JP4789243B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly, to a technique for displaying, for example, a tomographic image of a subject and an elastic image representing the hardness and softness of a biological tissue of the subject, for example.

  The ultrasonic diagnostic apparatus repeatedly transmits ultrasonic waves to a subject via a probe abutted on the subject at time intervals, receives time-series reflected echo signals generated from the subject, It is known as an apparatus that obtains a tomographic image, for example, a black and white B-mode image based on a reflected echo signal.

In such an ultrasonic diagnostic apparatus, the displacement of the biological tissue of the subject is measured based on a time-series reflected echo signal generated from the subject, and elasticity information such as the hardness and softness of the biological tissue is measured from the measured displacement. There has been proposed a technique for obtaining a color elastic image from the obtained elasticity information by obtaining strain, elastic modulus, and the like (for example, see Patent Document 1).
JP 2000-060853 A

  When generating elastic images by manual compression, the compression direction and the calculation direction are the same for linear probes, but for convex and radial probes, the problem is the scan direction. The compression direction and the calculation direction do not match and the accuracy is lowered.

  Therefore, the present invention uses a multi-plane technique to separate a probe having a transducer array for tomographic images and a probe having a transducer array for elastic images, thereby providing a wide range of tomographic images and high accuracy. The purpose is to display an elastic image.

  In order to solve the above-described problems, the present invention is configured as follows. An ultrasonic probe, an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves from the ultrasonic probe to a subject, and an elastic image for generating an elastic image by processing a signal detected by the ultrasonic probe In the ultrasonic diagnostic apparatus comprising: a configuration unit; a tomographic image configuration unit that processes the signal to generate a tomographic image; and a display unit that displays the elasticity image and the tomographic image. And a first ultrasonic probe for acquiring the elastic image and a second ultrasonic probe for acquiring the tomographic image. The first ultrasonic probe and the second ultrasonic probe are aligned in parallel in the longitudinal direction and the short direction.

  According to the present invention, it is possible to display a wide range of tomographic images and highly accurate elasticity images.

  A first embodiment of an ultrasonic diagnostic apparatus to which the present invention is applied will be described with reference to FIGS. FIG. 1 is a block diagram showing a configuration example of an ultrasonic diagnostic apparatus to which the present invention is applied.

  As shown in FIG. 1, the ultrasonic diagnostic apparatus 1 includes an ultrasonic probe 10 that is used in contact with a subject, and an ultrasonic wave that is spaced from the subject via the ultrasonic probe 10 at a time interval. Are repeatedly provided, a receiving unit 14 that receives a time-series reflected echo signal generated from the subject, and a phasing addition unit 16 that performs phasing addition of the received reflected echo.

  Further, based on the RF signal frame data from the phasing adder 16, a tomographic image constructing unit 18 for constructing a tomographic image of the subject, such as a black and white tomographic image, and the RF signal frame data of the phasing adder 16 from the RF signal frame data of the subject. An elasticity image constructing unit 20 is provided that measures the displacement of the living tissue and obtains elasticity data to construct a color elasticity image. An image combining unit 22 that combines the monochrome tomographic image and the color elastic image, and a display unit 24 that displays the combined image are provided.

  The ultrasonic probe 10 is formed by arranging a plurality of transducers and has a function of electronically transmitting and receiving ultrasonic waves to and from a subject via the transducers. Details of the ultrasonic probe 10 will be described later.

  The transmission unit 12 has a function of generating a transmission pulse for generating an ultrasonic wave by driving the ultrasonic probe 10 and setting a convergence point of the transmitted ultrasonic wave to a certain depth. Yes. The receiving unit 14 amplifies the reflected echo signal received by the ultrasonic probe 10 with a predetermined gain to generate an RF signal, that is, a received signal.

  The phasing addition unit 16 inputs the RF signal amplified by the reception unit 14 and performs phase control, and forms an ultrasonic beam at one point or a plurality of convergence points to generate RF signal frame data.

