JP4901273B2 - Ultrasonic diagnostic apparatus and image processing program thereof - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus and an image processing program thereof, and more particularly to an ultrasonic diagnostic apparatus and an image processing program thereof capable of improving the operability of the ultrasonic diagnostic apparatus.

  In the diagnosis using the ultrasonic diagnostic apparatus, the heart beat or heartbeat can be easily detected by simply applying an ultrasonic probe provided on the ultrasonic diagnostic apparatus to the body surface of a patient (hereinafter referred to as “subject”). The state of fetal movement can be displayed in real time, and unlike X-rays, there is no exposure and the safety is high. Therefore, repeated examinations can be performed. In addition, since the ultrasonic diagnostic apparatus has a smaller scale of the apparatus and its system than other medical image diagnostic apparatuses such as an X-ray diagnostic apparatus, an X-ray CT apparatus, and a magnetic resonance imaging apparatus, doctors and technicians (hereinafter, The “operator”) can easily examine the subject by moving the ultrasonic diagnostic apparatus itself to the bedside of the ward.

  Furthermore, in recent years, ultrasonic diagnostic apparatuses that are smaller and portable have been developed, and can be used for various applications such as medical care for obstetrics and gynecology and home medical care.

  By the way, at present, the medical society has been challenged to improve the evaluation method of myocardial ischemia in the clinical diagnosis of the heart. As one of the evaluation methods of myocardial ischemia, a color Doppler method in an ultrasonic diagnostic apparatus has been conventionally used. And a method of diagnosing an ischemic site by contrast imaging using a contrast agent or the like.

  In recent years, an ultrasonic diagnostic apparatus capable of reconstructing and displaying a three-dimensional image by scanning an ultrasonic beam in a three-dimensional region (for example, a three-dimensional contrast image, a power Doppler image, and a thickness of a myocardium). Has been proposed, and can be used for evaluation of myocardial ischemia and clinical diagnosis of various sites. ing.

  In an ultrasonic diagnostic apparatus capable of reconstructing and displaying a three-dimensional image, various three-dimensional image display methods (based on three-dimensional volume data acquired by scanning an ultrasonic beam in a three-dimensional region ( For example, a three-dimensional image is displayed by the MIP method (maximum intensity projection), the volume rendering method, or the like.

  However, 3D image display methods such as the MIP (maximum intensity projection) method and the volume rendering method are methods for projecting 3D volume data in 2D. When it is desired to view only a specific tomographic image, if a 3D image is displayed by such a 3D image display method, it becomes difficult for the operator to see a desired part of the subject, and conversely, diagnosis is difficult. turn into.

  Therefore, for example, a method for displaying a two-dimensional tomographic image at an arbitrary position from the acquired volume data has been proposed, such as an MPR (multi-planar reconstruction) display method (see, for example, Patent Document 1). .

  According to the method proposed in Patent Document 1, a two-dimensional tomographic image at an arbitrary position and a two-dimensional tomographic image in a vertical direction can be displayed simultaneously with the two-dimensional tomographic image at an arbitrary position. it can. As a result, the operator can diagnose the subject while considering the spatial positional relationship of the displayed tomographic images.

In addition, a method has been proposed in which arithmetic processing is performed on volume data in the vertical direction with respect to a two-dimensional tomographic image at an arbitrary position, and the tomographic image after the arithmetic processing is displayed.
US Pat. No. 5,546,807

  In the two-dimensional tomographic image display method proposed in Patent Document 1, when an operator tries to make a diagnosis without omission using a two-dimensional tomographic image at a predetermined position, the operator repeatedly performs the same display operation. By repeating the above, it is necessary to display a plurality of two-dimensional tomographic images at different positions to diagnose the subject. For this reason, a series of operations (such as display operation) for diagnosing the subject takes a lot of time, and there is a problem that it is troublesome for the operator.

  In view of this, there may be a method in which a two-dimensional tomographic image at various positions is stored once, and then the operator diagnoses the subject by sequentially displaying the stored two-dimensional tomographic images at various positions. However, as the number of stored images increases, the number of tomographic images that the operator has to check also increases, and eventually, a series of work time for diagnosis cannot be reduced so much, It was annoying for the operator.

  Further, a method of diagnosing a subject by once storing two-dimensional tomographic images at various positions and then simultaneously displaying a plurality of stored two-dimensional tomographic images at various positions can be considered. However, in this case, the operator can view a plurality of tomographic images at the same time, but the number of tomographic images that the operator has to check is still enormous, and a plurality of tomographic images are displayed at the same time. Each tomographic image becomes smaller, making it difficult for the operator to see each tomographic image itself.

  Furthermore, each of the two-dimensional tomographic images at a predetermined position based on the volume data is subjected to arithmetic processing in the vertical direction, and the tomographic image obtained as a result of the arithmetic processing is displayed. In order to increase the amount of information included in one tomographic image, a method of performing a calculation process over a wide range is conceivable. However, if a calculation process is performed over a wide range, the operator can search for other parts other than the desired part to be used for diagnosis. Extra information is also included, and a suitable tomographic image for diagnosis cannot be obtained.

  The present invention has been made in view of such a situation, and an ultrasonic diagnostic apparatus capable of improving the operability of the ultrasonic diagnostic apparatus when displaying a two-dimensional tomographic image at an arbitrary position, and An object is to provide the image processing program.

In order to solve the above-described problem, the ultrasonic diagnostic apparatus of the present invention transmits an ultrasonic wave by vibrating a plurality of ultrasonic transducers, and is converted from a reflected wave reflected from a subject by the ultrasonic transducer. Volume data generation means for generating volume data based on the received signal, and a plurality of first image data that is two-dimensional tomographic image data at a predetermined position based on the volume data. Based on one image data generating means and volume data , a maximum value holding operation, an addition average, and a minimum value holding calculation are performed on a plurality of calculation areas having thicknesses in a direction perpendicular to the cross sections of the plurality of first image data. at least one applied one calculation, a second image data generating means for generating a plurality of second image data, based on the volume data, a plurality of second image de among A third image data generating means for generating third image data having different display direction the display direction of the motor, and a plurality of second image based on the plurality of second image data, the third image data a third image display control means Ru is displayed on the display device based, on the third image, the required together to display an icon corresponding to a plurality of operation areas, using an icon, among the plurality of operation areas And a thickness adjusting means for adjusting the thickness of the calculation area .

The second image data generation means can perform calculation on a plurality of calculation areas at predetermined intervals based on the volume data to generate a plurality of second image data.

The plurality of calculation areas can be substantially parallel to each other.

The second image data generating means is configured to obtain a low luminance area having a luminance value smaller than a predetermined lower limit reference value or a high luminance value having a luminance value larger than a predetermined upper limit reference value from each calculation area of the plurality of calculation areas. The second image data can be generated by performing an operation on the partial region excluding the luminance region.

The ultrasonic diagnostic apparatus includes a reference value data acquisition means for acquiring data relating to at least one of the Tokoro lower reference value and a predetermined upper limit reference value of the constant, the reference values predetermined lower limit reference value which is acquired by the data acquisition means given on the basis of the data relating to at least one of the upper reference value, the reference value setting means for setting at least one of a predetermined lower limit reference value and a predetermined upper limit reference value, further comprising a second image data generating means, The second image data can be generated by performing an operation on the partial area based on at least one of the predetermined lower limit reference value and the predetermined upper limit reference value set by the reference value setting means.

Second image data generating means, when generating the second image data with respect to the cardiac area of the subject to extract endocardial, performing an operation in partial areas excluding the cardiac cavity region from the computation region, The second image data can be generated.

Display control means may further be so that is displayed by superimposing the luminance information on a given straight line in the tomographic image based on the first image data, the tomographic image based on the first image data.

The ultrasonic diagnostic apparatus includes a calculation condition data acquisition means for acquiring data about operational conditions in the decorated with Ru arithmetic when the second image data is generated by the second image data generating means, calculation condition data acquisition based on the data relating to the obtained operation conditions by means, and calculating condition setting means for setting an operation condition, further comprising a second image data generating means in accordance with the set operation condition by calculating condition setting means, arithmetic An operation can be performed on the region to generate second image data.

The data regarding the operational conditions in the decorated with Ru arithmetic when the second image data is generated by the second image data generating means, at least, data relating to a predetermined distance where the second image data is generated, and , it can be made to contain data related to a predetermined thickness perpendicular to the cross section of the first image data computation is performed when the second image data is generated.

