WO2012002006A1 - Dispositif de diagnostic ultrason et programme associé - Google Patents

Dispositif de diagnostic ultrason et programme associé Download PDF

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Publication number
WO2012002006A1
WO2012002006A1 PCT/JP2011/056213 JP2011056213W WO2012002006A1 WO 2012002006 A1 WO2012002006 A1 WO 2012002006A1 JP 2011056213 W JP2011056213 W JP 2011056213W WO 2012002006 A1 WO2012002006 A1 WO 2012002006A1
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WIPO (PCT)
Prior art keywords
sampling
data
display
sampling frequency
acquired
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PCT/JP2011/056213
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English (en)
Japanese (ja)
Inventor
加藤　美樹
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コニカミノルタエムジー株式会社
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Priority to JP2012522481A priority Critical patent/JP5803913B2/ja
Publication of WO2012002006A1 publication Critical patent/WO2012002006A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52023—Details of receivers
    • G01S7/52034—Data rate converters
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52023—Details of receivers
    • G01S7/52044—Scan converters

Definitions

  • the present invention relates to an ultrasonic diagnostic apparatus and a program.
  • a vibration probe provided with a large number of transducers (transducers) arranged in a one-dimensional or two-dimensional form, and transmits and receives ultrasonic waves to and from a subject such as a living body. Converts sound waves into electrical signals, samples them, performs phasing addition on the data obtained by sampling, generates an ultrasonic image based on the data obtained as a result, and displays this on the image display device.
  • transducers transducers
  • Such an ultrasonic diagnostic apparatus has been devised in various ways to obtain a good image in order to enable accurate diagnosis.
  • two interpolation lines at a line position shifted from the position of the reception line are weighted with data from the reception line in proportion to the interval from the reception line position to the scanning line, and the weighted data is combined to form the interpolation line.
  • display an ultrasonic image based on this for example, patent documents 1).
  • an echo signal in units of frames is sampled from a diagnostic region with a predetermined sampling clock and taken into the image memory, the whole image is taken into the first image memory with a sampling clock thinned to 1 / N, and an enlarged image is obtained.
  • a window signal indicating a region of interest which is gated with a predetermined sampling clock, fetched into a second image memory, and displays each image at the same frame rate (for example, Patent Document 2).
  • the received signal is sampled at as fine a pitch as possible, the S / N (Signal-Noise ratio) after phasing addition is improved and the reproducibility when the waveform is reproduced based on the sampled data. Since it becomes faithful, a higher sampling frequency can generate a better image.
  • the resolution of the image display device is about 1000 dots vertically, as long as image display is being performed, all of the sampled signals cannot be reflected in the image display, and the process of converting the number of display pixels (pixel number conversion) It was necessary to reduce the amount of data to a size that allows data to be displayed after processing. In many cases, this pixel number conversion process generates waveform distortion and interpolation error in principle.
  • An object of the present invention is to provide an ultrasonic diagnostic apparatus and program capable of displaying a good ultrasonic diagnostic image without causing an interpolation error or data distortion when converting a high acquisition sampling frequency to a low display-dependent sampling frequency. Is to provide.
  • the invention according to claim 1 is an ultrasonic diagnostic apparatus, An ultrasonic probe having a plurality of transducers for outputting a transmission signal by receiving a reflected ultrasonic wave from the subject and outputting a transmission ultrasonic wave toward the subject by a driving signal; A transmitter for supplying a drive signal to the vibrator; A reception unit that samples the reception signal obtained by the transducer at a preset acquisition sampling frequency, and obtains acquisition sampling data by phasing and adding the reception signal at each sampling point; A display unit for displaying an image; A control unit that thins out data from the acquired sampling data and down-samples to obtain a display-dependent sampling frequency set according to a display image size of the display unit; With The display unit displays an ultrasound diagnostic image based on the acquired sampling data down-sampled by the control unit.
  • the invention according to claim 2 is the ultrasonic diagnostic apparatus according to claim 1,
  • the control unit oversamples the acquired sampling data obtained by the receiving unit so as to be a least common multiple of the acquired sampling frequency and the display dependent sampling frequency, and then becomes the display dependent sampling frequency. It is characterized by downsampling.
