WO2013055129A2 - Procédé et dispositif pour éliminer un signal d'interférence hifu - Google Patents

Procédé et dispositif pour éliminer un signal d'interférence hifu Download PDF

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WO2013055129A2
WO2013055129A2 PCT/KR2012/008275 KR2012008275W WO2013055129A2 WO 2013055129 A2 WO2013055129 A2 WO 2013055129A2 KR 2012008275 W KR2012008275 W KR 2012008275W WO 2013055129 A2 WO2013055129 A2 WO 2013055129A2
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signal
hifu
image
ultrasound
ultrasonic
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PCT/KR2012/008275
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English (en)
Korean (ko)
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WO2013055129A3 (fr
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장진호
송재희
유양모
송태경
이유화
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서강대학교 산학협력단
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Priority claimed from KR1020110104581A external-priority patent/KR101312307B1/ko
Priority claimed from KR1020120083831A external-priority patent/KR101334375B1/ko
Application filed by 서강대학교 산학협력단 filed Critical 서강대학교 산학협력단
Priority to CN201280059157.0A priority Critical patent/CN103974665B/zh
Publication of WO2013055129A2 publication Critical patent/WO2013055129A2/fr
Publication of WO2013055129A3 publication Critical patent/WO2013055129A3/fr

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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
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N7/02—Localised ultrasound hyperthermia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37—Surgical systems with images on a monitor during operation
    • A61B2090/378—Surgical systems with images on a monitor during operation using ultrasound

Definitions

  • the present invention relates to a method for removing an HIFU interference signal, and more particularly, to a method for removing an HIFU interference signal by using a pulse inversion technique to obtain a monitor image by removing HIFU interference regardless of the length of the HIFU.
  • the reaction of the treatment area is continuously observed to confirm that lesions are formed at a desired position, and the clinician is provided with information to determine whether the treatment is continued by adjusting the dose of HIFU. It is necessary to monitor the treatment site in real time. In addition, tracking and compensating for such movements is also necessary because the organs may be affected by the patient's breathing or heart rhythm to move the treatment area out of the HIFU focal point.
  • an ultrasound imaging system may provide an image of a treatment area in real time, image quality of the image may be greatly degraded due to interference of a strong HIFU signal.
  • Various techniques have been developed to minimize the effects of interfering signals, and can be classified into short burst mode and long burst mode according to HIFU duty cycle.
  • a technique of synchronizing the HIFU irradiation point with the ultrasound image acquisition point is used to prevent the ROI from interfering.
  • Low HIFU utilization can increase treatment time and is difficult to apply in applications that use small HIFU transducers, such as the prostate, but the treatment area can be observed in real time.
  • interleaving technique can acquire continuous monitor image by adjusting pulse repetition frequency (PRF), but cannot maintain real-time.
  • PRF pulse repetition frequency
  • the method using a fixed notch filter and a barker code showed that the interference signal can be minimized by suppressing the interference signal and increasing the energy of the image signal.
  • PRF pulse repetition frequency
  • an interference cancellation method based on adaptive noise cancellation has also been proposed.
  • the first problem to be solved by the present invention is to provide a HIFU interference cancellation method that can obtain a monitor image by removing the HIFU interference irrespective of the length of the HIFU because the pulse inversion technique is used.
  • the second problem to be solved by the present invention is to provide a HIFU interference removal device that can observe in real time the process of lesion formation by removing the HIFU interference because the signal to obtain a monitor image at the same time as the HIFU signal will be.
  • the third problem to be solved by the present invention is to provide a method for setting the center frequency of the image ultrasonic signal.
  • the present invention provides a computer-readable recording medium having recorded thereon a program for executing the above method on a computer.
  • the present invention comprises the steps of: transmitting at least two or more HIFU signals while the phase difference from each other, transmitting the image ultrasound signal; If the at least two HIFU signals and the image ultrasound signal are reflected from an object, receiving an ultrasound signal including the reflected HIFU signal and the image ultrasound signal; And summing the received ultrasonic signals to remove fundamental frequency components and harmonic frequency components of the HIFU signal included in the received ultrasonic signals.
  • the transmitting of the image ultrasound signal may include transmitting an image ultrasound signal while transmitting two HIFU signals with a 180 degree phase difference.
  • the center frequency of the image ultrasound signal may be either an odd harmonic frequency or an even harmonic frequency of the HIFU signal.
  • the removing of the fundamental frequency component and the harmonic frequency component of the HIFU signal included in the received ultrasonic signal may include adding the received ultrasonic signal to the received ultrasonic signal.
  • the fundamental frequency component and the odd harmonic frequency component of the HIFU signal may be removed.
  • the transmitting of the image ultrasound signal may include transmitting an image ultrasound signal while transmitting an HIFU signal having a phase of 0 degrees, an HIFU signal having a phase of 180 degrees, and an HIFU signal having a phase of 0 degrees.
