CN103784165A - Ultrasonic diagnosis device - Google Patents

Abstract

The present invention is used to improve the position guidance of an ultrasound probe in ultrasound imaging using biophotometry. The ultrasonic diagnostic apparatus according to the present embodiment includes an ultrasonic probe, a photodetector, an image generation unit, a calculation unit, an assistance information generation unit, and an output unit. The photodetector has: a photoirradiation part arranged around the ultrasonic wave transmitting and receiving surface of the ultrasonic probe on the central axis in the longitudinal direction of the surface, and irradiating light into the subject from at least one position; and a plurality of light detecting parts , around the ultrasonic transceiving surface, arranged at different positions with the central axis in the longitudinal direction of the ultrasonic transceiving surface as the axis of symmetry. The calculation unit calculates the position and size of an abnormal site showing a predetermined light absorption coefficient in the subject based on the intensity of light detected by each light detection unit. The display unit displays an ultrasonic image in which the position and size of the abnormality are indicated.

Description

Ultrasonic diagnostic device

technical field

Embodiments of the present invention relate to an ultrasonic diagnostic apparatus.

Background technique

There are various techniques for non-invasively measuring the inside of a living body. Optical measurement, which is one of them, has the advantage of being able to select a compound to be measured by selecting a wavelength without the problem of being irradiated. As far as the general biological light measurement device is concerned, the light irradiation part is pressed against the skin surface of the living body, and the light is irradiated percutaneously into the inside of the living body, and the transmitted or reflected light is measured to pass through the skin again and go out of the living body. Based on the emitted light, various biological information is calculated. The basis for judging the existence of abnormal tissue in the living body by optical measurement is that the absorption coefficient of light is different from that of normal tissue. That is, since the absorption coefficients of abnormal tissues in the living body are different, a difference in the amount of detected light corresponding to the difference in the amount of absorption occurs. In other words, by solving the inverse problem based on the amount of detected light, the absorption coefficient of the abnormal tissue can be obtained, and the properties of the abnormal tissue can be distinguished from the obtained absorption coefficient. In addition, the measured position and depth are analyzed by the measured light. This analysis method includes: a method of adjusting the distance between the light irradiation part (hereinafter referred to as light source) and the detector (spatial decomposition method); and a method of obtaining depth information according to the difference in the arrival time of light by using a light source whose intensity varies with time. (time decomposition method); and a method of combining the above methods, etc. Through these analysis methods, a biological optical measurement device capable of obtaining high-quality signals has been realized. However, there is a problem of low spatial resolution in imaging information by light in a living body. Furthermore, in order to obtain accurate position information from the detection result of reflected light, it is necessary to operate a large amount of data using a complicated algorithm, and it is impossible to make a real-time determination.

In bioluminescence measurement, breast cancer examination can be cited as an application with high possibility of realization. However, when optical measurement is performed alone as described above, there are problems in resolution and analysis time, so it is preferable to use it in combination with other modality to improve inspection performance. Therefore, in the present application, a method for compensating the low spatial resolution of light by using the shape information of the ultrasonic echo is proposed. With this method, it is expected that the morphological characteristics in the biological tissue and the component distribution discrimination of the morphological characteristic parts can be distinguished in a shorter time than conventional ones, but there is still room for improvement in real-time determination.

However, breast cancer is one of the leading causes of death in women. Screening and early diagnosis of breast cancer are of great value in reducing mortality and curbing health management costs. In the current method, a palpable diagnosis of the tissue of the breast and radiography for finding suspicious tissue deformations are carried out. If there is a suspicious area in the X-ray photograph, ultrasound imaging is performed, and then surgical tissue examination is performed. It will take quite a long time for this series of inspections to reach a final conclusion. In addition, there are many young layers of mammary glands before amenorrhea, and there is also a problem that it is difficult to obtain high sensitivity in X-ray photography. Therefore, especially for young people, the significance of screening under ultrasound photography is very great.

Generally speaking, in ultrasound imaging, a certified operator acquires an ultrasound still image, and a dedicated reader (sometimes multiple) makes a judgment based on the morphological information on the image. In view of the risk of omissions due to operator fatigue and low concentration in examination and diagnosis, screening by one operator is limited to a maximum of 50 patients per day.

In imaging of ultrasonic images, the knowledge and experience of the operator are very important when obtaining still images capturing morphological features. Accurate and rapid screening also requires proficiency. For example, the inspection time for each subject is typically 5 minutes to 10 minutes, but it may take more time depending on the skill of the operator. That is, in current screening by ultrasound imaging, the accuracy of image acquisition may vary depending on the operator's proficiency. Moreover, when acquiring an image, it is necessary to keep an eye on the image and to rely on the operator's independent judgment. Therefore, even a skilled operator has a heavy mental burden. There is also a method of acquiring all image information as a moving image, but even in this case, the burden on the image reader side becomes large.

In order to solve the problems in such ultrasonic tomosynthesis diagnosis, a method has been proposed to reduce the burden on the technician by guiding the measurement position of the ultrasonic probe in the plane direction using the metabolic information of the living body obtained by the biophotometric measurement. . In this way, in ultrasonic imaging, it is possible to detect and distinguish an abnormal site more easily and in a shorter time than conventionally.

Prior art literature

patent documents

Patent Document 1: JP-A-2004-073559

Patent Document 2: JP-A-2009-247683

Patent Document 3: JP-A-2000-237196

Patent Document 4: JP-A-2005-331292

Patent Document 5: JP-A-2007-020735

Patent Document 6: JP-A-2009-077931

However, there is still room for improvement in the position guidance of ultrasound probes for ultrasound imaging using biophotometry.

Contents of the invention

The ultrasonic diagnostic apparatus according to the present embodiment includes an ultrasonic probe, a photodetector, an image generation unit, a calculation unit, a calculation unit, and a display unit. The ultrasonic probe transmits ultrasonic waves from the ultrasonic transmitting and receiving surface to the subject, and receives ultrasonic waves reflected in the subject via the ultrasonic transmitting and receiving surface. The photodetector has: a light irradiating part arranged on the central axis of the longitudinal direction of the ultrasonic transmitting and receiving surface around the ultrasonic transmitting and receiving surface, and irradiating light into the subject from at least one position; The periphery of the transceiving surface is arranged at different positions with the central axis in the longitudinal direction of the ultrasonic transmitting and receiving surface as a symmetric axis, and the intensity of light reflected in the subject is detected. The image generating unit generates an ultrasonic image using ultrasonic waves received by the ultrasonic probe. The calculation unit calculates the position and size of an abnormal site showing a predetermined light absorption coefficient in the subject based on the intensity of light detected by each light detection unit. The display unit displays an ultrasonic image in which the position and size of the abnormality are indicated.