Calculation condition data acquisition means, at least one or more, on the tomographic image of the cross section perpendicular to the center of the operation area in passing Ri calculation region may be configured to obtain data relating to operation conditions. The display control means displays a tomographic image based on the third image data on the display device, displays a marker on the tomographic image, and uses the marker to change the position of the second image. Can be further provided.

Display control means may further be so that is displayed superimposed by changing the cross-sectional layer image, and a second field image tone.

Third image data generating means may be adapted first as third image data to generate data of a vertical cross section of a tomographic image the center of the operation area in passing Ri calculation region.

The ultrasonic diagnostic apparatus may be so used in the contrast medium bubbles under the conditions of administration. In this case, the second image data generation means can perform a maximum value holding calculation on a plurality of calculation areas when capturing a contrast image, and generate a plurality of second image data. The first and third image generation means generate the first and third image data so that the display directions are orthogonal to each other, and the display directions are orthogonal to the first and third image data, respectively. And a display control means for displaying the fourth image based on the fourth image data side by side with the second and third images, The thickness adjusting means can display icons corresponding to a plurality of calculation areas on the fourth image in addition to the third image.

In order to solve the above-described problem, the image processing program of the ultrasonic diagnostic apparatus of the present invention transmits ultrasonic waves by vibrating a plurality of ultrasonic transducers, and generates ultrasonic vibrations from reflected waves reflected from the subject. A volume data generation step for generating volume data based on the received signal converted by the child; and first image data that is two-dimensional tomographic image data at a predetermined position based on the volume data at a plurality of positions. A plurality of first image data generation steps to generate, and based on the volume data , a maximum value holding operation, an arithmetic mean, and a plurality of operation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data ; subjected to minimum value holding at least one of operations of the operation, a second image data generation step of generating a plurality of second image data, volume data Based on the third image data generation step of generating a third image data of different display direction the display direction of the plurality of second image data, a plurality based on the plurality of second image data second image and the third third display step Ru is displayed on the display device an image based on the image data, on the third image, with displays icons corresponding to a plurality of operation areas, using an icon And a thickness adjusting step for adjusting a thickness of a required calculation area among the plurality of calculation areas .

In order to solve the above-described problem, the ultrasonic diagnostic apparatus of the present invention transmits an ultrasonic wave by vibrating a plurality of ultrasonic transducers, and is converted from a reflected wave reflected from a subject by the ultrasonic transducer. Volume data generation means for generating volume data based on the received signal, and a plurality of first image data that is two-dimensional tomographic image data at a predetermined position based on the volume data. Based on one image data generating means and volume data , a maximum value holding operation, an addition average, and a minimum value holding calculation are performed on a plurality of calculation areas having thicknesses in a direction perpendicular to the cross sections of the plurality of first image data. at least one applied one calculation, a second image data generating means for generating a plurality of second image data, based on the volume data, a plurality of second image de among A third image data generating means for generating third image data having different display direction the display direction of the data, the tomographic image based on the first image data, a second image based on the second image data of a superimposed image, a third image display control means Ru is displayed on the display device based on the third image data, on the third image, with displays icons corresponding to a plurality of operation areas, icons And a thickness adjusting means for adjusting the thickness of a required calculation area among the plurality of calculation areas .

In order to solve the above-described problem, the image processing program of the ultrasonic diagnostic apparatus of the present invention transmits ultrasonic waves by vibrating a plurality of ultrasonic transducers, and generates ultrasonic vibrations from reflected waves reflected from the subject. A volume data generation step for generating volume data based on the received signal converted by the child; and first image data that is two-dimensional tomographic image data at a predetermined position based on the volume data at a plurality of positions. A plurality of first image data generation steps to generate, and based on the volume data , a maximum value holding operation, an arithmetic mean, and a plurality of operation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data ; subjected to minimum value holding at least one of operations of the operation, a second image data generation step of generating a plurality of second image data, volume data Based on the third image data generation step of generating a third image data of different display direction the display direction of the plurality of second image data, the tomographic image based on the first image data, second and superimposed image of the second image based on the image data of a third display step of the Ru is displayed on the display device an image based on the third image data, on the third image, the plurality of operation areas In addition to displaying a corresponding icon, the computer is caused to execute a thickness adjustment step of adjusting a thickness of a required calculation area among a plurality of calculation areas using the icon .

In the ultrasonic diagnostic apparatus of the present invention, ultrasonic data is transmitted by vibrating a plurality of ultrasonic transducers, and volume data is based on a reception signal converted from a reflected wave reflected from a subject by the ultrasonic transducer. Are generated , a plurality of first image data, which is two-dimensional tomographic image data at a predetermined position, is generated at a plurality of positions based on the volume data, and a plurality of first image data are generated based on the volume data. At least one of the maximum value holding calculation, the addition average, and the minimum value holding calculation is performed on a plurality of calculation areas having a thickness in the vertical direction with respect to the cross section of the image to generate a plurality of second image data multiple is based on the volume data, the third image data having different display direction the display direction of the plurality of second image data is generated, based on the plurality of second image data A second image, a third image based on the third image data is displayed on the display device, on the third image, with icons corresponding to a plurality of operation areas is displayed, the icon is used Thus, the thickness of a required calculation area among the plurality of calculation areas is adjusted .

In the image processing program of the ultrasonic diagnostic apparatus of the present invention, ultrasonic waves are transmitted by vibrating a plurality of ultrasonic transducers, and the received signals converted from the reflected waves reflected from the subject are converted by the ultrasonic transducers. based volume data is generated, based on the volume data, the first image data is a two-dimensional tomographic image data of a predetermined position, a plurality of generated at a plurality of positions, based on the volume data, a plurality of second the maximum value holding operation to a plurality of operation areas having a thickness in a direction perpendicular to the cross section of the first image data, averaging, and at least any one of the operation of the minimum value holding operation is performed, a plurality second image data is generated, based on the volume data, and the display direction of the plurality of second image data is generated third image data of different display direction, a plurality of second field A plurality of second image based on the data and the third image based on the third image data is displayed on the display device, on the third image, with icons corresponding to a plurality of operation areas are displayed, An icon is used to adjust the thickness of a required calculation area among the plurality of calculation areas .

In the ultrasonic diagnostic apparatus of the present invention, ultrasonic data is transmitted by vibrating a plurality of ultrasonic transducers, and volume data is based on a reception signal converted from a reflected wave reflected from a subject by the ultrasonic transducer. Are generated , a plurality of first image data, which is two-dimensional tomographic image data at a predetermined position, is generated at a plurality of positions based on the volume data, and a plurality of first image data are generated based on the volume data. At least one of the maximum value holding calculation, the addition average, and the minimum value holding calculation is performed on a plurality of calculation areas having a thickness in the vertical direction with respect to the cross section of the image to generate a plurality of second image data is, based on the volume data, and the display direction of the plurality of second image data is generated third image data of different display direction, a tomographic image based on the first image data And superimposed image of the second image based on the second image data, and a third image based on the third image data is displayed on the display device, on the third image, corresponding to a plurality of operation areas An icon is displayed, and the icon is used to adjust the thickness of a required calculation area among the plurality of calculation areas .

In the image processing program of the ultrasonic diagnostic apparatus of the present invention, ultrasonic waves are transmitted by vibrating a plurality of ultrasonic transducers, and the received signals converted from the reflected waves reflected from the subject are converted by the ultrasonic transducers. based volume data is generated, based on the volume data, the first image data is a two-dimensional tomographic image data of a predetermined position, a plurality of generated at a plurality of positions, based on the volume data, a plurality of second the maximum value holding operation to a plurality of operation areas having a thickness in a direction perpendicular to the cross section of the first image data, averaging, and at least any one of the operation of the minimum value holding operation is performed, a plurality second image data is generated, based on the volume data, the third image data of different display directions are generated from the display direction of the plurality of second image data, first image data And the tomographic image based on the superimposed image of the second image based on the second image data, and a third image based on the third image data is displayed on the display device, on the third image, a plurality The icon corresponding to the calculation area is displayed, and the icon is used to adjust the thickness of the required calculation area among the plurality of calculation areas .

  According to the present invention, it is possible to improve the operability of the ultrasonic diagnostic apparatus when displaying a two-dimensional tomographic image at an arbitrary position.

  Embodiments of the present invention will be described with reference to the drawings.

  FIG. 1 shows an internal configuration of an ultrasonic diagnostic apparatus 1 to which the present invention is applied.

  The ultrasonic diagnostic apparatus 1 includes a main body 11, an ultrasonic probe 12 connected to the main body 11 via an electric cable, an input device 13, and a monitor 14.