  • Invention of Claim 3 is a program, Comprising: A computer provided in an ultrasonic diagnostic apparatus having a plurality of transducers that outputs a reception signal by receiving a reflected ultrasonic wave from a subject while outputting a transmission ultrasonic wave toward the subject by a drive signal, A function of acquiring the acquired sampling data of the received signal sampled at a preset acquisition sampling frequency and phased and added for each sampling point; A function of thinning down the data from the acquired sampling data and down-sampling so as to obtain a display-dependent sampling frequency set according to the display image size of the display unit that displays an ultrasound diagnostic image based on the acquired sampling data; , A function of outputting the downsampled acquired sampling data; It is characterized by realizing.
  • FIG. 1 It is a figure which shows the external appearance structure of the ultrasound diagnosing device in embodiment of this invention. It is a block diagram which shows schematic structure of an ultrasound diagnosing device. It is a flowchart explaining a sampling frequency setting process. It is a flowchart explaining a sampling frequency conversion process. It is a figure explaining the reception timing of the reflected ultrasonic wave in a vibrator
  • the ultrasonic diagnostic apparatus S transmits ultrasonic waves (transmission ultrasonic waves) to a subject such as a living body (not shown), and this subject.
  • the ultrasonic probe 2 that receives the reflected wave of reflected ultrasonic waves (reflected ultrasonic wave: echo) is connected to the ultrasonic probe 2 via the cable 3 and an electric signal is sent to the ultrasonic probe 2.
  • the ultrasonic probe 2 transmits the transmission ultrasonic wave to the subject, and in response to the reflected ultrasonic wave from the subject received by the ultrasonic probe 2.
  • An ultrasonic diagnostic apparatus main body 1 that images the internal state of the subject as an ultrasonic image based on a reception signal that is an electrical signal generated by the ultrasonic probe 2 is configured.
  • the ultrasonic probe 2 includes a transducer 2a made of a piezoelectric element. As shown in FIG. 5, a plurality of transducers 2a are arranged in a one-dimensional array in the azimuth direction (scanning direction or vertical direction). Has been. In the present embodiment, the ultrasonic probe 2 including n (for example, 128) transducers 2a is used. Note that the vibrators 2a may be arranged in a two-dimensional array. The number of vibrators 2a can be set arbitrarily. Further, in the present embodiment, the ultrasonic probe 2 that performs the linear scanning method is applied, but the one that performs the sector scanning method or the one that performs the convex scanning method may be applied.
  • the ultrasonic diagnostic apparatus body 1 includes an operation input unit 11, a transmission unit 12, a reception unit 13, an image generation unit 14, a memory unit 15, and a DSC (Digital Scan Converter). 16, a display unit 17, and a control unit 18.
  • an operation input unit 11 a transmission unit 12, a reception unit 13, an image generation unit 14, a memory unit 15, and a DSC (Digital Scan Converter).
  • a display unit 17 a control unit 18.
  • DSC Digital Scan Converter
  • the operation input unit 11 includes, for example, various switches, buttons, a trackball, a mouse, a keyboard, and the like for inputting data such as a command to start diagnosis and personal information of a subject, and the like. Output to the control unit 18.
  • the transmission unit 12 is a circuit that supplies a drive signal, which is an electrical signal, to the ultrasonic probe 2 via the cable 3 under the control of the control unit 18 to generate transmission ultrasonic waves in the ultrasonic probe 2. .
  • the transmission unit 12 includes, for example, a clock generation circuit, a delay circuit, and a pulse generation circuit.
  • the clock generation circuit is a circuit that generates a clock signal that determines the transmission timing and transmission frequency of the drive signal.
  • the delay circuit sets a transmission signal transmission timing for each individual path corresponding to each transducer 2a, delays transmission of the drive signal by the set delay time, and is a transmission beam constituted by transmission ultrasonic waves. This is a circuit for performing focusing.
  • the pulse generation circuit is a circuit for generating a pulse signal as a drive signal at a predetermined cycle.
  • the receiving unit 13 is a circuit that receives a reception signal of an electrical signal from the ultrasonic probe 2 via the cable 3 under the control of the control unit 18.
  • the frequency of the reception signal received by the reception unit 13 is 15 MHz, for example, but varies depending on the frequency of the pulse signal generated by the transmission unit 12.
  • the receiving unit 13 includes, for example, an amplifier, an A / D conversion circuit, and a phasing addition circuit.
  • the amplifier is a circuit for amplifying the received signal with a predetermined amplification factor set in advance for each individual path corresponding to each transducer 2a.
  • the A / D conversion circuit is a circuit for sampling the amplified received signal at a predetermined sampling frequency and performing A / D conversion.
  • the phasing addition circuit adjusts the time phase by giving a delay time to each individual path corresponding to each transducer 2a with respect to the A / D converted received signal, and adds these (phasing addition) to generate a sound. It is a circuit for generating line data.
