JP2003190160A - Ultrasonic imaging system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic imaging system for performing three- dimensional (3D) imaging in which a sound ray density, a frame rate and an imaging are practical. <P>SOLUTION: This system has transmitting/receiving means (33, 36 and 48) for successively sending ultrasonic waves in a plurality of azimuths by repeating a skip scan in the azimuth of a two-dimensional (2D) azimuth matrix and for performing a scan in the azimuth not overlapped with the last scan each time the skip scan is repeated, a signal generating means (44) for generating the virtually received signal of the present time in the skipped azimuth by correcting the received signals in the past in the skipped azimuth corresponding to the quantity of a change from the last signal received in the scan azimuth of the present time for each of skip scans, and an image generating means (44) for generating a 3D image on the basis of the received signal in the scan azimuth of the present time and the virtual received signal. <P>COPYRIGHT: (C)2003,JPO

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic imaging apparatus, and more particularly to an ultrasonic imaging apparatus for taking a three-dimensional image.

[0002]

2. Description of the Related Art An ultrasonic imaging apparatus for capturing a three-dimensional image sequentially transmits ultrasonic waves to a plurality of orientations set as a two-dimensional orientation matrix (matrix) and receives echoes (echo). , 3 based on echo received signal
Generate a three-dimensional image.

[0003]

The speed of sound in a living body is about 1
Since it is 500 m / s, when the imaging range in the depth direction is set to, for example, 150 mm, the maximum number of times of transmission / reception allowed per second is about 5000 times. Shooting frame rate (fr
If the average rate is set to 10 frames / s, the number of times of transmission / reception per frame is about 500 times. When three-dimensional imaging is performed with this number of times, the size (size) of the two-dimensional orientation matrix is approximately 22 × 22. With this azimuth matrix size, the solid angle is, for example, 60
When a three-dimensional region of about 3 ° is photographed, the three-dimensional image has a poor lateral resolution, that is, a sound ray density, and is not practical.

Therefore, in order to obtain a practical sound ray density, the frame rate or the photographing range must be reduced to an impractical level. That is, the sound ray density,
It was not possible to make all of the frame rate and shooting range practical.

Therefore, an object of the present invention is to realize an ultrasonic imaging apparatus for three-dimensional imaging in which the sound ray density, the frame rate and the imaging range are practical.

[0006]

(1) In one aspect of the invention for solving the above-mentioned problems, an ultrasonic wave is sequentially transmitted to a plurality of directions to receive an echo. A transmission / reception unit that performs interlaced scanning of the directions in the matrix and scans a direction that does not overlap with the previous time each time the interlaced scanning is repeated, and an image generation unit that generates a three-dimensional image based on the received signal of the echo. An ultrasonic imaging apparatus comprising:

In the invention according to the aspect (1), ultrasonic waves are sequentially transmitted to a plurality of azimuths and echoes are received by repeating interlace scanning of the azimuths in the two-dimensional azimuth matrix, and interlacing is performed. Since the azimuth that does not overlap with the previous one is scanned each time the scanning is repeated, it is possible to obtain the same result as that when the frame rate is increased and the sound ray density is increased by interlacing the azimuths.

(2) In another aspect of the invention for solving the above-mentioned problems, an interlaced scanning of azimuths in a two-dimensional azimuth matrix is performed by sequentially transmitting ultrasonic waves to a plurality of azimuths and receiving echoes. And the transmitting and receiving means for scanning an azimuth that does not overlap with the previous time each time the interlaced scanning is repeated, and each time the interlaced scanning is performed, the received signal of the past time in the interlaced azimuth is scanned in the azimuth. By correcting according to the amount of change of the received signal from the previous time, a signal generation means for generating a virtual received signal of this time in the jumped azimuth, and a received signal in the azimuth scanned this time for each time of the interlaced scanning. And an image generation unit that generates a three-dimensional image based on the virtual received signal. It is the location.