  As shown in FIG. 1, the main body 11 of the ultrasonic diagnostic apparatus 1 includes a control processor 21, a transmission / reception unit 22, a B-mode processing unit 23, a Doppler mode processing unit 24, an image generation circuit 25, a storage unit 26, and an internal storage device. 27, an image reconstruction unit 28, an input data acquisition unit 29, a calculation condition setting unit 30, and an interface unit 31. Note that the control processor 21, the storage unit 26, the internal storage device 27, the image reconstruction unit 28, the input data acquisition unit 29, the calculation condition setting unit 30, and the interface unit 31 are buses within the main body 11 of the ultrasonic diagnostic apparatus 1. Are connected to each other.

  The control processor 21 includes a CPU (Central Processing Unit) or an MPU (Micro Processing Unit). The control processor 21 reads out a control program that executes ultrasonic transmission / reception processing, image generation / display processing, and the like stored in the internal storage device 27, and stores the read control program on the software storage unit 26 b of the storage unit 26. In addition to executing various processes, the system generates various control signals and supplies them to the respective units to control the driving of the ultrasonic diagnostic apparatus 1 as a whole.

  The transmission system circuit in the transmission / reception unit 22 includes a rate pulse generator, a transmission delay circuit, and a pulser (all not shown). The rate pulse generator is based on a control signal supplied from the control processor 21. A rate pulse that determines the pulse repetition frequency of the ultrasonic pulse incident inside the subject P is generated and supplied to the transmission delay circuit. The transmission delay circuit is a delay circuit for setting the focal position and deflection angle of the ultrasonic beam at the time of transmission, and based on the control signal supplied from the control processor 21, the focus of the ultrasonic beam at the time of transmission. A delay time is added to the rate pulse supplied from the rate pulse generator so that the position and deflection angle become a predetermined focal position and deflection angle, and the pulse is supplied to the pulser. Furthermore, the pulser is a drive circuit that generates a high-pressure pulse for driving the ultrasonic transducer, and generates a high-voltage pulse for driving the ultrasonic transducer based on the rate pulse supplied from the transmission delay circuit. Then, the generated high-pressure pulse is output to the ultrasonic probe 12.

  The transmission / reception unit 22 can instantaneously change the delay time, the transmission frequency, the transmission drive voltage, and the like added to the rate pulse in accordance with an instruction from the control processor 21. In particular, the transmission / reception unit 22 is provided with, for example, a linear amplifier type transmission circuit or a circuit that can electrically switch a plurality of power supply units so that the transmission drive voltage can be changed instantaneously.

  The reception system circuit in the transmission / reception unit 22 includes a preamplifier, an A / D converter, a reception delay circuit, an adder (all not shown), and the like, and the preamplifier enters the subject P from the ultrasonic probe 12. A reception signal based on the reflected wave of the ultrasonic pulse thus obtained is acquired, the acquired reception signal is amplified to a predetermined level, and the amplified reception signal is supplied to the A / D converter. The A / D converter converts the reception signal supplied from the preamplifier from an analog signal to a digital signal, and supplies it to the reception delay circuit.

  The reception delay circuit, based on the control signal supplied from the control processor 21, delay times (respectively required for determining the reception directivity for the A / D converted reception signal supplied from the A / D converter. A delay time corresponding to the difference in the propagation time of the ultrasonic wave from the focus position of the ultrasonic vibrator is provided and supplied to the adder. The adder adds the reception signals from the ultrasonic transducers supplied from the reception delay circuit, and supplies the added reception signals to the B mode processing unit 23 and the Doppler mode processing unit 24. Note that the reflection component from the direction corresponding to the reception directivity of the reception signal is enhanced by the addition of the adder.

  The B-mode processing unit 23 includes a logarithmic amplifier, an envelope detection circuit, and a TGC (Time Gain Control) circuit (all not shown), and the following processing is performed based on a control signal supplied from the control processor 21. I do.

  That is, the logarithmic amplifier of the B-mode processing unit 23 logarithmically amplifies the reception signal supplied from the transmission / reception unit 22 and supplies the logarithmically amplified reception signal to the envelope detection circuit. The envelope detection circuit is a circuit for removing only the ultrasonic frequency component and detecting only the amplitude. The envelope detection circuit detects the envelope of the reception signal supplied from the logarithmic amplifier and supplies the detected reception signal to the TGC circuit. To do. The TGC circuit adjusts the intensity of the reception signal supplied from the envelope detection circuit so that the final luminance of the image becomes uniform, and supplies the adjusted data to the image generation circuit 25. The adjusted data is supplied to the monitor 14 via the image generation circuit 25, and then displayed as a B-mode image in which the intensity of the received signal is represented by luminance.

  The Doppler mode processing unit 24 includes a reference signal generator, a π / 2 phase shifter, a mixer, an LPF (Low Pass Filter), a Doppler signal storage circuit, an FFT (Fast Fourier Transform) analyzer, an arithmetic unit, an MTI (Moving Target Indication Filter). ) Filter, autocorrelator, average speed calculator, dispersion calculator, power calculator (all not shown), etc., and the received signal supplied from the transmitter / receiver 22 is mainly used for quadrature detection and FFT analysis. MTI arithmetic processing or the like is performed, and the generated data is supplied to the image generation circuit 25. This data is supplied to the monitor 14 via the image generation circuit 25, and then displayed as a Doppler mode image combining an average speed image, a dispersion image, a power image, and the like.

  The image generation circuit 25 acquires the data supplied from the B mode processing unit 23 and the Doppler mode processing unit 24, and converts the acquired data from the scanning line signal sequence of the ultrasonic scan to the scanning line signal sequence of the video format. Thus, B-mode image data and Doppler mode image data are generated, and the generated B-mode image data and Doppler mode image data are supplied to the monitor 14 and the image memory 26 a of the storage unit 26.

  Further, the image generation circuit 25 acquires various image data supplied from the image memory 26 a under the control of the control processor 21, and supplies the acquired various image data to the monitor 14.

  The storage unit 26 includes an image memory 26a and a software storage unit 26b. The image memory 26a acquires B-mode image data and Doppler mode image data supplied from the image generation circuit 25, and acquires the acquired B-mode image data. Stores Doppler mode image data. Thereby, for example, after the diagnosis, the operator can read the image data stored during the diagnosis and display it on the monitor 14 via the image generation circuit 25 as a still image or a moving image.

  Further, the image memory 26 a receives raw data such as an output signal (RF signal) supplied from the transmission / reception unit 22, volume data supplied from the image reconstruction unit 28, various reconstructed image data, and the network 32. The image data acquired in this way is stored as appropriate, and supplied to each unit as necessary.

  The software storage unit 26 b stores various control programs supplied from the internal storage device 27 under the control of the control processor 21.

  The internal storage device 27 includes a control program for executing a scan sequence, image generation / display processing, difference image generation processing, luminance value holding calculation processing, superimposed display, diagnostic information (patient ID, doctor's findings, etc.), diagnostic protocol In addition, a data group regarding ultrasonic transmission / reception conditions, calculation conditions of calculation processing performed in the image reconstruction unit 28, and the like are stored. Further, the internal storage device 27 stores various image data supplied from the image memory 26a of the storage unit 26 as necessary. The internal storage device 27 can transfer various data to an external device (not shown) via the interface unit 31 as necessary.

  The image reconstruction unit 28 reads out the B-mode image data and the Doppler mode image data stored in the image memory 26a of the storage unit 26 under the control of the control processor 21, and reads the read B-mode image data and the Doppler mode image. The data is converted into volume data having a common coordinate axis, and the converted volume data is supplied to the image memory 26a. The image reconstruction unit 28 reads out the calculation condition setting data stored in the internal storage device 27, and reconstructs it using predetermined calculation processing based on the read calculation condition setting data and volume data. Is generated, and the generated two-dimensional tomographic image data at a predetermined position is supplied to the image memory 26a.

  The image reconstruction unit 28 generates predetermined three-dimensional image data by reconstructing using predetermined arithmetic processing based on the volume data, and the generated predetermined three-dimensional image data is stored in the image memory. 26a.

  The input data acquisition unit 29 acquires various data such as data related to calculation conditions input by the operator operating the input device 13 via the interface unit 31, and sets the acquired data related to the calculation conditions as calculation conditions. While supplying to the part 30, the acquired other data are suitably supplied to each part. Note that various data such as data related to calculation conditions such as an external storage device (not shown) may be acquired via the interface unit 31.

  The calculation condition setting unit 30 acquires data related to the calculation condition supplied from the input data acquisition unit 29 according to the control of the control processor 21, and the calculation performed in the image reconstruction unit 28 based on the acquired data related to the calculation condition. The calculation condition for the process is set, and calculation condition setting data that is data relating to the set calculation condition is supplied to the internal storage device 27.