Description of drawings

FIG. 1 is a diagram showing a block configuration diagram of an ultrasonic diagnostic apparatus 1 according to a first embodiment.

FIG. 2 is a block configuration diagram of a biological optical measurement device 4 composed of a photodetector 40 and an optical measurement processing unit 42 .

FIG. 3 is a diagram showing an example of arrangement of the light irradiation unit 400 and the light detection units 401 a to 401 a to d with respect to the ultrasound probe 12 .

4( a ), ( b ), and ( c ) are diagrams for explaining the measurement process of the degree of adhesion performed using the arrangement example of FIG. 3 .

5( a ), ( b ), and ( c ) are diagrams for explaining the measurement process of the three-dimensional orientation and distance of the abnormal site.

FIG. 6 is a diagram showing an arrangement example of the light irradiation unit 400 and the light detection units 401 a to 401 a to d used in the process of measuring the three-dimensional orientation and distance of the abnormal site.

FIG. 7 is an example of support information displayed on the monitor 14 when the degree of adhesion to the breast and the three-dimensional orientation and distance of the abnormal site are measured in breast cancer examination.

FIG. 8 shows a modified example of the support information displayed on the monitor 14 .

FIG. 9 is a diagram showing an example of support information for the purpose of primary guidance for positioning an abnormal site within an ultrasonic scanning region.

FIG. 10 is a diagram showing an example of support information for secondary guidance aimed at maximizing the signal amount of light from an abnormal site after moving the ultrasound probe 12 according to the primary guidance.

11 is an example in which the absorption signal intensity (or attenuation signal intensity) of each photodetector 401 calculated based on the signal intensity of the detected light of each photodetector 401 is used as supporting information and displayed with a level meter. .

12( a ) and ( b ) are diagrams showing an example of support information output as a sound signal.

FIG. 13 is a modified example of the arrangement shown in FIG. 6 .

FIG. 14 is another modified example of the arrangement shown in FIG. 6 .

FIG. 15 is another modified example of the arrangement shown in FIG. 6 .

FIG. 16 is another modified example of the arrangement shown in FIG. 6 .

FIG. 17 is another modified example of the arrangement shown in FIG. 6 .

FIG. 18 is another modified example of the arrangement shown in FIG. 6 .

FIG. 19 is a block configuration diagram of a biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the second embodiment.

FIG. 20 is a block configuration diagram of the biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the third embodiment.

FIG. 21 is a diagram showing an example of a procedure for determining the degree of adhesion and determining the orientation of an abnormal site using the optical biometric measurement device 4 shown in FIG. 20 .

FIG. 22 is a block configuration diagram of the biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the fourth embodiment.

FIG. 23 is a view of the probe of the ultrasonic diagnostic apparatus 1 according to the fifth embodiment viewed from the subject contact surface side.

FIG. 24 is a diagram schematically showing the position and size of the probe P and the abnormality identified on the ultrasonic scanning section when the abnormality is approximated as a sphere.

FIG. 25 is a diagram showing ultrasonic images corresponding to ultrasonic scanning sections.

FIG. 26 is a diagram for explaining a display form of an abnormal site whose position and size are specified on an ultrasonic image.

FIG. 27 is a diagram showing Modification 1 of the arrangement of the light irradiation unit 400 and the light detection unit 401 of the probe of the ultrasonic diagnostic apparatus 1 according to the fifth embodiment.

28 is a diagram showing Modification 2 of the arrangement of the light irradiation unit 400 and the light detection unit 401 of the probe of the ultrasonic diagnostic apparatus 1 according to the fifth embodiment.

29 is a diagram showing Modification 3 of the arrangement of the light irradiation unit 400 and the light detection unit 401 of the probe of the ultrasonic diagnostic apparatus 1 according to the fifth embodiment.

30 is a diagram showing a mode in which the proximity state of an abnormal site specified by biophotometry and a probe is represented as brightness (change) of a part (such as an icon) of an ultrasound image screen.

FIGS. 31( a ) to ( d ) are diagrams illustrating how the brightness of the icon changes as the detector approaches the identified abnormal site.

FIGS. 32( a ) to ( d ) are diagrams illustrating how the color of the icon changes as the probe approaches the identified abnormal site.

FIGS. 33( a ) to ( d ) are diagrams illustrating how the display area of the icon changes as the detector approaches the identified abnormal site.

FIGS. 34( a ) to ( d ) are diagrams illustrating how the display positions of the icons change as the detector approaches the identified abnormal site.

FIGS. 35( a ) to ( d ) are diagrams illustrating how the amplitude of the vibration of the icon changes as the probe approaches the identified abnormal site.

FIGS. 36( a ) to ( d ) are diagrams illustrating how the shape of the icon changes as the probe approaches the identified abnormal site.

Explanation of reference signs

1...ultrasonic diagnostic device, 11...apparatus main body, 12...ultrasonic probe, 13...input device, 14...monitor, 21...ultrasonic sending unit, 22...ultrasonic receiving unit, 23...B Pattern processing unit, 24...Doppler processing unit, 25...RAW data memory, 26...Volume data generation unit, 28...Image processing unit, 30...Display processing unit, 31...Control processor (CPU ), 32...storage unit, 33...interface unit, 40...photodetector, 42...optical measurement processing unit, 44...support information generation unit, 400...light irradiation unit, 401...light detection Section, 420...Light source 420, 422...Optical signal control section, 424...Optical analysis section, 426...Operating circuit

Detailed ways

Hereinafter, each embodiment will be described with reference to the drawings. In addition, in the following description, the same code|symbol is attached|subjected to the component which has substantially the same function and structure, and repeated description is performed only when necessary.

(first embodiment)

FIG. 1 shows a block configuration diagram of an ultrasonic diagnostic apparatus 1 according to the present embodiment. The ultrasonic diagnostic apparatus 1 shown in the figure includes an ultrasonic probe 12, an input device 13, a monitor 14, an ultrasonic transmitting unit 21, an ultrasonic receiving unit 22, a B-mode processing unit 23, a Doppler processing unit 24, and a RAW data memory. 25 . A volume data generation unit 26 , an image processing unit 28 , a display processing unit 30 , a control processor (CPU) 31 , a storage unit 32 , and an interface unit 33 . In addition, the ultrasonic diagnostic apparatus 1 according to this embodiment further includes: an optical probe 40 and an optical measurement processing unit 42 for realizing the biological optical measurement device 4; A support information generating unit 44 of support information for support.

In addition, in the present embodiment, as shown in FIG. 1 , an ultrasonic diagnostic apparatus 1 incorporating a biological optical measurement device (integrated with the biological optical measurement device) will be described as an example. However, it is not limited to this example, and the biological optical measurement device and the ultrasonic diagnostic device may have separate structures.

