JPH04254754A - Ultrasonic three-dimensional imaging device - Google Patents

Abstract

PURPOSE:To realize three-dimensional ultrasonic image pickup of high pickup speed and high resolution by forming simultaneously a number of three- dimensional reception beams being uniform in sensitivity. CONSTITUTION:In a three-dimensional reception focusing means 4, a plurality of three-dimensional reception beams in directions at equal angles to one direction of transmission are formed simultaneously. Since the three-dimensional beams being uniform in sensitivity can be formed in large numbers simultaneously in this constitution, three-dimensional ultrasonic image pickup of high pickup speed and high resolution can be realized.

Description

[Detailed description of the invention]

0001

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic three-dimensional imaging device used in medical ultrasonic diagnostic equipment, nondestructive testing equipment, and the like.

0002

[Prior art] The prior art is Japanese Patent Application Laid-Open No. 62-12852.
As described above, a configuration has been proposed in which a plurality of reception beams are formed for a two-dimensional ultrasound image using a one-dimensional array of transducers. In the case of a two-dimensional ultrasound image, the number of beams required within one tomographic image to obtain the desired resolution is 100 to 200 beams. For example, when the imaging depth is 15 cm, the time required to transmit and receive one beam is 0.2 msec. Therefore, if one or two receiving beams are simultaneously formed for one transmitting beam, an imaging speed of 25 to 50 frames per second can be obtained, and images of moving organs can be obtained in real time.

0003

In the case of a three-dimensional ultrasonic image, the number of beams required in one stereo to obtain the desired resolution is one order of magnitude or more (for example, 10 times more) than in a two-dimensional image. Therefore, if one or two received beams were formed for one transmitted beam, it would be necessary to either extremely slow down the imaging speed or increase the imaging speed by degrading the resolution.

0004

[Means for Solving the Problems] As a means for solving the above problems, a configuration is provided in which multiple (three or more) three-dimensional receiving beams are simultaneously formed at equal angles with respect to one three-dimensional transmitting direction. And so.

[0005]

[Operation] With the above configuration, a large number of three-dimensional received beams with uniform sensitivity can be formed simultaneously, so three-dimensional ultrasound imaging with high imaging speed and high resolution can be realized.

[0006]

Embodiments Hereinafter, embodiments of the present invention will be explained in detail with reference to the drawings.

FIG. 1 is a diagram showing an example of a circuit configuration according to the present invention. Reference numeral 1 denotes a two-dimensional array vibrator, which forms a three-dimensional transmission beam T by a three-dimensional transmission means 2. After the signal received at R1 is amplified by the amplification means 3, the three-dimensional reception focusing means 4 converts the signal into a reception beam R1 in four directions, for example.
~R4 is formed simultaneously. The output of 4 is subjected to signal processing such as detection and compression by signal processing means 5, and then stored in three-dimensional memory means 6.
is input. The output of 6 follows the signal of the control means 8,
The display means 7 displays a three-dimensional display or an arbitrary cross section. Transmitting beam direction T and receiving beam direction R1 to R
4 is controlled by control means 8.

FIG. 2 is a diagram showing an example of element division of the two-dimensional array vibrator 1. As shown in FIG. (a) is a case of rectangular division, (b) is a case of concentric circle and radial division, and (c) is a case of hexagonal division. Although other division shapes may be considered, it is clear that in any shape of two-dimensional array element division, it is better for phasing and addition to divide the elements so that the area of each element is approximately equal. In addition, so that the directivity of the transmitted beam T has approximately the same sensitivity on the surface of the solid angle cone with T as the central axis, the two-dimensional array of transducers shown in FIG. Drives the element for transmission and reception. Therefore, by forming the reception beam so that r1=r2=r3=r4, where the angles between T and R1 to R4 are r1 to r4, a plurality of beams with uniform transmission and reception sensitivity can be formed at the same time.