  The interface unit 31 is an interface related to the input device 13, the network 32, and an external storage device (not shown), and various data supplied from each unit of the main body 11 are transferred to the external device (not shown) via the network 32. It can be supplied to an external storage device.

  The ultrasonic probe 12 is connected to the main body 11 via an electric cable, and is an ultrasonic transducer that transmits and receives ultrasonic waves by bringing the front surface of the subject P into contact with the front surface of the subject P. The ultrasonic transducers (not shown) arranged in a matrix or two-dimensionally are arranged at the tip. This ultrasonic transducer is an electroacoustic transducer as a piezoelectric transducer. A matching layer for efficiently transmitting ultrasonic waves is provided in front of the ultrasonic transducer, and a packing material for preventing ultrasonic waves from propagating backward is provided behind the ultrasonic transducer.

  The ultrasonic probe 12 converts an electric pulse incident from the transmission / reception unit 22 of the main body 11 into an ultrasonic pulse (transmission ultrasonic wave) at the time of transmission, and converts a reflected wave reflected by the subject P into an electric signal at the time of reception. And output to the main body 11. A part of the ultrasonic wave transmitted into the subject P is reflected by the boundary surface or tissue between organs in the subject P having different acoustic impedances. In addition, when the transmitted ultrasonic wave is reflected by a moving blood flow or a surface such as a heart wall, it undergoes a frequency shift due to the Doppler effect.

  The input device 13 is connected to the main body 11 via an electric cable, and a display panel (not shown) for inputting various instructions of the operator on the operation panel, a trackball 13a, various operation switches 13b, various types It has input devices such as a button 13c, a mouse 13d, and a keyboard 13e, and includes patient information, measurement parameters, physical parameters, template sizes, calculation conditions for calculation processing performed in the image reconstruction unit 28, time phases, This is used by an operator to input a lattice interval or the like.

  The monitor 14 is connected to the image generation circuit 25 of the main body 11 via a cable, and includes an LCD (Liquid Crystal Display) (not shown) or a CRT (Cathode Ray Tube) (not shown). B-mode image data, Doppler mode image data, three-dimensional image data, and the like from the image generation circuit 25 converted into a scanning line signal sequence in a video format are acquired, and an image and a Doppler mode image based on the acquired B-mode image data An image based on data, an image based on 3D image data, and the like are displayed.

  Next, the tomographic image display processing with depth information in the ultrasonic diagnostic apparatus 1 in FIG. 1 will be described with reference to the flowchart in FIG. In addition, before the tomographic image display processing with depth information is started, the contrast agent is administered to the subject P in advance by the operator.

  In step S1, the image generation circuit 25 generates a plurality of two-dimensional tomographic image data. Specifically, a plurality of two-dimensional tomographic image data is generated as follows.

  The transmission / reception unit 22 transmits an ultrasonic beam to the subject P based on the transmission control signal supplied from the control processor 21. That is, the rate pulse device of the transmission / reception unit 22 is configured so that the pulse repetition frequency of the ultrasonic pulse incident on the subject P becomes a predetermined pulse repetition frequency based on the transmission control signal supplied from the control processor 21. A rate pulse to be determined is generated and supplied to the transmission delay circuit. Further, the transmission delay circuit is based on the transmission control signal supplied from the control processor 21 so that the focal position and deflection angle of the ultrasonic beam at the time of transmission become a predetermined focal position and deflection angle (θ1). A delay time is added to the rate pulse supplied from the pulse generator, and the pulse is supplied to the pulser. Further, the pulser generates a high-pressure pulse for driving the ultrasonic transducer based on the rate pulse supplied from the transmission delay circuit, and outputs the generated high-pressure pulse to the ultrasonic probe 12. The ultrasonic probe 12 converts the high-pressure pulse (electric pulse) input from the transmission / reception unit 22 into an ultrasonic pulse, and transmits the converted ultrasonic pulse to the subject P. A part of the ultrasonic wave transmitted into the subject P is reflected at the boundary surface or tissue between organs in the subject P having different acoustic impedances.

  The ultrasonic probe 12 converts the reflected wave reflected by the subject P into an electric signal and outputs it to the main body 11. The transmission / reception unit 22 amplifies the reception signal input from the ultrasonic probe 12 based on the reception control signal supplied from the control processor 21, adds a predetermined delay time, and combines the B-mode processing unit 23 and the Doppler mode. This is supplied to the processing unit 24. That is, the preamplifier of the reception system circuit of the transmission / reception unit 22 acquires a reception signal based on the reflected wave of the ultrasonic wave incident on the subject P from the ultrasonic probe 12, and amplifies the acquired reception signal to a predetermined level. The amplified received signal is supplied to the A / D converter. The A / D converter converts the reception signal supplied from the preamplifier from an analog signal to a digital signal, and supplies it to the reception delay circuit.

  The reception delay circuit is based on the reception control signal supplied from the control processor 21 and has a delay time necessary for determining the reception directivity for the reception signal after A / D conversion supplied from the A / D converter ( (Delay time corresponding to the difference in propagation time of ultrasonic waves from the focus position of each ultrasonic transducer) is supplied to the adder. The adder adds the reception signals from the ultrasonic transducers supplied from the reception delay circuit, and supplies the added reception signals to the B mode processing unit 23 and the Doppler mode processing unit 24.

  The B mode processing unit 23 and the Doppler mode processing unit 24 perform various processes on the reception signal supplied from the transmission / reception unit 22, generate data in the θ1 direction, and supply the data to the image generation circuit 25. The image generation circuit 25 acquires θ1 direction data supplied from the B mode processing unit 23 and the Doppler mode processing unit 24, and scans the acquired θ1 direction data in a video format from a scanning line signal sequence of ultrasonic scanning. The B-mode image data and Doppler mode image data in the θ1 direction are generated by converting into a line signal sequence, and the generated B-mode image data and Doppler mode image data in the θ1 direction are supplied to the image memory 26a of the storage unit 26. .

  The image memory 26a of the storage unit 26 acquires the B-mode image data and Doppler mode image data in the θ1 direction supplied from the image generation circuit 25, and stores the acquired B-mode image data and Doppler mode image data in the θ1 direction. To do.

  Next, the ultrasonic wave transmission / reception direction is updated by [Delta] [theta] sequentially to [[theta] 1+ (N-1) [Delta] [theta]], and ultrasonic waves are transmitted / received in the same procedure as above by scanning in the N direction. Is scanned in real time. At this time, the control processor 21 switches [θ1 + Δθ to θ1 + (N−] while sequentially switching the delay times of the transmission delay circuit and the reception delay circuit of the transmission / reception unit 22 corresponding to a predetermined ultrasonic transmission / reception direction by the control signal. 1) Generate each of B-mode image data and Doppler mode image data in the Δθ] direction.

  The image memory 26a also generates the B-mode image data and Doppler mode image data in the [θ1 + Δθ to θ1 + (N−1) Δθ] directions and the B-mode image data and Doppler mode images in the θ1 direction that are already stored. Along with the data, it is stored as two-dimensional B-mode image data and Doppler mode image data of a predetermined time phase.

  In this way, one two-dimensional B-mode image data and Doppler mode image data of a predetermined time phase can be generated and stored. In the embodiment of the present invention, since a contrast agent is used, tomographic image data (B-mode image data and Doppler mode image data) is generated based on the received signal in the harmonic mode.

  Next, by performing the same operation under different spatial conditions, a tomographic image over a three-dimensional region composed of a plurality of two-dimensional tomographic image data (two-dimensional B-mode image data and Doppler mode image data). Collect data.

  Specifically, when the operator performs manual scanning using the ultrasonic probe 12 having a plurality of ultrasonic transducers arranged in a one-dimensional array, for example, tilt scanning or parallel scanning is performed manually. By performing at a speed, tomographic image data over a three-dimensional region constituted by a plurality of two-dimensional tomographic image data is collected. Of course, the scanning may be performed mechanically using the ultrasonic probe 12 having a plurality of ultrasonic transducers arrayed in a one-dimensional array.

  Alternatively, tomographic image data over a three-dimensional region may be collected by directly performing three-dimensional scanning using an ultrasonic probe 12 having a plurality of ultrasonic transducers arranged in a two-dimensional matrix. In the present invention, it is only necessary to collect tomographic image data over a three-dimensional region, and the present invention can be applied to collecting tomographic image data over three dimensions by any scanning method.

