WO2005013829A1 - 超音波撮像装置および超音波撮像方法 - Google Patents
超音波撮像装置および超音波撮像方法 Download PDFInfo
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- WO2005013829A1 WO2005013829A1 PCT/JP2004/008391 JP2004008391W WO2005013829A1 WO 2005013829 A1 WO2005013829 A1 WO 2005013829A1 JP 2004008391 W JP2004008391 W JP 2004008391W WO 2005013829 A1 WO2005013829 A1 WO 2005013829A1
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
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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
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8995—Combining images from different aspect angles, e.g. spatial compounding
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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
- G01S7/52077—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 with means for elimination of unwanted signals, e.g. noise or interference
Definitions
- the present invention relates to an ultrasonic imaging apparatus used for medical diagnosis and the like, and particularly relates to a compound scanning image in which image signals obtained by scanning from various angles are combined and displayed as one image. And a technique for obtaining high-quality tomographic images referred to as "high-quality tomographic images. Background art
- the ultrasonic imaging device applies an ultrasonic probe to the surface of the object, transmits ultrasonic waves from the probe to the object, and receives a reflected wave (echo signal) from inside the object,
- a reflected wave echo signal
- the state of each part of the subject is displayed as a tomographic image on the basis of the echo signal for diagnosis and the like.
- FIG. 1A is a diagram illustrating a general configuration of an ultrasonic imaging apparatus.
- 10 is an information processing device such as a personal computer.
- 11 is a CPU
- 12 is a memory
- 13 is a hard disk
- 21 is an input device
- 22 is a display device.
- the hard disk 13 stores various programs and data necessary for the operation of the ultrasonic imaging apparatus.
- the programs and data are called up as necessary and stored in the memory 12, and are managed under the control of the CPU 11. , Used for operation.
- the input device 21 is a keyboard, a mouse, or the like, and is used by a user of the ultrasonic imaging apparatus to input necessary setting information or to give an operation signal.
- the display device 13 displays a necessary operation screen, a screen of an imaging result, and the like.
- Reference numerals 23 and 24 denote an ultrasonic transmission beam former and a reception beam former, which are connected to the path 14 of the information processing device 10. Further, the transmission beamformer 23 and the reception beamformer 24 include a transmission / reception separator 3 1 Is connected to the ultrasonic probe 32 of the ultrasonic wave. The transmission beamformer 23 responds to the digital signal supplied from the information processing device 10 so that the ultrasonic signal corresponding to the program corresponding to the operation signal of the user is transmitted from the ultrasonic probe 32. The ultrasonic transmission signal is generated and sent to the ultrasonic probe 32 via the transmission / reception separator 31.
- the transmitted ultrasonic signal is received by the ultrasonic probe 32 as a reflected wave from the inside of the subject, a signal corresponding thereto is transmitted via the transmission / reception separator 31 to the reception beamformer 2.
- the receiving beamformer 24 performs necessary signal processing such as digitization on the signal and sends it to the information processing device 10.
- the received signal is processed by a program corresponding to the purpose of imaging, and the result is displayed on the display device 13.
- FIG. 1 (B) is a diagram showing an example of an ultrasonic probe 32, in which n sets of vibrators 1-1, 112 and 113 arranged in a straight line divided into three are arranged in parallel. This is an example of arrangement.
- a transmission signal from the transmission control circuit 23 is sent to these transducers, and a signal corresponding to the reflected wave from the inside of the subject detected by the transducer is sent to the reception control circuit 24. Wiring for sending is provided.
- a metal powder and a metal powder for efficiently bringing the transducer into contact with the subject and efficiently transmitting and receiving ultrasonic waves to and from the subject are provided.
- An acoustic matching layer 5 made of a mixture of materials and an acoustic lens also made of a polymer material are provided.
- the depth direction can be controlled like F i-F or F 2 -F 2 shown in the figure.
- control is performed so that the beam directions are in the directions of A, B, and C on the axis of the focal point. Can be done.
- the ultrasonic probe 32 also has a handle for the user to hold, but is not shown.
- the ultrasonic probe 32 is not limited to the example shown in FIG. 1 (B), and is formed by arranging a plurality of transducers at regular intervals in a linear, curved, or planar shape according to the purpose of imaging. Etc. are produced in various forms.
