JP2009050389A - Ultrasonic image displaying method, its apparatus, and ultrasonic image displaying program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To quantify a temporal variation of image brightness values of ultrasonic images by using a contrast agent with a high precision by minimizing influence by a speckle noise. <P>SOLUTION: An ultrasonic image displaying method includes the search of an intermediate value sequentially from each pixel value in a plurality of frames of the ultrasonic images by using a contrast agent by an intermediate value search part 17, generation of ultrasonic image data by an image creating part 18 from the searched intermediate values, and display of TIC in which the temporal variation of image brightness values of data of ultrasonic images by using a contrast agent is quantified by a quantification part 19 on a monitor 14. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to an ultrasonic image display method and apparatus for quantifying and displaying an ultrasonic image representing the dynamics of a contrast agent in a subject when the contrast agent is injected into a subject such as a heart or liver, and an ultrasonic wave. The present invention relates to an image display program.

  An ultrasound diagnostic apparatus, for example, injects an ultrasound contrast agent into a subject such as the heart or liver, emits ultrasound from the ultrasound probe to the subject, receives the reflected wave, A moving image of the ultrasonic image representing the dynamics of the ultrasonic contrast agent is created and displayed on the monitor. The interpretation doctor determines the state of blood flow from the dynamics of the ultrasound contrast agent in the subject displayed on the monitor, and diagnoses a lesion such as a myocardial infarction in the subject such as the heart or liver.

  There are various documents on imaging techniques for moving images using such an ultrasonic contrast agent. Among these, there is a technique (TIC: Time Intensity Curve) that analyzes and quantifies the temporal change of the staining of the ultrasound contrast agent when the ultrasound contrast agent is injected. An example of such a quantification technique is Patent Document 1. An ultrasound image when the ultrasound contrast agent is injected (hereinafter referred to as an ultrasound contrast image) has clinical significance by capturing the sharpness as a temporal change. However, the temporal change of the image luminance value of the ultrasonic contrast image is graphed by TIC, and the temporal change of the image luminance value is quantitatively captured by curve fitting.

  FIG. 11 shows a display example of a TIC in which temporal changes in image luminance values of an ultrasound contrast image are quantified. On the TIC display screen 1, an ultrasound contrast image display screen 2 is displayed side by side. The result of quantifying the temporal change of the image luminance value is fine and greatly fluctuates up and down due to the influence of speckle noise. Speckle noise is a spot-like image that is seen in an image of an ultrasonic diagnostic apparatus and does not accurately correspond to an actual particle shape in a subject such as a heart or a liver. For this reason, the result of curve fitting largely depends on the speckle noise component.

  If the image brightness value of the contrast-enhanced image is fine and greatly fluctuates up and down due to the influence of speckle noise, it is possible to accurately curve-fit the temporal change in the image brightness value of the contrast-enhanced image. It becomes impossible. In other words, curve fitting is calculated by computer processing. However, if the image brightness value is fine and fluctuates up and down, the computer cannot accurately curve fitting by capturing this fluctuation. .

In the contrast-enhanced image taken at the time of ultrasound contrast inspection, speckle noise is an obstacle to seeing the defect of the contrast of the ultrasound contrast agent. For this reason, not only is it difficult to interpret an ultrasound contrast image, but there is a risk of erroneous interpretation. What is necessary for quantifying the temporal change in the image luminance value of the contrast-enhanced image is to eliminate the so-called lack of objectivity that results vary depending on the evaluator or software operator. The result of quantification obtained by the TIC shown in FIG. 11 is fine and greatly fluctuates up and down due to the influence of speckle noise, and lacks objectivity.
Quantification of Myocardial Blood Flow With Ultrasound-Induced Destruction of Microbubbles Administrated as a Contrast Venous Infusion, Kevin Wei, Circulation. 1998; 97: 473-483

  An object of the present invention is to provide an ultrasonic image display method, an apparatus thereof, and an ultrasonic image capable of accurately quantifying temporal changes in image luminance values of an ultrasonic contrast image while minimizing the influence of speckle noise. To provide a display program.

  The ultrasonic image display method according to claim 1 of the present invention radiates an ultrasonic wave to a subject into which a contrast agent has been injected, receives a reflected wave from the subject, and controls the dynamics of the contrast agent in the subject. In an ultrasonic image display method for displaying a moving image of an ultrasonic image to be represented, an intermediate value is sequentially searched from each pixel value in a plurality of frames of an ultrasonic image within an arbitrary period, and an ultrasonic wave is detected from the searched intermediate values. Create and display image data.

  According to a fifteenth aspect of the present invention, an ultrasonic image display device radiates an ultrasonic wave to a subject into which a contrast agent has been injected, receives a reflected wave from the subject, and monitors the dynamics of the contrast agent in the subject. In an ultrasonic image display device that displays a moving image of an ultrasonic image to represent, an intermediate value search unit that sequentially searches for an intermediate value from each pixel value in a plurality of frames of an ultrasonic image within an arbitrary period, a display unit, An image creation unit that creates ultrasound image data from the intermediate value searched by the intermediate value search unit and displays the ultrasonic image data on the display unit.

  The ultrasonic image display program according to claim 30 of the present invention emits ultrasonic waves to a subject into which a contrast agent has been injected, receives a reflected wave from the subject, and controls the dynamics of the contrast agent in the subject. In an ultrasonic image display program for displaying a moving image of an ultrasonic image to be represented, an intermediate value of each pixel value in a plurality of frames of an ultrasonic image within an arbitrary period is sequentially searched, and an ultrasonic image composed of these searched intermediate values Sound image data is obtained.

  According to the present invention, an ultrasonic image display method, an apparatus thereof, and an ultrasonic image capable of accurately quantifying temporal changes in image luminance values of an ultrasonic contrast image while minimizing the influence of speckle noise. A display program can be provided.