  • the received ultrasonic signal may be passed through a band cut filter or a notch filter, one or more of even-numbered harmonic frequency components of the HIFU signal included in the received ultrasonic signal may be removed, and the received ultrasonic signal may be
  • the image ultrasonic signal may be selected by passing a band pass filter having a frequency band of the image ultrasonic signal as a bandwidth.
  • the HIFU signal and the image ultrasound signal is synchronized to the ultrasound image frame, synchronization using the ultrasound image frame is the image ultrasound signal and the HIFU signal of the previous frame in any one frame HIFU signal with 180 degree phase difference can be transmitted and received together.
  • the HIFU signal and the image ultrasound signal is synchronized with the scan line of the ultrasound image, the synchronization using the scan line, the image ultrasound signal of any one image scan line, and the HIFU signal of the previous scan line phase 180 degrees You can send and receive HIFU signals that differ.
  • the step of transmitting the HIFU signal while transmitting two image ultrasound signals 180 degrees out of phase If the image ultrasound signal and the HIFU signal are reflected from an object, receiving an ultrasound signal including the reflected image ultrasound signal and a HIFU signal; And calculating a difference between the received ultrasonic signals and removing the fundamental frequency components and the harmonic frequency components of the HIFU signal included in the received ultrasonic signals.
  • HIFU signal transmission unit for transmitting at least two or more HIFU signal to be out of phase with each other;
  • An image ultrasonic signal transmitter for transmitting an image ultrasonic signal;
  • An ultrasound signal receiver configured to receive an ultrasound signal including the reflected HIFU signal and the image ultrasound signal when the at least two HIFU signals and the image ultrasound signal are reflected from an object;
  • a signal adder configured to sum the received ultrasonic signals and remove a fundamental frequency component and a harmonic frequency component of the HIFU signal included in the received ultrasonic signal.
  • HIFU signal transmission unit for transmitting a HIFU signal;
  • An image ultrasound signal transmitter configured to transmit an image ultrasound signal that transmits two image ultrasound signals to be 180 degrees out of phase;
  • An ultrasound signal receiver configured to receive an ultrasound signal including the reflected HIFU signal and an image ultrasound signal when the HIFU signal and the image ultrasound signal are reflected from an object;
  • a signal adder configured to calculate a difference between the received ultrasonic signals and remove a fundamental frequency component and a harmonic frequency component of the HIFU signal included in the received ultrasonic signal.
  • the present invention includes the steps of transmitting and receiving a HIFU signal 180 degrees out of phase difference; Removing the fundamental frequency component and the odd harmonic frequency component of the HIFU signal by summing the two received HIFU signals; And setting one of odd-numbered harmonic frequencies of the removed HIFU signal as a center frequency of the image ultrasonic signal.
  • the present invention provides a computer readable recording medium having recorded thereon a program for executing the above-described method for removing the HIFU interference signal in a computer.
  • the HIFU interference may be removed regardless of the length of the HIFU, thereby obtaining a monitor image.
  • the process of lesion formation can be observed in real time by eliminating the HIFU interference.
  • the treatment site may be monitored using real-time images.
  • the present invention it is possible to calculate the center frequency of the ultrasound image signal that can minimize the interference of the HIFU signal in the ultrasound image signal, it is possible to generate a B-mode image of good image quality.
  • FIG. 1 is a block diagram of a HIFU interference cancellation apparatus according to an embodiment of the present invention.
  • Figure 2 shows the frequency spectrum of the HIFU interference signal and the ultrasound image signal, a case where the 0 ° phase HIFU signal is transmitted.
  • Figure 3 shows the frequency spectrum of the HIFU interference signal and the ultrasound image signal, a case where a 180 ° phase HIFU signal is transmitted.
  • Figure 4 shows the frequency spectrum of the signal from which the first, third and fifth harmonic signals of HIFU are removed by pulse inversion.
  • 5 is a frequency spectrum of an ultrasound image signal obtained after removing HIFU interference.
  • FIG. 6 illustrates an experimental environment for removing HIFU interference signals using a single element ultrasonic transducer.
  • FIG. 7 shows a block diagram of a HIFU real-time monitoring experiment environment using a commercial ultrasonic imaging apparatus.
  • FIG. 8 illustrates a time waveform and a frequency spectrum of a signal obtained by transmitting and receiving a phantom using a single element ultrasonic transducer.
  • Figure 9 shows a photo (a) and the structure (b) of the phantom produced in the present invention.
  • Figure 11 shows the time waveform and frequency spectrum of the signal from which the fundamental frequency of the HIFU signal and the third and fifth harmonic signals are removed using pulse inversion.
  • FIG. 12 shows the time waveform and frequency spectrum of the signal from which the second and fourth harmonic signals of the HIFU signal are removed using a band pass filter.
  • FIG. 13 is a comparison of HIFU interference cancellation results.
  • FIG. 13 (a) is compared with a reference signal and
  • FIG. 13 (b) is compared with a reference signal to which a band pass filter is applied.
  • FIG. 14 is a photograph of a phantom including lesions according to HIFU usage.
  • FIG. 15 illustrates a reference image when the HIFU utilization rate is 10%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 16 illustrates a reference image, a HIFU interference image, an image in which pulse inversion is applied, and an image in which a band pass filter is applied when the HIFU utilization rate is 30%.