- a linear scanning type ultrasonic imaging apparatus uses a predetermined aperture selection function to select a group of transducers that are driven at the same time to form an aperture, and sequentially moves the aperture to move the inside of the subject or object. Is scanned with an ultrasonic beam. The same applies to a competas running type ultrasonic imaging apparatus.
- the second advantage is that it has a great effect on removing speckle, which causes deterioration of contrast performance. This is because the speckle patterns are different between images captured from directions with sufficiently different angles, and the signal intensity is increased by the sum of the reflected portion of the original object due to the addition. However, since the signal strength of the speckle pattern increases only in proportion to the square root of the addition, the contrast resolution improves in proportion to the square root of N, where N is the number of additions.
- An aperture synthesizing method as disclosed in Non-Patent Document 1 is also known as a method for performing the method.
- Aperture synthesis adds signals from a plurality of different directions at the coherent stage, which is equivalent to effectively increasing the aperture and contributing to an improvement in spatial resolution.
- the above two known examples disclose a method of estimating a positional shift between images by using a correlation method before synthesizing the images to minimize blurring of the images due to the movement of the subject.
- the current image synthesis method has two types, the compound imaging method and the aperture synthesis method, and each has different advantages.
- the transfer function of the ultrasonic probe 32 has a width of about several waves on the time axis because the width ′ in the frequency space is limited.
- transmission of ultrasonic waves from the ultrasonic probe 32 is performed by transmitting and receiving ultrasonic waves reflected from the subject by the ultrasonic probe 32.
- Ultrasonic probe 32 The width of the envelope is about 2 to 4 waves because the transfer function is affected twice. In other words, it can be seen that the effect on the motion differs by about 10 times between the coherent case and the incoherent case. If the amount of displacement between the synthesized images can be perfectly ideally corrected for each pixel, the effect of motion can be corrected by one of the two known methods. In reality, it is difficult to accurately estimate local deviations because the accuracy of the acquired values is not guaranteed due to the influence of noise, and there is a deviation in the direction orthogonal to the tomographic image.
- the correction of the local deviation is completely abandoned, and if the deviation is small (for example, smaller than 1/4 of the wavelength) from the global deviation amount, the synthesis is performed between the RF data. If the deviation is large, synthesis is performed using the envelope detection signal.
- the magnitude of the shift can be determined by focusing on the cross-correlation of the RF data between images of different frames. Furthermore, by controlling the reference frequency of the heterodyne detection, it is possible to separate the synthesis from the RF data or the synthesis using the envelope detection signal.
- FIG. 1 (A) is a diagram showing a general configuration of an ultrasonic imaging apparatus
- FIG. 1 (B) is a diagram showing an example of an ultrasonic probe. .
- FIG. 2 is a diagram showing a signal processing flow of Embodiment 1 of the ultrasonic imaging apparatus of the present invention.
- FIG. 3 is a diagram showing a signal processing flow of a second embodiment of the ultrasonic imaging apparatus of the present invention.
- FIG. 4 is a diagram showing a signal processing flow of Embodiment 3 of the ultrasonic imaging apparatus of the present invention.
- FIG. 5 (A) schematically shows the directions of beams in three directions A, B, and C in which the beam traveling directions received by the transmitting and receiving transducer 32 are different, and (B) shows the direction of the receiving and transmitting transducer 32.
- FIG. 6C is a diagram showing a beam pattern of an RF signal in each beam traveling direction
- FIG. 7C is a diagram showing a beam pattern of the RF signal received by the transmitting / receiving transducer 32 after envelope detection.
- FIG. 6 (A) is a diagram showing an example of a setting curve for setting the reference frequency ⁇ for heterodyne detection.
- Figures 8 (A), (B), (C) and (D) show the center frequency ⁇ of the ultrasonic wave.
- Figure 2 shows an example of a beam pattern showing the results after heterodyne detection when the frequency ⁇ ⁇ of the reference wave is It is.
- FIG. 2 is a diagram showing a signal processing flow of Embodiment 1 of the ultrasonic imaging apparatus of the present invention.
- Numeral 101 is a preparation step in which the type of the ultrasonic probe to be used, a code indicating the target part of the image, and the like are input via the input device 21.
- Numeral 103 denotes a step for designating the number of frames to be image-combined in which the image of the target region to be imaged is to be synthesized, which is input via the input device 21.
- the number of frames used for image synthesis is at least three or more.