  The tomographic image construction unit 18 includes a signal processing unit 30 and a black and white scan converter 32. Here, the signal processing unit 30 receives the RF signal frame data from the phasing addition unit 16 and performs signal processing such as gain correction, log compression, detection, contour enhancement, and filter processing to obtain tomographic image data. is there. The monochrome scan converter 32 includes an A / D converter that converts tomographic image data from the signal processing unit 30 into a digital signal, a frame memory that stores a plurality of converted tomographic image data in time series, and a control controller. It is comprised including. The black and white scan converter 32 acquires tomographic frame data in the subject stored in the frame memory by the control controller as one image, and reads the acquired tomographic frame data in synchronization with the television.

  The elastic image construction unit 20 includes an RF signal selection unit 34, a displacement measurement unit 35, a pressure measurement unit 36, an elastic data calculation unit 37, an elastic signal processing unit 38, and a color scan converter 39. The phasing adder 16 is branched to the subsequent stage.

  The RF signal selection unit 34 includes a frame memory and a selection unit. The RF signal selection unit 34 stores a plurality of RF signal frame data from the phasing addition unit 16 in a frame memory, and selects one set, that is, two RF signal frame data from the stored RF signal frame data group by the selection unit. It is what you choose. For example, the RF signal selection unit 34 sequentially secures RF signal frame data generated from the phasing addition unit 16 based on the time series, that is, the frame rate of the image, in the frame memory, and in response to a command from the control unit 26 The currently reserved RF signal frame data (N) is selected by the selection unit as the first data, and at the same time, the RF signal frame data group (N-1, N-2, N-3... NM) to select one RF signal frame data (X). Here, N, M, and X are index numbers assigned to the RF signal frame data, and are natural numbers.

  The displacement measuring unit 35 obtains a displacement of a living tissue from a set of RF signal frame data. For example, the displacement measurement unit 35 performs one-dimensional or two-dimensional correlation processing from a set of data selected by the RF signal selection unit 34, that is, RF signal frame data (N) and RF signal frame data (X), and A one-dimensional or two-dimensional displacement distribution relating to the displacement or movement vector in the living tissue corresponding to each point of the image, that is, the direction and magnitude of the displacement is obtained. Here, a block matching method is used to detect the movement vector. The block matching method divides an image into blocks consisting of N × N pixels, for example, focuses on the block in the region of interest, searches the previous frame for the block that most closely matches the block of interest, and refers to this Then, predictive encoding, that is, processing for determining the sample value by the difference is performed.

  The pressure measurement unit 36 measures and estimates the internal pressure at the diagnosis site of the subject. For example, a pressure measuring unit having a pressure sensor is attached to the ultrasonic probe 10 used in contact with the body surface of the subject, and the head of the ultrasonic probe 10 is pressurized and depressurized. The stress distribution is given to the body of the diagnosis site of the subject. At this time, in an arbitrary time phase, the pressure sensor measures and holds the pressure applied to the body surface by the probe head.

  The elasticity data calculation unit 37 calculates the strain and elastic modulus of the living tissue corresponding to each point on the tomographic image from the measurement value from the displacement measurement unit 35, for example, the pressure value from the pressure measurement unit 36, An elastic image signal, that is, elastic frame data is generated based on strain and elastic modulus.

  At this time, the strain data is calculated by spatially differentiating the movement amount of the living tissue, for example, the displacement. The elastic modulus data is calculated by dividing the change in pressure by the change in moving amount. For example, if the displacement measured by the displacement measuring unit 35 is ΔL and the pressure measured by the pressure measuring unit 36 is ΔP, the strain (S) can be calculated by spatially differentiating ΔL, so S = It is obtained using the equation ΔL / ΔX. Further, the Young's modulus Ym of the elastic modulus data is calculated by the equation Ym = (ΔP) / (ΔL / L). Since the Young's modulus Ym determines the elastic modulus of the living tissue corresponding to each point of the tomographic image, two-dimensional elastic image data can be obtained continuously. The Young's modulus is a ratio of a simple tensile stress applied to the object and a strain generated in parallel with the tension.

