JP2003024332A - Ultrasonic diagnostic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To form an ultrasonic image expressing the inner wall of a blood vessel three-dimensionally by setting a visual point inside of the blood vessel. SOLUTION: An insertion part 14 is inserted into the blood vessel and an array vibrator 22 is rotated and driven. Ultrasonic beams 26 are formed at respective axial directional position and respective rotation angle in an axial direction 100. A pixel value is decided by each ultrasonic beam. On a displaying coordinate system, the axial directional position of the ultrasonic beams is made to correspond to a radius (r) and the rotation angle of the ultrasonic beams is made to correspond to an azimuth θ to constitute a mapping image. A similar mapping image can be formed also by drawing and scanning a simple vibrator.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to imaging of tissue inside a body cavity.

[0002]

2. Description of the Related Art An ultrasonic probe of a body cavity insertion type is known which is inserted into an esophagus, a urethra, a blood vessel or the like.
For example, a so-called small probe inserted into a blood vessel is
It has a catheter-shaped sheath, a torque wire inserted through the inside thereof, a single oscillator provided at the tip thereof, and the like.
When the torque wire is rotated, a single oscillator provided at the tip of the torque wire is rotationally scanned, and as a result, a single ultrasonic beam formed by the single oscillator is mechanically radially scanned. If the magnitude of the echo data on each ultrasonic beam is made to correspond to the brightness value, a tubular ultrasonic image (B mode image) can be formed. In this case, the azimuth angle in the display coordinate system corresponds to the radial scanning angle, and the radius in the display coordinate system corresponds to the distance from the single oscillator to the echo data (sample point).

[0003]

However, the ultrasonic image as described above is only one cross section of the luminal tissue such as a blood vessel, and the observation should be performed at a time in the axial direction of the luminal tissue. I can't. Here, it is possible to continuously display ultrasonic images while pulling out the small diameter probe, but in that case, it is impossible to stereoscopically represent the inner peripheral surface of the luminal tissue. On the other hand, although it is possible to combine the three-dimensional image display technology with the above, complicated calculations are required to construct an ultrasonic image with a perspective within the luminal tissue and a sense of depth. There are aspects that are lacking or require expensive hardware. Japanese Patent Laid-Open No. 10-33538 discloses a method for forming a three-dimensional ultrasonic image by applying the volume rendering method.

The present invention has been made in view of the above conventional problems, and an object of the present invention is to display the inside of the lumen tissue of a living body as an ultrasonic image with a sense of depth.

Another object of the present invention is to quickly form an ultrasonic image showing the inside of luminal tissue without requiring complicated calculation.

[0006]

(1) In order to achieve the above-mentioned object, the present invention inserts a luminal tissue along its axial direction to provide a plurality of axial positions and a plurality of axial positions. A means for forming an ultrasonic beam at a rotation angle, a transmitting / receiving means for outputting an echo data string for each ultrasonic beam, and a pixel value for the echo data string for each ultrasonic beam. A pixel value calculation means for performing a calculation for obtaining the value, and an axial position of the ultrasonic beam corresponding to a radius of the display coordinate system, and a rotation angle of the ultrasonic beam corresponding to an azimuth angle of the display coordinate system. Display processing means for forming an ultrasonic image having a sense of depth by mapping the pixel value for each ultrasonic beam on a display coordinate system.

According to the above configuration, the pixel value is obtained for each ultrasonic beam (for each echo data string), and the pixel value is the radius corresponding to the axial position of the ultrasonic beam on the display coordinate system. (R) and a position (that is, coordinates (r, θ)) corresponding to the azimuth angle (θ) corresponding to the rotation angle of the ultrasonic beam. By this mapping, the pixel value for each ultrasonic beam is represented on a two-dimensional plane to form an ultrasonic image. This ultrasonic image represents information on the tissue structure (for example, information on the inside of the blood vessel), and also represents the tissue structure in a pseudo three-dimensional manner. Since complicated calculations such as viewpoint calculation and line-of-sight calculation are unnecessary, an ultrasonic image can be formed quickly.

