by an operator after diagnosis, for example, and become ultrasonic image data for display via the image generation unit 15.

  The internal storage unit 17 stores various data such as a control program for performing ultrasonic transmission / reception, image processing and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), diagnostic protocol, and various body marks. To do. The internal storage unit 17 is also used for storing image data stored in the image memory 16 as necessary.

  The control unit 18 controls the entire processing of the ultrasonic diagnostic apparatus. Specifically, the control unit 18 is based on various setting requests input from the operator via the input device 3 and various control programs and various data read from the internal storage unit 17. 12. Control processing of the B-mode processing unit 13, the Doppler processing unit 14, and the image generation unit 15. The control unit 18 controls the monitor 2 to display the display image data stored in the image memory 16 or the internal storage unit 17. The control unit 18 also controls to store the display image data generated by the image generation unit 15 in the internal storage unit 17 or the like. The control unit 18 also transfers the medical image data received from the operator via the input device 3 from the external device 6 to the internal storage unit 17 and the image generation unit 15 via the network 100 and the interface unit 18. Control.

  The overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment has been described above. Under such a configuration, the ultrasonic diagnostic apparatus according to the first embodiment includes an interpolation filter in the receiving unit 12 and improves the accuracy of phasing addition by using the interpolation filter, and has high resolution. Generate ultrasound image data.

2A and 2B are diagrams for explaining the interpolation filter. FIG. 2A shows an example of a digital signal input to the interpolation filter, and FIG. 2B shows an example of a digital signal output from the interpolation filter. 2A and 2B, the horizontal axis indicates time, and the vertical axis indicates voltage. Black points indicate sample points (I ₁ , I ₂ , I ₃ , I ₄ , I ₅ ...) Of the digital signal sampled from the analog received signal, and white points are digital signals interpolated by an interpolation filter. Signals (O ₁₁ , O ₁₂ , O ₁₃ , O ₂₁ , O ₂₂ , O ₂₃ ...) Are shown. 2A and 2B illustrate an interpolation filter that interpolates an input signal four times.

For example, when a plurality of digital signals are input, the interpolation filter generates a digital signal that interpolates between sample points of the input digital signal. In the example shown in FIG. 2, when the digital signals I ₁ , I ₂ , I ₃ , I ₄ and I ₅ corresponding to one period are input, the interpolation filter samples the input digital signals I ₁ and I ₂ . Three digital signals O ₁₁ , O ₁₂ and O ₁₃ are generated by interpolating between the points. Thus, the interpolation filter increases the accuracy of the phasing addition for forming the reception beam by interpolating between the sample points, so that the resolution can be increased. In particular, the interpolation filter has a higher effect of improving the accuracy of the phasing addition as the center frequency of the ultrasonic probe 1 is higher or as the frequency used for imaging is higher. On the other hand, the interpolation filter is not indispensable for the interpolation filter because the lower the center frequency or the lower the frequency used for imaging, the lower the distance resolution required for the ultrasound image data. In addition, the interpolation filter has a feature that it consumes more power than other circuits.

  However, the conventional ultrasonic diagnostic apparatus always performs interpolation using an interpolation filter regardless of the center frequency of the ultrasonic probe 1 and the frequency used for imaging. For this reason, in the conventional ultrasonic diagnostic apparatus, the interpolation filter always operates, and the power consumption is constantly increased.

  Therefore, the receiving unit 12 included in the ultrasonic diagnostic apparatus according to the first embodiment is configured as described below in order to reduce power consumption.

  FIG. 3 is a block diagram illustrating a configuration example of the receiving unit 12 according to the first embodiment. As illustrated in FIG. 3, the reception unit 12 includes a plurality of reception circuits 121 a, 121 b, and 121 c, a phasing addition circuit 122, and a reception control unit 123. Here, the reception circuits 121a, 121b, and 121c are installed for each reception channel. In the example shown in FIG. 3, each of “N + 1” vibrating elements 1a, 1b,..., 1c included in the ultrasonic probe 1 has “N + 1” receiving channels (ch0, ch1,..., ChN). Is shown. In the example illustrated in FIG. 3, “N + 1” reception circuits 121a, 121b, and 121c are provided for each “N + 1” reception channels. In addition, this embodiment may be a case where the several vibration element 1a forms one receiving channel. In FIG. 3, an amplifier circuit that performs gain correction for each reception channel is omitted. The plurality of receiving circuits 121a, 121b, and 121c are collectively referred to as a receiving circuit 121 when collectively referred to.