According to the invention described in (2), (1)
In addition, for each interlaced scan, the received signal of the past time in the interlaced direction is corrected according to the amount of change in the received signal in the direction scanned this time from the previous time, so Since a three-dimensional image is generated based on the received signal in the direction scanned this time and the virtual received signal, the sound ray density of the three-dimensional image can be increased.

(3) In another aspect of the invention for solving the above-mentioned problems, an ultrasonic interlaced scanning in a two-dimensional azimuth matrix is performed by sequentially transmitting ultrasonic waves to a plurality of azimuths and receiving echoes. And the transmitting and receiving means for scanning the azimuth that does not overlap with the previous time each time the interlaced scanning is repeated, and the interlaced azimuth by the interpolation calculation from the received signal in the azimuth scanned this time for each of the interlaced scanning. And a signal generation means for generating a three-dimensional image based on the received signal in the direction scanned this time and the virtual received signal for each time of the interlaced scanning. And an ultrasonic imaging apparatus.

According to the invention described in (3), (1)
In addition to this, for each interlaced scan, a virtual received signal of this time in the jumped azimuth is generated by interpolation calculation from the received signal in the azimuth scanned this time, and the received signal in the azimuth scanned this time and the virtual Since the three-dimensional image is generated based on the received signal, the sound ray density of the three-dimensional image can be increased.

(4) In another aspect of the invention for solving the above-mentioned problems, an ultrasonic interlaced scanning in a two-dimensional azimuth matrix is performed by sequentially transmitting ultrasonic waves to a plurality of azimuths and receiving echoes. While performing by repeating, the transmitting and receiving means for scanning the azimuth that does not overlap with the previous time each time the interlaced scanning is repeated, and each time of the interlaced scanning, by substituting the received signal of the past times in the interlaced azimuth, A signal generation unit that generates a virtual reception signal of this time in the jumped azimuth, and a three-dimensional image is generated for each of the interlaced scans based on the reception signal in the azimuth scanned this time and the virtual reception signal. An ultrasonic imaging apparatus, comprising: an image generating unit.

According to the invention described in (4), (1)
In addition, by substituting the received signals of the past times in the jumped direction for each interlaced scanning,
Since the virtual reception signal of this time in the jumped direction is generated and the three-dimensional image is generated based on the reception signal in the direction scanned this time and the virtual reception signal, it is possible to increase the sound ray density of the three-dimensional image. it can.

(5) In another aspect of the invention for solving the above-mentioned problems, an ultrasonic interlaced scanning in a two-dimensional azimuth matrix is performed by sequentially transmitting ultrasonic waves to a plurality of azimuths and receiving echoes. And the receiving and transmitting means for scanning the azimuth that does not overlap with the previous time each time the interlaced scanning is repeated, and the received signal of the nearest azimuth among the received signals in the azimuth scanned this time for each of the interlaced scanning. By substituting, the signal generation means for generating the virtual reception signal of this time in the jumped azimuth, and 3 for each time of the interlaced scanning based on the reception signal in the azimuth scanned this time and the virtual reception signal. An ultrasonic imaging apparatus, comprising: an image generating unit that generates a three-dimensional image.

According to the invention described in (5), (1)
In addition, for each interlaced scan, the received signal of the closest azimuth is substituted for the received signal in the azimuth scanned this time to generate the virtual received signal of this azimuth in the azimuth jumped and scanned this time. Since the three-dimensional image is generated based on the received signal in the azimuth and the virtual received signal, the sound ray density of the three-dimensional image can be increased.

It is preferable that the transmitting / receiving means performs the interlacing at a predetermined azimuth interval in order to make scanning regular. The azimuth intervals may be equal intervals or unequal intervals.

[0017]

BEST MODE FOR CARRYING OUT THE INVENTION Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. The present invention is not limited to the embodiment. FIG. 1 shows a block diagram of the ultrasonic imaging apparatus. This device is an example of an embodiment of the present invention. The configuration of this device shows an example of an embodiment relating to the device of the present invention.