- the number of frames may be increased from 7 to about 15. The more the number of frames, the greater the effect of image synthesis and the disadvantages due to the synthesis.
- Reference numeral 105 denotes a step for setting the transmission direction of the ultrasonic wave to the imaging target site, which is input via the input device 21. This may correspond to the number of frames for performing image synthesis specified in step 103, and may be automatically set by a program according to the number of frames that have been imaged.
- the transmission direction of the ultrasonic wave means, in Fig. 1 (B), changing the direction in which the ultrasonic wave is transmitted in different directions A, B, and C on the plane of the focal point F t —.
- FIG. 5 (A) this is schematically shown as a rectangle A shown by a solid line, a rectangle B shown by an alternate long and short dash line, and a rectangle C shown by a broken line. That is, rectangles A, B, and C schematically show the state in which an ultrasonic beam is transmitted to the subject at the same depth of focus and at different angles, respectively, and re-scanning is performed.
- Step 107 is a step of transmitting and receiving ultrasonic waves for one frame and storing RF data.
- the number of frames to be imaged is specified (step 103) and the transmission direction is set (step 105).
- An ultrasonic pulse signal corresponding to the program is generated, and this is converted into a signal to be given to the transducer of the ultrasonic probe 32 by the transmission beamformer 23, and the ultrasonic probe is transmitted through the transmission / reception separator 31.
- Element 32 is given to the oscillator.
- the ultrasonic signal reflected from the imaging target is received by the transducer of the ultrasonic probe 32, converted into an electric signal, and given to the receiving beam former 24 via the transmission / reception separator 31.
- Step 109 evaluates the number of frames that have been imaged, and checks whether the transmission and reception of ultrasonic waves and the storage of RF data for the number of frames specified in step 103 have been completed. If the storage for the number of frames specified in step 103 has not been completed, the process returns to step 105 to transmit and receive one frame of ultrasonic waves in the next transmission direction. Do. If it is determined in step 108 that the number of frames that have been imaged has reached the number of frames specified in step 103, the process proceeds to data evaluation.
- Step 113 evaluates whether the deformation between images of different frames is larger than a set value. That is, if the RF data cross-correlation between images of different frames calculated in step 11 is larger than the set value, the RF data of each frame stored in memory 12 is detected by envelope detection. Then, from this detected data, data synthesis between images of different frames is performed (step 1 17). If the RF data cross-correlation between images of different frames calculated in step 1 1 is smaller than the set value, the RF data of each frame stored in (Step 1 2 1). The combined RF data 'is subjected to envelope detection (step 12 1).
- Reference numeral 123 denotes an image display step, which displays a surface image according to a predetermined program on the display device 22 from one of the data of the step 117 and the data of the step 121.
- 1 25 is a step for judging the necessity of image quality adjustment. For example, in the image display step 123, a question “Do you need to obtain data again?" Display the "NO" switch. Then, when the user is dissatisfied with the image displayed on the display device 22 and selects “YES”, the process returns to step 103 and executes the necessary settings again. When "NO" is selected, the imaging ends.
- the target region of the imaging between the signals to be synthesized is different between the case of a coherent signal such as an RF signal and the case of an incoherent signal such as an envelope detection signal.
- the effect of displacement is very different. In other words, in the case of coherence, if there is a shift of half the wave length, the signals completely cancel each other out, and the effect can be neglected with a shift of less than 1/4. On the other hand, in the case of incoherence, there is no cancellation, so if the displacement is less than the width of the envelope, the effect is small.
- the RF data cross-correlation between images of different frames is calculated in step 11, and the deformation between the images of different frames is set in step 11 13. Evaluate whether it is greater than. If the displacement of the imaging target between images of different frames is larger than the set value. Incoherent signals are processed with little effect due to the shift between frame images, and different frames are used. To be captured between images If the displacement of the part is smaller than the set value, it is processed as a coherent signal.
- M be the number of data in the depth direction of one frame
- N be the number of data in the horizontal direction.
- the coordinates increase in the order of the raster running.
- the scanning order is to run sequentially from the next.
- the luminance of the i-th pixel in the depth direction and the horizontal direction of the frame number k; the luminance of the j-th pixel, and the amplitude of the RF signal at the same position are ⁇ ”.
- the depth method obtains coarser data in the azimuth direction than sampling in finer than the Nyquist frequency of the RF wave.