  The elasticity data processing unit 38 is configured to include a frame memory and an image processing unit. The elasticity data processing unit 38 secures the elasticity frame data output in time series from the elasticity data calculation unit 37 in the frame memory, and stores the secured frame data. Image processing is performed by the image processing unit in response to a command from the control unit 26.

  The color scan converter 39 has a function of adding hue information to the elastic frame data from the elastic data processing unit 38. That is, the light is converted into the three primary colors of light, that is, red (R), green (G), and blue (B) based on the elastic frame data. For example, elastic data having a large strain is converted into a red code, and simultaneously elastic data having a small strain is converted into a blue code.

  The image composition unit 22 according to the present invention includes a frame memory, an image processing unit, and an image selection unit. Here, the frame memory stores tomographic image data from the monochrome scan converter 32 and elastic image data from the color scan converter 39. The image processing unit adds and combines the tomographic image data and elasticity image data secured in the frame memory at a set ratio in accordance with a command from the control unit 26. The luminance information and hue information of each pixel of the composite image is obtained by adding each information of the black and white tomographic image and the color elastic image at a set ratio. Further, the image selection unit selects an image to be displayed on the image display unit 24 from the tomographic image data and elasticity image data in the frame memory and the composite image data of the image processing unit in accordance with a command from the control unit 26. is there.

  The operation of the ultrasonic diagnostic apparatus 1 configured as described above will be described. The ultrasonic diagnostic apparatus 1 repeatedly transmits ultrasonic waves by the transmission unit 12 at time intervals to the subject via the ultrasonic probe 10 brought into contact with the subject, and generates a time series generated from the subject. The reflected echo signal is received by the receiver 14 and phased and added to generate RF signal frame data. Based on the RF signal frame data, the tomographic image construction unit 18 obtains a tomographic image, for example, a black and white B-mode image. At this time, when the ultrasonic beam is scanned in a certain direction, one tomographic image is obtained. On the other hand, a color elastic image is obtained by the elastic image construction unit 20 based on the RF signal frame data phased and added by the phase adjusting and adding unit 16. Then, the obtained black and white tomographic image and the color elasticity image are added by the image composition unit 22 to create a composite image.

  Here, a first embodiment of the present invention will be described. FIG. 2 shows a specific form of the ultrasonic probe 10. As shown in FIG. 2 (a), the ultrasound probe 10 is configured by independently including a probe having a transducer array for tomographic images and a probe having a transducer array for elastic images. Yes. Specifically, the ultrasonic probe 10 is provided with a linear probe 40 and a convex probe 41 in parallel. The linear probe 40 is for obtaining an elastic image, and the convex probe 41 is for obtaining a tomographic image. As shown in FIG. 2 (b), the reception signal received by the linear probe 40 is output to the elastic image construction unit 20, and an elastic image is constructed. Further, the received signal received by the convex probe 41 is output to the tomographic image construction unit 18 to construct a tomographic image.

  The linear probe 40 and the convex probe 41 include an ultrasonic transducer, an acoustic lens that converges an ultrasonic beam on the subject side of the ultrasonic transducer, an ultrasonic transducer, and a subject. An acoustic matching layer that matches the acoustic impedance of the ultrasonic transducer is disposed, and a backing material that absorbs the propagation of ultrasonic waves is provided on the back side of the ultrasonic transducer. In addition, the linear probe 40 and the convex probe 41 have the same longitudinal direction and the short direction, and the ultrasonic transducers are arranged in the same direction. Images with the same cross section can be obtained.

  The apex of the convex probe 41 is connected to the upper end surface of the linear probe 40 horizontally without any step. That is, when the ultrasonic probe 10 is in contact with the subject, the upper end surface of the linear probe 40 and the apex of the convex probe 41 come into contact with the subject.