  The reception circuit 121 performs predetermined signal processing on the analog reception signal input from the corresponding reception channel, and outputs the analog reception signal to the phasing addition circuit 122. The reception circuit 121 is controlled by a reception control unit 123 described later.

  FIG. 4 is a block diagram illustrating a configuration example of the receiving circuit 121 according to the first embodiment. As illustrated in FIG. 4, the reception circuit 121 includes an ADC (analog to digital converter) 1211, an interpolation filter 1212, and a memory group 1213. The reception circuit 121 has a bypass signal line 1214 that bypasses the interpolation filter 1212. The reception circuit 121 is controlled by a reception control unit 123 described later.

  The ADC 1211 samples the analog reception signal of the corresponding reception channel and converts it to a digital signal. For example, the ADC 1211 samples an analog reception signal received by the vibration element 1a corresponding to the channel 0 (ch0) at a predetermined timing and converts it into a digital signal. The converted digital signal is, for example, several bits to several tens of bits, and the larger the number of bits, the higher the resolution of the analog reception signal that can be sampled.

  The interpolation filter 1212 is installed at the subsequent stage of the corresponding ADC 1211, and outputs a digital signal obtained by interpolating between the sample points of the digital signal output by the preceding ADC 1211. For example, when the sampling point is quadrupled, the interpolation filter 1212 is based on the voltage of the digital signal between two digital signals output from the previous ADC 1211 as shown in FIG. 2A. Three digital signals are generated. The interpolation filter 1212 stores the generated digital signal in a plurality of memory groups 1213.

The memory group 1213 is installed for each reception channel after the interpolation filter 1212. The memory group 1213 includes a memory 1213a that stores the interpolation source digital signal output from the preceding interpolation filter 1212, and interpolation data memories 1213b, 1213c, and 1213d that store the interpolation digital signal output from the interpolation filter 1212. Here, the number of interpolation data memories 1213b, 1213c, and 1213d is set by the number of interpolations interpolated between sample points by the interpolation filter 1212. Further, if the three interpolation digital signals between the respective sample points are the first interpolation digital signal, the second interpolation digital signal, and the third interpolation digital signal in time series order, the memory 1213a and the interpolation data memories 1213b, 1213c, and 1213d are: Various digital signals are stored as follows. Specifically, the memory 1213a stores digital signals (I ₁ , I ₂ , I ₃ , I ₄ , I ₅ ...) That are interpolation sources. The interpolation data memory 1213b stores the first interpolation digital signal (O ₁₁ , O ₂₁ , O ₃₁ , O ₄₁ ...). The interpolation data memory 1213c stores the second interpolation digital signal (O ₁₂ , O ₂₂ , O ₃₂ , O ₄₂ ...). Further, the interpolation data memory 1213d stores the third interpolation digital signals (O ₁₃ , O ₂₃ , O ₃₃ , O ₄₃ ...).

  The bypass signal line 1214 forms a bypass path connecting the ADC 1211 of the corresponding reception channel and the memory 1213a. As shown in FIG. 3, the bypass signal line 1214 is installed for each corresponding reception channel.

  Returning to the description of FIG. The phasing / adding circuit 122 is installed in the subsequent stage of the plurality of receiving circuits 121 and performs phasing addition of the input digital signals. For example, the phasing addition circuit 122 performs phasing addition of digital signals read from the memory group 1213 of each of the plurality of reception channels. Then, the phasing addition circuit 122 outputs the received beam data generated by the phasing addition to at least one of the B-mode processing unit 13 and the Doppler processing unit 14.

  The reception control unit 123 controls the reception circuit 121 under the control of the control unit 18. For example, the reception control unit 123 causes the data added in the phasing addition circuit 122 to be output from the memory group 1213, respectively. Specifically, the reception control unit 123 calculates a delay time according to the distance between the focal point of the living tissue in the subject P and each vibration element. Then, the reception control unit 123 causes each of the memories included in the memory group 1213 to output to the phasing addition circuit 122 so that the phases of the digital signal data of the reflected wave signals received at different times in the respective vibration elements are matched. .