Hereinafter, an embodiment of the present invention will be described with reference to the drawings.
FIG. 1 is a configuration diagram of an ultrasonic image display device applied to an ultrasonic diagnostic apparatus. A transmitter 11 and a receiver 12 are connected to the ultrasonic probe 10. The ultrasonic probe 10 includes a plurality of piezoelectric vibrators. The ultrasonic probe 10 generates an ultrasonic pulse from each piezoelectric vibrator based on the drive signal from the transmission unit 11, receives a reflected wave from the subject S, and converts it into an electric signal. Accordingly, the ultrasonic probe 10 transmits an ultrasonic pulse into the subject S, for example. The ultrasonic pulses transmitted into the subject S are reflected one after another by discontinuous surfaces of acoustic impedance such as in-vivo tissue and blood flow in the subject S, and enter the ultrasonic probe 10 as reflected waves. The ultrasonic probe 10 receives the reflected wave, converts it into an electrical signal, and outputs it. The transmitter 11 sends a drive signal to each compression transducer of the ultrasonic probe 10 to generate an ultrasonic pulse. The receiving unit 12 amplifies and outputs the electrical signal from the ultrasonic probe 10.

  The image processing unit 13 sends a drive signal to the transmission unit 11 by computer processing, converts the electrical signal output from the reception unit 12 into a digital signal, performs an imaging process, and forms an ultrasonic image composed of a plurality of frames. Data is created and a moving image of the ultrasonic image in the subject is displayed on the monitor 14. On the other hand, at the time of the ultrasound contrast examination, the image processing unit 13 creates ultrasound contrast image data when the ultrasound contrast agent is injected into the subject S, and represents the dynamics of the ultrasound contrast agent in the subject S. A moving image of the ultrasonic image is displayed on the monitor 14.

  The image processing unit 13 has the following functions. The image processing unit 13 includes a program memory 15 and an image memory 16. The program memory 15 stores an ultrasonic image display program. This ultrasonic image display program emits ultrasonic waves to a subject S into which an ultrasonic contrast agent has been injected, receives a reflected wave from the subject S, and represents the dynamics of the ultrasonic contrast agent in the subject S. A moving image of the ultrasonic image is displayed on the monitor 14, and an intermediate value of each pixel value in a plurality of frames of the ultrasonic contrast image data within an arbitrary period is sequentially searched, and an ultrasonic image composed of the searched intermediate values is obtained. The sonic contrast image data is obtained. The ultrasound image display program quantifies the temporal change in the image luminance value of the ultrasound contrast image data, that is, analyzes and quantifies the temporal change in the contrast of the ultrasound contrast agent when the ultrasound contrast agent is injected. The TIC result to be converted is displayed on the monitor 14.

  The image memory 16 includes ultrasonic image data composed of a plurality of frames created by the image processing unit 13 and ultrasound contrast image data composed of a plurality of frames created by the image processing unit 13 during the ultrasonic contrast examination. Remembered.

  The image processing unit 13 includes an intermediate value search unit 17, an image creation unit 18, a quantification unit 19, and an in-phase detection unit 20. An electrocardiograph 22 is connected to the image processing unit 13 via an input unit 21. The intermediate value search unit 17 reads out each frame of the ultrasound contrast image data within an arbitrary period from the image memory 16 at the time of the ultrasound contrast examination, and calculates an intermediate value from each pixel value in each frame of the ultrasound contrast image data. Search sequentially. In this case, the intermediate value search unit 17 searches for an intermediate value from a plurality of temporally continuous frames, for example, three frames. Note that the intermediate value search unit 17 may search for an intermediate value from a plurality of temporally discrete frames. The image creation unit 18 creates ultrasound contrast image data from the intermediate value searched by the intermediate value search unit 17 and displays it on the monitor 14.

Here, the intermediate value search unit 17 and the image creation unit 18 will be specifically described. FIG. 2 shows frames f ₁ , f ₂ ,..., Fn that are temporally continuous in the ultrasound contrast image data. For example, as shown in FIG. 3, the intermediate value search unit 17 performs intermediate processing from the pixel values of the pixels g ₁ , g ₂ , and g _{3 having} the same coordinates in three temporally continuous frames f ₁ , f ₂ , and f ₃ . Search for pixel values. For example, if the pixel value of the pixel g _{1 in} the frame f ₁ is “5”, the pixel value of the pixel g _{2 in} the frame f ₂ is “3”, and the pixel value of the pixel g _{3 in} the frame f ₁ is “1”, the intermediate value The value search unit 17 searches the pixel value “3” that is in the middle from the pixel values “5”, “3”, and “1” as an intermediate pixel value. If the pixel values are “5”, “20”, and “1”, the intermediate value search unit 17 searches for the intermediate pixel value “5” in the middle from the pixel values “5”, “20”, and “1”. Hereinafter, similarly, the intermediate value search unit 17 searches for intermediate pixel values from all the pixel values of the same coordinates in three temporally consecutive frames f ₂ , f ₃ , and f ₄ , and then the three frames f _3, f _4, retrieves the intermediate pixel value from each pixel value of f _5, searches the intermediate pixel value from each pixel value of the finally three frames fn-2, fn-1, fn. The intermediate value search unit 17 searches for a pixel value in the middle of each pixel value, and is also referred to as an intermediate value filter.