It is desirable that the radius be gradually increased as the axial position of each ultrasonic beam moves from the inner side to the front side of the luminal tissue. According to this configuration,
A region near the central portion in the ultrasonic image corresponds to the back side in the axial direction, and a peripheral portion in the ultrasonic image corresponds to the front side in the axial direction. Therefore, a viewpoint can be set in the luminal tissue, and an image can be formed that looks from the viewpoint to the inner side in the axial direction (similar to the field of view when looking forward in the tunnel). Here, preferably, the ultrasonic beam is electronically linearly scanned in the axial direction.

(2) In order to achieve the above object,
The present invention is means for forming an ultrasonic beam at a plurality of deflection angles with respect to an axial direction and at a plurality of rotation angles about an axis, which are inserted into a luminal tissue along its axial direction, A transmitting / receiving unit that outputs an echo data string for each ultrasonic beam, a pixel value calculating unit that performs a calculation for obtaining a pixel value for the echo data string for each ultrasonic beam, and an ultrasonic beam Pixel values for each ultrasonic beam are mapped on the display coordinate system by making the deflection angle correspond to the radius of the display coordinate system and the rotation angle of the ultrasonic beam correspond to the azimuth angle of the display coordinate system. Accordingly, the display processing means for forming an ultrasonic image having a sense of depth is included.

According to the above configuration, a pixel value is obtained for each ultrasonic beam (for each echo data string), and the pixel value has a radius (corresponding to the deflection angle of the ultrasonic beam on the display coordinate system). r) and the position (that is, the coordinates (r, θ)) corresponding to the azimuth angle (θ) corresponding to the rotation angle of the ultrasonic beam. By this mapping, the pixel value for each ultrasonic beam is represented on a two-dimensional plane to form an ultrasonic image. Here, the deflection angle corresponds to the angle at which the ultrasonic beam intersects the axial direction, and the ultrasonic beam most inclined to the inner side in the axial direction (for convenience,
A plurality of ultrasonic beams are formed at each deflection angle from the minimum deflection angle) to the ultrasonic beam most inclined to the front side in the axial direction (for convenience, the deflection angle is maximum). Also in the above configuration, complicated calculations such as viewpoint calculation and line-of-sight path calculation are unnecessary, so that an ultrasonic image can be formed quickly.

It is desirable that the deflection angle of each ultrasonic beam changes from the back side to the front side of the luminal tissue (according to the definition for convenience described above, the deflection angle changes from the minimum to the maximum). The radius is gradually increased. Here, it is desirable that the ultrasonic beam is scanned by an electronic sector in the axial direction.

(3) Preferably, it includes means for setting at least one of a minimum value and a maximum value for the radius.
According to this configuration, for example, the radius for mapping the pixel value of the ultrasonic beam whose axial position or deflection angle is the farthest side (or the most front side) can be adjusted. The central portion (circular region) smaller than the minimum radius may be uniformly displayed with a predetermined brightness or may be subjected to other image processing. This also applies to the outside of the maximum radius.

Preferably, the wave transmitting / receiving means executes an electronic scan of an array transducer composed of a plurality of vibrating elements aligned along the axial direction and an ultrasonic beam formed by the array transducer. And a mechanical scanning unit that rotates the array transducer to perform mechanical radial scanning of an ultrasonic beam formed by the array transducer.

Preferably, the transmitting / receiving means includes a probe unit including an insertion portion to be inserted into the luminal tissue and an operation portion provided on a proximal end side of the insertion portion, The insertion section includes a hollow sheath tube, a torque wire inserted into the sheath tube, and an array transducer including a plurality of vibrating elements arranged at the tip of the torque wire and aligned in the axial direction. , And the operation unit includes a drive motor which is provided on the proximal end side of the torque wire and rotationally drives the torque wire.