As shown in the figure, this device has an ultrasonic probe 33. The ultrasonic probe 33 is used by being pressed against the body surface of the target 7 by the user. Ultrasonic probe 3
3 is an ultrasonic transducer array (transducer array) 300 as shown in FIG. 2, for example.
Have. The ultrasonic transducer array 300 is a two-dimensional array and includes, for example, 1024 ultrasonic transducers 302 forming a 32 × 32 square matrix. The two-dimensional array is not limited to the square matrix, but may be an anisotropic matrix such as 32 × 16. The ultrasonic transducer 302 is, for example, PZT (titanium (T
i) Zirconate (Zr) lead) ceramics (cera
mics) or other piezoelectric material.

The ultrasonic probe 33 is connected to the transmitting / receiving section 36. The transmission / reception unit 36 gives a drive signal to the ultrasonic probe 33 to transmit an ultrasonic wave. The transmitter / receiver 36
Also, the echo signal received by the ultrasonic probe 33 is received. The portion including the ultrasonic probe 33 and the transmission / reception unit 36 is an example of the embodiment of the transmission / reception means in the present invention.

The transmission / reception unit 36 performs scanning as shown in FIG. 3, for example. That is, three-dimensional scanning is performed by scanning a cone-shaped imaging range having the center of the ultrasonic transducer array 300 as an apex with the ultrasonic beam (beam) 303 in the angle θ direction and the angle φ direction. Note that the length direction of the ultrasonic beam 303 is the z direction. z
The direction is also the depth direction of the shooting. The θ direction and the φ direction are two directions perpendicular to each other. Such a three-dimensional scan is also called a pyramid scan.

FIG. 4 is a block diagram of another type of ultrasonic imaging apparatus. This device is an example of an embodiment of the present invention. The configuration of this device shows an example of an embodiment relating to the device of the present invention.

As shown in the figure, this device has an ultrasonic probe 33 '. The ultrasonic probe 33 'is used by being pressed against the body surface of the target 7 by the user. The ultrasonic probe 33 'has, for example, an ultrasonic transducer array 300' as shown in FIG. The ultrasonic transducer array 300 ′ is a one-dimensional array, for example, 12
It consists of eight ultrasonic transducers 302 '. Ultrasonic transducer 3
02 'is made of a piezoelectric material such as PZT.

The ultrasonic probe 33 'is connected to the transmitting / receiving section 36'. The transmission / reception unit 36 'includes the ultrasonic probe 3
A drive signal is given to 3'to transmit ultrasonic waves. The transceiver unit 36 'also receives the echo signal received by the ultrasonic probe 33'.

The transmitter / receiver 36 'performs scanning as shown in FIG. 6, for example. That is, a so-called sector scan is performed by scanning the fan-shaped two-dimensional region 206 in the θ direction with the ultrasonic beam that propagates in the z direction from the radiation point 200, that is, the sound ray 202.

Transmit and receive apertures
ure) is formed by using a part of the ultrasonic transducer array, by sequentially moving the aperture along the array, for example, scanning as shown in FIG. 7 can be performed. That is, the sound ray 202 emitted in the z direction from the radiating point 200 is moved in parallel along the linear locus 204 to scan the rectangular two-dimensional area 206 in the x direction, so-called linear scan (linea).
r scan).

The ultrasonic transducer array is
A so-called convex array (convex array) formed along an arc extending in the ultrasonic wave transmission direction.
In the case of y), a sound ray scan similar to the linear scan is performed, and, for example, as shown in FIG.
Needless to say, so-called convex scan can be performed by moving 00 along the arcuate locus 204 and scanning the fan-shaped two-dimensional region 206 in the θ direction.

Three-dimensional scanning is performed by continuously scanning the two-dimensional region 206 while the inclination or position of the ultrasonic probe 33 'is continuously changed by the sweep mechanism 31. Sweep mechanism 3
1. The portion including the ultrasonic probe 33 ′ and the transmitting / receiving unit 36 ′ is an example of the embodiment of the transmitting / receiving means in the present invention.

