Abstract:
PURPOSE: An ultrasound signal processing method for removing an HIFU(High Intensity Focused Ultrasound) signal and an ultrasound signal processing apparatus are provided to produce an intermediate frequency of an ultrasound image signal to minimize interference of the HIFU signal in the ultrasound image signal. CONSTITUTION: An HIFU signal and an ultrasound image signal are transmitted(210). An ultrasound signal including the HIFU signal and the ultrasound image signal are received twice(220). A basic frequency element and an odd harmonic frequency element of the HIFU signal are removed by adding the ultrasound signals which are received twice(230). A B-mode image is generated from the ultrasound signal(240). [Reference numerals] (210) Transmitting an HIFU signal two times to have 180 degrees phase difference and transmitting an ultrasound image signal; (220) Receiving an ultrasound signal including the HIFU signal and the ultrasound image signal two times; (230) Removing a basic frequency element and an odd harmonic frequency element of the HIFU signal by adding the ultrasound signals which are received twice; (240) Generating a B-mode image from the ultrasound signal; (AA) Start; (BB) End;
Abstract:
PURPOSE: An adaptively receiving beam focusing apparatus and a method are provided to reduce the distortion which is produced by CF unintentionally, by reducing the interference of other than purpose reflector inside the medium and the influence of noise. CONSTITUTION: A transducer(110) receives the ultrasonic signal reflected from photopoint. A delay offset application unit(140) applies the delay offset of each channel of the received ultrasonic signal to the received ultrasonic signal. A beam combiner(150) synthesizes the ultrasonic signal in which the delay time is compensated for each of the channel. The coefficient calculation unit(160) divides the aperture to a plurality of sub-aperture, and calculates the total coefficient which will be applied to the synthesized ultrasonic signal using the CF coefficient for each of the sub apertures. A coefficient application unit(170) applies the calculated total coefficient to the synthesized ultrasonic signal. [Reference numerals] (130) Delay time calculation unit; (140) Delay offset application unit; (150) Beam combiner; (160) Coefficient calculation unit; (170) Coefficient application unit; (180) Beam buffer unit
Abstract:
본 발명은 합성빔 수를 결정하는 장치에 관한 것으로서 출력된 빔포밍 영상에서 움직임 정도를 측정하는 움직임 측정부, 합성구경 기법을 적용할 경우에 측정된 움직임 정도에 기초하여 안정적인 합성빔의 갯수를 결정하는 합성빔 수 결정부, 및 합성빔 수 결정부에서 결정된 합성빔의 갯수를 디스플레이하는 디스플레이부를 포함하는 것을 특징으로 하며, 합성구경 빔집속기법을 사용하는 시스템에 있어 영상 내의 움직임을 감지하여 이를 다양한 방법으로 화면에 표시하여 줌으로써 사용자로 하여금 합성 빔의 수를 줄이거나 늘이는 등 능동적으로 대응하거나 사전에 저장된 데이터를 참조하여 시스템이 즉각적으로 합성 빔수를 변경하도록 한다.
Abstract:
PURPOSE: A synthetic aperture beam forming method for determining the number of synthetic beams according to the degree of motion and a device thereof are provided to select and reflect a proper number of synthetic beams, thereby reducing errors due to motion. CONSTITUTION: A motion measuring unit(100) measures a motion degree in an output beam forming image. A synthetic beam number determining unit(110) automatically determines the number of stable synthetic beams based on the degree of motion by using a synthetic aperture technique. A display unit(120) displays the number of the synthesized beams. The display unit increases/decreases the number of arrows in the beam forming image according to the degree of motion and displays the image.
Abstract:
PURPOSE: A method for creating a synthetic image and an ultrasonic image device using the same are provided to have uniform energy distribution by mixing a synthetic aperture beam convergence image and a reception static beam concentration image. CONSTITUTION: A reception static beam concentration unit(150) creates image data by a reception static beam concentration method. The reception static beam concentration unit has a reception channel of N. A synthetic aperture beam convergence unit(140) creates image data created by a synthetic aperture beam convergence method. The synthetic aperture beam convergence unit has a sub-aperture of M. A domain data synthetic unit(160) applies a weighted value to the created image data. The weighted value is proportional to the distance that ultrasonic waves advance.
Abstract:
본 발명은 초음파 빔포머에서의 지연시간 보간 방법에 관한 것으로서 3 개의 영상점 P1, P2, P3의 지연시간을 레지스터에 저장하고, P2가 P1과 P3 사이에 위치할 때, P1과 P2 사이의 지연시간 증가분과 P1과 P3 사이의 지연시간 증가분을 산출한 다음, P1과 P2 사이의 지연시간 증가분과 P1과 P3 사이의 지연시간 증가분을 이용하여 P1과 P2 사이에 존재하는 영상점들의 지연시간을 보간하는 것을 특징으로 하며, 모든 채널에 대해서 하나의 지연 시간 계산기를 가지고 지연 시간을 계산할 수 있고, 동일한 하드웨어 복잡도를 갖는 경우에 지연시간 보간의 정확도를 높일 수 있다.
Abstract:
PURPOSE: An ultrasonic diagnostic device and a control method thereof are provided to conveniently and accurately diagnose an ultrasonic image by automatically controlling image parameters. CONSTITUTION: A probe(10) comprises a plurality of transducers(11). A beam former(20) focuses an ultrasonic signal transmitted by each transducer of the probe to an object. An image signal processor(30) forms ultrasonic image data by executing envelope detection processing. TGC(Time Gain Compensation) parameters are produced from the ultrasonic image data. A scan converter(40) scans and changes the ultrasonic image data. A display unit(70) displays the ultrasonic image data outputted from a video processor to an ultrasonic image.
Abstract:
본 발명은 다중 주사선 생성 방법에 관한 것으로서 복수의 주사선들 각각에 대응하는 채널 정수 지연시간의 최대값을 선택하고, 선택된 최대값이 변화될 때마다 레지스터를 시프트하여 채널 데이터를 저장하는 한편, 선택된 최대값과 복수의 주사선들 각각에 대응하는 채널 정수 지연시간 간의 차이에 기초하여 저장된 채널 데이터들을 선택하고, 선택된 채널 데이터들을 각 주사선별로 합성하는 단계를 포함하는 것을 특징으로 하며, 한번에 여러 주사선을 생성함으로써, 영상의 프레임율을 증가시키거나 동일한 프레임율을 유지하면서 주사선 해상도를 증가시킬 수 있다.
Abstract:
PURPOSE: A method for estimating an ultrasound speed using edge conspicuity and a device thereof are provided to estimate the optimum ultrasound speed using edge conspicuity after an edge of image data is detected. CONSTITUTION: An ultrasound speed estimating device performs beam-forming at each ultrasound speed in a target ultrasound speed interval(220). The device detects an edge about image data of each ultrasound speed(230). The device calculates edge conspicuity of each ultrasound speed by a slope of the detected edge. The device estimates an ultrasound speed corresponding to the clear edge conspicuity as an ultrasound speed for generating an ultrasound image(270).