  • FIG. 17 illustrates a reference image when the HIFU utilization rate is 50%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 18 illustrates a reference image when the HIFU utilization rate is 70%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 19 illustrates a reference image when the HIFU utilization rate is 90%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 20 illustrates a conceptual diagram of inter-PRI interference according to HIFU usage rate.
  • 21 is a conceptual diagram of a transmission and reception method for removing residual HIFU interference.
  • FIG. 22 illustrates an image in which residual HIFU interference is removed at a HIFU utilization rate of 90%.
  • FIG. 23 is a flowchart illustrating a method for removing an HIFU interference signal according to an exemplary embodiment of the present invention.
  • FIG. 24 illustrates an HIFU interference cancellation apparatus according to another embodiment of the present invention.
  • 25 is a flowchart of a method for canceling an HIFU interference signal according to another embodiment of the present invention.
  • FIG. 26 is a graph illustrating the HIFU interference cancellation method of FIG. 25.
  • FIG. 27 illustrates an image according to the method of removing the HIFU interference signal of FIG. 25 before and after the HIFU interference signal is removed.
  • HIFU interference cancellation method using a pulse inversion in the phase modulation (phase modulation) method of the pulse inversion (PI: pulse inversion) and the bandpass (bandpass) filter or band-pass filter in real time interference
  • PI phase modulation
  • bandpass bandpass filter
  • HIFU interference cancellation method using a pulse inversion in the phase modulation (phase modulation) method of the pulse inversion (PI: pulse inversion) and the bandpass (bandpass) filter or band-pass filter in real time interference
  • PI phase modulation
  • bandpass bandpass filter
  • FIG. 1 is a block diagram of a HIFU interference cancellation apparatus according to an embodiment of the present invention.
  • the HIFU interference cancellation apparatus includes an ultrasonic transceiver 100, a signal adder 110, a filter 120, and an ultrasonic image processor 130.
  • the ultrasonic transceiver 100 includes a HIFU signal transmitter 101, an image ultrasonic signal transmitter 102, and an ultrasonic signal receiver 103.
  • the HIFU signal transmitter 101 transmits at least two or more HIFU signals to be out of phase with each other.
  • the HIFU signal is preferably a nonlinear chirp signal.
  • a nonlinear chirp signal may be used as the HIFU signal to secure a wider image window in the frequency domain.
  • the linear chirp signal there is a disadvantage in that the frame rate decreases and a motion defect occurs.
  • frequency overlap can be effectively reduced, and the disadvantage of the linear chirp signal can be solved.
  • the HIFU signal transmitter 101 may transmit two HIFU signals to have a 180 degree phase difference.
  • the image ultrasound signal transmitter 102 transmits an image ultrasound signal.
  • the image ultrasound signal may be any one of a short pulse, a barker code, a golay code, and a chirp code.
  • the image ultrasound signal transmitter 102 transmits an image ultrasound signal to the treatment target to obtain an internal image of the treatment target.
  • the center frequency of the image ultrasonic signal is one of the odd harmonic frequencies of the HIFU.
  • the interference of the HIFU can be minimized by using one of the odd-numbered harmonic frequencies of the HIFU as the center frequency of the image ultrasonic signal.
  • the beam is focused through a beamformer to transmit an image ultrasonic signal to a target to be photographed through an image transducer. Short pulse can be used as an image ultrasonic signal.
  • the short pulse has a disadvantage in that it is difficult to use for diagnosing deeply located organs due to limited penetration.
  • Barker, Golay, or linear Chirp codes can be used to overcome limited penetration.
  • SNR signal-to-noise ratio
  • the linear chirp code By using the linear chirp code, the length and bandwidth of the video signal can be adjusted.
  • the image ultrasonic signal transmitter 102 may generate an image ultrasonic signal. Send.
  • the HIFU signal and the image ultrasonic signal may be transmitted sequentially or simultaneously.
  • the center frequency of the image ultrasound signal may be any one of an odd harmonic frequency and an even harmonic frequency of the HIFU signal.
  • the HIFU signal transmitting unit 101 and the image ultrasonic signal transmitting unit 102 may be synchronized with an ultrasonic image frame, and the synchronization using the ultrasonic image frame may be performed using the image ultrasonic signal and the HIFU signal of the previous frame in one frame. Synchronization is achieved by transmitting and receiving HIFU signals with phase differences.
  • the HIFU signal transmitter 101 and the image ultrasound signal transmitter 102 may be synchronized with the scan line of the ultrasound image, and the synchronization using the scan line may include the image ultrasound signal of one image scan line and the previous scan line. Synchronization is achieved by transmitting and receiving a HIFU signal 180 degrees out of phase with the HIFU signal.
  • the ultrasound signal receiver 103 receives an ultrasound signal including the reflected HIFU signal and the image ultrasound signal.
  • the ultrasonic signal includes a HIFU signal component and an image ultrasonic component.
  • the ultrasound signal received through the transducer is beam focused through a beamformer.