  And the reception control part 123 determines whether the interpolation process using the some interpolation filter 1212 is performed or avoided according to the frequency band of a transmission ultrasonic wave. When performing the interpolation process, the reception control unit 123 inputs the digital signal output from each of the plurality of interpolation filters 1212 to the phasing addition circuit 122. Specifically, when performing the interpolation process, the reception control unit 123 sends the digital signals output from the plurality of interpolation filters 1212 to the corresponding reception channel memory 1213a and interpolation data memories 1213b, 1213c, and 1213d. Output each.

  Further, when avoiding the interpolation process, the reception control unit 123 causes the digital signal output from each ADC 1211 to be input to the phasing addition circuit 122 using the bypass path of the bypass signal line 1214. Specifically, when avoiding the interpolation process, the reception control unit 123 applies the digital signal output from each of the plurality of reception circuits 121 by using the bypass path of the bypass signal line 1214 of the corresponding reception channel. The data is output to the memory 1213a of the reception channel. The reception control unit 123 stops the operation of the interpolation filter 1212 for each of the plurality of reception channels when avoiding the interpolation process. Further, when avoiding the interpolation process, the reception control unit 123 stops the operation of each of the interpolation data memories 1213b, 1213c, and 1213d for each of the plurality of reception channels.

  As described above, the reception control unit 123 controls the transition from the normal mode in which the interpolation process is performed to the bypass mode in which the interpolation process is avoided, and the transition from the bypass mode to the normal mode. Hereinafter, the mode transition control process performed by the reception control unit 123 will be described with reference to the drawings.

  FIG. 5 is a diagram for explaining processing for shifting from the normal mode to the bypass mode. FIG. 5 shows on / off of the illustrated function in time series. As shown in FIG. 5, the reception control unit 123 detects that the switching to the low frequency probe or the switching to the low frequency usage mode has been accepted. For example, the reception control unit 123 detects the insertion of the ultrasonic probe 1 into the apparatus main body 10. And the reception control part 123 acquires ID of the inserted ultrasonic probe 1, and determines whether the center frequency of the inserted ultrasonic probe 1 is below a threshold value. And the reception control part 123 detects that the ultrasonic probe 1 switched from the high frequency probe to the low frequency probe, when a center frequency is below a threshold value. Further, for example, when the user inputs a request for switching to the low frequency usage mode to the input unit 3, the reception control unit 123 detects that the mode has been switched from the high frequency mode to the low frequency usage mode. Note that the threshold value set here may be set, for example, according to the image processing capability of the ultrasonic diagnostic apparatus itself, or an arbitrary value may be set by a user using the ultrasonic diagnostic apparatus. .

  When detecting that the high-frequency probe is switched to the low-frequency probe or that the high-frequency mode is switched to the low-frequency use mode, the reception control unit 123 receives control information for shifting from the normal mode to the bypass mode. A control information setting period to be set in each processing unit is set. Here, the reason why the reception control unit 123 sets the control information setting period is that it is considered that it takes a certain time to switch on / off the function of each processing unit in the reception unit 12. For this reason, the control information setting period is set to a sufficient time that is considered necessary for switching on / off the function of each processing unit in the receiving unit 12.

  The reception control unit 123 turns off reception of the reflected wave signal when the control information setting period is set. That is, the reception control unit 123 temporarily blocks the reflected wave signal output from the ultrasonic probe 1 to the reception unit 12 in order to shift from the normal mode to the bypass mode.

  Subsequently, the reception control unit 123 switches from the normal path in the normal mode to the bypass path. Then, the reception control unit 123 stops the clock to the interpolation filter 1212 and the interpolation data memories 1213b, 1213c, and 1213d. As a result, as shown in FIG. 5, the interpolation filter 1212 and the interpolation data memories 1213b, 1213c, and 1213d stop their operations substantially simultaneously with the stop of the clock.

  Then, the reception control unit 123 turns on reception of the reflected wave signal when the set control information setting period elapses. That is, the reception control unit 123 restarts the output of the reflected wave signal from the ultrasonic probe 1 that has been blocked. Thereafter, the receiving unit 12 operates in the bypass mode.