Preferably, the transmitting / receiving means includes a single oscillator, and a radial scanning means for rotating the single oscillator to perform mechanical radial scanning of an ultrasonic beam formed by the single oscillator. And the rotation of the single oscillator and the pulling out of the single oscillator in the axial direction are performed. The extraction may be performed automatically or manually. In order to prevent distortion of the ultrasonic image, it is desirable to perform the extraction at a constant speed, but the extraction may be performed at an arbitrary speed as long as the data of the extraction position can be obtained. The radial scanning may be performed simultaneously with the extraction, or the extraction may be performed in stages and the radial scanning may be performed at each extraction position.

[0016] Preferably, the wave transmitting / receiving means includes a probe unit including an insertion portion to be inserted into the luminal tissue and an operation portion provided on a proximal end side of the insertion portion, The insertion portion includes a hollow sheath tube, a torque wire inserted into the sheath tube, and a single oscillator provided at a tip portion of the torque wire, and the operation portion is a base of the torque wire. A drive motor that is provided on the end side and that rotationally drives the torque wire is included, and rotational driving of the single oscillator and extraction of the single oscillator in the axial direction are performed.

Preferably, the luminal tissue is a blood vessel of a living body. In this case, an ultrasonic image in which the blood vessel is three-dimensionally expressed is formed, and the structure of the inner surface can be three-dimensionally expressed.

[0018]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT A preferred embodiment of the present invention will be described below with reference to the drawings.

FIG. 1 is a conceptual diagram showing the overall configuration of the ultrasonic diagnostic apparatus according to the present invention.

In FIG. 1, the ultrasonic diagnostic apparatus is roughly divided into a probe unit 10 and an apparatus main body 12.

The probe unit 10 constitutes an ultrasonic probe for insertion into a body cavity, and the probe unit 10 is connected to the apparatus main body 12 via a cable.

The probe unit 10 comprises an insertion portion 14 and an operation portion 16. The insertion portion 14 is, for example, a portion to be inserted into a blood vessel of a living body, and has a bendable shape according to the running state of the blood vessel.

The insertion portion 14 has a sheath tube 18, a torque wire 20 and an array transducer 22. The sheath tube 18 is a catheter tube, and the inside 18A thereof is filled with a medium (for example, distilled water) for ensuring sound propagation. The torque wire 20 is inserted into the sheath tube 18, and particularly inserted in the sheath tube 18 in a rotatable state. The array transducer 22 is provided at the tip of the torque wire 20, and the array transducer 22 is composed of a plurality of vibrating elements 24. In FIG. 1, the array vibrator 22 is configured by m vibrating elements from the vibrating element 24-1 to the vibrating element 24-m. The vibrating elements 24 are linearly aligned in the example shown in FIG.

Incidentally, in the torque wire 20, a plurality of signal lines corresponding to the plurality of vibrating elements 24 are inserted.

The ultrasonic beam 2 is transmitted by the array transducer 22.
6 is formed, and the scanning surface is formed by electronically scanning the ultrasonic beam. Here, when the electronic linear scanning of the ultrasonic beam is performed, the ultrasonic beam 2 is moved in the moving direction along the axial direction 100 as shown in FIG.
6 is linearly moved and scanned, whereby n ultrasonic beams from the ultrasonic beam 26-1 to the ultrasonic beam 26-n are formed. Incidentally, the electronic scanning direction may be a direction toward the inner side of the blood vessel, or may be a direction opposite to the axial direction thereof. In any case, the n ultrasonic beams 26 as described above form a scanning plane which is a two-dimensional echo data acquisition region. As will be described later, when the torque wire 20 is rotationally driven, the array transducer 22 also rotates around the axis, and the electronic scanning of the ultrasonic beam is executed at each rotation angle. As a result, a scanning plane is formed for each rotation angle, and a three-dimensional echo data acquisition area is formed as an aggregate of the scanning planes.