  Since the linear type probe 40 is a quadrangle and the convex type probe 41 is a fan shape, if the linear type probe 40 and the convex type probe 41 are arranged in parallel, the apex of the convex type probe 41 A gap is formed between the other surface and the upper end surface of the linear probe 40. Therefore, a front surface of the convex probe 41 is provided with a rubber-like case 42 filled with ultrasonic jelly (not shown) so as to fill the gap. In this way, by interposing an ultrasonic jelly between the convex probe 41 and the body surface of the subject, air that becomes an obstacle to propagation of ultrasonic waves from the convex probe 41 into the subject Prevent the intervention.

  The linear type probe 40 and the convex type probe 41 may be arranged in parallel, but the convex type probe 41 for acquiring a tomographic image for observing the same part is predetermined on the linear type probe 40 side. You may tilt only this angle. As a specific example, a side view of the ultrasonic probe 10 is shown in FIG. FIG. 3 (a) shows the form of the ultrasonic probe 10. FIG.

  Since the linear probe 40 is a probe for obtaining an elastic image, it is required to push it perpendicularly to the surface of the subject. Therefore, the linear probe 40 is arranged so that ultrasonic waves are transmitted and received in the same direction as the compression direction. Then, the convex probe 41 is arranged to be inclined toward the linear probe 40. That is, they are arranged so that the ultrasonic scanning surface of the linear probe 40 and the ultrasonic scanning surface of the convex probe 41 intersect. Although not shown, an ultrasonic jelly is interposed between the convex probe 41 and the body surface of the subject.

  FIG. 3 (b) shows a focus diagram by each probe. A broken line 50 is a line indicating the scanning surface of the linear probe 40, and a broken line 51 is a line indicating the scanning surface of the convex probe 41. The broken line 50 is in contact with the end face of the linear probe 40, and the broken line 51 passes through the short center of the convex probe 41.

Here, the point A is the transmission focus position of the linear probe 40 and the convex probe 41. The transmission focus positions of the linear probe 40 and the convex probe 41 are adjusted to point A, respectively. For example, if the depth of focus of the linear probe 40 is 3 cm, the length of the broken line 50 is 3 cm. The length and angle θ of the solid line 52 are uniquely determined by the size of the convex probe 41 and its angle. Here, for example, the length of the solid line 52 is 1 cm. If the lengths of the broken line 50 and the solid line 52 are obtained, the focus position of the convex probe 41 can be obtained from the three-square theorem. The length of the broken line 51 here is √10 cm. Here, when the elastic image construction unit 20 sets the focus position of the elastic image as 3 cm, the tomographic image construction unit 18 sets the focus position of the tomographic image as √10 cm.
Further, the angle θ of the convex probe 41 may be adjusted according to the focus position. If the focus position is deep, the angle θ is made obtuse, and if the focus position is shallow, the angle θ is made acute.

  Fig. 4 shows the scanning image of each probe. Fig. 4 (a) shows the scanning image (long axis) by the convex probe 41 and the scanning image (long axis) by the linear probe 40, and Fig. 4 (b) shows the scanning range by each probe. It is a scanning image figure when these are overlapped.

  As shown in FIG. 4 (a), the scanning range of the linear probe 40 is the scanning range 60, which scans in the 7.5 MHz band. Then, an elastic image is created from a plurality of RF signal frame data scanned in the scanning range 60. The scanning range of the convex probe 41 is a scanning range 61, which scans in the 3Mhz band. Then, a tomographic image is created from the RF signal frame data scanned in the scanning range 61.

  As shown in FIG. 4B, the scanning range 61 is included in the scanning range 61 when the respective scanning ranges are overlapped. The focus position (depth) of the linear scanning range 60 is, for example, 3 cm, and scanning is performed with a focus position (depth) of √10 cm in the convex scanning range 61 so that the focus of the convex probe 41 corresponds to that position.

  In the arrangement of the two probes as shown in FIG. 3, the tomographic image and the elasticity image are obtained from different cross sections. Therefore, in the vicinity of the position where the focus positions of the two probes are matched, the two images can be compared and observed, but there is a problem that the contrast observation cannot be performed at other positions.