FIG. 3 is a block diagram showing an example of the circuit configuration of the receiving phasing circuit 4 according to the present invention. A1 to An are output terminals of the amplification means 3 in FIG. 1, and MPX is a selection means. M.P.
X output can be adjusted according to variable aperture or variable focus.
A set of arbitrary adjacent terminals from 1 to An is selected and inputted to the first delay means P1 to P4. At P1 to P4, the phases of adjacent terminals (for example, four terminals) are matched, and the signals are input to the second delay means B1 to B4. In B1 to B4, phase matching is performed between each block (for example, 4 blocks), and the respective outputs are designated as a, b, c, and d. By adding a, b, c, and d, a receiving beam can be formed in the same direction as the transmitting direction T. Therefore, a, b, c, d are connected to the bus line BL.
are input to the third delay means C1 to C4, respectively. In C1 to C4, there are small angles r1 to r with respect to the wave transmission direction T.
The phases are adjusted so that the received beams are deflected by 4, and are added by the adding means D1 to D4. D
The outputs of 1 to D4 become reception beams R1 to R4 that are simultaneously formed in the transmission direction T.

FIG. 4 is a diagram showing another embodiment of the receiving phasing circuit according to the present invention. A1~An, MPX, P1~P
4 is similar to FIG. AD1 to AD4 are A/D
The converters M1-M4 are memories. That is, P1~
The output of P4 is A/D converted by AD1 to AD4 and then stored in M1 to M4, respectively. The outputs of M1 to M4 are sent to digital delay means E1 to E1 through bus line BL.
It is input to E4. For E1 to E4, B1 to B4 in FIG.
The phase matching between blocks performed in step 1 and the phase matching of minute angles r1 to r4 performed in steps C1 to C4 are performed simultaneously. E1~
The respective outputs of E4 are added by digital addition means F1 to F4, respectively, to form received beams R1 to R4.

In the above embodiment, the case where four receiving beams are simultaneously formed from the second delay means of four blocks has been explained, but it is possible to simultaneously form four or more receiving beams from the second delay means of any number of blocks. It is clear that the method can also be applied to the case of forming. In addition, the second delay signal can be obtained from the received signal of each element A1 to An without being divided into blocks by the first delay means.
It is also possible to directly form a plurality of received beams using the third delay means.

0012

[Effects of the Invention] Since a large number of three-dimensional receiving beams with uniform sensitivity can be formed simultaneously, three-dimensional ultrasound imaging with high imaging speed and high resolution can be realized.

[Brief explanation of the drawing]

FIG. 1 is a diagram showing an example of a circuit configuration according to an embodiment of the present invention.

FIG. 2 is a diagram showing an example of element division of a two-dimensionally arrayed vibrator.

FIG. 3 is a block diagram showing an example of a circuit configuration of a receiving phasing circuit according to an embodiment of the present invention.

FIG. 4 is a diagram showing another embodiment of the receiving phasing circuit according to the present invention.

[Explanation of symbols]

DESCRIPTION OF SYMBOLS 1... Two-dimensional array transducer, 2... Three-dimensional wave transmission focus means, 3... Amplification means, 4... Three-dimensional wave reception focus means, 5...
Signal processing means, 6... Three-dimensional memory, 7... Display means, 8...
Control means, MPX...selection means, P1-P4...first delay means, B1-B4...second delay means, C1-C4...third delay means, D1-D4...addition means, AD1-AD4...A/D
Converter, M1-M4...memory, E1-E4...digital delay means, F1-F4...digital addition means.

Claims (3)

[Claims] Claim 1: A two-dimensional array transducer that transmits and receives ultrasonic waves;
A three-dimensional focusing means for three-dimensionally converging an ultrasound beam, a three-dimensional receiving focusing means for simultaneously forming receiving ultrasound beams in a plurality of directions, and an output of the three-dimensional receiving focusing means. a signal processing means for detecting and compressing the wave;
A supercomputer comprising: a three-dimensional memory means for storing the output of the signal processing means; a means for displaying the output of the three-dimensional memory means in three dimensions or an arbitrary cross section; and a control circuit for controlling each of the means. Sonic three-dimensional imaging device. 2. The three-dimensional reception focusing means according to claim 1, characterized in that a plurality of three-dimensional reception beams in the same angular direction are simultaneously formed with respect to one transmission direction. Device. 3. An ultrasonic three-dimensional imaging apparatus characterized in that an A/D converter and a memory are used as the three-dimensional wave reception focusing means according to claim 1.