  In the embodiment of the present invention, as shown in FIG. 3, three-dimensional scanning is performed by directly scanning three-dimensionally using an ultrasonic probe 12 having a plurality of ultrasonic transducers arranged in a two-dimensional matrix. Collect tomographic image data over a region. Specifically, tomographic image data of the heart over a three-dimensional region is collected by directly scanning an ultrasonic wave three-dimensionally from the heart apex.

  A plurality of two-dimensional tomographic image data (two-dimensional B-mode image data and Doppler mode image data) collected (generated) in this manner are sequentially stored in the image memory 26 a of the storage unit 26.

  In step S <b> 2, the image reconstruction unit 28 reads and reads a plurality of two-dimensional B-mode image data and Doppler mode image data stored in the image memory 26 a of the storage unit 26 under the control of the control processor 21. The plurality of two-dimensional B-mode image data and Doppler mode image data are converted into volume data having a common coordinate axis and supplied to the image memory 26a of the storage unit 26.

  In step S <b> 3, the image reconstruction unit 28 generates tomographic image data of three orthogonal cross sections based on the converted volume data in accordance with the control of the control processor 21. That is, the image reconstruction unit 28, based on the converted volume data, the two-dimensional tomographic image data at a predetermined position designated by the operator operating the input device 13, and the predetermined position. Two two-dimensional tomographic image data orthogonal to the tomographic image based on the two-dimensional tomographic image data are generated. A method of generating a two-dimensional tomographic image at a predetermined position and two tomographic screens orthogonal to the two-dimensional tomographic image and simultaneously displaying three cross sections based on the generated three two-dimensional tomographic image data is “orthogonal. This is called “three-section display method”.

  For example, as shown in FIG. 4, when the operator designates the cross section A as a desired cross section by operating the input device 13, three orthogonal cross sections including the cross section B and the cross section C orthogonal to the cross section A Two-dimensional tomographic image data of (Section A, Section B, and Section C) is generated.

  In the orthogonal three-section display method for generating and displaying tomographic image data of three orthogonal sections based on the volume data, the subject is used as a default of the ultrasonic diagnostic apparatus 1 unless the operator operates the input device 13 in particular. Normal two-dimensional tomographic image data generated by transmitting and receiving ultrasonic waves from the ultrasonic probe 12 at a position in contact with the body surface of P, and two two-dimensional tomographic screen data orthogonal to the two-dimensional tomographic image data are generated. Is done. Of course, the operator can generate two-dimensional tomographic image data at an arbitrary position in three dimensions and two two-dimensional tomographic screen data orthogonal to the three-dimensional image by operating the input device 13. is there.

  The image reconstruction unit 28 supplies the generated two-dimensional tomographic image data of three orthogonal cross sections to the image memory 26a. The image memory 26 a supplies two-dimensional tomographic image data having three orthogonal cross sections supplied from the image reconstruction unit 28 to the monitor 14 via the image generation circuit 25.

  In step S4, the monitor 14 acquires the two-dimensional tomographic image data of the three orthogonal cross sections supplied from the image generation circuit 25, and 2 of the three orthogonal cross sections based on the acquired two-dimensional tomographic image data of the three orthogonal cross sections. A dimensional tomographic image is displayed as shown in FIG.

  FIG. 5 shows a display example of a two-dimensional tomographic image having three orthogonal cross sections displayed on the monitor 14.

  As shown in FIG. 5, tomographic images 41 to 43 are displayed on the monitor 14, and each of the tomographic images 41 to 43 is a tomographic image at a predetermined position (a tomographic image corresponding to the cross section A in FIG. 4). A tomographic image normally obtained by twisting and scanning the ultrasonic probe 12 in contact with the subject P so as to generate the tomographic image 41 (tomographic image corresponding to the cross section B in FIG. 4), tomographic image 41 and a tomographic image orthogonal to the tomographic image 42 (a tomographic image corresponding to the cross section C in FIG. 4). The tomographic image 43 is called a so-called C-mode tomographic image.

  As a result, the operator can diagnose the subject P while considering the spatial positional relationship between the three displayed tomographic images 41 to 43.

  However, in the conventional orthogonal three-section display method, the tomographic image displayed as a so-called C-mode tomographic image is only one of the tomographic images 43. For example, when the operator observes the ischemic site of the myocardium. In order to sufficiently observe a heart having a size of about 10 cm to 15 cm, a C-mode tomographic image at spatially different positions is sequentially displayed by operating the input device 13 many times. It must be observed whether there is an ischemic site.

  In addition, when an operator observes a myocardial ischemic region of the heart using the orthogonal three-section display method, even when a contrast medium is administered, the ischemic region of the myocardial region where ischemia is usually generated on a tomographic image. The gradation at is slightly darker than the gradation on the tomographic image of the myocardial region where ischemia has not occurred. Therefore, when observing the myocardial ischemic region of the heart using the orthogonal three-section display method, it is difficult for the operator to accurately determine whether or not the subject P has a myocardial ischemic region. .

  Therefore, a predetermined calculation process is performed with a predetermined thickness in the vertical direction on the C-mode tomographic image at a predetermined position, and a plurality of C-mode tomographic images to which depth information is added by this calculation process are generated at predetermined intervals. -Display. As a result, a plurality of substantially parallel C-mode tomographic images to which depth information is added (hereinafter referred to as “tomographic images with depth information”) are generated and displayed. As a result, the operator can efficiently diagnose the subject P in a short time using a plurality of tomographic images with depth information whose three-dimensional information has increased. A method for generating / displaying a plurality of tomographic images with depth information will be specifically described below.

  First, the operator operates the input device 13 to input data related to calculation conditions for calculation processing performed in the image reconstruction unit 28. Specifically, as shown in FIG. 6, the operator operates the switches 13b-2 to 13b-4 provided in the input device 13 so that each of them can perform a predetermined arithmetic process in the vertical direction. A predetermined thickness, the number of tomographic images with depth information to be displayed, and a predetermined interval at which the tomographic images with depth information are displayed can be input. In the case of the example in FIG. 6, the operator operates the input device 13 to perform a predetermined thickness in the vertical direction on which a predetermined calculation process is performed, the number of tomographic images with depth information to be displayed, and depth information. “5 mm”, “3 sheets”, and “2 cm” are respectively input as predetermined intervals at which the attached tomographic images are displayed.

  Further, the operator can start the arithmetic processing in the image reconstruction unit 28 by operating the switch 13b-1 provided in the input device 13, and the switch 13b-5 provided in the input device 13 can be operated. By operating, the calculation condition setting unit 30 can set calculation conditions.

  In general, the heart can be divided into, for example, 16 parts for convenience, but the vertical direction in which arithmetic processing is performed when observing a predetermined part of the 16 parts. If the predetermined thickness is set too large, there is a possibility that extra information of different parts may be included in the tomographic image with depth information subjected to the calculation process. Therefore, in order to prevent a region where observation is not desired from being included in the calculation region where the calculation process is performed, the range of the predetermined thickness input by the operator is about 5 mm to 30 mm, more preferably about 5 mm to 20 mm. Should.

  In step S <b> 5, the input data acquisition unit 29 receives data related to calculation conditions of calculation processing performed in the image reconstruction unit 28 input by the operator operating the input device 13 (in the vertical direction in which predetermined calculation processing is performed). Data relating to the predetermined thickness, data relating to the number of tomographic images with depth information to be displayed, and data relating to predetermined intervals at which the tomographic images with depth information are displayed), and the obtained image reconstruction unit 28 Data relating to the calculation conditions of the calculation processing performed in step S is supplied to the calculation condition setting unit 30.

  Next, the operator operates the switch 13b-5 provided in the input device 13 to cause the calculation condition setting unit 30 to set calculation conditions.

  In step S <b> 6, when the switch 13 b-5 provided in the input device 13 is operated by the operator, the calculation condition setting unit 30 follows the control of the control processor 21 and the image reconstruction unit supplied from the input data acquisition unit 29. 28, the data regarding the calculation conditions of the calculation processing performed in the image reconstruction unit 28 is acquired, and the calculation conditions of the calculation processing performed in the image reconstruction unit 28 based on the acquired data regarding the calculation conditions of the calculation processing performed in the image reconstruction unit 28 Is set, and calculation condition setting data, which is data relating to the set calculation condition, is supplied to the internal storage device 27.

  In the case of the example in FIG. 6, as calculation conditions for the calculation processing performed in the image reconstruction unit 28, a predetermined thickness in the vertical direction on which the predetermined calculation processing is performed, the number of tomographic images with depth information to be displayed, and The predetermined intervals at which the tomographic images with depth information are displayed are set to “5 mm”, “3 sheets”, and “2 cm”, respectively. In this case, the tomographic images with depth information are generated at positions of 2 cm, 4 cm, and 6 cm from the ultrasonic probe 12.