  FIG. 6 is a diagram for explaining processing for shifting from the bypass mode to the normal mode. FIG. 6 shows on / off of the illustrated function in time series. As illustrated in FIG. 6, the reception control unit 123 detects that switching to a high-frequency probe or switching to a high-frequency usage mode has been accepted. For example, the reception control unit 123 detects the insertion of the ultrasonic probe 1 into the apparatus main body 10. And the reception control part 123 acquires ID of the inserted ultrasonic probe 1, and determines whether the center frequency of the inserted ultrasonic probe 1 is below a threshold value. And the reception control part 123 detects that the ultrasonic probe 1 switched from the low frequency probe to the high frequency probe, when a center frequency is not below a threshold value. In addition, for example, when the user inputs a request for switching to the high frequency usage mode to the input unit 3, the reception control unit 123 detects that the low frequency mode has been switched to the high frequency usage mode.

  When it is detected that the low-frequency probe is switched to the high-frequency probe or that the low-frequency mode is switched to the high-frequency use mode, the reception control unit 123 receives control information for shifting from the bypass mode to the normal mode. A control information setting period to be set in each processing unit is set. Here, the reason why the reception control unit 123 sets the control information setting period is that it is considered that it takes a certain time to switch on / off the function of each processing unit in the reception unit 12. For this reason, the control information setting period is set to a sufficient time that is considered necessary for switching on / off the function of each processing unit in the receiving unit 12.

  The reception control unit 123 turns off reception of the reflected wave signal when the control information setting period is set. That is, the reception control unit 123 temporarily blocks the reflected wave signal output from the ultrasonic probe 1 to the reception unit 12 in order to shift from the bypass mode to the normal mode.

  Subsequently, the reception control unit 123 switches from the bypass route to the normal route. Then, the reception control unit 123 resumes the supply of the clock to the interpolation filter 1212 and the interpolation data memories 1213b, 1213c, and 1213d. As a result, the interpolation filter 1212 and the interpolation data memories 1213b, 1213c, and 1213d start their operations. At this time, as shown in FIG. 6, the interpolation filter 1212 and the interpolation data memories 1213b, 1213c, and 1213d start their operations after some time has passed since the clock supply was resumed.

  Then, the reception control unit 123 turns on reception of the reflected wave signal when the set control information setting period elapses. That is, the reception control unit 123 restarts the output of the reflected wave signal from the ultrasonic probe 1 that has been blocked. Thereafter, the receiving unit 12 operates in the normal mode.

  Next, a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment will be described with reference to FIGS. 7 and 8. 7 and 8 are flowcharts for explaining an example of a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment.

  In the example illustrated in FIG. 7, a case will be described in which the reception control unit 123 switches between the normal mode and the bypass mode when the insertion of the ultrasonic probe 1 is detected. As illustrated in FIG. 7, when the reception control unit 123 detects the insertion of the ultrasonic probe 1 into the apparatus body 10 (Yes in Step S101), the reception control unit 123 acquires the ID of the inserted ultrasonic probe 1 (Step S102). Note that the reception control unit 123 does not start the process of switching between the normal mode and the bypass mode until the insertion of the ultrasonic probe 1 into the apparatus main body 10 is detected (No at Step S101).

  The reception control unit 123 determines whether or not the center frequency of the inserted ultrasonic probe 1 is equal to or lower than a threshold value (step S103). Then, when the center frequency is equal to or lower than the threshold (Yes at Step S103), the reception control unit 123 switches from the normal path to the bypass path and turns off the interpolation filter 1212 (Step S104). Then, the reception control unit 123 turns off the interpolation data memories 1213b, 1213c, and 1213d (step S105).

  On the other hand, when the center frequency is not equal to or lower than the threshold (No at Step S103), the reception control unit 123 switches from the bypass route to the normal route and turns on the interpolation filter 1212 (Step S106). Then, the reception control unit 123 turns on the interpolation data memories 1213b, 1213c, and 1213d (step S107).

  Note that the processing procedure shown in FIG. 7 is not necessarily performed in the above order. For example, when the process of step S103 is affirmed, the process of step S104 may be executed after the process of step S105 is executed.

  In the example illustrated in FIG. 8, a case will be described in which the reception control unit 123 switches between the normal mode and the bypass mode when receiving a mode change for switching between the normal mode and the bypass mode. As shown in FIG. 8, when receiving the mode change (Yes at Step S201), the reception control unit 123 determines whether the received mode change is a mode change to the low frequency mode (Step S202). Note that the reception control unit 123 does not start the process of switching between the normal mode and the bypass mode until the mode change is accepted (No at Step S201).