The ultrasonic probe 12 is a device (probe) that transmits ultrasonic waves to a subject, typically a living body, and receives reflected waves reflected from the subject based on the transmitted ultrasonic waves. Piezoelectric vibrators, matching layers, pad components, etc. The piezoelectric vibrator transmits ultrasonic waves in a desired direction within the scanning area based on a drive signal from the ultrasonic wave transmitting unit 21, and converts reflected waves from the subject into electrical signals. The matching layer is provided on the piezoelectric vibrator, and is an intermediate layer for efficiently propagating ultrasonic energy. The spacer member prevents ultrasonic waves from propagating backward from the piezoelectric vibrator. When ultrasonic waves are transmitted from the ultrasonic probe 12 to the subject, the transmitted ultrasonic waves are continuously reflected by discontinuous surfaces of the acoustic impedance of tissues in the body, and received by the ultrasonic probe 12 as echo signals. The amplitude of this echo signal depends on the difference in acoustic impedance of the reflected discontinuous surface. In addition, the echo when the transmitted ultrasonic pulse is reflected by the moving blood flow receives a frequency shift depending on the velocity component in the direction of the ultrasonic transmission/reception of the moving body due to the Doppler effect.

In addition, in the present embodiment, the ultrasonic probe 12 is assumed to be a one-dimensional array probe in which a plurality of ultrasonic vibrators are arranged along a predetermined direction. However, it is not limited to this example. As a structure capable of obtaining volume data, the ultrasonic probe 12 may also be a two-dimensional array probe (a probe in which a plurality of ultrasonic vibrators are arranged in a two-dimensional matrix) or a mechanical 4D probe ( A probe capable of mechanically sweeping an array of ultrasonic vibrators in a direction perpendicular to the direction in which they are arranged) while performing ultrasonic scanning).

The input device 13 is connected to the main body 11 of the device, and has various means for taking various instructions from the operator, such as setting instructions for conditions and regions of interest (ROI), setting instructions for various image quality conditions, etc., into the main body 11 of the device. Switches, buttons, trackballs, mice, keyboards, etc. In addition, the input device 13 has a button and the like for instructing the timing of acquiring puncture information including the position of the needle tip of the puncture needle in a puncture support function described later, and the like.

The monitor 14 displays morphological information or blood flow information in the living body as an image based on the video signal from the display processing unit 30 .

The ultrasonic transmission unit 21 has a trigger generation circuit, a delay circuit, a pulse circuit, and the like, which are not shown. In the trigger generating circuit, a trigger pulse for forming and transmitting ultrasonic waves is repeatedly generated at a predetermined rate frequency frHz (period; 1/fr second). In addition, in the delay circuit, a delay time required for converging ultrasonic waves into a beam for each channel and determining transmission directivity is given to each trigger pulse. The pulse circuit applies a drive pulse to the probe 12 at a timing based on the trigger pulse.

The ultrasonic receiving unit 22 has an amplifier circuit, an A/D converter, a delay circuit, an adder, and the like, which are not shown. In the amplification circuit, the echo signal acquired via the probe 12 is amplified for each channel. In the A/D converter, the amplified analog echo signal is converted into a digital echo signal. In the delay circuit, the receiving directivity is determined for the digitally converted echo signal, and the delay time required for receiving dynamic focus is given, and then added in the adder. This addition emphasizes the reflection component from the direction corresponding to the reception directivity of the echo signal, and forms an integrated beam of ultrasonic transmission/reception signals by the reception directivity and transmission directivity.

The B-mode processing unit 23 receives the echo signal from the receiving unit 22, performs logarithmic amplification, envelope detection processing, etc., and generates data expressing the signal strength in terms of brightness.

The Doppler processing unit 24 extracts blood flow signals from the echo signals received from the receiving unit 22 to generate blood flow data. The extraction of blood flow is usually performed by CFM (Color Flow Mapping: color blood flow map). In this case, the blood flow signal is analyzed, and blood flow information such as average velocity, dispersion, and energy is obtained for a plurality of points as blood flow data.

The RAW data memory 25 uses a plurality of B-mode data received from the B-mode processing unit 23 to generate B-mode RAW data as B-mode data on a three-dimensional ultrasonic scanning line. Also, the RAW data memory 25 generates blood flow RAW data as blood flow data on a three-dimensional ultrasonic scan line using a plurality of blood flow data received from the Doppler processing unit 24 . In addition, in order to reduce noise and enhance image correlation, a three-dimensional filter may be inserted after the RAW data memory 25 to perform spatial smoothing.

The volume data generation unit 26 generates B-mode volume data and blood fluid data by performing RAW-voxel conversion including interpolation processing that takes spatial position information into consideration.

The image processing unit 28 performs predetermined image processing such as volume rendering, multi planar reconstruction display (MPR: multi planar reconstruction), and maximum intensity projection display (MIP: Maximum intensity projection) on the volume data received from the volume data generating unit 26 . In addition, in order to reduce noise and increase image correlation, a two-dimensional filter may be inserted after the image processing unit 28 to perform spatial smoothing.

The display processing unit 30 executes various processing such as dynamic range, brightness, contrast, γ-curve correction, and RGB conversion on the various image data generated and processed by the image processing unit 28 .

The control processor 31 has a function as an information processing device (computer), and controls the operation of each component. In addition, the control processor 31 executes processing based on an ultrasonic probe operation support function described later.

The storage unit 32 stores a dedicated program for realizing the ultrasound probe operation support function described later, captured volume data, diagnostic information (patient ID, doctor's opinion, etc.), diagnostic protocol, signal transmission and reception conditions, and other data groups. In addition, it is also used for storage of images in an unshown image memory, etc., as necessary. The data of the storage unit 32 can also be transferred to an external peripheral device via the interface unit 33 .

The interface unit 33 is an interface related to the input device 13 , a network, and a new external storage device (not shown). In addition, an external bio-optical measurement device can also be connected to the ultrasonic diagnostic device main body 11 via the interface unit 33 . Data such as ultrasonic images or analysis results obtained by this device can be transmitted to other devices via the network through the interface unit 33 .

FIG. 2 is a block configuration diagram of a biological optical measurement device 4 composed of a photodetector 40 and an optical measurement processing unit 42 .

The photodetector 40 has at least one light irradiation unit 400 and a plurality of photodetection units 401 . The light irradiation unit 400 irradiates the light (near-infrared light) generated by the light source 420 toward the subject. The photodetection unit 401 has a detection surface formed of, for example, an end portion of an optical fiber, and includes a plurality of detection elements for photoelectrically converting reflected light from the subject input from the detection surface via the optical waveguide. As the detection element, in addition to light receiving elements such as photodiodes and phototransistors, CCDs, APDs, photomultiplier tubes, and the like can be used, for example. An optical matching layer may be provided on the contact surfaces of the light irradiation unit 400 and the light detection units 401 that come into contact with the subject.