  As a result, the operator can cause the calculation condition setting unit 30 to set a desired calculation condition.

  In the embodiment of the present invention, the number of tomographic images with depth information to be displayed is set to “3”. However, the present invention is not limited to this, and the operator's favorite number is set. be able to. However, when observing the heart divided into 16 parts for convenience, the number of displayed tomographic images with depth information is 2 to 6 so that the operator can identify which part is not difficult to see. It is preferable to set the degree.

  In the case of the example of FIG. 6, “5 mm” and “2 cm” are respectively set as the predetermined thickness in the vertical direction on which the predetermined arithmetic processing is performed and the predetermined interval at which the tomographic image with depth information is displayed. However, the present invention is not limited to such a case, and can be set to an arbitrary thickness, interval and position according to the preference of the operator.

  Subsequently, the operator operates the switch 13b-1 provided in the input device 13 to cause the ultrasonic diagnostic apparatus 1 to start arithmetic processing. The control processor 21 reads out a control program such as arithmetic processing stored in the internal storage device 27, expands the read control program such as arithmetic processing on the software storage unit 26 b of the storage unit 26, and executes the processing. To do.

  In step S <b> 7, when the operator operates the switch 13 b-1 provided in the input device 13 in accordance with the control of the control processor 21, the image reconstruction unit 28 stores calculation condition setting data stored in the internal storage device 27. And volume data stored in the image memory 26a. The image reconstruction unit 28 performs a predetermined calculation process based on the read calculation condition setting data and volume data, thereby generating a plurality of tomographic image data with depth information, which is data of a tomographic image with depth information.

  Specifically, for example, as shown in FIG. 7, using a maximum value holding calculation processing method, an addition average calculation processing method, a minimum value holding calculation processing method, or a simple addition calculation processing method as a predetermined calculation processing method. Is calculated with respect to the feature amount (for example, signal intensity) of the image with the thickness set to (5 mm in the example of FIG. 6).

  When the maximum value holding calculation processing method is used, the feature amount of the largest image at the set thickness is used as the calculation result. When the addition average calculation processing method is used, a value obtained by adding and averaging the feature amounts of all the images at the set thickness is used as the calculation result. When the minimum value holding calculation processing method is used, the feature amount of the smallest image at the set thickness is used as the calculation result.

  For example, when the operator observes a myocardial ischemic region of the heart, as shown in FIGS. 8A to 8C, the shallowest portion and the deepest portion of the set thickness are compared with the surrounding portions. The feature amount of the image is only 0.1, for example (the feature amount of the image of the surrounding region is, for example, 1.0 and the feature amount of the image of the myocardial ischemia region is, for example, 0.9), but the set thickness In the middle portion, the feature amount of the image is 0.2 smaller than the surrounding portion (the feature amount of the image of the surrounding portion is 1.0, for example, and the feature amount of the image of the myocardial ischemia portion is, for example, 0.8 ), When the calculation process is performed using the minimum value holding calculation processing method, as a result, as shown in FIG. 0.8 is used as the feature amount of the blood region image.

  Further, for example, when the operator observes the myocardial ischemic region of the heart, as shown in FIGS. 9A to 9C, the shallowest portion of the set thickness is compared with the surrounding region. For example, the feature amount of the image of the surrounding part is 1.0 and the feature amount of the image of the myocardial ischemia part is 0.9, for example. The feature amount of the image in the portion is set to 0.6, for example, smaller than the surrounding (the feature amount of the image of the surrounding region is, for example, 1.0 and the feature amount of the image of the myocardial ischemic region is, for example, 0.4). In the deepest part of the thickness, the image feature amount is, for example, 0.2 smaller than the surrounding portion (the feature amount of the image of the surrounding portion is, for example, 1.0, and the feature amount of the image of the myocardial ischemia portion is (E.g., 0.8), when the addition average calculation process is performed, as a result, as shown in FIG. As the feature 1.0 is used in the region of the image, 0.7 is used as the feature amount of the image of myocardial ischemic area.

  As a result, the feature amount of the image of the myocardial ischemic site can be made relatively low compared to the surrounding site, and as a result, compared with the case where the myocardial ischemic site of the heart is observed without performing arithmetic processing. The contrast ratio between the ischemic region of the myocardium and the surrounding region can be improved within the thickness range preset by the operator.

  On the other hand, since there are many new blood vessels in the tumor, using a contrast agent, the tumor part is strongly shaded compared to other surrounding parts. For example, when the operator observes the tumor part of the heart, As shown in FIGS. 10A to 10C, in the shallowest portion of the set thickness, the feature amount of the image is, for example, 1.0 larger than the surrounding portion (the image of the surrounding portion is The feature amount is 0.5, for example, and the feature amount of the image of the tumor portion is, for example, 1.5. The feature amount of the image of the region is 0.5, for example, and the feature amount of the image of the tumor portion is, for example, 1.5). For example, 2.0 is larger (the feature amount of the image of the surrounding region is 0.5, for example, When the feature value is 2.5), for example, the maximum value holding calculation process is performed. As a result, as shown in FIG. 10D, 0.5 is used as the feature value of the image of the surrounding region, and the tumor 2.5 is used as the feature amount of the partial image.

  As a result, the feature amount of the image of the tumor part can be made relatively higher than that of the surrounding part, and as a result, the operator can preliminarily compare with the case of observing the tumor part of the heart without performing arithmetic processing. The contrast ratio between the tumor part and the surrounding part can be improved within the set thickness range.

  Note that other calculation processing methods other than the maximum value holding calculation processing method, the addition average calculation processing method, the minimum value holding calculation processing method, or the simple addition calculation processing method may be used.

  Further, when the image reconstruction unit 28 generates a plurality of tomographic image data with depth information, at the same time, the remaining two tomographic images other than the C-mode tomographic image among the three tomographic images displayed in the three orthogonal sections are displayed. Image data is read from the image memory 26a, and based on the calculation condition setting data, position information where the tomographic image data with depth information is generated is added to the two read tomographic image data.

  Specifically, in the example of FIG. 6, three pieces of tomographic image data with depth information are generated at intervals of 2 cm, so that position information is added to the 2 cm, 4 cm, and 6 cm positions from the ultrasonic probe 12. The Note that the tomographic image data to which the position information from which the tomographic image data with depth information has been added is referred to as “tomographic image data with position information”.

  The image reconstruction unit 28 supplies the generated tomographic image data with depth information and tomographic image data with position information to the image memory 26a. The image memory 26a acquires the plurality of tomographic image data with depth information and the tomographic image data with position information supplied from the image reconstruction unit 28, and the acquired plurality of tomographic image data with depth information and tomographic image with position information. Data is stored and supplied to the monitor 14 via the image generation circuit 25.

  In step S8, the monitor 14 acquires the plurality of tomographic image data with depth information and the tomographic image data with position information supplied from the image memory 26a, and the acquired plurality of tomographic image data with depth information and the tomographic image with position information. A plurality of tomographic images with depth information and tomographic images with position information based on image data are displayed simultaneously.

  FIG. 11 shows a display example of a tomographic image with depth information and a tomographic image with position information displayed on the monitor 14.

  As shown in FIG. 11, the tomographic images 51 to 53-3 are displayed on the monitor 14 at the same time. The tomographic images 51 to 53-3 each have the position information where the tomographic image data with depth information is generated. The tomographic image with position information added to the tomographic image 41 in FIG. 5, the tomographic image with position information added to the tomographic image 42 in FIG. A tomographic image with depth information at a shallowest position (a position 2 cm from the ultrasonic probe 12) among three tomographic images with depth information, which is a tomographic image orthogonal to the image 52; A tomographic image orthogonal to the tomographic image 51 and the tomographic image 52, which is an intermediate position among the three tomographic images with depth information that have been subjected to predetermined calculation processing (the ultrasonic probe 1 The tomographic image with depth information at a position 4 cm from the tomographic image, and a tomographic image orthogonal to the tomographic image 51 and the tomographic image 52, and among the three tomographic images with depth information that have been subjected to predetermined calculation processing A tomographic image with depth information at a deep position (position 6 cm from the ultrasonic probe 12) is shown. Note that the tomographic images 53-1 to 53-3 are in a substantially parallel relationship.

  When ultrasound is scanned from the apex, the tomographic images 53-1 to 53-3 are images at the base of the short axis of the heart, the papillary muscle level, and the apex.