  • the signal summing unit 110 adds the received ultrasonic signal to remove the fundamental frequency component and the harmonic frequency component of the HIFU signal included in the received ultrasonic signal. In particular, it is preferable to remove the fundamental frequency components and odd-numbered harmonic frequency components of the HIFU signal included in the received ultrasonic signal.
  • the received ultrasonic signal includes a high magnitude HIFU signal component.
  • the HIFU signal interferes with imaging the ultrasound signal.
  • the HIFU signal transmitter 101 transmits the HIFU signal twice so that there is a 180 degree phase difference.
  • the received ultrasonic signal includes two types of HIFU signal components having a 180 degree phase difference.
  • the ultrasonic signals including the two types of HIFU signal components are summed.
  • the sum of the ultrasonic signals removes the fundamental frequency component and the odd harmonic frequency component of the HIFU signal. By using one of the frequencies of the odd-numbered harmonic frequency components of the HIFU signal as the center frequency of the image ultrasonic signal, an image ultrasonic signal may be obtained without interference of the HIFU signal.
  • the signal adder 110 receives the previous frame signal and the newly received signal from the signal storage unit. Take the signal and add the two signals together.
  • the two signals include HIFU signal components having a 180 degree phase difference from each other, and by adding the two signals, the fundamental frequency component and the odd harmonic frequency component of the HIFU signal are removed.
  • the filter unit 120 removes one or more of even-numbered harmonic frequency components of the HIFU signal included in the received ultrasonic signal by passing the ultrasonic signal summed by the signal adding unit 110 through a band cut filter or a notch filter. .
  • the image ultrasound signal may be selected by passing the ultrasound signal summed by the signal adding unit 110 through a band pass filter having a frequency band of the image ultrasound signal as a bandwidth.
  • the ultrasound image processor 130 generates a B mode image from the ultrasound signal from which the fundamental frequency component and the harmonic frequency component are removed.
  • the ultrasound image processor 130 generates an image using the ultrasound signal from which the interference of the HIFU signal is removed by the signal summing of the signal summing unit 110.
  • a band cut filter or a notch filter By passing the received ultrasonic signal through a band cut filter or a notch filter, one or more of even-numbered harmonic frequency components of the HIFU signal may be removed from the ultrasonic signal.
  • the image ultrasonic signal may be selected by passing the received ultrasonic signal through a band pass filter having a frequency band of the image ultrasonic signal as a bandwidth. When the ultrasonic signal is transmitted and received using the transducer, only a signal having a specific bandwidth may pass according to the performance of the transducer.
  • a B-mode image is generated from the selected ultrasonic signal.
  • the B-mode image is an image of a cross section of a subject using ultrasound.
  • the strong and weak reflected echoes are represented by the difference in brightness.
  • the B-mode image is a black and white anatomical image.
  • the B-mode image is generated by analyzing the ultrasonic signal.
  • the B-mode image may be generated from the ultrasound signal by using one or more of short pulse, barker, golay, and chirp codes.
  • the signal storage unit and the control unit may further include.
  • the signal storage unit stores the ultrasonic signal until the ultrasonic image processing unit 130 receives the signal of the next frame to add the signals. When the next frame of the stored signal is received, the stored signal is input to the ultrasound image processor 130. It can be implemented using memory.
  • the control unit controls the HIFU signal transmitter 101 to transmit the HIFU signal twice so that the HIFU signal transmitter 101 has a 180 degree phase difference.
  • the video ultrasonic signal transmission unit 102 also controls the video ultrasonic signal transmission.
  • the signal storage unit stores the signal and controls the input of the signal to the signal summing unit 110. It may be implemented as a processor.
  • harmonic components are produced. Harmonic imaging has been used clinically because it has the effect of improving the resolution and contrast than when using the fundamental frequency component.
  • a band pass filter or a phase modulation technique is used to selectively extract desired harmonic components from the received signal.
  • the pulse reversal method is to detect the second harmonic signal, and transmits two pulses with 180 ° phase difference in the same place, and then removes the fundamental frequency and odd harmonic components by adding the two received signals. .
  • the ultrasonic transceiver 100 the signal adder 110, and the filter 120 will be described in more detail.
  • the ultrasonic transceiver 100 transmits and receives two pulses each having a 180 ° phase difference in the same place to remove the HIFU interference signal by using pulse inversion.
  • the signal r (t) received by the ultrasonic signal receiving unit 103 may be expressed as follows. As shown in Equation 1, harmonic signals including the fundamental frequency, the second order and the third order of the HIFU signal and the image signal are included.
  • the ultrasonic image transducer Since the ultrasonic image transducer has the characteristics of a band pass filter, considering the center frequency and bandwidth of the HIFU transducer and the ultrasonic image transducer, the image signal is received only from the fundamental frequency component, and the HIFU signal is received from the fundamental frequency to the fifth harmonic component.
  • the received signal r (t) may be expressed as in Equation 2.
  • Figure 2 shows the frequency spectrum of the HIFU interference signal and the ultrasound image signal, a case where the 0 ° phase HIFU signal is transmitted.