By the way, by sampling the received signal for one ultrasonic beam, an echo data string consisting of a plurality of echo data arranged in time series is acquired.

Of course, in the example shown in FIG. 1, electronic linear scanning is shown, but a similar array transducer 22 is used.
It is also possible to apply electronic sector scanning to.

The operation section 16 is arranged outside the body and has a drive motor 30 and an encoder 32 in this embodiment. The drive motor 30 applies a rotational force to the torque wire 20, as conceptually shown in FIG. That is, the torque wire 20 is rotationally driven by the drive motor 30, which causes the array transducer 22 to move.
Rotates around the axis. Then, a scanning surface is formed for each rotation angle.

The encoder 32 is a detector for detecting the rotation angle of the torque wire 20, and outputs the detected angle signal.

In the apparatus main body 12, the transmission / reception section 36 supplies a transmission signal to the plurality of vibrating elements 24 forming the array transducer 22, and phase-adds the reception signals output from the plurality of vibrating elements. By doing so, the phase-added reception signal is formed. Under the control of the controller 38, the transmission / reception unit 36 electronically scans the ultrasonic beam 26, that is, forms the ultrasonic beam 26 at each axial position (i) in the axial direction 100.

The drive control section 34 is controlled by the controller 38 and outputs a drive signal to the drive motor 30 described above. The controller 38 controls the operation of the apparatus body 12, and the angle signal from the encoder 32 is input to the controller 38. The controller 38 controls the mechanical radial scanning of the array transducer 22 and the electronic scanning of the ultrasonic beam based on the angle signal.

The rendering operation unit 40 includes a transmitting / receiving unit 3
The received signal (echo data string) after phasing and addition output from 6 is input. In the present embodiment, the rendering calculation unit 40 executes calculation for determining a pixel value for each ultrasonic beam, that is, for each echo data string. Here, as the calculation method, the above-mentioned Japanese Patent Laid-Open No. 10-33 is used.
Various methods such as the method, integration method, and representative value determination method described in Japanese Patent No. 538 can be used. In any case, the pixel value reflecting the plurality of echo data on the ultrasonic beam is determined. Therefore, the rendering calculation unit 40 sequentially performs the above calculation on the echo data string that is continuously input in accordance with the electronic scanning of the ultrasonic beam and the mechanical scanning of the array transducer 22, and the echo data string is obtained. The pixel value is determined for each and the data representing the pixel value is output to the display processing unit 42.

The display processing unit 42 has a frame memory 44, and data of each pixel value is mapped on the frame memory 44 as described later with reference to FIG. Then, the mapping image 54 is formed on the frame memory 44. The mapping image 54 is a pseudo three-dimensional image in which a backside of the blood vessel is observed from the viewpoint of the inside of the blood vessel, and as described later with reference to FIG. It is a real representation. The ultrasonic image (mapping image) formed in this way is displayed on the display 48.

The input unit 46 is composed of, for example, an operation panel, and the user can use the input unit 46 to set calculation conditions in the rendering calculation unit 40 and processing conditions in the display processing unit 42.

Incidentally, the display processing unit 42 has a data interpolation function, a coordinate conversion function and the like in addition to the above-mentioned mapping function. For example, the display processing unit 42 is constituted by a digital scan converter (DSC) or the like.

FIG. 2 shows a three-dimensional data acquisition space 52 formed based on electronic linear scanning. Further, FIG. 3 shows a three-dimensional data acquisition space 53 formed based on the electronic sector scanning.

As shown in FIG. 2, a rectangular scan plane 50.
Is composed of n ultrasonic beams from the ultrasonic beams 26-1 to 26-n, and a plurality of scanning surfaces 50 are formed by radially scanning the scanning surface 50, thereby forming a cylindrical shape. A three-dimensional data acquisition space 52 is formed.