When continuously changing the inclination of the ultrasonic probe 33 ', for example, as shown in FIG. 9, the inclination angle φ of the two-dimensional area 206 is changed and scanning in the φ direction can be performed. When continuously changing the position of the ultrasonic probe 33 ', for example, as shown in FIG.
The position y of 06 changes and scanning in the y direction can be performed.

Hereinafter, scanning in the θ direction or x direction is also called main scanning, and scanning in the φ direction or y direction is also called sub scanning. The sub-scan is electronically performed by the transmitting / receiving unit 36 in the two-dimensional array, and mechanically by the sweep mechanism 31 in the one-dimensional array. If the sweep mechanism 31 is not used, it may be performed manually. When mechanically performing sub-scanning, the combination of main scanning and sub-scanning is (θ, φ),
There can be four ways: (θ, y), (x, φ) and (x, y). The mechanical sub-scan may be performed manually.

Since the three-dimensional scanning is performed by the combination of the main scanning and the sub-scanning, the azimuth of the sound ray is two-dimensionally changed.
That is, the directions of the sound rays form a two-dimensional matrix.
Hereinafter, the two-dimensional matrix of the direction of the sound ray is also referred to as a two-dimensional direction matrix.

FIG. 11 shows an example of a two-dimensional orientation matrix. As shown in the figure, the two-dimensional orientation matrix is, for example, a 66 × 66 square matrix. It should be noted that the matrix size may be appropriate, and it is not limited to a square matrix and may be an anisotropic matrix. Hereinafter, the two-dimensional azimuth matrix is also simply referred to as an azimuth matrix. The row direction of the azimuth matrix is the main scanning (θ or x) direction, and the column direction is the sub scanning (φ or y) direction.

The present apparatus performs three-dimensional scanning by performing interlaced scanning on such an orientation matrix. The interlaced scanning will be described below. Each azimuth in the azimuth matrix is grouped in, for example, a 3 × 3 matrix unit. There is no overlap between groups. Hereinafter, this is also referred to as a partial matrix. 66
In the x66 azimuth matrix, 22 × 22 partial matrices can be formed. The matrix size of the partial matrix is not limited to 3 × 3 and may be any size. Further, it is not limited to a square matrix, but may be an anisotropic matrix.

FIG. 12 shows one of the partial matrices. In the figure, the numbers 1 to 9 in the cells of the partial matrix represent the relative order of interlaced scanning. Note that the order may be given to the cells. Interlaced scanning is performed for azimuths with the same relative order in each submatrix.
This is performed by sequentially transmitting and receiving ultrasonic waves in units of partial matrix.

Specifically, the first scanning is performed by sequentially transmitting and receiving ultrasonic waves in the unit of partial matrix for the azimuth of relative order 1 in each partial matrix. As a result, ultrasonic wave transmission / reception for 22 × 22 azimuth is performed by one scan. The azimuth at this time is shown in FIG. 13 by the shaded cells in the matrix.

The second scanning is performed by sequentially transmitting and receiving ultrasonic waves in the unit of partial matrix for the azimuth of relative order 2 in each partial matrix. As a result, ultrasonic wave transmission / reception for 22 × 22 azimuth is performed by one scan. The azimuth at this time is shown in FIG. 14 by the shaded cells in the matrix.

Similarly, the third to ninth interlaced scans are similarly performed for the orientations of relative numbers 3 to 9 in each partial matrix. The azimuth of the ninth scan is shown in FIG.
Shown in. The sequence is completed in the tenth interlaced scan.
Return to the state shown in. This is repeated below. Less than,
Interlaced scanning is also simply called scanning. One scan corresponds to one frame of a three-dimensional image.

In this way, the 66 × 66 azimuth matrix is interlaced and scanned 9 times, that is, 9 frames. Since the azimuth per frame is 22 × 22, even if the shooting range in the depth direction is set to 150 mm,
For example, three-dimensional imaging can be performed at a frame rate of about 10 frames / s.

The azimuth per frame is 22 × 2
2, the transmission / reception is performed in a direction that does not overlap each time until one scan is completed, and the transmission / reception is performed in the 66 × 66 direction as a whole.
(rrace) reduces the roughness of the scan. Therefore, it is possible to obtain a three-dimensional image that is sufficiently practical even when a three-dimensional region having a solid angle of, for example, about 60 ° is photographed.