  • H (t) present in the received signal must be removed because it serves as an interference signal that degrades the quality of the monitor image. Therefore, two signals h 1 (t) and h 2 (t) with a 180 ° phase difference are used as HIFU signals to remove the interference signal using the pulse reversal technique.
  • Equation 4 Equation 4 below, and have a spectrum as shown in FIGS. 2 and 3 in terms of frequency, respectively.
  • Figure 3 shows the frequency spectrum of the HIFU interference signal and the ultrasound image signal, a case where a 180 ° phase HIFU signal is transmitted.
  • Figure 4 shows the frequency spectrum of the signal from which the first, third and fifth harmonic signals of HIFU are removed by pulse inversion.
  • Equation 6 a signal similar to the original ultrasonic image signal u f (t) can be obtained as shown in Equation 6, and FIG. Frequency spectrum of an ultrasound image signal obtained after removing HIFU interference.
  • FIG. 6 illustrates an experimental environment for removing HIFU interference signals using a single element ultrasonic transducer.
  • the single-element HIFU transducer used in the experiment has a 20 mm center open for image acquisition, a center frequency of 1.1 MHz, and a geometric focusing distance of 62.6 mm.
  • two pulses used for pulse inversion were generated at a pulse repetition interval, and then input to a function generator.
  • the signal amplified with a gain of 49 dB in the high frequency amplifier is transmitted to the phantom in the tank through an impedance matching network that resonates around 1.1 MHz.
  • the water in the tank was boiled and then cooled to room temperature to remove bubbles, and an ultrasonic sound absorber was installed at the bottom of the tank to remove the reverberation signal from the bottom of the tank.
  • the ultrasonic pulser / receiver Synchronized at the time of HIFU signal generation, a short pulse was delivered to the 3.5 MHz single-element ultrasonic transducer.
  • the signal received through the ultrasonic transducer was sampled at 100 MHz using a high-speed digitizer and stored in internal memory. After data acquisition, it was transferred to PC and necessary signal processing was performed using MATLAB.
  • the phantom used in the experiment was prepared using agar and glass beads having an average diameter of 25 ⁇ m.
  • FIG. 7 shows a block diagram of a HIFU real-time monitoring experiment environment using a commercial ultrasonic imaging apparatus.
  • the experiment was performed while varying the utilization rate to 10%, 30%, 50%, 70%, and 90%. Same as FIG. 7.
  • Ultrasound imaging system, curver linear transducer, and bovine serum albumin gel phantom were used instead of single-element ultrasonic transducer and ultrasonic pulser / receiver to obtain monitor images of lesion formation. Phantom was prepared by incorporating BSA and scatterer agar into polyacrylamide at concentrations of 5% and 0.4% in w / v, respectively, and then hardening it into gel.
  • the ultrasonic imaging system As well as the HIFU must transmit ultrasonic waves twice at the same point, so the pulse transmission and reception process was modified using the Texo software development kit (SDK).
  • SDK Texo software development kit
  • the ultrasound imaging system was synchronized to generate the scan line, and the received beam focused signal was stored in the system internal memory, and then transmitted to a PC for signal processing on MATLAB.
  • FIG. 8 illustrates a time waveform and a frequency spectrum of a signal obtained by transmitting and receiving a phantom using a single element ultrasonic transducer.
  • Figure 9 shows a photo (a) and the structure (b) of the phantom produced in the present invention.
  • FIG. 8 a time waveform and a frequency spectrum of a reference signal obtained by transceiving a phantom with a single element ultrasonic transducer are shown.
  • the manufactured phantom is about 14 cm high and is composed of two layers, as shown in FIG.
  • the second layer increases the concentration of the scatterers by about 10%, increasing the attenuation coefficient there, suppressing strong signals reflected from the bottom.
  • Figure 11 shows the time waveform and frequency spectrum of the signal from which the fundamental frequency of the HIFU signal and the third and fifth harmonic signals are removed using pulse inversion.
  • FIG. 12 shows the time waveform and frequency spectrum of the signal from which the second and fourth harmonic signals of the HIFU signal are removed using a band pass filter.
  • the signal from which the HIFU interference has been removed is compared with a reference signal.
  • the signal obtained using the method according to the present invention is the low-frequency and high-frequency components are removed by the band pass filter to limit the bandwidth of the signal.
  • the energy of the entire signal was decreased, thereby reducing the amplitude of the signal.
  • FIG. 13 is a comparison of HIFU interference cancellation results.
  • FIG. 13 (a) is compared with a reference signal and
  • FIG. 13 (b) is compared with a reference signal to which a band pass filter is applied.
  • Equation 8 was used to obtain correlation coefficients between the image signal and the reference signal after the HIFU interference was removed, and then the maximum values were compared. The maximum value of the correlation coefficient increased significantly from 0.0685 to 0.9838 after HIFU interference was removed. This means that the HIFU interference cancellation method according to the present invention effectively removes the HIFU interference signal.
  • FIG. 14 is a photograph of a phantom including lesions according to HIFU usage.