FIG. 3 is a diagram showing an arrangement example of the light irradiation unit 400 and the light detection units 401 a to 401 a to d with respect to the ultrasonic probe 12 . In this figure, the light irradiation part 400 is arranged near the center of the ultrasonic transceiving surface 120 of the ultrasonic probe 12, and the ultrasonic transmitting and receiving surface 120 (with the detected An example in which the photodetectors 401 a to d are arranged at equal intervals in such a manner that the photodetectors 401 a to d are surrounded by a contact surface in which the body is in contact with each other. The contact surfaces of the light irradiation unit 400 and the light detection units 401 a to 401 a to d that come into contact with the subject are set to be, for example, at the same height level as the ultrasonic wave transmitting and receiving surface 120 , and are arranged so as to be directly or indirectly in contact with the surface of the subject during measurement. state of contact. In addition, the arrangement of the light irradiation unit 400 and the light detection unit 401 with respect to the ultrasonic probe 12 is not limited to the example shown in FIG. 3 . The application example of the configuration will be described in detail later.

The optical measurement processing unit 42 has a light source 420 , an optical signal control unit 422 , an optical analysis unit 424 , and an arithmetic circuit 426 . The light source 420 is a light-emitting element such as a semiconductor laser, a light-emitting diode, a solid-state laser, or a gas laser that generates light of a small wavelength absorbed in a living body (for example, near a wavelength band called a window of a living body, namely Light in the range of 600nm to 1800nm), light of a specific wavelength that has increased absorption in abnormal parts (for example, light in the wavelength range of 750 to 850nm that is absorbed by hemoglobin in blood within the wavelength band called the window of the living body ). The light generated by the light source 420 is supplied to the light irradiation unit 400 via an optical fiber or an optical waveguide formed of a thin-film optical waveguide (or directly propagates through space). In addition, the light source 420 may be configured integrally with the light irradiation unit 400 .

The optical signal control unit 422 dynamically or statically controls the biological optical measurement device 4 . For example, the optical signal control unit 422 controls the light source 420 under the control of the control processor 31 of the ultrasonic diagnostic apparatus 1 so that light is emitted from the light irradiation unit 400 at predetermined timing, frequency, intensity, and intensity variation cycle T. In addition, the optical signal control unit 422 controls the optical analysis unit 424 so that the optical analysis process is executed at a predetermined timing.

The optical analysis unit 424 amplifies the analog signal input from the optical detection unit 401 and converts it into a digital signal. Furthermore, the optical analysis unit 424 analyzes the intensity change of the detection light between the light detection units 401 .

The calculation circuit 426 calculates the degree of close contact between the photodetection part 401 and the surface of the subject based on the change in the intensity of the detected light between the photodetectors 401, so as to show an abnormal site with a predetermined light absorption coefficient in the subject (for example, A three-dimensional image of an abnormal site based on the depth between the surface of the subject and a predetermined position (for example, the light irradiation part 400, the center of the ultrasonic transmitting and receiving surface 120, etc.) location and distance. The calculation result in the arithmetic circuit 426 is sent to the support information generation unit 44 .

(ultrasonic probe operation support function)

Next, the ultrasonic probe operation support function included in the ultrasonic diagnostic apparatus will be described. This function is to calculate at least one of the degree of adhesion between the ultrasonic probe 12 and the surface of the subject, and the three-dimensional orientation and distance (proximity) of the abnormal part in the subject, and based on the result, generate and output The operation of the ultrasound probe is supported by guiding the support information such as the position, orientation, posture, pressure degree, etc. of the ultrasound probe 12 to the subject and the site to be diagnosed better.

(Measurement process of adhesion degree)

First, the measurement process of the degree of adhesion between the photodetection unit 401 and the surface of the subject will be described. Here, the degree of closeness refers to the thickness of the air layer present in the gap between the photodetection unit 401 and the surface of the living body and the ratio of the cross-sectional area occupying the optical path. Ideally, there is no air layer, or the thickness is not more than the wavelength of the detection light and the coverage is not more than 0.1%.

4( a ), ( b ), and ( c ) are diagrams for explaining the measurement process of the degree of adhesion performed using the arrangement example of FIG. 3 . 4(a), (b), and (c), the upper section shows the AA cross-sectional view of FIG. Projection map of the object surface projection.

As shown in FIG. 4( a ), first, with the probe P placed on the surface of the subject, near-infrared light is irradiated from the light irradiation unit 400 into the subject. At this time, it is assumed that the detection surfaces of the photodetectors 401b to d (corresponding to ch2 to 4, respectively) are in good contact with the surface of the subject, while the detection surface of the photodetector 401a (corresponding to ch1) is in good contact with the subject surface. Spaces (gaps) exist between specimen surfaces. In this case, in the photodetection unit 401 a separated from the surface of the subject, part of the reflected light emitted from the subject is reflected by the detection surface due to the difference in refractive index. As a result, the intensity of light incident on the photodetector 401 a is weaker than that of incident light on the photodetectors 401 b to 401 d. Such a change in light intensity between the light detection units 401 is analyzed by the light analysis unit 424 . The arithmetic circuit 426 calculates the signal level of the light intensity in the light detection unit 401a with the signal level of the preset light intensity or the signal level of the light intensity in the light detection units 401b-d to calculate the specified risk rate. values for comparison. As a result, when the signal level of the light intensity in the photodetector 401a is low, the arithmetic circuit 426 determines that the photodetector 401a is separated from the object surface (adhesion degree low state). When all the photodetectors 401 are judged to have an appropriate degree of adhesion, the degree of adhesion of the ultrasonic probe 12 surrounded by the photodetectors 401 is also judged to be in an appropriate range.

The support information generation unit 44 generates support information for instructing and guiding the position, posture, orientation, etc. of the ultrasonic probe 12 so that the ultrasonic transmitting and receiving surface 120 is in close contact with the subject based on the determination result and calculation result of the arithmetic circuit 42 . The generated support information is displayed on the monitor 14 in a predetermined form. In addition, specific examples of support information will be described in detail later.

The operator operates the ultrasonic probe 12 according to the guidance of the displayed support information, and performs the adhesion degree measurement again. As a result, when it is determined that the degree of adhesion falls within an appropriate range, ultrasound imaging is started.

(Measurement processing of three-dimensional orientation and distance of abnormal parts)

Next, the process of measuring the three-dimensional orientation and distance of the abnormal site will be described. 5( a ), ( b ), and ( c ) are diagrams for explaining the measurement process of the three-dimensional orientation and distance of the abnormal site. FIG. 6 is a diagram showing an arrangement example of the light irradiation unit 400 and the light detection units 401 a to 401 a to d used in the process of measuring the three-dimensional orientation and distance of the abnormal site. In addition, in each of Fig. 5(a), (b), and (c), the abnormal part is used as an absorber, and the AA cross-sectional view of Fig. 6 is shown in the upper stage, and the light irradiation part is shown in the lower stage. 400. A projected view of each detection surface of the light detection unit 401 on the surface of the subject.