Further, as shown in FIG. 3, when the electronic sector scanning is applied, the ultrasonic beam 2 which is radially expanded is applied.
The scanning surface 51 is configured by n ultrasonic beams from 7-1 to the ultrasonic beam 27-n, and the scanning surface 51 is radially scanned to form a rotation shape obtained by rotating the fan-shaped scanning surface 51. A three-dimensional data acquisition space 53 is formed. Here, in the electronic sector scanning, each ultrasonic beam 27 is formed with a different deflection angle, and specifically, the ultrasonic beam is formed by gradually changing the deflection angle with respect to the axial direction 100. Become.

FIG. 4 shows the mapping process in the display processing unit 42 shown in FIG. That is, this mapping process is a process of mapping each pixel value data on the display coordinate system defined on the frame memory 44.

By the way, in the mapping,
A polar coordinate system specified by a radius r centering on the origin O and an azimuth angle θ is used. However, in actual image formation, conversion from the polar coordinate system to the orthogonal coordinate system specified by x and y is generally required.

In this embodiment, when the pixel value data obtained for each ultrasonic beam is mapped to the display coordinate system, the axial position i (or deflection angle i) of the ultrasonic beam is set to the display coordinate system. It is associated with the radius r and the rotation angle θ of the ultrasonic beam is associated with the azimuth angle θ of the display coordinate system. Then, the pixel value data e1 corresponding to the farthest ultrasonic beam in the axial direction 100 is assigned on the radius R1, and the pixel value data en corresponding to the farthest ultrasonic beam in the axial direction 100 is the maximum radius R. Assigned above. That is, as the position i of the ultrasonic beam goes from the back to the front in the axial direction, r
Is set to gradually increase. Therefore, when n pixel value data corresponding to n ultrasonic beams forming a certain scanning plane are mapped, as shown by reference numeral 102 in FIG. 4, n pixel value data arranged on a certain radius are arranged. The pixel value data string 102 consisting of is mapped. Further, if such a pixel value data string 102 is mapped on all the scanning planes, a large number of pixel value data will be mapped over the entire ring-shaped region sandwiched by both the radius R1 and the radius R2. , Which constitutes the mapping image 54. Therefore, one mapping image 54 is formed for each rotation about the axis of the array transducer 22.

Each pixel value data may be used as a brightness value as it is, or may be weighted based on the radius r and then the brightness value of the pixel may be determined from the pixel value data. For example, as a general tendency, the brightness values may be weighted so that the front side is expressed brighter than the back side in the axial direction. Further, as is clear from FIG. 4, since the data density of the peripheral portion of the mapping image 54 is smaller than the data density of the portion near the central blank area in the mapping image, for example, data interpolation or data thinning For example, the mapping image 54 as a whole can be made uniform in apparent resolution by applying the above. In this case, various conventionally known interpolation processes can be applied.

In the display processing unit 42, actually, for each pixel value data, from (i, θ) to (r, θ).
The conversion from (r, θ) to (x, y) is performed, but the conversion from (i, θ) to (x, y) is performed directly. May be. In any case, in mapping pixel value data, the parameters r and θ are directly or indirectly used.

FIG. 5 shows a specific example of the mapping image 54 as shown in FIG. In the figure, reference numeral 56 indicates a ring-shaped pixel value data string drawn by each ultrasonic beam on the innermost side in the axial direction,
Reference numeral 58 indicates a pixel value data string drawn by each of the frontmost ultrasonic beams in the axial direction. Figure 5
According to the pseudo-stereoscopic ultrasonic image as shown in (3), the plaque attached to the inner wall of the blood vessel as shown by reference numeral 60, for example, can be recognized three-dimensionally, which can be useful for diagnosis of disease.

Of course, the minimum radius R1 and the maximum radius R2 shown in FIG. 4 can be variably set using the input section 46 shown in FIG. 1, and the blank area at the center shown in FIG. May have a white color or a predetermined brightness.