The transmitting / receiving unit 36 (36 ') is connected to the B-mode processing unit 40. The echo reception signal for each sound ray output from the transmission / reception unit 36 (36 ′) is input to the B-mode processing unit 40. The B-mode processing unit 40 forms B-mode image data. The B-mode processing unit 40
After the logarithmic amplification of the echo reception signal, envelope detection is performed to obtain a signal representing the intensity of the echo at each reflection point on the sound ray, that is, an A scope signal, and the instantaneous amplitude of this A scope signal is obtained. B-mode image data is formed as the brightness value. The B-mode processing unit 40 is connected to the image processing unit 44. The image processing unit 44 generates a three-dimensional image based on the data input from the B-mode processing unit 40. B-mode processing unit 40 and image processing unit 4
The part consisting of 4 is an example of an embodiment of the image generating means in the present invention.

The image processing unit 44, as shown in FIG.
Central processing unit (CPU: Cen
a true processing unit 140. The CPU 140 is provided with a main memory 14 by a bus 142.
4, external memory 146, control unit interface (in
interface) 148, input data memory (data)
memory) 152, digital scan converter (DSC: Digital Scan Conve)
rter) 154, an image memory 156, and a display memory (display memory) 158.
Are connected.

The external memory 146 stores a program executed by the CPU 140. External memory 146
In addition, various data used by the CPU 140 to execute the program are also stored in the.

The CPU 140 performs predetermined image processing by loading a program from the external memory 146 into the main memory 144 and executing the program. C
The PU 140 exchanges control signals with the control unit 48, which will be described later, through the control unit interface 148 during the program execution.

The B-mode image data, that is, the sound data, input from the B-mode processing unit 40 for each sound ray is stored in the input data memory 152. For example, FIGS.
When the interlaced scanning as shown in FIG. 3 is sequentially and repeatedly performed, since transmission and reception are performed only in the shaded azimuths in each frame, the sound ray data of the current frame exists only in those azimuths. Hereinafter, the sound ray data of the current frame is also referred to as current data.

Although the sound ray data stored in the input data memory 152 is processed into a form suitable for forming an image, it is substantially an echo reception signal. .

The direction in which the current data is obtained is sequentially changed according to the frame, and is returned to the original every 10th frame.
That is, the current data of each direction is obtained once every 9 frames, and the value is updated each time. Except for the present data, the past frame data obtained by the past scanning is referred to as past data. The input data memory 152 stores such current data and past data.

The sound ray data of the input data memory 152 is
Each frame is scan converted by the DSC 154 and written in the image memory 156. When writing the sound ray data in the image memory 156, the CPU 140 generates virtual present data for an orientation having no present data, that is, an orientation having only past data, and writes it as the present data in that orientation. The CPU 140 is an example of the embodiment of the signal generating means in the present invention. Note that C
The PU 140 may write only the current data in the image memory 156 without generating virtual current data.

Generation of virtual current data by the CPU 140 will be described. Virtual current data generation is
This can be done by any of four methods. The four methods will be sequentially described below.

The first method is a method for generating virtual current data by correcting past data based on the amount of change in current data. What is the amount of change in current data?
This is the amount of change from the previous time in the data that is updated once every 9 frames, and is specifically as follows.

Data of all directions of the direction matrix are obtained by scanning 9 times. If this is shown paying attention to one partial matrix, all the data A1 to A9 of the partial matrix A are aligned as shown in FIG. The same applies to adjacent partial matrices. The subscripts indicate the relative order of interlaced scanning.

In the tenth scan, an interlaced scan of relative order 1 is performed, and as shown in FIG.
1 ', B1', C1 ', D1' are obtained. Other than these are past data.