First, in order to calculate the three-dimensional orientation and distance of the abnormal part, in the state where the probe P is arranged on the surface of the subject, light of a specific wavelength that increases the absorption amount of the abnormal part is irradiated from the light irradiation part 400 toward the inside of the subject. Light. As shown in FIG. 5( a ), the photodetectors 401 a ′ to 401 d ′ are located near the light irradiation unit 400 (approximate positions) and are located far from the light irradiation unit 400 as shown in FIG. 5( b ). The photodetectors 401a to 401d at positions (peripheral positions) respectively detect the reflected light of the irradiated light from inside the subject.

The incident light passes through the living body while being scattered, but when it passes through the abnormal part, it is absorbed more. Therefore, the detection light of the photodetectors (in the example of FIG. 5 and FIG. 6 , the detector 401 a and the photodetector 401 a ′) arranged at a specific distance becomes the depth information including the abnormal part. The optical analysis unit 424 analyzes the detection light from the photodetectors 401 a to 401 d (corresponding to ch1 to 4 , respectively) and photodetectors 401 a ′ to 401 d ′ (corresponding to ch5 to 8 , respectively) arranged at each azimuth angle. As a result, for example, in the case of ch2<ch1<ch3, ch4 in Fig. 5(a), and ch5, 6<ch7, 8 in Fig. 5(b), it can be seen that between ch2 and ch1 (between ch5 and ch6) And there is an abnormal part near the ch2 (ch5) side. In addition, for example, since the signal strengths of ch5 and ch6 are weaker than the signal strengths of ch2 and ch1, it can be seen that the abnormal site exists at a relatively shallow position.

The calculation circuit 426 compares the analyzed signal intensity distribution of the approaching position with the signal intensity distribution of the outer peripheral position, and calculates a reference position (for example, the light irradiation unit 400 ) relative to the existing abnormal part as shown in FIG. 5( c ). In terms of three-dimensional direction and distance. Specifically, the light intensity signal in the normal tissue obtained as a function of the distance between the light irradiation unit 400 and the light detection unit 401 is used as a reference value, and the other The reference value of the position of the photodetector 401 is normalized. The normalized reference value is used as a coefficient of the light intensity at the position of each light detection unit 401, the difference between the light intensity signal actually measured by each light detection unit 401 and the light intensity reference value is obtained, and the difference and the light intensity reference value are calculated. The ratio is used as the rate of change, and the azimuth and approach state of the abnormal part are calculated according to the rate of change and position information. Then, the X-coordinate of each photodetector 401 is multiplied by the rate of change, and the sum or average value of the multiplied result is obtained as the X-direction component. Also, the Y-direction component and the Z-direction component were obtained in the same manner. The orientation angle (orientation information) of the abnormal site is generated by obtaining the orientation angle of the direction vector obtained by combining the components obtained as a result. Then, the X coordinates, the rate of change, and the coefficients of the respective photodetectors 401 are multiplied to obtain absolute values, and these are combined to obtain an X component. Similarly, the Y-direction component and the Z-direction component are obtained. The three-dimensional distance based on the light irradiation part 400 of the abnormal part is calculated using the value obtained by summing up the absolute values in each direction.

The support information generation unit 44 generates support information for instructing and guiding the movement of the ultrasound probe 12 based on the obtained three-dimensional orientation and three-dimensional distance in order to arrange the abnormal part in the ultrasound scanning area. The generated support information is displayed on the monitor 14 in a predetermined form. In addition, specific examples of support information will be described in detail later.

The operator moves the ultrasonic probe 12 according to the guidance of the displayed support information, and measures the three-dimensional orientation and distance of the abnormal part again. As a result, when it is determined that the abnormal site falls within an appropriate range (for example, it is determined that the abnormal site falls in the center of the ultrasonic scanning area), ultrasound imaging is started.

(support information)

FIG. 7 shows an example of support information displayed on the monitor 14 when the degree of adhesion to the breast and the three-dimensional orientation and distance of the abnormal site are measured in breast cancer examination. In the example in this figure, the degree of closeness of the ultrasonic transceiving surface 120 to the breast surface is displayed by the intensity of the image. For example, in the screen, the darker part on the lower right indicates a region with relatively low signal strength. In addition, the estimated depth of the abnormal part on the right side of the figure shows a zero position, indicating that the reason for the decrease in strength is the surface. According to the two displays, it is revealed that in the area of low signal strength, the detector floated from the surface of the biological body. According to the guidance of the displayed support information, the operator presses down the lower right side of the detector strongly in order to make the darker area have the same brightness as the other areas.

FIG. 8 is a modified example of the support information displayed on the monitor 14, in which detection failures are displayed with cross marks based on the calculated probe adhesion degree. In the example of the figure, the cross marks are concentrated on the lower right of the screen, so it can be seen that the detection surface of the photodetection unit 401 corresponding to the cross has a low degree of adhesion to the surface of the subject. The operator visually recognizes the displayed support information, and according to the guidance, performs an operation of pressing the lower right side of the detector strongly to increase the degree of closeness to the detection defect.

According to the support information shown in FIG. 7 or FIG. 8, the ultrasonic probe 12 is operated, and after the closeness between the probe 12 and the surface of the object falls within an appropriate range, the orientation information of the abnormal part and the information for relative The moving direction and moving amount of the ultrasonic probe 12 are more preferably arranged at the abnormal site as support information.

FIG. 9 is a diagram showing an example of support information for the purpose of primary guidance for positioning an abnormal site within an ultrasonic scanning region. By moving the ultrasonic probe 12 in the direction of the arrow and the distance (the length of the arrow) shown in the figure, the operator can easily arrange the abnormal part in the ultrasonic scanning area. FIG. 10 shows the signal amount for the light from the abnormal part after the ultrasonic probe 12 is moved according to one guide (when a plurality of photodetectors 401 detect the light from the abnormal part, the signal amount is and) A diagram of an example of support information for the purpose of maximizing secondary guidance. Through this secondary guidance, the ultrasonic probe 12 is moved so as to maximize the signal amount through the depth of the abnormality. By performing such step-by-step guidance, more signals can be obtained from abnormal parts than before.

FIG. 11 shows the absorption signal intensity (or attenuation signal intensity) of each photodetector 401 calculated based on the signal intensity of the detected light of each photodetector 401, and displayed on the level meter as support information. ) examples. In this figure, it can be seen from the balance of the signal intensity that the abnormal part exists near the light source.