  • FIG 14 it shows that the HIFU lesion formed according to the HIFU utilization. It can be seen that when the utilization rate is 30% or less, the applied energy is small and no lesion is formed.
  • 15 to 19 are obtained by applying a reference image obtained when the HIFU utilization rate is 10%, 30%, 50%, 70% and 90%, interference image by HIFU, image to which pulse inversion is applied, and band pass filter, respectively. Show an image. It can be confirmed that the monitor image can be obtained by removing the HIFU interference using the proposed method through each image.
  • FIG. 15 illustrates a reference image when the HIFU utilization rate is 10%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • the echo around the HIFU focus area is increased compared to the reference image. This is believed to be due to the increased echo of the ultrasound image signal by the microbubbles formed by the HIFU, which may be used to confirm that the energy of the HIFU is being delivered where desired during treatment.
  • FIG. 16 illustrates a reference image, a HIFU interference image, an image in which pulse inversion is applied, and an image in which a band pass filter is applied when the HIFU utilization rate is 30%.
  • FIG. 17 illustrates a reference image when the HIFU utilization rate is 50%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 18 illustrates a reference image when the HIFU utilization rate is 70%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 19 illustrates a reference image when the HIFU utilization rate is 90%, an HIFU interference image, an image to which pulse inversion is applied, and an image to which a band pass filter is applied.
  • FIG. 20 illustrates a conceptual diagram of inter-PRI interference according to HIFU usage rate.
  • 21 is a conceptual diagram of a transmission and reception method for removing residual HIFU interference.
  • the HIFU signals of phase 0 ° and 180 ° are transmitted and received, and then the HIFU signals of phase 0 ° are transmitted and received again.
  • the HIFU signal having a phase of 180 ° is also subjected to PRI interference, so the effect of pulse inversion can be obtained by adding the second and third transmitted and received signals.
  • FIG. 22 illustrates an image in which residual HIFU interference is removed at a HIFU utilization rate of 90%.
  • FIG. 23 is a flowchart illustrating a method for removing an HIFU interference signal according to an exemplary embodiment of the present invention.
  • the HIFU interference canceling method according to the present exemplary embodiment includes steps that are processed in time series in the HIFU interference canceling apparatus illustrated in FIG. 1. Therefore, even if omitted below, the above descriptions regarding the HIFU interference cancellation apparatus shown in FIG. 1 also apply to the HIFU interference cancellation method according to the present embodiment.
  • the HIFU interference canceling device transmits an image ultrasonic signal while transmitting at least two or more HIFU signals to be out of phase with each other.
  • the center frequency of the image ultrasound signal is preferably one of an odd harmonic frequency or an even harmonic frequency of the HIFU signal.
  • the image ultrasound signal can be transmitted.
  • the image ultrasonic signal may be transmitted while transmitting the HIFU signal having a phase of 0 degrees, the HIFU signal having a phase of 180 degrees, and the HIFU signal having a phase of 0 degrees.
  • the HIFU interference cancellation apparatus receives an ultrasound signal including the reflected HIFU signal and the image ultrasound signal.
  • the HIFU interference canceling apparatus may add the received ultrasonic signals to remove the fundamental frequency component and the harmonic frequency components of the HIFU signal included in the received ultrasonic signal.
  • the HIFU interference cancellation apparatus passes the received ultrasonic signal through a band cut filter or a band pass filter.
  • the received ultrasonic signal By passing the received ultrasonic signal through a band cut filter or a notch filter, one or more of even-numbered harmonic frequency components of the HIFU signal included in the received ultrasonic signal may be removed, and the received ultrasonic signal is converted into the image ultrasonic wave.
  • the image ultrasonic signal may be selected by passing a band pass filter having a frequency band of the signal as a bandwidth.
  • the HIFU interference cancellation apparatus generates a B mode image from the ultrasound signal from which the fundamental frequency component and the harmonic frequency component are removed.
  • the process of lesion formation can be observed in real time by removing the HIFU interference.
  • an increase in echo due to the formation of lesions in the HIFU focal region can be observed over time.
  • the method for setting the center frequency of the ultrasonic signal according to an embodiment of the present invention can be implemented by the following steps 2410 to 2440.
  • step 2410 the HIFU signal is transmitted and received twice so that there is a 180 degree phase difference.
  • the HIFU signal is transmitted and the HIFU signal is transmitted once more so that there is a 180 degree phase difference.
  • the beam is focused through the beamformer and the HIFU signal is transmitted to the target to be treated through the HIFU treatment transducer. Thereafter, the HIFU signal having a phase difference of 180 degrees with the transmitted HIFU signal is once again transmitted.
  • an echo of the transmitted HIFU signal is received.
  • the received signal has two signals having a 180 degree phase difference, and the two signals are received through the image transducer.
  • Step 2420 is a step of removing the fundamental frequency components and odd-numbered harmonic frequency components of the HIFU signal by summing the two received HIFU signals.
  • the HIFU signals received in step 2410 are added up.
  • the fundamental and odd harmonic frequency components of the HIFU signal are removed.