The image creating unit 18 creates one frame F ₁ of the contrast-enhanced image data from the intermediate values of the respective pixel values of the frames f ₁ , f ₂ , and f ₃ that are temporally consecutive searched by the intermediate value searching unit 17. To do. Similarly, the image creating unit 18 creates a frame F ₂ of the ultrasound contrast image data from the intermediate value of each pixel value of each frame f ₂ , f ₃ , f ₄ , and each frame f ₃ , f ₄ , f The frame F ₃ of the ultrasonic contrast image data is sequentially created from the intermediate value of the pixel values of ₅ . The image creation unit 18 creates ultrasound contrast image data from the sequentially created frames F ₁ , F ₂ , F ₃ ,..., Fm and displays them on the monitor 14 as a moving image.

Next, an intermediate value search method by the intermediate value search unit 17 will be described.
The intermediate value search method searches for the intermediate pixel value from the pixel values of the pixels g ₁ , g ₂ , and g _{3 having} the same coordinates in the _three frames f ₁ , f ₂ , and f 3 as shown in FIG. However, the intermediate value may be searched by the following search method. For example, as shown in FIG. 4, the intermediate value search unit 17 sets a matrix M of 3 × 3 pixels, for example, in each frame f ₁ , f ₂ , f ₃ of the ultrasound contrast image data. As shown in FIG. 5, the matrix M includes a target pixel a ₁ and peripheral pixels a _{2 to} a ₉ adjacent to each other around the target pixel a ₁ .

The intermediate value search unit 17 is a pixel value (hereinafter referred to as an intermediate pixel value) between the nine pixel values of the pixels a _{1 to} a ₉ in the matrix M set in the frames f ₁ , f ₂ , and f ₃ of the ultrasonic image data. , Referred to as a first intermediate pixel value). For example, the pixel values of the pixels a _{1 to} a ₉ in the matrix M set in the frame f ₁ are “5” “6” “4” “19” “14” “7” “8” “2” “3”. If so, the intermediate value search unit 17 searches the pixel value “6” as the first intermediate pixel value. The intermediate value search unit 17 searches for the first intermediate pixel value by setting the matrix M for all the pixels in the frame f ₁ . Similarly, the intermediate value search unit 17 sets the matrix M for all the pixels in each of the frames f _{2 to} fn and searches for each first intermediate pixel value.

Next, the intermediate value search unit 17 searches for a second intermediate pixel value that is further intermediate from the first intermediate pixel values of the searched frames f _{1 to} fn. For example, as shown in FIG. 6, the first intermediate pixel value when the matrix M is set in the frame f ₁ is “6”, and the first intermediate pixel value when the matrix M is set in the frame f ₂ is “6”. 8 ”and the first intermediate pixel value when the matrix M is set in the frame f ₃ is“ 7 ”, the intermediate value search unit 17 sets the first intermediate pixel values“ 6 ”and“ 8 ”. A pixel value “7” that is further intermediate from “7” is searched as a second intermediate pixel value.
Therefore, the image creation unit 18 sequentially creates each frame of the ultrasound contrast image data from the second intermediate pixel value searched by the intermediate value search unit 17, creates the ultrasound contrast image data from these frames, and creates a moving image. Is displayed on the monitor 14.

Next, another intermediate value search method by the intermediate value search unit 17 will be described.
Similar to the above search method, the intermediate value search unit 17 sets, for example, a matrix M of 3 × 3 pixels, for example, in each frame f ₁ , f ₂ , f ₃ of the ultrasound contrast image data as shown in FIG. . The intermediate value search unit 17 includes a _first intermediate value between the nine pixel values of the pixels a _{1 to} a ₉ in the matrix M set in the frames f ₁ , f ₂ , and f ₃ of the ultrasound contrast image data. Search for an intermediate pixel value.

Next, the intermediate value search unit 17 replaces all of the pixel values of all the pixels a _{1 to} a ₉ in the matrix M with the first intermediate pixel value for each frame f ₁ , f ₂ , f ₃ . For example, if the _first intermediate pixel value when the matrix M is set in the frame f ₁ is “6”, the intermediate value search unit 17 sets all the pixels a _{1 to} a in the matrix M as shown in FIG. All the ₉ pixel values are replaced with “6” which is the first intermediate pixel value. Similarly, if the first intermediate pixel value when the matrix M is set in the frame f ₂ is “8”, the intermediate value search unit 17 sets the pixel values of all the pixels a _{1 to} a ₉ in the matrix M. Are all replaced with “8” which is the first intermediate pixel value. If the first intermediate pixel value when the matrix M is set to the frame f ₃ is “7”, the intermediate value search unit 17 sets all the pixel values of all the pixels a _{1 to} a ₉ in the matrix M to the _first value. Instead of “7”, which is an intermediate pixel value of 1.

Next, the intermediate value search unit 17 is in the middle from among the first intermediate pixel values “6”, “8”, and “7” that are searched from the _three frames f ₁ , f ₂ , and f _3. The second intermediate pixel value, here the second intermediate pixel value “7” is searched.

The intermediate value search method of the intermediate value search unit 17 is such that all the pixel values of all the pixels a _{1 to} a ₉ in the matrix M are set to the first intermediate pixel value for each frame f ₁ , f ₂ , f _3. Therefore, it is possible to search for an intermediate value by thinning out pixels in each frame f ₁ , f ₂ ,..., Fn of the ultrasound contrast image data. For example, if a 3 × 3 pixel matrix M shown in FIG. 5 is set, the matrix M can be set by moving three pixels on the ultrasound contrast image data.
Therefore, the image creation unit 18 sequentially creates each frame of the ultrasound contrast image data from the second intermediate pixel value searched by the intermediate value search unit 17, creates the ultrasound contrast image data from these frames, and creates a moving image. Is displayed on the monitor 14.