FIGS. 7 to 11 exemplify cases in which support information indicating the degree of adhesion of the probe, the moving direction and amount of movement of the ultrasonic probe, and the like are output as images on the monitor 14 . On the other hand, it is also possible to output support information by a sound signal.

FIGS. 12( a ) and ( b ) show an example of support information output as a sound signal. In the example of FIG. 12( a ), the current adhesion degree of the photodetection unit 401 (or the ultrasonic wave transmitting and receiving surface) is notified to the operator in the periodicity of sound. For example, when all photodetectors 401 are judged to be non-contact, it is the silent state of the upper segment, and when at least one photodetector 40 is judged to be non-contact, the intermittent sound of the middle stage is output, and all photodetectors 401 When it is judged that the closeness is appropriate, the continuous sound of the lower stage is output. In addition, in the example of FIG.12(b), the approach information of an abnormal part is notified by the pitch of a sound (frequency). For example, as the detector approaches the abnormal part, the continuous sound output in the cycle shown in the upper part of FIG. 12( b ) is lowered in frequency as shown in FIG. 12( b ). Such support information based on the sound signal has an advantage that the operator can receive scanning guidance without looking at the monitor 14 . In addition, without being limited to this example, for example, by controlling the volume, tuning, tempo, melody, voice, etc., the support information can be output as a sound signal.

(configuration modification)

Next, a modified example of the arrangement of the light irradiation unit 400 and the light detection unit 401 with respect to the ultrasound probe 12 will be described.

FIG. 13 is a modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, the light irradiation part 400 (light source) is arranged on the central axis (symmetry axis) of the longitudinal direction of the ultrasonic wave transmitting and receiving surface 120, and the plurality of photodetecting parts 401 are arranged radially with respect to the light source. And they are arranged on double concentric circles so as to be line-symmetrical with respect to the central axis of the ultrasonic probe 120 . By making the axis of arrangement symmetry of the photodetector 401 substantially coincide with the central axis of the ultrasonic probe 12 (or making the axis of symmetry of the arrangement of the photodetector 401 fall within the range of the device width of the ultrasonic probe), two kinds of problems can be eliminated. The relative position error of the detection system, so, compared with Fig. 6, the configuration is better. In addition, since the maximum distance from the light irradiation part 400 to the light detection part 401 is required to be twice or more than the measurable depth of the abnormal part, the probe P as a whole tends to be larger. However, by arranging the light irradiation unit 400 at a position close to the center axis of the ultrasonic probe 12 as in this modified example, the overall size of the probe P can be reduced compared to the example of FIG. 6 .

FIG. 14 is another modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, the photodetectors 401 are arranged symmetrically so as to be long in the axial direction of the ultrasound probe 12 . With this arrangement, the overall width of the probe P can be suppressed, so that the scanning operation of the ultrasonic probe 12 is facilitated.

FIG. 15 is another modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, a plurality of light irradiation units 400 are symmetrically arranged on both ribs of the ultrasonic probe 12 . In addition, the plurality of photodetectors are arranged radially with respect to the centers of the plurality of light sources and line-symmetrically with respect to the central axis of the ultrasonic probe 12 . By aligning the axes of the optical measurement system and the ultrasonic probe 12, the relative position error of the two detection systems can be eliminated. Therefore, this embodiment is more convenient in arrangement than the example of FIG. 6 . In addition, selective detection using a plurality of light irradiation units 400 and a plurality of light detection units 401 substantially increases the distance from the light source, and has the advantage of being able to detect the presence of an abnormality over a wide range with a single light source.

FIG. 16 is another modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, a plurality of light irradiation units 400 are arranged symmetrically on both sides of the ultrasonic probe 12 , and other light irradiation units 400 are arranged on the central axis of the ultrasonic probe 12 . In addition, the plurality of photodetectors 401 are arranged radially with respect to the centers of the plurality of light sources and line-symmetrically with respect to the central axis of the ultrasound probe 12 . Also in this modification, the axes of the optical measurement system and the ultrasonic probe 12 are aligned, thereby eliminating the relative positional error of the two detection systems, and therefore, compared with the embodiment of FIG. 6 , the configuration is superior. In addition, there is an advantage of being able to detect the presence of abnormal parts in a wider range by using a plurality of light sources. In addition, more information can be obtained at the same time by adopting a structure that changes the wavelength of the output light of multiple light sources on both ribs of the probe and other light sources on the central axis of the ultrasonic probe 12 .

FIG. 17 is another modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, a plurality of ultrasonic probes 12 (two are illustrated in FIG. 17 ) are arranged in series so that their central axes are aligned, and at least one light irradiation unit 400 is arranged in the center of the gap. Also in this modification, the axes of the optical measurement system and the ultrasonic probe 12 can be aligned to eliminate the relative positional error of the two detection systems, so that the configuration is superior to that of the embodiment shown in FIG. 6 . In addition, by positioning the light irradiation unit 400 at the center of the arrangement of the plurality of ultrasound probes 12, there is an advantage of being able to detect the presence of an abnormality in a wide range.

FIG. 18 is another modified example of the arrangement shown in FIG. 6 . In the modified example shown in the figure, the photodetectors 401 are arranged so as to be densely packed near the final guiding position of the abnormal site. In this modification, the axes of the optical measurement system and the ultrasonic probe 12 are aligned to eliminate the relative position error of the two detection systems, so that the configuration is superior to that of the embodiment shown in FIG. 6 . In addition, locally densely arranging the photodetectors 401 has the advantage of being able to spatially and more accurately detect light absorption information of an abnormal site.

In each of the examples described above, the case where the plurality of photodetectors 401 are arranged in two concentric circles was exemplified. However, the present invention is not limited to these examples, and the photodetectors 401 may be arranged on two or more concentric circles.

According to the ultrasonic diagnostic apparatus according to the present embodiment described above, the following effects can be achieved.

First, the effect on the degree of adhesion between the photodetection unit and the surface of the subject. That is, in biological optical measurement, when the photodetector is not in close contact with the subject, reflection loss may occur on the detection surface (light incident part) of the photodetector, and may occur on the order of 10% at most. Loss. On the other hand, the difference caused by the absorption of the abnormal part is on the order of %, so the difference in signal caused by the above-mentioned poor arrangement of the photodetector is even larger. Therefore, it is conceivable that whether or not the degree of adhesion between the photodetection unit and the living body is appropriate is information that should be confirmed before detection of an abnormal site. According to this ultrasonic diagnostic apparatus, the degree of adhesion between the probe and the surface of the object is calculated using the bio-optical measurement function, and based on the result, support information for guiding the probe to a better position is generated and output. The operator grasps the current state of contact between the probe and the surface of the subject, and in the case of incomplete adhesion, can easily and quickly adjust the posture, orientation, pressurization direction, and movement of the probe according to the guidance of the support information. Orientation etc. are corrected.