  In the embodiment of the present invention, a plurality of depth information-added tomographic image data to which depth information is added by performing arithmetic processing at a predetermined thickness at a predetermined position are displayed simultaneously. Compared to the case where tomographic image data of a position is generated and displayed, a plurality of high-contrast tomographic images can be displayed simultaneously. Thereby, the operator can not only easily determine whether there is a myocardial ischemic site or tumor in the currently displayed tomographic image when observing the myocardial ischemic site or tumor of the heart, for example, By simultaneously viewing a plurality of currently displayed tomographic images, it is possible to easily estimate where the myocardial ischemia site or tumor is located in the heart.

  In addition, since the contrast ratio between the ischemic site of the myocardium and the surrounding site can be improved within the thickness range set in advance by the operator, the cross-section at a predetermined position indicated by the operator is somewhat Even in the case where a desired site exists at a remote location, it is possible to estimate where the myocardial ischemia site or tumor is located. Thus, even if the operator indicates a cross-section at a predetermined position without paying much attention to whether or not it is in the vicinity of the desired part, the heart is based on the displayed high-contrast tomographic image. It is possible to estimate where the myocardial ischemia site or tumor is located.

  Furthermore, since the tomographic image data with depth information is generated and displayed by performing arithmetic processing with a predetermined thickness at a predetermined position, the tomographic image data at the predetermined position is simply displayed. Compared to the case of generating and displaying, the operator can display a tomographic image of a desired part in a short time with fewer display operations.

  Therefore, when displaying a two-dimensional tomographic image at an arbitrary position, the operability of the ultrasonic diagnostic apparatus can be improved.

  Note that the operator may operate the input device 13 on the display screen of FIG. 11 to enlarge and display a desired tomographic image among the tomographic images 53-1 to 53-3. This makes it possible to more easily determine whether there is a myocardial ischemic site or a tumor when observing the myocardial ischemic site or tumor of the heart, for example.

  In addition, the operator operates the trackball 13a provided on the input device 13 to move the position information on the tomographic image 51 and the tomographic image 52 to a predetermined position, and then moves to a predetermined position after the movement. You may make it display the tomographic image 53-1 thru | or 53-3 in a position. Thereby, in the case of displaying a two-dimensional tomographic image at an arbitrary position, the operability of the ultrasonic diagnostic apparatus can be further improved.

  By the way, when the operator inputs data related to the calculation conditions in the calculation processing performed in the image reconstruction unit 28 by operating the input device 13, the operator reconstructs the image while viewing the display screen as shown in FIG. You may make it input the data regarding the calculation conditions in the calculation processing performed in the structure part 28, etc. FIG.

  As shown in FIG. 12, the operator designates a range with the thickness setting icon 54 on the display screen by using the input device 13, whereby a predetermined thickness in a vertical direction on which a predetermined calculation process is performed, A predetermined interval, position, and the like can be input.

  In addition, in order to prevent a region that is not desired to be observed from being included in the calculation region on which the calculation process is performed, the operator may input a region that is excluded from the calculation region as desired. For example, as shown in FIG. 12, luminance information (luminance profile) 55 of the image is superimposed on the tomographic image 43, and the operator uses the input device 13 to specify a range using the region setting icon 56. By doing so, a predetermined area to be excluded from the calculation area where the predetermined calculation process is performed may be input. As a result, it is possible to generate and display more suitable tomographic image data with depth information by excluding a high-luminance region, a low-luminance region, or the like that hinders predetermined arithmetic processing. Accordingly, tomographic image data with depth information having a higher contrast ratio can be generated and displayed.

  Of course, with reference to the luminance information of the superimposed image, a threshold (reference value) for excluding the high luminance region and the low luminance region from the calculation region where the operator operates the input device 13 to perform a predetermined calculation process. One or a plurality of luminance values may be input. Thus, the calculation process is performed by excluding the high-luminance area and the low-luminance area from the calculation area based on the input luminance value, so that the predetermined calculation process can be performed according to the preference of the operator.

  In addition, since there is a large amount of blood in the heart chamber of the heart, when the contrast agent is used, the portion in the heart chamber of the heart is strongly shaded and brighter than other parts, and as a result, This may hinder predetermined arithmetic processing. Therefore, when the image reconstruction unit 28 starts the arithmetic processing, the operator operates an intima extraction process by operating an intima extraction start button of the button 13c provided on the input device 13, as shown in FIG. May be excluded and the voxels in the heart chamber may be excluded from the calculation area where the predetermined calculation processing is performed. Thereby, more suitable tomographic image data with depth information can be generated and displayed. Accordingly, tomographic image data with depth information with higher contrast can be generated and displayed.

  When displaying a tomographic image with depth information, as shown in FIG. 14, the generated tomographic image with depth information at a predetermined position and a two-dimensional tomographic image that has not been subjected to predetermined arithmetic processing at that position. An image may be superimposed and displayed.

  In the case of the example in FIG. 14, the generated tomographic image with depth information at a predetermined position and a two-dimensional tomographic image that has not been subjected to predetermined arithmetic processing at the position are superimposed and displayed with different colors. In the case of the example in FIG. 14, a color bar 57 indicating the color of the tomographic image with depth information superimposed on the lower right is displayed.

  As a result, for example, when the contrast ratio between the myocardial ischemic region and the other portion is largely changed between the two images by performing predetermined arithmetic processing, the generated ischemia 58 is clearly depicted. . Therefore, the operator can more easily determine whether or not a myocardial ischemic site or the like is present in the tomographic image of the currently displayed site when observing the myocardial ischemic site or the like of the heart. As a result, it is possible to improve the operability of the ultrasonic diagnostic apparatus when displaying a two-dimensional tomographic image at an arbitrary position.

  In the embodiment of the present invention, the present invention is applied to the case of observing the heart of the subject P by scanning ultrasonic waves from the apex of the heart. However, the present invention is not limited to such a case. For example, the present invention can also be applied when observing a part such as a mammary gland.

  In the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, the case where the contrast medium is administered to the subject P has been described. However, the case where the contrast medium is not administered to the subject P can also be applied. it can.

  Furthermore, in the embodiment of the present invention, the operator may operate the input device 13 to generate and display tomographic image data with depth information instead of the arithmetic processing method. Accordingly, tomographic image data with depth information corresponding to a predetermined part can be generated and displayed using a suitable calculation processing method at a predetermined position designated by the operator.

  Further, in the ultrasonic diagnostic apparatus 1 shown in the embodiment of the present invention, depth information is added to a so-called C-mode tomographic image. However, the present invention is not limited to such a case, and the operator can select any tomographic image. Can be specified to add depth information.

  The series of processes described in the embodiment of the present invention can be executed by hardware, but can also be executed by software.

  In the embodiment of the present invention, the steps of the flowchart show examples of processing performed in time series in the described order. However, even if they are not necessarily processed in time series, they are performed in parallel or individually. The process to be executed is also included.

The block diagram which shows the internal structure of the ultrasonic diagnosing device to which this invention is applied. The flowchart explaining the tomographic image display process with depth information in the ultrasonic diagnostic apparatus of FIG. Explanatory drawing explaining the principle in the case of scanning an ultrasonic wave directly three-dimensionally using the ultrasonic probe which has the ultrasonic transducer arranged in a two-dimensional matrix. Explanatory drawing explaining the principle of an orthogonal 3 cross-section display method. The figure which shows the example of a display of the two-dimensional tomographic image of three orthogonal cross sections displayed on the monitor of FIG. FIG. 2 is an overview diagram illustrating a schematic overview configuration of the input device of FIG. 1. Explanatory drawing explaining the concept of the arithmetic processing method in step 7 of FIG. Explanatory drawing explaining the specific method of the arithmetic processing in step 7 of FIG. Explanatory drawing explaining the specific method of the other arithmetic processing in step 7 of FIG. Explanatory drawing explaining the specific method of the other arithmetic processing in step 7 of FIG. The figure which shows the example of a display of the some tomographic image with depth information displayed on the monitor of FIG. The figure which shows the example of a display of the input display screen of the calculation conditions displayed on the monitor of FIG. FIG. 2 is an explanatory diagram for explaining a method for excluding an intracardiac region from a calculation region on which calculation processing is performed in the ultrasonic diagnostic apparatus of FIG. 1. The figure which shows the example of a display which superimposes and displays the tomographic image with depth information displayed on the monitor of FIG. 1, and a normal two-dimensional tomographic image.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 11 Main body 12 Ultrasonic probe 13 Input device 13a Track ball 13b Switch 13c Button 13d Mouse 13e Keyboard 14 Monitor 21 Control processor 22 Transmission / reception part 23 B mode processing part 24 Doppler mode processing part 25 Image generation circuit 26 Storage part 26a Image memory 26b Software storage unit 27 Internal storage device 28 Image reconstruction unit 29 Input data acquisition unit 30 Calculation condition setting unit 31 Interface unit 32 Network