The quantification unit 19 generates the contrast-enhanced image data generated by the image generation unit 18, for example, the contrast-enhanced image data composed of the frames F ₁ , F ₂ , F ₃ ,... Fm shown in FIG. Alternatively, the temporal change of the image luminance value of the ultrasonic contrast image data composed of the second intermediate pixel values shown in FIG. 7 is quantified, that is, the temporal change of the image luminance value of the ultrasonic contrast image data is graphed by TIC, Quantitatively capture temporal changes in image brightness values by curve fitting.

  On the other hand, at the time of ultrasonic contrast examination, for example, the ultrasonic contrast image data of the subject S that moves repeatedly, such as the heart and the liver, is acquired, and the temporal change of the image luminance value of the ultrasonic contrast image data due to the injection of the ultrasonic contrast agent Is graphed, and it is necessary to read out each frame of the same cardiac time phase of the heartbeat of the subject S from the ultrasonic contrast image data in order to quantitatively grasp the temporal change of the image luminance value by curve fitting.

  In order to read out each frame of the same cardiac time phase of the heartbeat of the subject S, the intermediate value search unit 17 sets an arbitrary period at the time of the ultrasonic contrast examination. Here, the setting of the arbitrary period is specifically described. Explained. The electrocardiograph 22 generates an electrocardiogram synchronization signal C corresponding to the heartbeat of the subject S. The electrocardiogram synchronization signal C includes an R waveform that is one of peaks as shown in FIG.

The in-phase detection means 20 synchronizes the heart beat of the subject S with the same heart in synchronization with the R (R ₁ , R ₂ , R ₃ ,...) Waveform appearing in the electrocardiogram synchronization signal C output from the electrocardiograph 22. An arbitrary period is set for each repetition period of the heartbeat and the time phase. The phase detection means 20 includes a fixed time counting unit 23, a trigger signal generating unit 24, and a frame number counting unit 25.

The fixed time counting unit 23 sets an arbitrary period within the elapse of a preset time t, for example, the elapse of the time t (= 200 msec), starting from each R wave appearing in the electrocardiogram synchronization signal C.
The trigger signal generator 24 measures the time interval between the R waves appearing in the electrocardiogram synchronization signal C (RR), and when a predetermined ratio of time between RR has elapsed, for example, 20 between RR. A trigger signal is generated at the elapse of% time, and an arbitrary period is set from when the R wave appears until the trigger signal is generated.
The frame number counting unit 25 counts the number of frames f ₁ , f ₂ ,..., Fn of the ultrasound contrast image data starting from each R wave appearing in the electrocardiogram synchronization signal C, and the number of frames is a constant value. For example, a period until reaching the number of 6 frames is set as an arbitrary period.
However, the in-phase detection means 20 sets an arbitrary period by any one of the fixed time counting unit 23, the trigger signal generating unit 24, and the frame number counting unit 25.

Therefore, the intermediate value search unit 17 includes the frames f ₁ in the same cardiac time phase in the ultrasound contrast image data from an arbitrary period set by the fixed time counting unit 23, the trigger signal generating unit 24, or the frame number counting unit 25. Read f ₂ ,..., fn from the image memory 16. For example, as shown in FIG. 8, each frame f ₁ , f ₂ ,... Of the ultrasound contrast image data in synchronization with an R waveform appearing in the electrocardiogram synchronization signal C, for example, an R ₁ waveform, an R ₂ waveform, an R ₃ waveform, etc. If fn is stored in the image memory 16, respectively, the frame _{f 1} which starts _{R 1} waveform, the frame _{f 1} which starts _{R 2} waveform, frame _{f 1} and the same mind that starting from the _{R 3} waveform Become a time phase. Similarly, the frame _{f 2} which starts _{R 1} waveform, the frame _{f 2} which starts _{R 2} waveform, the frame _{f 2} both same cardiac phase which starts _{R 3} waveforms. Thus, the intermediate value search section 17, for example, R ₁ waveform in ultrasound contrast image data stored in the image memory 16 as a frame f ₁ as a starting point, and the frame f ₁ which starts R ₂ waveform, The frame f ₁ starting from the R ₃ waveform is read out, and the intermediate pixel value or the second intermediate pixel value is searched by applying each of the intermediate value search methods described above to these three frames f ₁ . .

Next, the TIC display operation by the apparatus configured as described above will be described.
An ultrasonic contrast agent is injected into the subject S during the ultrasonic contrast examination. This ultrasonic contrast agent flows into the blood vessel in the subject S. The ultrasonic probe 10 generates an ultrasonic pulse from each piezoelectric vibrator based on the drive signal from the transmission unit 11. The ultrasonic pulse transmitted into the subject S is reflected by the body tissue, blood flow, ultrasonic contrast agent, etc. in the subject S, and enters the ultrasonic probe 10 as a reflected wave. The receiving unit 12 of the ultrasonic probe 10 receives the reflected wave, converts it into an electrical signal, and amplifies and outputs this electrical signal.

  The image processing unit 13 digitally converts the electrical signal output from the receiving unit 12, performs imaging processing to create ultrasound contrast image data including a plurality of frames, and the ultrasound contrast agent in the subject S. A moving image of an ultrasound contrast image representing the dynamics is displayed on the monitor 14. At the same time, the image processing unit 13 stores the ultrasound contrast image data in the image memory 16.

Here, if the subject S is, for example, an organ in a stationary state, the intermediate value search unit 17 images _three consecutive frames f ₁ , f ₂ , and f ₃ as shown in FIG. 3, for example. Read from the memory 16. The intermediate value search unit 17 searches for the intermediate pixel value from the pixel values of the pixels g ₁ , g ₂ , and g _{3 having} the same coordinates in the frames f ₁ , f ₂ , and f ₃ . For example, if the pixel value of the pixel g _{1 in} the frame f ₁ is “5”, the pixel value of the pixel g _{2 in} the frame f ₂ is “3”, and the pixel value of the pixel g _{3 in} the frame f ₁ is “1”, the intermediate value The value search unit 17 searches the pixel value “3” that is in the middle from the pixel values “5”, “3”, and “1” as an intermediate pixel value. Similarly, the intermediate value search unit 17 obtains intermediate pixel values in the final three frames fn-2, fn-1, and fn such as _three temporally continuous frames f ₂ , f ₃ , and f _4. Search for.