Second, the effect of effective use of depth information on abnormal parts. Abnormalities present near the surface of the skin are different in relative position to the detector from which the maximum signal is obtained compared to abnormalities present at a depth of several centimeters (cm). In addition to azimuth calculations for the depth of anomalies, position guidance should also be appropriately performed. According to the ultrasonic diagnostic apparatus according to the present embodiment, the three-dimensional orientation and distance of the abnormal part in the subject are calculated using the biological optical measurement function, and based on the result, the abnormal part is placed at a good position in the ultrasonic scanning area. In this way, support information for guiding the position of the ultrasonic probe is generated and output. The operator can intuitively grasp the current positional relationship between the ultrasonic probe and the abnormal part, and if the abnormal part does not exist in the ultrasonic scanning area, the operator can follow the guidance of the support information so that the abnormal part is included in the ultrasonic scan The method within the area can easily and quickly correct the position, posture, orientation, etc. of the ultrasonic probe.

Third, about the alignment (alignment) effect of the ultrasonic detector and the optical detection system. In this embodiment, the ultrasound probe, at least one light irradiation unit, and the plurality of light detection units are arranged such that the symmetry axes of the light irradiation unit and the plurality of light detection units are located within the ultrasound transmission and reception plane. As a result, it is possible to correct a subtle error generated between the optimal position guided by the signal analysis of the optical system and the position where the image is observed by the ultrasonic echo.

As described above, regardless of the operator's experience, etc., it is possible to always obtain a good ultrasonic image of the abnormal part in a state where the ultrasonic transmitting and receiving surface is in good contact with the surface of the subject, which contributes to the improvement of ultrasonic image diagnosis. the quality of.

(Second Embodiment)

FIG. 19 is a block configuration diagram of a biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the second embodiment. In the ultrasonic diagnostic apparatus 1 according to the present embodiment, the light source 420 generates light of a specific wavelength absorbed by the abnormal site, and calculates the degree of adhesion, specifies the three-dimensional orientation of the abnormal site, and the like using the light. In addition, in the arithmetic circuit 426, an ultrasonic image is taken in from the ultrasonic imaging system, for example, the position of the abnormal part in the ultrasonic scan area image is estimated based on the change of the brightness value on the ultrasonic image, and by using the estimated position, We perform improvement of positional accuracy in bioluminescence measurement and precision identification of abnormality of part. By using the biological optical measurement system and the ultrasonic imaging system in combination in this way, it is possible to more accurately calculate the degree of adhesion, specify the three-dimensional orientation of the abnormal site, and the like.

(third embodiment)

FIG. 20 is a block configuration diagram of the biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the third embodiment. The biological optical measurement device 4 shown in this figure includes two light sources, a light source 420a and a light source 420b. The light source 420a has a wavelength light with small absorption and high transmittance of the subject when an abnormality occurs, and the light source 420b generates an abnormality. The specific wavelength light absorbed by the site; and the light mixer 421, which mixes the light of the two light sources. In this configuration, by relatively comparing the amount of detected light at a wavelength with high transmittance of the subject and a specific wavelength, it is possible to separate the effect of the degree of adhesion of the photodetector 401 from the effect of absorption due to an abnormal site. Furthermore, by normalizing the detected light quantity of a specific wavelength with the detected light quantity of the wavelength transmitted through the subject, it is possible to reduce measurement errors caused by variations in the degree of adhesion between the ultrasonic probe 12 and the subject.

In addition, the biological optical measurement device 4 shown in FIG. 20 has calculation circuits 426a and 426b. For example, when guiding the ultrasonic probe 12, the calculation circuit 426a performs simple calculations for specifying the degree of adhesion and the orientation of abnormal parts. , On the other hand, at the time of abnormal identification, in the arithmetic circuit 426b, precise calculations for determining the degree of closeness and the orientation of the abnormal part are performed. However, if the calculation circuit 426a or the calculation circuit 426b has sufficient calculation speed and calculation capability, either one of the calculation circuits may be used to guide the ultrasound probe 12 .

FIG. 21 shows an example of a procedure for determining the degree of adhesion and determining the orientation of an abnormal site using the optical biometric measurement device 4 shown in FIG. 20 . As shown in the figure, the light irradiation unit 400 alternately emits a wavelength with high transmittance of the subject and a specific wavelength absorbed by the abnormal part into the living body. As described above, in the photodetector 401 separated from the surface of the subject, part of the signal light emitted from the subject is reflected on the surface due to the difference in refractive index, thereby reducing the incident light intensity to the detector. .

Then, as shown in FIG. 21( a ), when the measurement signal intensity is small compared with the preset light intensity signal level using a wavelength with high transmittance of the subject first, it is determined that the position is The photodetector 401 is away from the surface of the subject. Support information is generated and displayed based on the adhesion degree determination result, thereby providing instructions and guidance for applying pressure in a direction in which the entire probe is in close contact with the subject. As a result, as shown in FIG. 21( b ), the pressure applied by the photodetection unit 401 to the surface of the subject is adjusted.

Next, as shown in FIG. 21( c ), the specific wavelength absorbed by the abnormal part is incident into the living body, and the emitted light is detected by each light detection unit 401 . The rate of change in the amount of detection light due to the degree of adhesion is the same in the case of a wavelength with high transmittance of the living body and in the case of a specific wavelength absorbed by an abnormal part, and the difference between the two is very large. Small. Significant differences in the detection light quantities of the two wavelengths are caused by the presence or absence of an abnormal site. Therefore, after normalizing the amount of light of a specific wavelength absorbed by the abnormal site by light of a wavelength with high transmittance in the living body, the three-dimensional dimension of the abnormal site in the subject is obtained by the same method as in the first embodiment. The azimuth and distance, generate azimuth information and distance information. Support information is generated and displayed based on the orientation information and distance information, thereby instructing and guiding the moving direction and pressurizing direction of the entire ultrasonic probe 12 . As a result, when it is determined that the probe measurement position is within an appropriate range, ultrasound imaging is started.

(Fourth embodiment)

FIG. 22 is a block configuration diagram of the biological optical measurement device 4 included in the ultrasonic diagnostic device 1 according to the fourth embodiment. The biological optical measurement device 4 shown in this figure is based on the example shown in FIG. 20 , and the ultrasonic image obtained by ultrasonic imaging is taken in as data in the optical calculation, and the improvement of the positional accuracy and the abnormality of the site can be realized. precision identification. In this embodiment, the measurement is completed in the following order: guidance of the probe related to the degree of adhesion, guidance of the ultrasonic probe 12 to the abnormal site, imaging of ultrasonic images, precise optical measurement, and comparison of ultrasonic images and optical data. Link and recalculate, correct image formation. In addition, in the example shown in FIG. 22, the operation circuit 426a, which is a simple calculation circuit, is usually used in the guidance of the ultrasonic probe 12, but when the signal strength is high, the operation circuit 426a as a precision calculation circuit may be selected. Operation circuit 426b.