  • the receiving unit 13 includes a memory (not shown) that temporarily stores sound ray data generated by the phasing addition circuit.
  • the image generation unit 14 performs logarithmic amplification, envelope detection processing, and the like on the sound ray data from the reception unit 13 to generate B-mode image data.
  • the B-mode image data generated in this way is transmitted to the memory unit 15.
  • the memory unit 15 is configured by a semiconductor memory such as DRAM (Dynamic Random Access Memory), for example, and stores the B-mode image data transmitted from the image generation unit 14 in units of frames. That is, it can be stored as frame image data.
  • the stored frame image data is transmitted to the DSC 16 under the control of the control unit 18.
  • the DSC 16 converts the frame image data received from the memory unit 15 into an image signal based on a television signal scanning method, and outputs the image signal to the display unit 17.
  • the display unit 17 is a display device such as an LCD (Liquid Crystal Display), a CRT (Cathode-Ray Tube) display, an organic EL (Electronic Luminescence) display, and a plasma display.
  • the display unit 17 displays an image on the display screen according to the image signal output from the DSC 16.
  • the control unit 18 includes, for example, a CPU (Central Processing Unit), a ROM (Read Only Memory), and a RAM (Random Access Memory), and reads various processing programs such as a system program stored in the ROM to read the RAM.
  • the operation of each part of the ultrasonic diagnostic apparatus S is centrally controlled according to the developed program.
  • the ROM is composed of a nonvolatile memory such as a semiconductor, and is a system program corresponding to the ultrasonic diagnostic apparatus S and various processing programs such as a sampling frequency setting process and a sampling frequency conversion process, which will be described later, which can be executed on the system program. And various data.
  • These programs are stored in the form of computer-readable program code, and the CPU sequentially executes operations according to the program code.
  • the RAM forms a work area for temporarily storing various programs executed by the CPU and data related to these programs.
  • sampling frequency setting process executed in the ultrasonic diagnostic apparatus S configured as described above will be described with reference to FIG.
  • This sampling frequency setting process is, for example, a process executed when the power is turned on or when a setting operation is performed by the operation input unit 11.
  • the control unit 18 sets a display dependent sampling frequency (Fsd) that matches the display size of the display unit 17 (step S101).
  • the setting of the display-dependent sampling frequency is performed by referring to a predetermined table and selecting a corresponding sampling frequency from the display size information output from the display unit 17, for example.
  • an image having a maximum display size of 1000 dots is displayed on the display unit 17 and an image that is about four times the display image size is taken into consideration in order to implement a zoom function for enlarging a part of the portion.
  • the display dependent sampling frequency is set to 60 MHz.
  • the setting of the display dependent sampling frequency may be arbitrarily selected by the user.
  • the control unit 18 sets the acquisition sampling frequency (Fss) according to the signal frequency to be extracted (step S102), and then ends this process.
  • This acquired sampling frequency is preferably set to a relatively high frequency in order to improve the S / N in the data after phasing addition, for example, and is set to 200 MHz in the present embodiment.
  • the receiving unit 13 samples the 15 MHz reception signal at a sampling frequency of 200 MHz, and performs phasing addition at this data rate.
  • the sampling data acquired as a result is referred to as acquired sampling data.
  • the acquired sampling frequency may be determined in advance, or may be arbitrarily selected by the user.
  • This sampling frequency conversion process is a process that is executed, for example, every time the received signal sampled by the receiving unit 14 is phased and added to generate sound ray data.
  • the control unit 18 sets a sampling frequency (Fso) that is the least common multiple of the acquisition sampling frequency (Fss) and the display dependent sampling frequency (Fsd), and the sampling data acquired at the acquisition sampling frequency (Fss) Oversampling is performed by inserting zero data (zero padding) so that the set sampling frequency (Fso) is obtained (step S201).
  • the sampling frequency (Fso) that is the least common multiple is set to 600 MHz. Then, by inserting two pieces of zero data between each piece of acquired sampling data, the acquired sampling data with a sampling frequency of 200 MHz is oversampled to 600 MHz.
  • the control unit 18 performs a band limiting filter (BPF (Band-Pass Filter) or LPF (Low-Pass Filter)) process on the oversampled acquired sampling data (Step S202). Specifically, it is realized by applying a band-limiting filter about half the display-dependent sampling frequency (Fsd) to the oversampled acquired sampling data.