  • the signals containing the two types of HIFU signal components are summed. Summing up the signals removes the fundamental frequency components and odd-numbered harmonic frequency components of the HIFU signal.
  • the received signal is stored and the signal of the next frame is received, the previous frame signal and the newly received signal are summed.
  • the two signals include HIFU signal components having a 180 degree phase difference from each other, and by adding the two signals, the fundamental frequency component and the odd harmonic frequency component of the HIFU signal are removed.
  • one of the odd-numbered harmonic frequencies of the removed HIFU signal is set as the center frequency of the ultrasound image signal.
  • one of the odd harmonic frequencies of the HIFU signal removed in step 2410 is set as the center frequency of the image ultrasonic signal.
  • the odd-numbered harmonic frequency component of the HIFU signal is removed by the method of steps 2410 to 2420, and the odd-numbered harmonic frequency of the removed HIFU signal is used as the center frequency of the image ultrasonic signal, thereby being used for the image ultrasonic signal. Bandwidth can be obtained.
  • one of the odd harmonic frequencies of the HIFU signal is set as the center frequency of the image ultrasonic signal so that the bandwidth can be used for the image ultrasonic signal.
  • the first harmonic frequency may be set as the center frequency of the image ultrasonic signal, or the other odd harmonic frequency may be set as the center frequency of the image ultrasonic signal.
  • the most efficient odd-numbered harmonic frequency may be set as the center frequency of the image ultrasonic signal in consideration of the frequency of the transmittable image ultrasonic wave of the apparatus for transmitting the image ultrasonic signal.
  • the frequency with the least interference from HIFU can be used as the center frequency of the ultrasonic signal. That is, a frequency having the highest intensity may be used within the frequency of the transmittable image ultrasonic wave of the apparatus for transmitting the image ultrasonic signal.
  • FIG. 24 illustrates an HIFU interference cancellation apparatus according to another embodiment of the present invention.
  • HIFU interference cancellation apparatus is composed of a HIFU signal transmitter 2401, an image ultrasonic signal transmitter 2402, an ultrasonic signal receiver 2403, and a signal difference calculator 2410, ultrasonic image
  • the processor 2420 may be further included.
  • the HIFU signal transmitter 2401 transmits a HIFU signal.
  • the HIFU signal transmitter 2401 has the same configuration as the HIFU signal transmitter 101 of FIG. 1 except for the configuration of transmitting the HIFU signal without phase difference, and the description of the other components is described with respect to the HIFU signal transmitter 101 of FIG. 1. Instead of
  • the image ultrasonic signal transmitter 2402 transmits the image ultrasonic signal for transmitting the two image ultrasonic signals to have a 180 degree phase difference.
  • two projection ultrasound signals are transmitted to have a 180 degree phase difference using an inverted pulse technique. Except for the configuration of transmitting two image ultrasonic signals to have a 180 degree phase difference, the configuration is the same as that of the image ultrasonic signal transmitter 102 of FIG. 1, and the description of the other components will be described with reference to the image ultrasonic signal transmitter 102 of FIG. 1. Replace with description.
  • the ultrasound signal receiver 2403 receives an ultrasound signal including the reflected HIFU signal and the image ultrasound signal.
  • the HIFU signal transmitter 2401 and the image ultrasonic signal transmitter 2402 transmit an ultrasonic signal including the reflected HIFU signal and the image ultrasonic signal.
  • a detailed description of the ultrasonic signal receiver 2403 is the same as that of the ultrasonic signal transmitter 103 of FIG. 1, and a description of another configuration is replaced with the description of the ultrasonic signal transmitter 103 of FIG. 1.
  • the signal difference calculator 2401 calculates a difference between the received ultrasound signals and removes a fundamental frequency component and a harmonic frequency component of the HIFU signal included in the received ultrasound signal.
  • the ultrasonic signals received by the ultrasonic signal receiver 2403 are two kinds of signals.
  • the HIFU signal included in both types of signals is the same type.
  • the image ultrasonic signal is a reflection of the image ultrasonic signal transmitted by the image ultrasonic signal transmitter 2402 so that the phase difference is 180 degrees.
  • the two types of image ultrasonic signals have a phase difference of 180 degrees.
  • the difference between the two types of ultrasonic signals is calculated.
  • the HIFU signal portion has the same phase and the same magnitude and is removed, and the image ultrasonic signal portion having the 180 degree phase difference has twice the size.
  • the fundamental frequency component and the harmonic frequency component of the HIFU signal included in the received ultrasonic signal may be removed.
  • 25 is a flowchart of a method for canceling an HIFU interference signal according to another embodiment of the present invention.
  • step 2500 the HIFU signal is transmitted while transmitting two image ultrasound signals to be 180 degrees out of phase.
  • the HIFU signal is transmitted without phase difference, and the image ultrasound signal is transmitted twice so as to have a 180 degree phase difference.
  • the pulse inversion technique is used to make the image ultrasonic signal 180 degrees out of phase.