Next, the image creating unit 18 generates ultrasonic waves from the intermediate values of the pixel values of the frames f ₁ , f ₂ , f _{3 to the} frames fn-2, fn−1, and fn searched by the intermediate value searching unit 17. Each frame F ₁ , F ₂ , F ₃ ,..., Fm of the contrast image data is sequentially generated, and the ultrasound contrast image data including these frames F ₁ , F ₂ , F ₃ ,. indicate. The image creating unit 18 stores ultrasonic contrast image data including frames F ₁ , F ₂ , F ₃ ,..., Fm in the image memory 16.

The intermediate value search method by the intermediate value search unit 17 may be performed as follows. For example, the intermediate value search unit 17 sets, for example, a matrix M of 3 × 3 pixels, for example, in each frame f ₁ , f ₂ , f ₃ of the ultrasound contrast image data as shown in FIG. The first intermediate pixel value that is in the middle of the nine pixel values of each of the pixels a _{1 to} a ₉ is searched. For example, the pixel values of the pixels a _{1 to} a ₉ in the matrix M set in the frame f ₁ are “5” “6” “4” “19” “14” “7” “8” “2” “3”. If so, the intermediate value search unit 17 searches the pixel value “6” as the first intermediate pixel value. Next, the intermediate value search unit 17 searches for a second intermediate pixel value that is further intermediate from the first intermediate pixel values for each of the searched frames f _{1 to} fn. For example, as shown in FIG. 6, the first intermediate pixel value of the frame f ₁ is “6”, the first intermediate pixel value of the frame f ₂ is “8”, and the first intermediate pixel value of the frame f ₃ If the value is “7”, the intermediate value search unit 17 searches for the pixel value “7” as the second intermediate pixel value. However, the image creation unit 18 sequentially creates each frame of the ultrasound contrast image data from the second intermediate pixel value searched by the intermediate value search unit 17, creates the ultrasound contrast image data from these frames, and creates a moving image. Is displayed on the monitor 14.

As another search method, the intermediate value search unit 17 sets a matrix M of 3 × 3 pixels, for example, in each frame f ₁ , f ₂ , f ₃ of the ultrasound contrast image data as shown in FIG. The first intermediate pixel value that is in the middle of the nine pixel values of each of the pixels a _{1 to} a ₉ is searched. Next, the intermediate value search unit 17 replaces all the pixel values of all the pixels a _{1 to} a ₉ in the matrix M with the first intermediate pixel value for each frame f ₁ , f ₂ , f ₃ , In addition, a _second intermediate pixel value that is intermediate from the first intermediate pixel values “6”, “8”, and “7” retrieved from the frames f ₁ , f ₂ , and f ₃ , respectively, The second intermediate pixel value “7” is searched.

  However, the image creation unit 18 sequentially creates each frame of the ultrasound contrast image data from the second intermediate pixel value searched by the intermediate value search unit 17, creates the ultrasound contrast image data from these frames, and creates a moving image. Is displayed on the monitor 14.

Next, the quantification unit 19 stores the ultrasound contrast image data stored in the image memory 16, for example, the ultrasound contrast image data including the frames F ₁ , F ₂ , F ₃ ,. Quantifying temporal changes in image luminance values, that is, graphing temporal changes in image luminance values of ultrasound contrast image data using a TIC technique, and capturing temporal changes in image luminance values quantitatively by curve fitting, A graph of the temporal change in the image luminance value of the ultrasonic contrast image data is displayed on the monitor 14. FIG. 9 shows a display example of the TIC in which the temporal change of the image luminance value of the ultrasonic contrast image is quantified. The TIC displayed on the display screen 1 of the TIC minimizes the influence of speckle noise, does not fluctuate finely and greatly, and accurately changes temporally the image luminance value of an ultrasound contrast image. Curve fitting is possible.

The influence of speckle noise in the TIC can be minimized by the intermediate value search unit 17, for example, each of the pixels g ₁ , g ₂ , and g _{3 having} the same coordinates in the _three frames f ₁ , f ₂ , and f ₃ . By retrieving the intermediate pixel value from the pixel value. For example, if there are pixel values “5”, “20”, and “1”, and pixel value “20” depends on speckle noise, an intermediate value of these pixel values “5”, “20”, and “1” is searched. As a result, the pixel value “20” is not searched and is always excluded. Even if each of the pixel values “20”, “1”, and “8” is searched, the pixel value “20” is not searched by searching the intermediate value. Accordingly, the pixel value corresponding to the speckle noise is not searched, and the influence of the speckle noise can be minimized in the TIC.
The ultrasound contrast image display screen 2 displays the dynamics of the ultrasound contrast agent G injected into the subject S such as an organ in a stationary state.