  • a 28 MHz LPF (Low-Pass Filter) which is a frequency slightly lower than half of the display dependent sampling frequency (Fsd) is applied in order to provide a margin.
  • control unit 18 performs gain adjustment (step S203). Specifically, the control unit 18 adjusts the acquired sampling data so as to obtain a gain by applying a coefficient corresponding to an oversampled multiple.
  • control unit 18 performs data decimation (decimation processing) so as to obtain the display-dependent sampling frequency (Fsd) from the acquired sampling data oversampled to the sampling frequency (Fso) (step S204). . Specifically, the control unit 18 obtains sampling data with a sampling frequency of 60 MHz by thinning out the acquired sampling data oversampled to a sampling frequency of 600 MHz so that it becomes 1/10.
  • control part 18 outputs the acquisition sampling data downsampled as mentioned above to the image generation part 14 (step S205).
  • image data without distortion can be obtained by generating image data as described above. The reason will be described with reference to the drawings.
  • n transducers 2 a are arranged in the azimuth direction (scanning direction) in the ultrasound probe 2.
  • the time until the reflected ultrasonic wave is received from the echo source E differs for each transducer.
  • the distance from the echo source E to the transducer 2a is 30 mm and the transducer pitch is 0.15 mm
  • the distance from the echo source E to the reception position of the transducer 2a arranged at the position “0” L0 is expressed by the following formula (1)
  • the distance L15 from the echo source E to the receiving position of the transducer 2a arranged at the position “15” is expressed by the following formula (2). Note that the distance indicated by LC in FIG.
  • the distance to the receiving position of the child 2a is 0.075 mm, which is half the pitch of the transducer 2a.
  • the amount of sampling timing deviation until the reflected ultrasonic wave from the echo source E is received is (L0-L15) / 1540 * 200 * 10 6 ⁇ 11.6 (3)
  • the reception signal acquired from the transducer 2a arranged at the position “0” is delayed by 12 samples from the reception signal obtained from the transducer 2a arranged at the position “15”.
  • a phasing addition is performed by adding to the data.
  • the sampling frequency of the received signal is as high as possible because good data can be obtained.
  • a sampling frequency of wavelength ( ⁇ ) / 8 or more it is said that it is preferable. This is because when the phasing addition is performed, the delay amount of the sample often does not become an integer ratio as shown in the above-described equation (3), and even if the delay processing is performed on the sampled data, This is because the waveforms are not necessarily matched and data is added, but for example, data shifted by one sample may be added.
  • FIG. 6 shows a case where data for one sample is shifted and phased. As shown in FIG. 6, at a sampling frequency of 60 MHz, only 4 points of sampling data can be obtained for one period. Then, when the sampling data phased in this way is added for each sampling point after phasing, the result is as shown in FIG.
  • FIG. 8 shows a case where data for one sample is similarly shifted and phased. As shown in FIG. 8, at a sampling frequency of 200 MHz, about 13 sampling data can be obtained for one period. Then, when the sampling data phased in this way is added for each sampling point after phasing, the result is as shown in FIG.
  • FIG. 10 data (original data) sampled at a sampling frequency of 60 MHz with respect to a reception signal composed of four 15 MHz sine waves, and the original data and data delayed by one sample from the original data are added.
  • the result of performing 1024-point fast Fourier transform (FFT) on the object is shown.
  • the original data is represented by a broken line, and the original data and a sum of data delayed by one sample from the original data are represented by a solid line.
  • FIG. 11 shows data (original data) sampled at a sampling frequency of 200 MHz with respect to a reception signal composed of four 15 MHz sine waves, and original data and data delayed by one sample from the original data.
  • the result of performing 1024-point fast Fourier transform (FFT) on the sum is shown.
  • the original data is represented by a broken line, and the original data and a sum of data delayed by one sample from the original data are represented by a solid line.
  • a transmission ultrasonic wave is output to an object at a distance of 50 mm from the transducer 2a, and then a reflected ultrasonic wave is output.
  • the number of data sampled until the reception of is completed as shown in the following formula (4).
  • the speed of the transmission ultrasonic wave and the reflected ultrasonic wave is 1540 m / s. 50 * 10 ⁇ 3 * 2/1540 * 200 * 10 6 ⁇ 12987 (4)
  • the display size of the LCD used for the display unit 17 has, for example, a standard as shown in FIG. Of the display size standards shown in FIG. 12, high-resolution LCDs such as SXGA and UGA are generally used most frequently.
  • the display capability of such an LCD is 1024 dots vertically for SXGA and 1200 dots vertically for UGA.