- the sampling interval in the depth direction is 15 ⁇ m.
- the sampling interval in the azimuth direction is usually about the element pitch or about half thereof, if the element width is assumed to be about half of the wavelength at the center frequency, then when the center frequency is 3 MHz, 1 It is about 25 / Zm, which is about 10 times the sampling interval in the depth direction. Therefore, if the frame rate is sufficiently fast for the movement of the object, the deformation need only be measured in the depth direction.
- the window is set for correlation for the following two reasons. First, if all the data for one raster at a time is used, it is disadvantageous if it cannot be treated as a rigid body like a living body, and if the deformation varies depending on the depth. Secondly, in the present invention, since correlation is made between images having different angles, it is not possible to match the locations in the entire depth direction when comparing one raster as a whole. However, if the window width is limited, it is possible to keep the raster from straddling within the window.
- the raster number of the correlating partner changes as the window is moved.
- the displacement at pixel ij is determined by these methods, if the effect of noise is small, it can be used as it is, but if the effect of noise is large, a spatial low-pass filter can be used. It is also possible to perform the processing by replacing the value with the averaged value through.
- two-dimensional deformation can be calculated by two-dimensional correlation including the azimuth direction.
- the correlation between the integration patterns of It is also possible to calculate the deformation in the azimuth direction and calculate the two-dimensional deformation in combination with the deformation in the depth direction already explained.
- the horizontal axis shows the shift between the images of the frame
- the vertical axis shows an example of the envelope detection and the addition selection in the RF data performed correspondingly.
- the difference between the frame images is the center frequency ⁇ of the ultrasonic wave. This is an example in which 1/4 of the wavelength is set as a threshold.
- the difference between the images is the center wave number of the ultrasonic wave ⁇ . If the wavelength exceeds 14 of the wavelength, processing is performed by envelope detection, that is, processing is performed as an incoherent signal. On the other hand, the difference between the images is the center frequency ⁇ of the ultrasonic wave. If the wavelength is smaller than 1/4, the signal is added to the RF data and then processed by envelope detection, that is, processed as a coherent signal.
- the contrast resolution and the spatial resolution can be improved at the same time.
- An imaging method with less image degradation due to motion is realized.
- the type of the ultrasound probe to be used, the target region for imaging are set (step 101), and the number of image frames to be subjected to image synthesis is specified (step 101).
- Step 103 set the transmission direction of the ultrasonic wave to the target part of the imaging (Step 105), store the ultrasonic transmission / reception of one frame and RF data (Step 107), and perform imaging.
- Evaluate the number of completed frames (Step 109) and repeat until the number of frames specified in Step 103 is reached.
- the RF data cross-correlation between images of different frames is calculated.
- FIG 6 (beta) is a diagram showing an example of a setting curve for the setting of the optical heterodyne detection of the reference frequency omega iota to Step 1 1 4.
- the horizontal axis is the center frequency ⁇ of the ultrasonic wave.
- the difference between the images of the frame with respect to the wavelength is taken, and the vertical axis is the center frequency ⁇ of the ultrasonic wave of the frequency after mixing corresponding to the reference frequency determined correspondingly.
- the difference between the images of the frame is the center frequency ⁇ of the ultrasonic wave.
- Let 1 ⁇ 4 of the wavelength be the threshold. That is, the difference between the images is the center frequency ⁇ of the ultrasonic wave.
- the reference frequency for heterodyne detection is the center frequency ⁇ of the ultrasonic wave. And the same frequency.
- the difference between the frame images is the center frequency of the ultrasonic wave ⁇ . If the wavelength is different from 1 ⁇ 4, determine the reference frequency so that it becomes the frequency after mixing shown in the figure. As a result, the difference between the images is the center frequency ⁇ of the ultrasonic wave. Only when the wavelength is 1/4 of the wavelength, processing by envelope detection, that is, processing is performed as an incoherent signal. On the other hand, the difference between the images is the center frequency ⁇ of the ultrasonic wave. If the wavelength is different from 1/4 of the wavelength, a reference frequency according to the degree is selected, and after heterodyne detection is performed by RF data, processing by envelope detection, that is, processing as a coherent signal is performed. Done. '
- the reference frequency ⁇ ⁇ is set to the center frequency ⁇ of the ultrasonic wave only when the RF data cross-correlation between the images of different frames calculated in step 11 is at a predetermined threshold.