On the other hand, if the subject S is an organ such as the heart or a liver that reciprocally moves in accordance with the heartbeat motion of the heart, an ultrasound contrast agent is injected into the subject S. The electrocardiograph 22 generates an electrocardiogram synchronization signal C corresponding to the heartbeat of the subject S.
As shown in FIG. 8, the in-phase detection means 20 synchronizes the heartbeat of the subject S with the same cardiac time phase in synchronization with the R waveform appearing in the electrocardiogram synchronization signal C output from the electrocardiograph 22, and the heart An arbitrary period is set for each repetition period of heartbeat. For example, the fixed time counting unit 23 sets an arbitrary period within the elapse of a preset time t, for example, the elapse of the time t (= 200 msec), starting from each R wave appearing in the electrocardiogram synchronization signal C. The trigger signal generator 24 measures the time interval between the R waves appearing in the electrocardiogram synchronization signal C (RR), and when a predetermined ratio of time between RR has elapsed, for example, 20 between RR. A trigger signal is generated at the elapse of% time, and an arbitrary period is set from when the R wave appears until the trigger signal is generated. The frame number counting unit 25 counts the number of frames f ₁ , f ₂ ,..., Fn of the ultrasound contrast image data starting from each R wave appearing in the electrocardiogram synchronization signal C, and the number of frames is a constant value. For example, a period until reaching the number of 6 frames is set as an arbitrary period. However, the in-phase detection means 20 sets an arbitrary period by any one of the fixed time counting unit 23, the trigger signal generating unit 24, and the frame number counting unit 25.

The intermediate value search unit 17 includes the frames f ₁ and f ₂ of the same cardiac phase in the ultrasound contrast image data from an arbitrary period set by the fixed time counting unit 23, the trigger signal generating unit 24, or the frame number counting unit 25. ,..., Fn are read from the image memory 16. Origin For example, the intermediate value search section 17 includes a frame f ₁ which starts R ₁ waveform become the same cardiac phase as shown in FIG. 8, the frame f ₁ which starts R ₂ waveform, the R ₃ waveform It reads a frame _{f 1} to read the frame _{f 2} which starts _{R 1} waveform, the frame _{f 2} which starts _{R 2} waveform, and the frame _{f 2} which starts _{R 3} waveforms.

Then, an intermediate value search unit 17, when an ultrasound contrast examination, for example, a frame f ₁ which starts R ₁ waveform become the same cardiac phase, the frame f ₁ which starts R ₂ waveform, R ₃ waveform Find the intermediate value from each pixel value of the frame f ₁ as a starting point, the frame f ₂ which starts R ₁ waveform, the frame f ₂ which starts R ₂ waveform, starting from the R ₃ waveform Search intermediate value from each pixel value of the frame f _2.

Then, an intermediate value search section 17 includes a frame f ₁ which starts R ₁ waveform become the same cardiac phase, the frame f ₁ which starts R ₂ waveform, frame f ₁ which starts R ₃ waveform An intermediate pixel value is searched from each pixel value of each pixel having the same coordinates. Similarly, an intermediate value search unit 17, frame _f 2, _{f 3} which starts _{R 1} waveform become the same cardiac phase, ... and the frame _f 2, _{f 3} which starts _{R 2} waveform, ... and , R ₃ , and an intermediate pixel value is searched from each pixel value of each pixel having the same coordinates in frames f ₂ , f ₃ ,.
Note that the intermediate value search method by the intermediate value search unit 17 may be performed by another search method as described above. Description of another search method is omitted here because it overlaps with the above description.

  Next, the image creation unit 18 sequentially creates each frame of the ultrasound contrast image data from each intermediate pixel value searched by the intermediate value search unit 17, and the ultrasound contrast image data including these frames is displayed as a moving image on the monitor 14. To display. The image creating unit 18 stores ultrasonic contrast image data including each frame in the image memory 16.

  Next, the quantification unit 19 quantifies the temporal change in the image brightness value of the ultrasound contrast image data stored in the image memory 16, that is, the time of the image brightness value of the ultrasound contrast image data by the TIC technique. The temporal change of the image luminance value is quantitatively captured by curve fitting, and a graph of the temporal change of the image luminance value of the ultrasonic contrast image data is displayed on the monitor 14. Like the TIC shown in FIG. 9, the TIC displayed on the display screen 1 of the TIC on the monitor 14 has the effect of speckle noise being minimized and does not fluctuate finely and greatly. It is possible to accurately curve-fit the temporal change of the image luminance value of the ultrasound contrast image of the subject S such as the liver that repeatedly moves reciprocally according to the heartbeat movement of the heart.

  As described above, according to the above-described embodiment, the intermediate value is sequentially searched from each pixel value in the plurality of frames of the ultrasound contrast image, and the ultrasonic image data is generated from the searched intermediate value. The TIC is displayed by quantifying the temporal change in the image luminance value of the contrast-enhanced image data. As a result, the pixel value corresponding to the speckle noise is not searched, the influence of the speckle noise can be minimized in the TIC, and the image brightness of the ultrasonic contrast image does not fluctuate finely and greatly. Curve fitting can be performed accurately over time. Therefore, at the time of the ultrasound contrast examination, the interpretation doctor is not affected by speckle noise, determines the state of blood flow from the dynamics of the ultrasound contrast agent in the subject S displayed on the monitor, and the heart and liver For example, a lesion such as myocardial infarction in the subject S can be diagnosed.

If the subject S is, for example, an organ such as the heart or a liver that reciprocally moves in accordance with the heartbeat motion of the heart, for example, a constant time counting unit 23, a trigger signal based on the electrocardiogram synchronization signal C corresponding to the heartbeat of the heart. Since the frames f ₁ , f ₂ ,..., Fn, etc. of the same cardiac phase in the ultrasound contrast image data are read from an arbitrary period set by the generation unit 24 or the frame number counting unit 25, the influence of the heartbeat motion of the heart Without receiving, it is possible to create ultrasonic contrast image data in a state where the subject S such as the heart or the liver is stationary at a certain cardiac phase. As a result, the contrast-enhanced image data is displayed on the display screen 2 of the contrast-enhanced image as if it is stationary at a fixed cardiac phase, and the contrast-enhanced image is displayed on the display screen 1 of the TIC. The TIC for the data can be displayed.

Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.
For example, the intermediate value search unit 17 sets a matrix M of 3 × 3 pixels as shown in FIG. 5 to search for intermediate values, but uses a matrix of n × n (n: integer) pixels. Also good.
The image creating unit 18 obtains one frame F ₁ of the ultrasound contrast image data from the intermediate value of each pixel value of each frame f ₁ , f ₂ , f ₃ , for example, that is temporally searched for by the intermediate value search unit 17. However, the present invention is not limited to this, and it may be replaced with a plurality of temporally discrete frames, and a frame of ultrasonic contrast image data may be generated from an intermediate value of each pixel value of these frames. For example, at the time of ultrasonic contrast examination, this corresponds to reading out the frames f ₁ , f ₂ ,..., Fn, etc. that are temporally discrete in the same cardiac phase based on the electrocardiogram synchronization signal C corresponding to the heartbeat of the heart. In particular, when ultrasonic contrast image data is acquired by the flash echo method at the time of ultrasonic contrast examination, it is effective to read out each frame at a predetermined interval based on the electrocardiogram synchronization signal C in order to obtain the same cardiac phase. .

In the above-described embodiment, by reading out the frames f ₁ , f ₂ ,..., Fn, etc. of the same cardiac time phase in the ultrasound contrast image data, the subject S such as the heart or liver is as if a certain cardiac time phase. However, the present invention is not limited to this. For example, as shown in FIG. 10, two regions of interest (on the ultrasound contrast image data displayed on the monitor 14a ( ROI) 26 and 27 are set. Note that the subject S is displayed on the monitor 14a with a plurality of curves superimposed, which indicates the subject S that moves in accordance with the heartbeat movement of the heart.
Next, a change in each speckle pattern in each ROI 26, 27 is detected.
Next, the movement distance of the image of the subject S in each frame of the ultrasound contrast image data is obtained from the change of each speckle pattern, and the image of the subject S is placed at the same display position on the monitor 14a based on this movement distance. In this manner, the position of the image of the subject S in each frame is controlled. As a result, the subject S such as the heart or the liver is displayed with its motion corrected as if it were still as displayed on the monitor 14b as shown in FIG.

1 is a configuration diagram showing an embodiment of an ultrasonic image display device according to the present invention. The schematic diagram which shows each flame | frame of the ultrasonic contrast image data acquired by the apparatus. The schematic diagram which shows the search method of the intermediate value by the intermediate value search part of the apparatus. The schematic diagram which shows the matrix set to ultrasonic contrast image data by the intermediate value search part of the apparatus. The schematic diagram which shows the matrix used in the intermediate value search part of the apparatus. The schematic diagram which shows the search method of the 2nd intermediate pixel value by the intermediate value search part of the apparatus. The schematic diagram which shows another search method of the intermediate value by the intermediate value search part of the apparatus. The figure for demonstrating the setting of the arbitrary periods which read each flame | frame of the ultrasonic contrast image data at the time of the ultrasonic contrast inspection by the intermediate value search part of the apparatus. The figure which shows the example of a display of TIC which quantified the time change of the image luminance value of the ultrasonic contrast image obtained by the same apparatus. The figure for demonstrating the motion correction of the subject by the same apparatus. The figure which shows an example of the curve fitting of the time change of the image luminance value in the ultrasonic contrast image obtained by the conventional TIC.

Explanation of symbols

  S: subject, 10: ultrasonic probe, 11: transmission unit, 12: reception unit, 13: image processing unit, 14: monitor, 15: program memory, 16: image memory, 17: intermediate value search unit, 18: Image creation unit, 19: quantification unit, 20: in-phase detection means, 21: input unit, 22: electrocardiograph, 23: constant time counting unit, 24: trigger signal generation unit, 25: frame number counting unit.

Claims (31)