  When the received mode change is a mode change to the low frequency mode (Yes at Step S202), the reception control unit 123 switches from the normal path to the bypass path and turns off the interpolation filter 1212 (Step S203). The reception control unit 123 turns off the interpolation data memories 1213b, 1213c, and 1213d (step S204).

  On the other hand, when the received mode change is not a mode change to the low frequency mode (No at Step S202), the reception control unit 123 turns on the interpolation filter 1212 (Step S205). Then, the reception control unit 123 turns on the interpolation data memories 1213b, 1213c, and 1213d (step S206).

  Note that the processing procedure shown in FIG. 8 is not necessarily performed in the above order. For example, when the process of step S202 is affirmed, the process of step S203 may be executed after the process of step S204 is executed.

  As described above, the ultrasonic diagnostic apparatus according to the first embodiment does not perform the interpolation process using the interpolation filter 1212 when the effect of the interpolation filter 1212 cannot be expected, thereby reducing power consumption. Can do.

  Further, for example, the ultrasonic diagnostic apparatus according to the first embodiment stops the operation of the interpolation filter 1212 when the interpolation process is avoided. For this reason, the ultrasonic diagnostic apparatus according to the first embodiment can reduce the power consumed to maintain the interpolation filter 1212 in a processable state.

  For example, the ultrasound diagnostic apparatus according to the first embodiment stops the operation of the interpolation data memories 1213b, 1213c, and 1213d when the interpolation process is avoided. For this reason, the ultrasonic diagnostic apparatus according to the first embodiment can reduce the power consumed to maintain the interpolation data memories 1213b, 1213c, and 1213d in a state in which the interpolation digital signals can be stored.

(Second Embodiment)
In the second embodiment, a modified example of the bypass path will be described. The ultrasonic diagnostic apparatus according to the second embodiment has the same configuration as the ultrasonic diagnostic apparatus according to the first embodiment shown in FIG. In the second embodiment, differences from the first embodiment will be described. Among the processing units of the ultrasonic diagnostic apparatus according to the second embodiment, the processing unit having the same function as the processing unit described in the first embodiment is denoted by the same reference numeral as in FIG. Description is omitted.

  FIG. 9 is a block diagram illustrating a configuration example of the receiving unit 12 according to the second embodiment. As illustrated in FIG. 9, the reception unit 12 includes a plurality of reception circuits 121 a, 121 b, and 121 c, a phasing addition circuit 122, and a reception control unit 123. Here, the reception circuits 121a, 121b, and 121c are installed for each reception channel. In the example shown in FIG. 9, each of “N + 1” vibrating elements 1a, 1b,..., 1c included in the ultrasonic probe 1 has “N + 1” receiving channels (ch0, ch1,..., ChN). Is shown. In the example illustrated in FIG. 9, “N + 1” reception circuits 121a, 121b, and 121c are provided for each “N + 1” reception channels. In addition, this embodiment may be a case where the several vibration element 1a forms one receiving channel. In FIG. 9, an amplifier circuit that performs gain correction for each reception channel is omitted.

  As illustrated in FIG. 9, the reception circuit 121 includes an ADC 1211, a memory 1213 a, and an interpolation filter 1212. The reception circuit 121 has a bypass signal line 1215 that bypasses the interpolation filter 1212.

The memory 1213a stores the digital signal output from the preceding ADC 1211 as the memory of the corresponding reception channel. Using the example shown in FIG. 2A, the memory 1213a stores the digital signals (I ₁ , I ₂ , I ₃ , I ₄ , I ₅ ...) Output from the ADC 1211.

  The interpolation filter 1212 performs an interpolation process using the digital signal stored in the memory 1213a of the corresponding reception channel. In the example illustrated in FIG. 2B, the interpolation filter 1212 generates three digital signals between two digital signals output from the memory 1213a based on the voltage of the digital signal. Then, the interpolation filter 1212 outputs the two digital signals output from the memory 1213a and the generated digital signal to the phasing addition circuit 122.

  The bypass signal line 1215 forms a bypass path connecting the memory 1213 a of the corresponding reception channel and the phasing addition circuit 122.

  When performing the interpolation process, the reception control unit 123 outputs the digital signal stored in the memory of the corresponding reception channel to the interpolation filter 1212 of the corresponding reception channel. Further, the reception control unit 123 causes the phasing addition circuit 122 to output the digital signal stored in the memory of the corresponding reception channel to the phasing addition circuit 122 through the bypass path when the interpolation processing is not performed. Note that the mode transition control process performed by the reception control unit 123 according to the second embodiment performs control on the interpolation filter 1212 among the mode transition control processes illustrated in FIGS. 5 and 6.