Claims (19)

A volume data generating means for transmitting ultrasonic waves by vibrating a plurality of ultrasonic transducers and generating volume data based on a reception signal converted by the ultrasonic transducers from a reflected wave reflected from a subject;
First image data generating means for generating a plurality of first image data, which is two-dimensional tomographic image data at a predetermined position, at a plurality of positions based on the volume data;
Based on the volume data, at least one of a maximum value hold calculation, an addition average, and a minimum value hold calculation is performed on a plurality of calculation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data. Second image data generating means for performing two operations and generating a plurality of second image data;
Third image data generating means for generating third image data in a display direction different from the display direction of the plurality of second image data based on the volume data;
A plurality of second image based on the plurality of second image data, and the third third display control means for Ru is displayed on the display device an image based on the image data of,
A thickness adjusting means for displaying an icon corresponding to the plurality of calculation areas on the third image, and adjusting a thickness of a required calculation area among the plurality of calculation areas by using the icon; An ultrasonic diagnostic apparatus comprising: Said second image data generating means, according to claim, wherein the performing the operation on the plurality of operation areas in predetermined intervals on the basis of the volume data, and generates the plurality of second image data The ultrasonic diagnostic apparatus according to 1. The ultrasonic diagnostic apparatus according to claim 1, wherein the plurality of calculation areas are substantially parallel to each other. The second image data generation means generates a low luminance area having a luminance value smaller than a predetermined lower limit reference value or a luminance value larger than a predetermined upper limit reference value from each calculation area of the plurality of calculation areas. The ultrasonic diagnostic apparatus according to claim 1, wherein the second image data is generated by performing the calculation on a partial region excluding a high luminance region. And reference value data acquisition means for acquiring data relating to at least one of the previous SL predetermined upper limit reference value and a predetermined lower limit reference value,
Based on data relating to at least one of the predetermined lower limit reference value and the predetermined upper limit reference value acquired by the reference value data acquisition means, at least one of the predetermined lower limit reference value and the predetermined upper limit reference value is set. a reference value setting means for, further comprising a
The second image data generation means performs the calculation on the partial area based on at least one of the predetermined lower limit reference value and the predetermined upper limit reference value set by the reference value setting means, and the second image data generation means The ultrasonic diagnostic apparatus according to claim 4 , wherein the image data is generated. Said second image data generating means, the time of generating the second image data with respect to the object of the heart region, extracts the endocardium, the exclusion portion area cardiac cavity region from the calculation region The ultrasonic diagnostic apparatus according to claim 1, wherein an operation is performed to generate the second image data. Said display control means further said the tomographic image based on the first image data, wherein Rukoto superimposed to display the luminance information on a given straight line in the tomographic image based on the first image data The ultrasonic diagnostic apparatus according to claim 1. A calculation condition data acquisition means for acquiring data about operational conditions before Ki演 calculation to be performed when the second image data by the second image data generation unit is generated,
Based on the data relating to the acquired operation condition by the operation condition data acquisition means, further comprising a an arithmetic condition setting means for setting the operation condition,
It said second image data generating means, according to in accordance with the operation condition set by the operation condition setting unit performs pre Ki演 calculated in the calculation region, and generates the second image data Item 2. The ultrasonic diagnostic apparatus according to Item 1. Wherein the data relating to operational conditions before Ki演 calculation to be performed when the second image data by the second image data generation unit is generated, at least, of a predetermined said second image data is generated data relating to interval, and, characterized in that contains data for a given thickness perpendicular to the cross section of the first image data to which the operation is performed when the second image data is generated The ultrasonic diagnostic apparatus according to claim 8 . The operation condition data acquisition means, at least one or more, on the center of the passing Ri tomographic image of a cross section perpendicular to the operation region of the operation region, claim 8, characterized in that to obtain the data relating to the operational condition An ultrasonic diagnostic apparatus according to 1. The display control means displays a tomographic image based on the third image data on the display device,
The ultrasonic diagnostic apparatus according to claim 1, further comprising a position changing unit that displays a marker on the tomographic image and changes the position of the second image using the marker. The display control means further before and Kidan layer image, the ultrasonic diagnostic apparatus according to claim 1, characterized in Rukoto be displayed by superimposing the second images with different color tones. Said third image data generating means, as the third image data, wherein, wherein the benzalkonium generates the data of the tomographic image of the cross section perpendicular to the center of the operational area through Ri the calculation region Item 2. The ultrasonic diagnostic apparatus according to Item 1. The ultrasonic diagnostic apparatus includes an ultrasonic diagnostic apparatus according to claim 1, characterized in that used in the contrast medium bubbles under the conditions of administration. 15. The second image data generation unit generates the plurality of second image data by performing the maximum value holding calculation on the plurality of calculation regions when capturing a contrast image. The ultrasonic diagnostic apparatus as described. The first and third image generation means generate the first and third image data so that the display directions are orthogonal to each other.
A fourth image data generating unit configured to generate fourth image data in a display direction orthogonal to the first and third image data,
The display control means displays a fourth image based on the fourth image data side by side with the second and third images;
15. The thickness adjusting unit displays icons corresponding to the plurality of calculation areas on a fourth image in addition to the third image. An ultrasonic diagnostic apparatus according to 1. A volume data generation step of generating a volume data based on a reception signal converted by the ultrasonic transducer from a reflected wave reflected from a subject, transmitting ultrasonic waves by vibrating a plurality of ultrasonic transducers;
A first image data generation step of generating a plurality of first image data as a two-dimensional tomographic image data at a predetermined position at a plurality of positions based on the volume data;
Based on the volume data, at least one of a maximum value hold calculation, an addition average, and a minimum value hold calculation is performed on a plurality of calculation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data. A second image data generation step for performing two operations and generating a plurality of second image data;
A third image data generation step for generating third image data in a display direction different from a display direction of the plurality of second image data based on the volume data;
A display step Ru is displayed on the display device and the third image and the plurality of second image based on the plurality of second image data based on the third image data,
A thickness adjustment step of displaying an icon corresponding to the plurality of calculation areas on the third image and adjusting a thickness of a required calculation area among the plurality of calculation areas using the icon. An image processing program for an ultrasonic diagnostic apparatus, which is executed by a computer. A volume data generating means for transmitting ultrasonic waves by vibrating a plurality of ultrasonic transducers and generating volume data based on a reception signal converted by the ultrasonic transducers from a reflected wave reflected from a subject;
First image data generating means for generating a plurality of first image data, which is two-dimensional tomographic image data at a predetermined position, at a plurality of positions based on the volume data;
Based on the volume data, at least one of a maximum value hold calculation, an addition average, and a minimum value hold calculation is performed on a plurality of calculation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data. Second image data generating means for performing two operations and generating a plurality of second image data;
Third image data generating means for generating third image data in a display direction different from the display direction of the plurality of second image data based on the volume data;
And the tomographic image based on the first image data, and superimposed image of the second image based on the second image data, Ru is displayed on the display device and a third image based on the third image data Display control means ;
A thickness adjusting means for displaying an icon corresponding to the plurality of calculation areas on the third image, and adjusting a thickness of a required calculation area among the plurality of calculation areas by using the icon; An ultrasonic diagnostic apparatus comprising: A volume data generation step of generating a volume data based on a reception signal converted by the ultrasonic transducer from a reflected wave reflected from a subject, transmitting ultrasonic waves by vibrating a plurality of ultrasonic transducers;
A first image data generation step of generating a plurality of first image data as a two-dimensional tomographic image data at a predetermined position at a plurality of positions based on the volume data;
Based on the volume data, at least one of a maximum value hold calculation, an addition average, and a minimum value hold calculation is performed on a plurality of calculation areas having thicknesses in a direction perpendicular to a cross section of the plurality of first image data. A second image data generation step for performing two operations and generating a plurality of second image data;
A third image data generation step for generating third image data in a display direction different from a display direction of the plurality of second image data based on the volume data;
And the tomographic image based on the first image data, and superimposed image of the second image based on the second image data, Ru is displayed on the display device and a third image based on the third image data A display step ;
A thickness adjustment step of displaying an icon corresponding to the plurality of calculation areas on the third image and adjusting a thickness of a required calculation area among the plurality of calculation areas using the icon. An image processing program for an ultrasonic diagnostic apparatus, which is executed by a computer.

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