  An embodiment for solving this problem is shown in FIG. In FIG. 5, the linear probe 40 and the convex probe 41 each have an array transducer divided in the short axis direction, and a circuit for focusing in the short axis direction is added to the phasing adder 16. By doing so, each probe is focus-controlled in the short axis direction, so that an ultrasonic beam can be formed on the same line.

Further, as shown in FIG. 5, the linear probe 40 and the convex probe 41 are arranged in parallel, but the ultrasonic scanning of each of the linear probe 40 and the convex probe 41 is performed. The amount of delay in focus is set so that the two have the same focus. This focus 62-67 shows a scanning image (short axis).
This focus is moved in the vertical direction on the vertical line at the midpoint between the linear probe 40 and the convex probe 41, and the respective focus is set. This vertical line is the same direction as the compression direction.

  The ultrasonic transmission / reception with the probe shown in FIG. 5 is performed by, for example, first setting the transmission focus point of the linear probe 40 to C and transmitting the ultrasonic wave into the subject. Move the focus point as shown in B and perform dynamic focus reception. When the acquisition of tomographic images by the linear probe 40 is completed, next, the transmission focus point of the convex probe 41 is set to C and ultrasonic waves are transmitted into the subject. At the time of reception, D → C → Move the focus point as shown in B and perform dynamic focus reception. By such a method, tomographic image data and elasticity image data are obtained from the same cross section.

  Next, a method for superimposing the elastic image and the tomographic image is shown in FIG. A plurality of scanning lines and enlarged views 72 and 73 of four-point interpolation in the scanning lines are shown.

As shown in FIG. 6, one address in the scanning range 70 of the linear probe 40 is interpolated at four surrounding points. Specifically, the color scan converter 39 uses the spatial interpolation coefficients e to h that indicate the weighting of the image data of the surrounding four points E, F, G, and H as the pixel data at the address QL (target coordinate position). Is calculated by the following equation (1).
QL = e ・ E + f ・ F + g ・ G + h ・ H (1)
The spatial interpolation coefficient is set to a smaller value as the distance from the address QL is larger, and the weight is reduced. With this method, interpolation is performed for all addresses in the scanning range 70.

One address in the scanning range 71 of the convex probe 41 is also interpolated at four surrounding points. Specifically, the monochrome scan converter 32 uses the spatial interpolation coefficients a to d indicating the weighting of the image data of the surrounding four points A, B, C, and D for the pixel data of the address PC (attention coordinate position). Calculation is performed according to equation (2) described below.
PC = a · A + b · B + c · C + d · D (2)
The spatial interpolation coefficient is set to a smaller value as the distance from the address PC is larger, and the weighting is reduced. The address PC is a coordinate (depth R, angle θ) obtained by orthogonal coordinate system-polar coordinate system conversion. By this method, interpolation is performed for all addresses in the scanning range 71.

The image synthesis unit 22 synthesizes an image from the tomographic image data from the monochrome scan converter 32 and the elastic image data from the color scan converter 39. At this time, the synthesized image 75 is synthesized so that the display addresses coincide with each other.
A display form of the synthesized image is shown in FIG. The linear elastic image 80 is included in the convex tomographic image 81 and synthesized. As described above, the ultrasonic wave is transmitted / received in parallel to the compression direction of the linear probe 40, whereby an elastic image 80 with high accuracy can be obtained. The convex probe 41 can obtain a wide range of convex tomographic images 81 so as to correspond to the scanning range of the linear probe 40.

  Here, FIG. 8 shows an operation sequence for creating this composite image. After the convex scanning for the tomographic image is performed by the convex probe 41, the linear scanning for the elastic image is performed by the linear probe 41. Then, convex scanning for tomographic images is performed again, and linear scanning for elastic images is performed. A tomographic image is created by one convex scan, and an elastic image is created by two linear scans for the elastic image.

  The frame signal is generated after two linear scans have been confirmed. Each time the linear scan by the linear probe 40 and the subsequent convex scan by the convex probe 41 are completed once. Is output from the control unit 26 and is added to the RF frame data as indicating the acquisition order.