- the RF data of the ultrasonic wave reception is converted into a coherent signal, and the image is formed by envelope detection.
- the reference frequency ⁇ Frequency ⁇ .
- heterodyne detection is used to determine whether the RF data cross-correlation between images of different frames.
- the RF signal as shown in Fig. 5 (B) can be described as a function of time F (t) as in equation (3).
- Figure 8 shows the center frequency ⁇ of the ultrasonic wave.
- the frequency ⁇ ⁇ of the reference wave is 2 ⁇ ⁇ , that is, the frequency after mixing with the reference wave and passing through the low-pass filter (frequency after heterodyne detection) is 0 ⁇ ⁇ .
- the contrast resolution is the best and the spatial resolution is the worst.
- FIG. 8 (C) shows that the frequency ⁇ i of the reference wave is 0 MHz, that is, the frequency after heterodyne detection is 2 MHz, so that the received RF signal is detected. This corresponds to performing envelope detection after combining the RF data in step 1 19 of the above.
- FIG. 8 ( ⁇ ) shows that the frequency ⁇ i of the reference wave is 0 MHz, that is, the frequency after heterodyne detection is 2 MHz, so that the received RF signal is detected. This corresponds to performing envelope detection after combining the RF data in step 1 19 of the above.
- FIG. 8 (B) shows that the frequency ⁇ of the reference wave is 1 MHz, that is, the frequency after the detection of the dyke is 0 MHz, so that the intermediate state between (A) and (C) described above is obtained. Results.
- FIG. 8 (D) shows that the frequency ⁇ t of the reference wave is ⁇ 1 MHz, that is, the frequency after heterodyne detection is 3 MHz (the reference wave is in the opposite phase of FIG. 7 (B)), The resolution is excellent and the contrast resolution is poor.
- the third embodiment is different from the second embodiment in that the reference frequency of the mouth dyne detection is automatically selected according to the RF data cross-correlation between images of different frames (steps 114).
- the only difference is that in step 104, the user can operate and change the reference frequency of heterodyne detection based on his / her own idea.
- Other processing is the same as the processing flow shown in Fig. 3.
- the user can accumulate experience based on how the obtained image changes according to the target object or the target disease, and can select either the contrast resolution or the spatial resolution depending on the case. Whether to give priority can be made variable according to the user's judgment.
- the number of images to be combined was three, but this number It is also possible to increase the size of a part of the image, and to synthesize a coherent image, and to synthesize an incoherent image with the rest.
Abstract
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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JP2005512903A JP4426530B2 (ja) | 2003-08-06 | 2004-06-09 | 超音波撮像装置および超音波撮像方法 |
EP04745943.3A EP1652475B1 (en) | 2003-08-06 | 2004-06-09 | Ultrasonographic device and ultrasonographic method |
US10/562,465 US7473226B2 (en) | 2003-08-06 | 2004-06-09 | Ultrasonographic device and ultrasonographic method |
US12/348,135 US8079956B2 (en) | 2003-08-06 | 2009-01-02 | Ultrasonographic device and ultrasonographic method |
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JP2003-206184 | 2003-08-06 | ||
JP2003206184 | 2003-08-06 |
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US10562465 A-371-Of-International | 2004-06-09 | ||
US12/348,135 Division US8079956B2 (en) | 2003-08-06 | 2009-01-02 | Ultrasonographic device and ultrasonographic method |
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US (2) | US7473226B2 (ja) |
EP (1) | EP1652475B1 (ja) |
JP (2) | JP4426530B2 (ja) |
CN (1) | CN1805710A (ja) |
WO (1) | WO2005013829A1 (ja) |
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EP1652475B1 (en) | 2016-08-31 |
JPWO2005013829A1 (ja) | 2006-09-28 |
EP1652475A1 (en) | 2006-05-03 |
JP5357684B2 (ja) | 2013-12-04 |
JP4426530B2 (ja) | 2010-03-03 |
JP2010042266A (ja) | 2010-02-25 |
US20060173334A1 (en) | 2006-08-03 |
US20090118617A1 (en) | 2009-05-07 |
US8079956B2 (en) | 2011-12-20 |
CN1805710A (zh) | 2006-07-19 |
EP1652475A4 (en) | 2011-03-30 |
US7473226B2 (en) | 2009-01-06 |
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