Another embodiment is shown in FIGS. 6 and 7. FIG. 6 shows a cross section of the blood vessel 70, and the insertion portion 62 of the probe unit is inserted into the blood vessel 70. The insertion portion 62 is composed of a sheath tube 64 and a torque wire 66. Torque wire 66
A single oscillator 68 is provided at the tip of the, and the ultrasonic beam 26 is formed by this single oscillator. Torque wire 6
The ultrasonic beam 26 is radially scanned by rotating 6 to form a circular data acquisition region. When the insertion portion 62 is pulled out to the front side while forming such a scanning plane, the scanning planes 26 are sequentially moved to the front side, that is, a plurality of scanning planes 26 are formed by the pulling out. .

Here, the ultrasonic beam forming the scanning surface formed on the farthest side is indicated by the reference numeral 26, and the ultrasonic beam forming the scanning surface formed on the frontmost side is indicated by the reference numeral 26 '. It is shown. Here, the number of scanning surfaces is n. Also, the movement amount of the extraction or the axial position of the scanning surface is L.

A cylindrical three-dimensional echo data acquisition region can also be formed by such radial scanning and extraction scanning, and the pixel value is determined from the echo data string obtained for each ultrasonic beam, If the pixel values are mapped by the method shown in FIG.
An image as shown in can be obtained.

Specifically, as shown in FIG. 7, pixel value data of each ultrasonic beam 26 forming the innermost scanning surface is mapped on the minimum radius R1 and mapped according to the movement amount L. By gradually increasing the radius r, the ring-shaped pixel value data sequence 76 can be gradually formed on the concentric circles, and the mapping image 74 can be finally constructed. In this case, one rotation of the radial scan corresponds to the formation of one ring-shaped data string 76, and the entire extraction scan corresponds to the entire mapping image 74. Incidentally, the rotation angle θ of the ultrasonic beam in the radial scan corresponds to the azimuth angle θ in the mapping image 74, as in the method shown in FIG. More precisely, the mapping image 74 may be formed in a spiral shape.

[0050]

As described above, according to the present invention,
The inside of the luminal tissue of the living body can be expressed as an ultrasonic image with a sense of depth. Further, according to the present invention, the inside of the luminal tissue can be quickly imaged without requiring complicated calculation.

[Brief description of drawings]

FIG. 1 is a conceptual diagram showing a preferred embodiment of an ultrasonic diagnostic apparatus according to the present invention.

FIG. 2 is a diagram showing a three-dimensional data acquisition space when electronic linear scanning is applied.

FIG. 3 is a diagram showing a three-dimensional data acquisition space when electronic sector scanning is applied.

FIG. 4 is a diagram for explaining a mapping process.

FIG. 5 is a diagram showing an example of an ultrasonic image.

FIG. 6 is a diagram showing a configuration of an insertion portion according to another embodiment.

FIG. 7 is a diagram for explaining a mapping process according to another embodiment.

[Explanation of symbols]

10 probe unit, 12 device main body, 14 insertion part, 16 operation part, 18 sheath tube, 20 torque wire, 22 array transducer, 30 drive motor, 3
2 encoder, 36 transmitting / receiving unit, 40 rendering arithmetic unit, 42 display processing unit.

   ─────────────────────────────────────────────────── ─── Continued front page    F-term (reference) 4C301 AA02 BB01 BB02 BB03 BB05                       BB13 BB22 BB28 BB30 DD30                       EE10 EE20 FF01 FF09 GA01                       GA15 GB04 GC02 GD10 JB06                       JB29 KK17 LL02                 5B057 AA07 BA05 CA08 CA12 CA16                       CB08 CB13 CB16 CD18 CE08

Claims (12)