  For example, when the frame signal “1” is generated, the tomographic image obtained by the first scanning by the convex probe 41 is displayed on the image display unit 24. At the same time, the tomographic image obtained by the first scanning by the linear probe 40 is taken into the elastic image construction unit 20. Next, when the frame signal “2” is emitted, the tomographic image obtained by the second scanning by the convex probe 41 is displayed on the image display unit 24 and the second time of the linear probe 40. The tomographic image obtained by the above scanning is taken into the elastic image construction unit 20. Then, an elastic image is calculated from the information obtained by the first and second scans of the linear probe 40 in the elastic image construction unit 24, and obtained by the second scan of the convex probe 41. The tomographic image and the elasticity image are combined by the image combining unit 22, and the combined image is displayed on the image display unit 24.

  Next, a second embodiment is shown in FIGS. The probe shown in FIG. 9A is a transrectal or transesophageal probe, and a radial probe 90 and a linear probe 91 are arranged in parallel. The radial type probe 90 and the linear type probe 91 have the same longitudinal direction and the short direction, and the ultrasonic transducers are arranged in the same direction. Obtainable.

  In the radial probe 90, a plurality of transducer elements are arranged in parallel in the central axis direction of the insertion portion to form a transducer group, and the transducer group is arranged around the central axis of the insertion portion, that is, around the central axis. Arranged at 360 degrees as the center. A tomographic image is acquired by the radial probe 90, and an elastic image is acquired by the linear probe 91.

  A protrusion 92 is provided in the same direction as the linear probe 91. When pressing in the direction having the projection 92, the linear probe 91 is pushed perpendicularly to the subject surface. Therefore, a highly accurate elastic image can be obtained with the linear probe 91.

  A rubber-like case 94 is installed so as to cover the radial probe 90 and the linear probe 91. A saline solution or an ultrasonic jelly is inserted between the case 94 and the probe, and the gap formed between the radial probe 90 and the linear probe 91 is filled and closely attached to the subject. It has a configuration like this.

  The probe shown in FIG. 9 (b) is a transrectal probe, and is different from the configuration of FIG. 9 (a) in that a convex probe 93 and a linear probe 91 are arranged in parallel. It is the point which is arranged. The convex probe 93 and the linear probe 91 have the same longitudinal direction and the short direction, and the ultrasonic transducers are arranged in the same direction. Obtainable.

  The probe shown in FIG. 10 is a transrectal or transesophageal probe. The difference from the configuration shown in FIG. 9 is that the compression direction is detected and the linear probe is detected according to the detected compression direction. It is a point to move 91. In the probe shown in FIG. 10 (a), a radial probe 90 and a linear probe 91 are arranged in parallel. The radial type probe 90 and the linear type probe 91 have the same longitudinal direction and the short direction, and the ultrasonic transducers are arranged in the same direction. Obtainable. A plurality of pressure sensors 95 are provided around 360 degrees around the radial probe 90. Then, the compression information 96 by the plurality of pressure sensors 95 is sent to the pressure measuring unit 36, and the linear probe 91 rotates and moves to the position of the pressure sensor 95 at which the largest pressure is detected. The linear probe 91 includes a rotating mechanism that rotates around the central axis of the ultrasonic probe 10 and a rotating unit that includes the linear probe 91. These rotation mechanisms are provided in the ultrasonic probe 1, and the linear probe 91 rotates about 120 degrees. FIG. 10B shows the position of the linear probe 91 after the rotational movement. Therefore, since the compression direction and the position of the linear probe 91 can be matched, an elastic image with high accuracy can be obtained.