  As described above, the ultrasonic diagnostic apparatus according to the second embodiment avoids the interpolation process using the interpolation filter 1212 when the effect of the interpolation filter 1212 cannot be expected, thereby reducing power consumption. Can do.

  Incidentally, the first and second embodiments described above can also be applied to a case where parallel simultaneous reception is performed in which reflected wave signals are received by a plurality of scanning lines with respect to transmission of one ultrasonic pulse. Specifically, the configuration of FIG. 3 described in the first embodiment can be applied to the case where parallel simultaneous reception is performed. The configuration of FIG. 9 described in the second embodiment can be applied by installing an interpolation filter 1212 and a phasing addition circuit 122 corresponding to the number of scanning lines received simultaneously. For example, when performing parallel simultaneous reception in which four scanning lines are simultaneously received, four interpolation filters 1212 are installed for each reception channel, and four phasing and addition circuits 122 are installed. It becomes. In the following, mode transition control processing performed by the reception control unit 123 will be described. In this case, the receiving unit 12 includes a phasing addition circuit for interpolation data that performs phasing addition of the interpolation data stored by the interpolation filter 1212 in addition to the phasing addition circuit 122 described above.

  FIG. 10 is a diagram for explaining a process of shifting from the normal mode to the bypass mode when performing parallel simultaneous reception in the second embodiment. FIG. 10 shows on / off of the illustrated function in time series. As illustrated in FIG. 10, the reception control unit 123 detects that the switching to the low frequency probe or the switching to the low frequency usage mode has been accepted.

  When detecting that the high-frequency probe is switched to the low-frequency probe or that the high-frequency mode is switched to the low-frequency use mode, the reception control unit 123 receives control information for shifting from the normal mode to the bypass mode. A control information setting period to be set in each processing unit is set. Here, the reason why the reception control unit 123 sets the control information setting period is that it is considered that it takes a certain time to switch on / off the function of each processing unit in the reception unit 12. For this reason, the control information setting period is set to a sufficient time that is considered necessary for switching on / off the function of each processing unit in the receiving unit 12.

  The reception control unit 123 turns off reception of the reflected wave signal when the control information setting period is set. That is, the reception control unit 123 temporarily blocks the reflected wave signal output from the ultrasonic probe 1 to the reception unit 12 in order to shift from the normal mode to the bypass mode.

  Subsequently, the reception control unit 123 switches from the normal route to the bypass route. The reception control unit 123 stops the clock to the interpolation filter 1212 and the interpolation data phasing addition circuit. As a result, as shown in FIG. 10, the interpolation filter 1212 and the interpolation data phasing addition circuit stop their operations almost simultaneously with the stop of the clock.

  Subsequently, the reception control unit 123 stops the clock to the interpolation filter 1212. As a result, the interpolation filter 1212 stops its operation.

  Then, the reception control unit 123 turns on reception of the reflected wave signal when the set control information setting period elapses. That is, the reception control unit 123 restarts the output of the reflected wave signal from the ultrasonic probe 1 that has been blocked. Thereafter, the receiving unit 12 operates in the bypass mode.

  FIG. 11 is a diagram for explaining a process of shifting from the bypass mode to the normal mode when performing parallel simultaneous reception in the second embodiment. FIG. 11 shows on / off of the illustrated function in time series. As illustrated in FIG. 11, the reception control unit 123 detects that switching to a high-frequency probe or switching to a high-frequency usage mode has been accepted.

  When it is detected that the low-frequency probe is switched to the high-frequency probe or that the low-frequency mode is switched to the high-frequency use mode, the reception control unit 123 receives control information for shifting from the bypass mode to the normal mode. A control information setting period to be set in each processing unit is set. Here, the reason why the reception control unit 123 sets the control information setting period is that it is considered that it takes a certain time to switch on / off the function of each processing unit in the reception unit 12. For this reason, the control information setting period is set to a sufficient time that is considered necessary for switching on / off the function of each processing unit in the receiving unit 12.

  The reception control unit 123 turns off reception of the reflected wave signal when the control information setting period is set. That is, the reception control unit 123 temporarily blocks the reflected wave signal output from the ultrasonic probe 1 to the reception unit 12 in order to shift from the bypass mode to the normal mode.