  • pixels of about 1000 dots are usually used for display. That is, when sampling is performed at a sampling frequency of 200 MHz, all the sampled data cannot be converted into an image and cannot be displayed. Therefore, in the example shown in the above formula (4), until about 1/12. It is necessary to thin out the sampled data.
  • the ultrasonic diagnostic apparatus in order to enlarge and display a part of the image, it is performed to hold image data about four times the display size. It is preferable to hold sampling data with a sampling frequency of 60 MHz.
  • the transmission ultrasonic wave is output to the object at a distance of 50 mm from the transducer 2a and then the reflected ultrasonic wave is output as in the above example.
  • the number of data sampled until the reception of the sound wave is completed is expressed by the following equation (5). 50 * 10 ⁇ 3 * 2/1540 * 60 * 10 6 ⁇ 3896 (5)
  • sampling data can be calculated as follows.
  • the sampling point with a sampling frequency of 60 MHz is located at positions a to c in the figure. That is, the sampling points a and b do not coincide with the sampling points at the sampling frequency of 200 MHz, and thus need to be calculated by interpolation processing.
  • the sampling data can be simply calculated by calculating by linear interpolation as follows.
  • the value (sampling value) which the sampling data in each sampling point by the sampling frequency of 200 MHz shows in FIG.
  • the sampling values at the sampling points “6” and “7” at the sampling frequency of 200 MHz are generated by linear interpolation. That is, as shown in FIG. 16, when the distance from the sampling point “6” to “7” at the sampling frequency of 200 MHz is 1, the sampling point b is 2/3 from the sampling point “6” at the sampling frequency of 200 MHz. Therefore, the sampling value at the sampling point b is as shown in the following formula (7). 0.707107 * 1/3 + 0.309017 * 2 / 3 ⁇ 0.4417137 (7)
  • FIG. 17 shows the result of sampling a 15 MHz received signal at a sampling frequency of 600 MHz.
  • sampling values are obtained by performing linear interpolation on sampling points a and b
  • these sampling values have errors when compared with values obtained by actual sampling. Recognize. That is, such an error becomes a waveform distortion or an interpolation error and is reflected in the image data as it is, which may cause an artifact.
  • THI that images waveform distortion that occurs during propagation of ultrasound waves is applied
  • such an error is directly imaged as an artifact.
  • a 15 MHz reception signal is sampled at a sampling frequency of 200 MHz, and phasing addition is performed to obtain a sampling result shown in FIG. 14, and then, as shown in FIG. Oversampling is performed by inserting two zeros between each piece of acquired sampling data so that the frequency becomes 600 MHz.
  • the BPF process is performed on the oversampled data, as shown in FIG. 19, a result almost same as the result obtained by actually sampling at the sampling frequency of 600 MHz is obtained.
  • the sampling data over-sampled as described above is thinned out to 1/10 and down-sampled so that the sampling frequency is 60 MHz, the result shown in FIG. 20 is obtained. . That is, the result is almost the same as the original data obtained by sampling the 15 MHz received signal at the sampling frequency of 60 MHz, and the data is highly accurate.
  • the ultrasonic probe 2 outputs a transmission ultrasonic wave toward the subject by the drive signal and receives a reflected ultrasonic wave from the subject. Accordingly, a plurality of vibrators 2a that output reception signals are provided. Then, the transmission unit 12 supplies a drive signal to the vibrator 2a. Then, the reception unit 13 samples the reception signal obtained by the transducer 2a at a preset acquisition sampling frequency. Then, the receiving unit 13 obtains acquired sampling data by phasing and adding the received signals for each sampling point. Then, the display unit 17 displays an ultrasound diagnostic image based on the acquired sampling data.
  • the control unit 18 performs downsampling by thinning out the data from the acquired sampling data so that the display-dependent sampling frequency set according to the display image size of the display unit 17 is obtained.
  • the display unit 17 displays an ultrasound diagnostic image based on the acquired sampling data downsampled by the control unit 18.
  • control unit 18 after oversampling the acquired sampling data obtained by the receiving unit 13 so as to be the least common multiple of the acquired sampling frequency and the display dependent sampling frequency, Downsampling to a display-dependent sampling frequency.
  • generation of interpolation data associated with downsampling becomes unnecessary, generation of artifacts due to interpolation errors caused by generating interpolation data can be suppressed, and highly accurate image data can be generated.
  • the description in the embodiment of the present invention is an example of the ultrasonic diagnostic apparatus according to the present invention, and the present invention is not limited to this.