  Although the ultrasonic probe 10 is schematically represented in FIG. 10, FIG. 11 shows a cross-sectional view having a cross section of the linear probe 91 of the ultrasonic probe 10. The ultrasonic probe 10 includes a rotating mechanism 102 and a rotating unit 101 having a linear probe 91. A shaft that supports rotation is provided at the center of the rotation mechanism 102 and the rotation unit 101, and rotates about this shaft. Further, gears are provided on the outer sides of the rotation mechanism 102 and the rotation unit 101, respectively, and the rotation unit 101 rotates by the amount of rotation of the rotation mechanism 102. A linear probe 91 is embedded in the rotating unit 101. This is because the rotating unit 101 is smoothly rotated even when the linear probe 91 touches the subject.

  Based on the compression information 96, the rotation mechanism 102 is rotated so that the position of the pressure sensor at which the pressure is detected most greatly is transmitted, the power is transmitted to the rotation unit 101, and the rotation unit 101 is rotated.

  Next, a third embodiment is shown in FIG. The difference from the first embodiment is that the linear probe 40 and the convex probe 41 are arranged independently of each other. It includes a source as a magnetic field generator attached to a bed and the like, and a magnetic sensor as a magnetic signal detection means attached to each of the linear probe 40 and the convex probe 41, and is output from the magnetic sensor. Based on the detection signal, the three-dimensional position and inclination (twist) of the probe (hereinafter referred to as position data) are calculated. Position information is displayed on the image display unit 24 so that the respective cross sections are aligned from the three-dimensional positions detected by the magnetic sensors of the linear probe 40 and the convex probe 41.

  Here, this position information will be described. For example, the short direction of the probe is the X coordinate, and the long direction (the transducer arrangement direction) is the Y coordinate. The direction perpendicular to the short direction and the long direction is taken as the Z coordinate. If the Z coordinates coincide, the linear probe 40 and the convex probe 41 are arranged in the same cross section. Then, according to the scanning range and inclination angle of the linear probe 40 and the convex probe 41, it is determined whether or not the respective cross sections match each other. If they do not match, the linear probe is determined. An arrow for guiding the child 40 or the convex probe 41 is displayed. Based on this position information, a tomographic image displayed as a convex image and an elastic image displayed as a linear image can be displayed with the scanning cross section aligned.

In the above description, the pressure sensor 95 is provided. However, a cMUT element may be arranged as a transducer of a radial probe or a convex probe, and the pressure may be measured by the cMUT element.
Further, the probe for acquiring a tomographic image may be a linear probe, or two linear probes may be arranged in parallel.
Further, the number of convex probes may be two or more. For example, two convex probes may be arranged so as to sandwich the linear probe.

The figure which shows the whole block diagram of this invention. The figure which shows the form of the probe of this invention. The figure which shows the side view of the probe of this invention. The figure which shows the scanning image (long-axis direction) of this invention. The figure which shows the scanning image (short-axis direction) of this invention. The figure explaining the four-point interpolation of this invention. The figure which shows the display form of this invention. The figure which shows the operation | movement sequence of this invention. The figure which shows the 2nd Embodiment of this invention. The figure which shows the 2nd Embodiment of this invention. The figure which shows the internal structure of the 2nd Embodiment of this invention. The figure which shows the 3rd Embodiment of this invention.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus, 10 Probe, 12 Transmission part, 14 Reception part, 16 Phased addition part, 18 Tomographic image structure part, 20 Elastic image structure part, 22 Image composition part, 24 Display part, 40 Linear type probe Tensile, 41 Convex probe, 60 Linear scan range, 61 Convex scan range, 90 Radial probe

Claims (1)

An ultrasonic probe, an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves from the ultrasonic probe to a subject, and an elastic image for generating an elastic image by processing a signal detected by the ultrasonic probe In the ultrasonic diagnostic apparatus comprising: a configuration unit; a tomographic image configuration unit that processes the signal to generate a tomographic image; and a display unit that displays the elasticity image and the tomographic image. The first ultrasonic probe for acquiring the elastic image and the second ultrasonic probe for acquiring the tomographic image , wherein the first ultrasonic probe and the The ultrasonic diagnostic apparatus characterized in that the second ultrasonic probe has a longitudinal direction and a short direction that are aligned with each other and are arranged in parallel .

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