Present data A1 ', B1', C1 ', D
For 1 ′, the amounts of change from the previous values A1, B1, C1, D1 are calculated, respectively. As a result, the amounts of change a1, b1, c1, and d1 are obtained as shown in FIG. When the data changes in this way in the azimuth of relative order 1, the past data of the other azimuths in the partial matrix A are likely to change in the same tendency at this time. Therefore, the amount of change in the past data at the present time is estimated based on the amounts of change a1, b1, c1, and d1.

The analogy is performed by interpolation calculation. The other directions in the partial matrix A are change amounts a1, b1, c
Since 1 and d1 are the eight directions inside the four determined directions, the amount of change in the data in those directions can be estimated by an interpolation calculation using the amounts of change a1, b1, c1, and d1. Is.

As the interpolation calculation, linear interpolation using two data is used, for example. That is, the change amount a
1 and b1 are used to linearly interpolate the amount of change in the data of the two orientations between them, and the amount of change a1 and c1 are used to linearly interpolate the amount of change in data of the two orientations between them. A1 and d1 are used to linearly interpolate the amount of change in the two azimuth data between them, and change amounts b1 and c1 are used to linearly interpolate the amount of change in the two azimuth data between them. The interpolation calculation is not limited to the linear interpolation using the two data, but may be the non-linear two-dimensional interpolation using all the four data a1, b1, c1, d1. As a result, as shown in FIG. 20, analogy values a2 to a9 of the change amount are obtained.

The past data is corrected by using the analogy values a2 to a9 of the variation amount. The correction is the analogy value a2 of the change amount.
To a9 are added to the past data A2 to A9 shown in FIG. 18, respectively. As a result, FIG.
As shown in 1, the current data A1 ′, B1 ′, C1 ′,
D1 'and virtual current data A2' to A obtained by correcting the past data using the amount of change from the previous time.
9'is obtained.

Virtual current data is similarly obtained for the other partial matrices. The same thing is performed in each of the subsequent frames.
In this way, by correcting the past data based on the change amount of the current data, it is possible to obtain virtual current data most suitable for the current frame.

The second method is a method of generating virtual current data by interpolation from the current data. For example, as shown in FIG. 22, when the current data A1 ′, B1 ′, C1 ′, D1 ′ is obtained in a certain frame,
Virtual current data in the partial matrix A is obtained by interpolation calculation from the current data A1 ', B1', C1 ', D1'. As the interpolation calculation, for example, linear interpolation is adopted, but the interpolation calculation is not limited thereto. As a result, as shown in FIG. 23, the virtual current data A2 ″ -A
9 '' is obtained respectively. Similar interpolation calculation is performed for other partial matrices. The same thing is performed in each frame. By such an interpolation calculation using the current data, virtual current data suitable for the current frame can be obtained. This method is preferable because it does not require past data to obtain virtual current data.

The third method is to substitute past data as virtual current data. In one frame after one round of three-dimensional scanning, for example, as shown in FIG. 24, when the current data A1 ′, B1 ′, C1 ′, D1 ′ is obtained, it is obtained in the previous frame in other directions. Since the past data A2 to A9 already exist, they are used as virtual current data as they are. Do the same for the other sub-matrices. The same thing is done in each frame. By substituting such past data, it is possible to easily obtain virtual present data.

The fourth method is to substitute the current data as virtual current data in another direction. For example, as shown in FIG. 22, when the current data A1 ′, B1 ′, C1 ′, D1 ′ is obtained in a certain frame, the virtual current data of the other orientation of the partial matrix A is in that orientation. The current data of the closest bearing, that is, the closest bearing is used as a substitute.

As a result, the data of the partial matrix A becomes as shown in FIG. That is, the relative order 2,
Since the azimuths closest to the azimuths 4 and 5 are the azimuths having the relative order 1, the virtual current data in those azimuths are all A1. Since the azimuth closest to the azimuths in the relative orders 3 and 6 is the azimuth in the relative order 1 of the partial matrix B, the virtual current data in those azimuths are all B1.
Becomes Since the azimuth closest to the azimuths in the relative orders 7 and 8 is the azimuth in the relative order 1 of the partial matrix C, the virtual current data in those azimuths are all C1.
Since the azimuth closest to the azimuth in the relative order 9 is the azimuth in the relative order 1 of the partial matrix D, the virtual current data in those azimuths is D1. The same applies to other partial matrices, and the same applies to other respective frames. Substitution of such current data makes it possible to easily obtain virtual current data.