  • the detailed configuration and detailed operation of each functional unit constituting the ultrasonic diagnostic apparatus can be appropriately changed.
  • the sampling frequency which is the least common multiple of the acquisition sampling frequency and the display dependent sampling frequency is set and oversampling is performed on the acquired sampling data.
  • the frequency is an integral multiple of the frequency, the oversampling process is not necessary.
  • the oversampling process and the downsampling process are realized by software processing by the control unit, but may be realized by hardware.
  • the oversampling process is performed by inserting zero data between the sampling data.
  • the oversampling process may be performed by another method.
  • the downsampling process is performed by thinning out the sampling data.
  • the downsampling process may be performed by other methods.
  • a hard disk, a semiconductor nonvolatile memory, or the like is used as a computer-readable medium of the program according to the present invention, but the present invention is not limited to this example.
  • a portable recording medium such as a CD-ROM can be applied.
  • a carrier wave is also used as a medium for providing program data according to the present invention via a communication line.

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  • Computer Networks & Wireless Communication (AREA)
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Abstract

La présente invention concerne un dispositif de diagnostic ultrason et un programme pouvant afficher de bonnes images de diagnostic ultrason. Une unité de réception (13) soumet un signal reçu obtenu au moyen d'un oscillateur (2a) à un échantillonnage, selon une fréquence d'échantillonnage d'acquisition préfixée. Ladite unité de réception (13) soumet ensuite le signal reçu à une addition de phasage à chaque point d'échantillonnage, et obtient ainsi des données d'échantillonnage d'acquisition. Une unité d'affichage (17) affiche alors une image. Puis une unité de commande (18) réalise un sous-échantillonnage en retirant des données aux données d'échantillonnage d'acquisition, de manière à satisfaire à une fréquence d'échantillonnage dépendante de l'affichage, fixée selon la taille d'image d'affichage de l'unité d'affichage (17). L'unité d'affichage (17) affiche alors une image de diagnostic ultrason, sur la base des données d'échantillonnage d'acquisition qui ont été soumises à un sous-échantillonnage par l'unité de commande (18).
PCT/JP2011/056213 2010-06-29 2011-03-16 Dispositif de diagnostic ultrason et programme associé WO2012002006A1 (fr)

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WO2017060144A1 (fr) 2015-10-07 2017-04-13 F. Hoffmann-La Roche Ag Anticorps bispécifiques tétravalents pour un récepteur de co-stimulation du tnf
WO2018127473A1 (fr) 2017-01-03 2018-07-12 F. Hoffmann-La Roche Ag Molécules bispécifiques de liaison à l'antigène comprenant un clone 20h4.9 anti-4-1bb
WO2018185045A1 (fr) 2017-04-04 2018-10-11 F. Hoffmann-La Roche Ag Nouvelles molécules bispécifiques de liaison à l'antigène capables de se lier spécifiquement à cd40 et à fap
WO2020007817A1 (fr) 2018-07-04 2020-01-09 F. Hoffmann-La Roche Ag Nouvelles molécules de liaison à l'antigène 4-1bb bispécifiques
WO2020070035A1 (fr) 2018-10-01 2020-04-09 F. Hoffmann-La Roche Ag Molécules bispécifiques de liaison à l'antigène ayant une liaison trivalent à cd40
JPWO2019230740A1 (ja) * 2018-05-28 2021-08-26 国立研究開発法人理化学研究所 オーバーサンプリングによる断層画像データの取得方法、取得装置、および制御プログラム
WO2024074727A1 (fr) 2022-10-07 2024-04-11 Genethon Immunothérapie cellulaire par car-t anti-fap pour traiter des myopathies squelettiques

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WO2017055398A2 (fr) 2015-10-02 2017-04-06 F. Hoffmann-La Roche Ag Anticorps bispécifiques spécifiques d'un récepteur de co-stimulation du tnf
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WO2020007817A1 (fr) 2018-07-04 2020-01-09 F. Hoffmann-La Roche Ag Nouvelles molécules de liaison à l'antigène 4-1bb bispécifiques
WO2020070035A1 (fr) 2018-10-01 2020-04-09 F. Hoffmann-La Roche Ag Molécules bispécifiques de liaison à l'antigène ayant une liaison trivalent à cd40
WO2024074727A1 (fr) 2022-10-07 2024-04-11 Genethon Immunothérapie cellulaire par car-t anti-fap pour traiter des myopathies squelettiques

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