Ultrasonic image display that emits ultrasonic waves to a subject injected with a contrast agent, receives a reflected wave from the subject, and displays a moving image of an ultrasonic image representing the dynamics of the contrast agent in the subject In the method
The intermediate value is sequentially searched from each pixel value in a plurality of frames of the ultrasonic image within an arbitrary period, and ultrasonic image data is created and displayed from the searched intermediate value.
An ultrasonic image display method characterized by the above.   The ultrasonic image display method according to claim 1, wherein the temporal change in the image luminance value of the ultrasonic image data is quantified and displayed.   The ultrasonic image display method according to claim 1, wherein the intermediate value is searched from a plurality of the temporally continuous frames.   The ultrasonic image display method according to claim 1, wherein the intermediate value is searched from a plurality of the frames that are discrete in time.   The ultrasonic image display method according to claim 1, wherein the intermediate value is searched from the pixel values of at least three frames. The subject periodically contracts,
The ultrasonic image display method according to claim 1, wherein the arbitrary period is set for each repetition period of the contraction movement of the subject.   The ultrasonic image display method according to claim 6, wherein the arbitrary period is set when the contraction motion of the subject has the same phase. Generating a synchronization signal according to the contraction movement of the subject;
Generating a trigger signal according to the synchronization signal, and setting the arbitrary period when the contraction movement of the subject is in the same phase;
The ultrasonic image display method according to claim 7. Generating a synchronization signal according to the contraction movement of the subject;
Setting the arbitrary period when the contraction motion of the subject is in the same phase from the number of frames of the ultrasound image according to the synchronization signal;
The ultrasonic image display method according to claim 7. Generating an ECG synchronization signal corresponding to the contraction movement of the subject;
An elapse of a preset time starting from each R wave appearing in the electrocardiogram synchronization signal, generation of a trigger signal when a predetermined rate of time elapses between the R waves, or counting of the number of frames of the ultrasonic image Do any one to set the arbitrary period,
The ultrasonic image display method according to claim 7. Search each intermediate first pixel value from the values of a plurality of adjacent pixels in the plurality of frames of the ultrasound image,
Next, an intermediate second pixel value is further searched from each of the first intermediate pixel values for each of the searched frames.
Creating the ultrasound image data from the retrieved second intermediate pixel values;
The ultrasonic image display method according to claim 1 or 2. Searching for a first intermediate pixel value from a plurality of adjacent pixel values for each frame of the ultrasound image;
Next, for each frame, the plurality of adjacent pixel values are all replaced with the first intermediate pixel value,
Next, the first intermediate pixel values in the frames of the ultrasonic image within the arbitrary period are sequentially searched, and the intermediate values are located among the searched first intermediate pixel values. Searching for the second intermediate pixel value and generating the ultrasound image data from the second intermediate pixel value;
The ultrasonic image display method according to claim 1 or 2.   The ultrasonic image display method according to claim 1 or 2, wherein the ultrasonic image data including the intermediate value is replaced with the frame under a preset condition.   14. The frame replacement of the ultrasound image data is performed when the ultrasound image data is acquired by a flash echo method in a contrast agent inspection by injecting the contrast agent into the subject. The ultrasonic image display method as described. Ultrasonic image display that emits ultrasonic waves to a subject injected with a contrast agent, receives a reflected wave from the subject, and displays a moving image of an ultrasonic image representing the dynamics of the contrast agent in the subject In the device
An intermediate value search unit that sequentially searches for an intermediate value from each pixel value in a plurality of frames of the ultrasonic image within an arbitrary period;
A display unit;
An image creation unit that creates ultrasound image data from the intermediate value searched by the intermediate value search unit and displays the ultrasonic image data on the display unit;
An ultrasonic image display device comprising:   The ultrasonic image display device according to claim 15, further comprising a quantification unit that quantifies a temporal change in an image luminance value of the ultrasonic image data and displays the quantification on the display unit.   The ultrasonic image display device according to claim 15 or 16, wherein the intermediate value search unit searches the intermediate value from a plurality of the temporally continuous frames.   The ultrasonic image display device according to claim 15 or 16, wherein the intermediate value search unit searches for the intermediate value from a plurality of the temporally discrete frames.   The ultrasonic image display device according to claim 15 or 16, wherein the intermediate value search unit searches for an intermediate value of the pixel values of at least three frames. The subject periodically contracts,
The ultrasonic image display device according to claim 15, wherein the intermediate value search unit sets the arbitrary period for each repetition period of the contraction movement of the subject.   The ultrasonic image display device according to claim 19, wherein the intermediate value search unit sets the arbitrary period when the contraction motion of the subject has the same phase. A synchronization signal generating unit that generates a synchronization signal according to the contraction motion of the subject;
The intermediate value search unit generates a trigger signal according to the synchronization signal generated by the synchronization signal generation unit, and sets the arbitrary period when the contraction motion of the subject has the same phase,
The ultrasonic image display device according to claim 20. A synchronization signal generating unit that generates a synchronization signal according to the contraction motion of the subject;
The intermediate value search unit sets the arbitrary period when the contraction movement of the subject has the same phase from the number of frames of the ultrasonic image according to the synchronization signal generated by the synchronization signal generation unit,
The ultrasonic image display device according to claim 20.   The ultrasonic image display device according to claim 22 or 23, wherein the synchronization signal generation unit includes an electrocardiograph that generates an electrocardiogram synchronization signal corresponding to the contraction motion. The synchronization signal generation unit includes an electrocardiograph that generates an electrocardiogram synchronization signal according to the contraction motion,
The intermediate value search unit is configured to generate a trigger signal when a predetermined period of time elapses from each R wave appearing in the electrocardiogram synchronization signal as a starting point, or to generate the ultrasonic image. The arbitrary period is set by performing any of the counting of the number of frames of
The ultrasonic image display apparatus according to claim 21. The intermediate value search unit searches each first pixel value in the middle from the values of a plurality of pixels adjacent to each other in the plurality of frames of the ultrasound image, and the searched for each of the searched frames A second intermediate pixel value that is further intermediate from each first intermediate pixel value;
The image creation unit creates the ultrasound image data from the second intermediate pixel value searched by the intermediate value search unit;
The ultrasonic image display device according to claim 15 or 16. The intermediate value search unit searches for a first intermediate pixel value from a plurality of adjacent pixel values for each frame of the ultrasound image, and determines the adjacent pixel values for each frame. Instead of all the first intermediate pixel values, the first intermediate pixel values in the frames of the ultrasonic image in the arbitrary period are sequentially searched, and the searched first intermediate values are sequentially searched. Search for a second intermediate pixel value in the middle from among the pixel values;
The image creation unit creates the ultrasound image data from the second intermediate pixel values searched within the arbitrary period by the intermediate value search unit;
The ultrasonic image display device according to claim 15 or 16.   The ultrasonic image display device according to claim 15, wherein the image creation unit replaces the frame of the ultrasonic image data including the intermediate value under a preset condition.   29. The ultrasonograph according to claim 28, wherein when the ultrasound image data is acquired by a flash echo method in a contrast agent inspection by injecting the contrast agent into the subject, the frame of the ultrasound image data is replaced. Sound image display device. Ultrasonic image display that emits ultrasonic waves to a subject injected with a contrast agent, receives a reflected wave from the subject, and displays a moving image of an ultrasonic image representing the dynamics of the contrast agent in the subject In the program
The intermediate value of each pixel value in a plurality of frames of the ultrasonic image within an arbitrary period is sequentially searched, and ultrasonic image data including the searched intermediate values is obtained.
An ultrasonic image display program characterized by that.   31. The ultrasonic image display program according to claim 30, wherein the temporal change in the image luminance value of the ultrasonic image data is quantified and displayed.

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