  • the detailed description of this step corresponds to the detailed description of the HIFU signal transmitter 2401 and the image ultrasonic signal transmitter 2402 of FIG. 24, and the HIFU signal transmitter 2401 and the image ultrasonic signal transmitter 2402 of FIG. 24. Replace with the detailed description of.
  • the difference between the received ultrasonic signals is calculated to remove the fundamental frequency component and the harmonic frequency components of the HIFU signal included in the received ultrasonic signal.
  • the ultrasound signal received in step 2510 has a 180 degree phase difference between the image ultrasound signals transmitted in step 2500, there is a part corresponding to the same HIFU signal and a part corresponding to the image ultrasound signal having a 180 degree phase difference. Accordingly, when the difference between the two types of ultrasonic signals is calculated, the fundamental frequency component and the harmonic frequency component of the HIFU signal corresponding to the HIFU signal may be removed.
  • the detailed description of this step corresponds to the detailed description of the signal difference calculator 2401 of FIG. 24, and is replaced with the detailed description of the signal difference calculator 2401 of FIG. 24.
  • the HIFU interference canceling device generates a B mode image from the ultrasonic signal from which the fundamental frequency component and the harmonic frequency component are removed.
  • the process of lesion formation can be observed in real time by removing the HIFU interference.
  • an increase in echo due to the formation of lesions in the HIFU focal region can be observed over time.
  • FIG. 26 is a graph illustrating the HIFU interference cancellation method of FIG. 25.
  • the two kinds of ultrasonic signals received by the ultrasonic signal receiver 2403 have the same portion corresponding to the HIFU signal, and the portions corresponding to the image ultrasonic signals have a 180 degree phase difference.
  • the difference between the two ultrasonic signals is calculated to remove the fundamental frequency component and the harmonic frequency component of the HIFU signal corresponding to the HIFU signal.
  • FIG. 27 illustrates an image according to the method of removing the HIFU interference signal of FIG. 25 before and after the HIFU interference signal is removed.
  • Embodiments of the present invention can be implemented in the form of program instructions that can be executed by various computer means and recorded in a computer readable medium.
  • the computer readable medium may include program instructions, data files, data structures, etc. alone or in combination.
  • Program instructions recorded on the media may be those specially designed and constructed for the purposes of the present invention, or they may be of the kind well-known and available to those having skill in the computer software arts.
  • Examples of computer readable recording media include magnetic media such as hard disks, floppy disks and magnetic tape, optical media such as CD-ROMs, DVDs, and magnetic disks such as floppy disks.
  • Examples of program instructions include not only machine code generated by a compiler, but also high-level language code that can be executed by a computer using an interpreter or the like.
  • the hardware device described above may be configured to operate as one or more software modules to perform the operations of the present invention, and vice versa.
  • the HIFU interference is eliminated regardless of the length of the HIFU to obtain a monitor image, and the HIFU interference is transmitted because a signal for acquiring the monitor image is transmitted simultaneously with the HIFU signal.
  • the process of lesion formation can be observed in real time, and the treatment site is monitored using real-time images to confirm the formation of the lesion at the desired position, the progress of treatment, and to observe and compensate for the movements occurring during the treatment. can do.

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Abstract

La présente invention concerne un procédé pour éliminer un signal d'interférence HIFU. Le procédé selon l'invention est caractérisé par la transmission de signaux d'image ultrasonore tout en transmettant au moins deux signaux HIFU déphasés, la réception de signaux ultrasonores, y compris des signaux HIFU réfléchis et des signaux d'image ultrasonore lorsqu'au moins deux signaux HIFU et signaux d'image ultrasonore sont réfléchis par un objet, l'addition des signaux ultrasonores reçus, et l'élimination des composantes de fréquence basiques et des composants de fréquence harmoniques des signaux HIFU dans les signaux ultrasonores reçus. Le procédé selon la présente invention peut intercepter une image de moniteur de laquelle des interférences HIFU sont éliminées quelle que soit la longueur des HIFU grâce à une technique d'inversion d'impulsions.
PCT/KR2012/008275 2011-10-13 2012-10-11 Procédé et dispositif pour éliminer un signal d'interférence hifu WO2013055129A2 (fr)

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KR1020110104581A KR101312307B1 (ko) 2011-10-13 2011-10-13 Ｈｉｆｕ 신호를 제거하는 초음파신호처리방법 및 초음파신호처리장치
KR10-2011-0104581 2011-10-13
KR1020120083831A KR101334375B1 (ko) 2012-07-31 2012-07-31 Ｈｉｆｕ 간섭 신호 제거 방법 및 장치
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KR100845495B1 (ko) * 2001-11-05 2008-07-10 베이징 유안데 바이오메디칼 프로젝트 컴파니 리미티드 체외 고강도 초점 초음파 치료 장치
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US6042556A (en) * 1998-09-04 2000-03-28 University Of Washington Method for determining phase advancement of transducer elements in high intensity focused ultrasound
KR100845495B1 (ko) * 2001-11-05 2008-07-10 베이징 유안데 바이오메디칼 프로젝트 컴파니 리미티드 체외 고강도 초점 초음파 치료 장치
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