[Claims] 1. Means for forming an ultrasonic beam at a plurality of axial positions and at a plurality of rotation angles about an axis, which is inserted into a luminal tissue along its axial direction, the means comprising: A wave transmitting / receiving unit that outputs an echo data string for each ultrasonic beam, a pixel value calculating unit that performs a calculation for obtaining a pixel value for the echo data string for each ultrasonic beam, and an axis of the ultrasonic beam Mapping the pixel value of each ultrasonic beam on the display coordinate system by making the direction position correspond to the radius of the display coordinate system and the rotation angle of the ultrasonic beam corresponding to the azimuth angle of the display coordinate system. And a display processing unit that forms an ultrasonic image having a sense of depth. 2. The apparatus according to claim 1, wherein the radius is set to be gradually larger as the axial position of each of the ultrasonic beams goes from the back side to the front side of the luminal tissue. Ultrasonic diagnostic equipment. 3. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic beam is electronically linearly scanned in the axial direction. 4. A means for forming an ultrasonic beam at a plurality of deflection angles with respect to the axial direction and at a plurality of rotation angles about the axis, the ultrasonic beam being inserted into a luminal tissue along its axial direction. A transmission / reception unit that outputs an echo data string for each ultrasonic beam; a pixel value calculation unit that executes a calculation for obtaining a pixel value for the echo data string for each ultrasonic beam; The deflection angle of each of the ultrasonic beams is mapped to the radius of the display coordinate system, and the rotation angle of the ultrasonic beam is mapped to the azimuth angle of the display coordinate system. Accordingly, a display processing unit for forming an ultrasonic image having a sense of depth, and an ultrasonic diagnostic apparatus comprising: 5. The apparatus according to claim 4, wherein the radius is set to be gradually larger as the deflection angle of each ultrasonic beam changes from the back side to the front side of the luminal tissue. And ultrasonic diagnostic equipment. 6. The ultrasonic diagnostic apparatus according to claim 4, wherein the ultrasonic beam is scanned by an electronic sector in the axial direction. 7. The ultrasonic diagnostic apparatus according to claim 1, further comprising means for setting at least one of a minimum value and a maximum value for the radius. 8. The apparatus according to claim 1 or 4, wherein the transmitting / receiving unit includes an array transducer including a plurality of vibrating elements aligned in the axial direction, and an ultrasonic transducer formed by the array transducer. An electronic scanning means for electronically scanning the acoustic wave beam; and a mechanical scanning means for rotating the array transducer to perform mechanical radial scanning of the ultrasonic beam formed by the array transducer. An ultrasonic diagnostic apparatus comprising: 9. The device according to claim 1 or 4, wherein the transmitting / receiving unit includes an insertion section to be inserted into the luminal tissue and an operation section provided on a proximal end side of the insertion section. A probe unit configured, wherein the insertion portion is a hollow sheath tube, a torque wire inserted into the sheath tube, and a plurality of torque wires that are provided at a distal end portion of the torque wire and are aligned along the axial direction. An ultrasonic diagnostic apparatus comprising: an array transducer including a vibrating element, wherein the operation unit includes a drive motor that is provided on a proximal end side of the torque wire and rotationally drives the torque wire. 10. The apparatus according to claim 1, wherein the transmitting / receiving unit includes a single oscillator, and mechanical radial scanning of an ultrasonic beam formed by the single oscillator by rotating the single oscillator. And a radial scanning unit for executing the rotational scanning of the single oscillator and the pulling out of the single oscillator in the axial direction. 11. The device according to claim 1, wherein the wave transmitting / receiving unit includes an insertion section to be inserted into the luminal tissue and an operation section provided on a proximal end side of the insertion section. The insertion portion includes a hollow sheath tube, a torque wire inserted into the sheath tube, and a single oscillator provided at a distal end portion of the torque wire. Is provided on the proximal end side of the torque wire,
An ultrasonic diagnostic apparatus including a drive motor that rotationally drives the torque wire, wherein rotational drive of the single oscillator and extraction of the single oscillator in the axial direction are executed. 12. The ultrasonic diagnostic apparatus according to claim 1, wherein the luminal tissue is a blood vessel of a living body.