  Subsequently, the reception control unit 123 switches from the bypass route to the normal route. Then, the reception control unit 123 resumes the supply of the clock to the interpolation filter 1212 and the interpolation data phasing addition circuit. As a result, the interpolation filter 1212 starts its operation. At this time, as shown in FIG. 11, the interpolation filter 1212 and the interpolation data phasing adder circuit start their operations after some time has elapsed since the clock supply restarted.

  Then, the reception control unit 123 turns on reception of the reflected wave signal when the set control information setting period elapses. That is, the reception control unit 123 restarts the output of the reflected wave signal from the ultrasonic probe 1 that has been blocked. Thereafter, the receiving unit 12 operates in the normal mode. By performing such control, the second embodiment described above can be applied to the case where parallel simultaneous reception is performed.

  According to at least one embodiment described above, power consumption can be reduced.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 10 Apparatus main body 12 Reception part 121 Reception circuit 1211 ADC
1212 Interpolation filter 1213 Memory group 1213a Memory 1213b, 1213c, 1213d Memory for interpolation data 1214, 1215 Signal line for bypass 122 Phased addition circuit 123 Reception control unit

Claims (6)

A plurality of conversion units installed for each of the plurality of reception channels, sampling analog reception signals of the corresponding reception channels, and converting them into digital signals,
A plurality of interpolation filters that are installed in the subsequent stage of each of the plurality of conversion units and that output a digital signal obtained by interpolating between sample points of the digital signal output by the previous conversion unit,
A phasing adder that is installed at a subsequent stage of the plurality of interpolation filters and performs phasing addition of the input digital signal;
In accordance with the frequency band of the transmission ultrasonic wave, it is determined whether or not to perform interpolation processing using the plurality of interpolation filters, and when performing the interpolation processing, digital signals output from the plurality of interpolation filters, A control unit that inputs the digital signal output from each of the plurality of conversion units to the phasing addition unit when input to the phasing addition unit and avoiding interpolation processing;
An ultrasonic diagnostic apparatus comprising:   The ultrasonic diagnostic apparatus according to claim 1, wherein the controller stops the operations of the plurality of interpolation filters when the interpolation process is avoided. A digital signal that is installed for each of the plurality of reception channels and that is output from the conversion unit of the corresponding reception channel bypasses the interpolation filter at the subsequent stage of the conversion unit and forms a bypass path that is output to the phasing addition unit A plurality of signal lines,
The ultrasonic diagnostic apparatus according to claim 1, wherein the control unit uses a bypass path of each of the plurality of signal lines when the interpolation process is avoided. As a memory group for each reception channel installed at the subsequent stage of each of the plurality of interpolation filters, a first memory for storing the interpolation source digital signal output by the previous interpolation filter, and the interpolation digital signal output by the interpolation filter A second memory for storing,
The phasing addition unit performs phasing addition of digital signals read from the memory groups of the plurality of reception channels,
Each of the plurality of signal lines forms a bypass path connecting the conversion unit of the corresponding reception channel and the first memory,
When performing the interpolation process, the control unit outputs the digital signal output from each of the plurality of interpolation filters to the first memory and the second memory of the corresponding reception channel, and when the interpolation process is avoided, 4. The ultrasonic diagnosis according to claim 3, wherein the digital signal output from each of the plurality of conversion units is output to a first memory of a corresponding reception channel using a bypass path of a signal line of the corresponding reception channel. apparatus.   The ultrasonic diagnostic apparatus according to claim 4, wherein the control unit stops the operation of the second memory of each of the plurality of reception channels when the interpolation process is avoided. As a memory for each of the plurality of reception channels, further comprising a memory for storing a digital signal output by a previous conversion unit,
Each of the plurality of interpolation filters performs an interpolation process using a digital signal stored in a memory of a corresponding reception channel,
Each of the plurality of signal lines forms a bypass path connecting the memory of the corresponding reception channel and the phasing addition unit,
When performing the interpolation process, the control unit outputs the digital signal stored in the memory of the corresponding reception channel to the interpolation filter of the corresponding reception channel, and when the interpolation process is avoided, the memory of the corresponding reception channel is The ultrasonic diagnostic apparatus according to claim 3, wherein a digital signal to be stored is output to the phasing addition unit.

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