The virtual current data generated in this manner is combined with the current data of the frame and the DSC 154.
Is scanned and converted and written in the image memory 156. The data in the image memory 156 is output to the display unit 46 through the display memory 158.

The display section 46 displays a three-dimensional image based on the image signal provided from the image processing section 44. The display unit 46 is a CRT capable of displaying a color image.
A graphic display using a (cathode-ray tube)
y) and the like.

By the above-described three-dimensional scanning and the processing of the sound ray data corresponding thereto, the sound ray density, the frame rate and the photographing range of the three-dimensional image become practical.

The sweep mechanism 31 and the transmission / reception unit 36 described above
The control unit 48 is connected to (36 ′), the B-mode processing unit 40, the image processing unit 44, and the display unit 46. The control unit 48 gives a control signal to each of these units to control the operation thereof. Various notification signals are input to the control unit 48 from each controlled unit. Under the control of the control unit 48, the B mode operation is executed.

An operation unit 50 is connected to the control unit 48. The operation unit 50 is operated by the user, and the control unit 48
It is designed to input appropriate commands and information. The operation unit 50 is, for example, a keyboard or a pointing device.
e) and other operating tools.

[0065]

As described in detail above, according to the present invention, it is possible to realize an ultrasonic imaging apparatus for performing three-dimensional imaging in which the sound ray density, the frame rate and the imaging range are practical.

[Brief description of drawings]

FIG. 1 is a block diagram of an example of an embodiment of the present invention.

FIG. 2 is a schematic diagram of an ultrasonic transducer array.

FIG. 3 is a conceptual diagram of sound ray scanning.

FIG. 4 is a block diagram of an example of an embodiment of the present invention.

FIG. 5 is a schematic diagram of an ultrasonic transducer array.

FIG. 6 is a conceptual diagram of sound ray scanning.

FIG. 7 is a conceptual diagram of sound ray scanning.

FIG. 8 is a conceptual diagram of sound ray scanning.

FIG. 9 is a conceptual diagram of sweep scanning.

FIG. 10 is a conceptual diagram of sweep scanning.

FIG. 11 is a conceptual diagram of a two-dimensional azimuth matrix.

FIG. 12 is a conceptual diagram of a partial matrix.

FIG. 13 is a conceptual diagram of scanning of a two-dimensional azimuth matrix.

FIG. 14 is a conceptual diagram of scanning a two-dimensional azimuth matrix.

FIG. 15 is a conceptual diagram of scanning of a two-dimensional azimuth matrix.

FIG. 16 is a block diagram of an image processing unit.

FIG. 17 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

FIG. 18 is a conceptual diagram of a data array in a two-dimensional azimuth matrix.

FIG. 19 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

FIG. 20 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

FIG. 21 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

FIG. 22 is a conceptual diagram of a data array in a two-dimensional azimuth matrix.

FIG. 23 is a conceptual diagram of a data array in a two-dimensional azimuth matrix.

FIG. 24 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

FIG. 25 is a conceptual diagram of a data array in a two-dimensional orientation matrix.

[Explanation of symbols]

31 Sweep mechanism 33,33 'Ultrasonic probe 36,36 'Transceiver 40 B mode processing unit 44 Image processing unit 46 Display 48 control unit 50 Operation part 140 CPU 144 main memory 146 external memory 148 Control unit interface 152 Input data memory 154 DSC 156 image memory 158 display memory

   ─────────────────────────────────────────────────── ─── Continued front page    (72) Inventor Hiroshi Hashimoto             127, 4-7 Asahigaoka, Hino City, Tokyo             GE Yokogawa Medical System Co., Ltd.             Within F-term (reference) 2G047 BA03 CA01 DB02 DB12 EA07                       EA08 EA09 GB02 GB17 GF15                       GF17 GF20 GG19 GG34 GG41                       GH09                 4C301 BB13 BB22 EE07 EE08 EE10                       GB10 HH08 HH12 HH13 JB17                       JB29 KK16                 4C601 BB03 BB05 BB06 EE04 EE05                       EE07 GB01 GB03 GB06 HH14                       HH16 HH17 HH22 JB34 JB45                       JB51 JC25 KK21                 5C024 AX10 CX37 DX06 EX06

Claims (8)

[Claims] 1. An ultrasonic wave is sequentially transmitted to a plurality of azimuths to receive an echo by repeating interlace scanning of the azimuth in a two-dimensional azimuth matrix, and each time the interlace scanning is repeated, overlap with the previous time is performed. An ultrasonic imaging apparatus comprising: a transmission / reception unit that scans a direction that does not exist; and an image generation unit that generates a three-dimensional image based on a received signal of the echo. 2. An ultrasonic wave is sequentially transmitted to a plurality of azimuths to receive an echo by repeating interlace scanning of the azimuths in a two-dimensional azimuth matrix, and each time the interlaced scanning is repeated, the overlap with the previous time is performed. Transmitting and receiving means for scanning the azimuth not to be performed, and each time the interlaced scanning is performed, the reception signal of the past time in the interlaced orientation is corrected in accordance with the change amount of the reception signal in the direction scanned this time from the previous time, and thus the interlace is skipped. Signal generation means for generating a virtual reception signal of this time in the azimuth direction, and 3 for each time of the interlaced scanning based on the reception signal in the azimuth direction of the current scan and the virtual reception signal.
An ultrasonic imaging apparatus, comprising: an image generating unit that generates a three-dimensional image. 3. Sequentially transmitting ultrasonic waves to a plurality of directions and receiving echoes by repeating interlace scanning of directions in a two-dimensional azimuth matrix, and repeating each time interlaced scanning repeats from the previous time. Transmitting and receiving means for scanning the azimuth not performed, each time the interlaced scanning, by the interpolation calculation from the received signal in the azimuth scanned this time, signal generation means for generating the virtual received signal of this time in the azimuth jumped, 3 for each interlaced scan based on the received signal in the direction scanned this time and the virtual received signal.
An ultrasonic imaging apparatus, comprising: an image generating unit that generates a three-dimensional image. 4. Sequentially transmitting ultrasonic waves to a plurality of azimuths and receiving echoes by repeating interlace scanning of azimuths in a two-dimensional azimuth matrix, and repeating each time interlaced scanning repeats from the previous time. A transmitting / receiving unit that scans an azimuth that does not exist, and a signal generation unit that generates a virtual reception signal of this time in the jumped azimuth by substituting the reception signal of the past times in the jumped azimuth for each time of the interlaced scanning Based on the received signal in the direction scanned this time and the virtual received signal for each interlaced scan.
An ultrasonic imaging apparatus, comprising: an image generating unit that generates a three-dimensional image. 5. An ultrasonic wave is sequentially transmitted to a plurality of azimuth directions to receive an echo by repeating interlace scanning of the azimuth in a two-dimensional azimuth matrix, and each time the interlaced scanning is repeated, the overlap with the previous time is performed. Not transmitting and receiving means for scanning the azimuth, each time the interlaced scanning, by substituting the received signal of the nearest azimuth among the received signals in the azimuth scanned this time, the virtual received signal of this time in the azimuth jumped A signal generating means for generating, and 3 for each time of the interlaced scanning based on the reception signal in the direction scanned this time and the virtual reception signal.
An ultrasonic imaging apparatus, comprising: an image generating unit that generates a three-dimensional image. 6. The ultrasonic imaging apparatus according to claim 1, wherein the transmitting / receiving unit performs the interlace at predetermined azimuth intervals. 7. The ultrasonic imaging apparatus according to claim 6, wherein the azimuth intervals are equidistant. 8. The ultrasonic imaging apparatus according to claim 6, wherein the azimuth intervals are unequal intervals.