In each of the above-described embodiments, it has been described that bioluminescence measurement is performed by manual operation. On the other hand, bioluminescence measurement can also be performed by automatic operation.

(fifth embodiment)

The ultrasonic diagnostic apparatus 1 according to the fifth embodiment can more quickly calculate the position and size of an abnormal site in the subject, and can clearly display it on an ultrasonic image.

FIG. 23 is a view of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment viewed from the subject contact surface side, and is a view showing an arrangement example of the light irradiation unit 400 and the light detection unit 401 . As shown in the figure, the light irradiation units 400 are arranged around the ultrasonic transmitting and receiving surface 120 on the central axis C in the longitudinal direction of the ultrasonic transmitting and receiving surface 120 . In the present embodiment, the light irradiation unit 400 irradiates the subject with light of two wavelengths simultaneously or selectively. A plurality of photodetectors 401 are arranged in pairs around the ultrasonic transceiving surface 120 with the central axis C in the longitudinal direction of the same ultrasonic transceiving surface as a symmetrical axis, and arranged radially around the light irradiation unit 400 . In addition, in the example of the figure, the plurality of photodetectors 401 are on the concentric circles of radii r1, r2, r3 (for example, r1=15mm, r2=25mm, r3=35mm, etc.) centered on the photoirradiation part 400, Three pairs (three sets) of photodetectors 401 are arranged axisymmetrically with respect to C on the central axis. In addition, the light irradiation unit 400 and each light detection unit 401 are covered by a light shielding plate 403 .

In addition, the arrangement of the light irradiation unit 400 and the plurality of light detection units 401 is not limited to the example shown in FIG. 23 , and various forms can be adopted. That is, as long as the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment has a configuration in which the ultrasonic scanning plane substantially coincides with the axis of symmetry (plane of symmetry) on which the plurality of photodetectors 401 are arranged, or the arrangement of the optical sensors is symmetrical, The configuration in which the axis falls within the range of the equipment width of the ultrasonic echo probe (or the width of the ultrasonic transmitting and receiving surface 120 in the short side direction) is sufficient, and it is optional.

In addition, the biological optical measurement device 4 according to the present embodiment further includes a storage unit for storing a database for specifying the position and size of the abnormal site in the ultrasonic scanning section. This storage unit may be either an internal memory or an external memory, but an embodiment in which the semiconductor memory in the device is used for storage is preferable in view of the need for faster processing and the required memory capacity. About other structures, it is substantially the same as that shown in FIGS. 20 and 22 . The database is created in advance for each combination of the position and size of the abnormality in the ultrasonic scanning plane of the ultrasonic probe 12 and the intensity of light detected by each light detecting unit 401 for each optical absorption coefficient (k). corresponding database. The calculation circuits 426a and 426b perform calculations for comparing the intensity of light actually detected by each light detection unit 401 with the value stored in the database in advance, and specify the position and size of the abnormal part in the ultrasonic scanning plane.

From the light irradiation unit 400 arranged as shown in FIG. 23 , light of two specific wavelengths (for example, the absorption wavelength of oxidized hemoglobin (near 770 nm) and the absorption wavelength of oxidized hemoglobin (near 770 nm) and deoxygenated Hemoglobin absorbs light of 2 wavelengths (around 900nm). The irradiated light propagates while being scattered in the subject, and is absorbed more when passing through the abnormal part. The plurality of photodetectors 401 arranged as shown in FIG. 23 detect light emitted from the subject at respective positions. The light detected by each light detection unit 401 includes depth information of the abnormal part. The light analysis unit 424 analyzes the light detected by each light detection unit 401 . The calculation circuits 426a and 426b calculate the degree of adhesion between the photodetection unit 401 and the surface of the subject and the position of the abnormal part showing a predetermined light absorption coefficient in the subject based on the change in the intensity of the detected light between the photodetectors 401 , size (dimensions).

The calculation circuits 426a and 426b calculate the degree of adhesion between the photodetector 401 and the surface of the subject based on the intensity change of the detected light between the photodetectors 401 based on the algorithm described above, and display a predetermined light absorption coefficient in the subject. The depth between the abnormal part and the surface of the subject, and the three-dimensional position and distance of the abnormal part based on the predetermined position. The calculation result in the arithmetic circuit 426 is sent to the support information generation unit 44 . The support information generation unit 44 generates support information for instructing and guiding (navigation) the position, posture, orientation, etc. of the ultrasonic probe 12 according to the above-described method. The generated support information is displayed in a predetermined form on, for example, the monitor 14 . According to the displayed support information, the operator moves the ultrasonic probe 120 so that the ultrasonic transmitting and receiving surface 120 comes directly above the abnormal part showing a predetermined light absorption coefficient. In addition, there are various types of display forms of the support information for moving the ultrasonic transmission/reception surface 120 directly above the abnormal site. This will be described in detail in the sixth embodiment.

On the surface of the subject, in such a manner that the ultrasonic transceiving surface 120 comes directly above the abnormal part showing a predetermined light absorption coefficient (or the abnormal part is located on the symmetry plane below the long-side symmetry axis of the ultrasonic probe 12), The ultrasonic probe 120 is configured. As a result, when the position of the ultrasonic probe 12 is determined to be within an appropriate range, calculation of the position and size of the abnormal site is performed by the method described below.

FIG. 24 is a diagram schematically showing the position and size of the probe P and the abnormality identified on the ultrasonic scanning section when the abnormality is approximated as a sphere. The center position (x, y) of the sphere, the size (diameter φ), and the level of the optical absorption coefficient (k) are used as parameters, and the light diffusion equation is treated as a forward problem (forward problem) to solve the light at the position of each photodetector. As for the intensity, data associating the solution with the light absorption information is stored in advance in the storage unit of the biological optical measurement device 4 as a database. When the light-absorbing region is approximated by the simplest spherical shape, it can be solved by the approximate solution of the analytical deformed Bessel function. However, in the case of more complex shapes, it is difficult to solve it analytically. . Then, an approximate value is obtained by using a light diffusion equation simulation with scattering using a finite element method. The database is capable of selecting appropriate levels of parameters to perform calculations, based on which the tables are made. Here, simulation is exemplified as a method of creating a table of light intensity, but there are also methods of creating a phantom that summarizes the levels of each parameter, and determining the numerical value through actual measurement, and using the actual This is a method in which part of the measurement data is combined with the simulation results to create it. Therefore, in the case of spherical approximation, the four unknowns to be solved are the position (x, y) on the cross-sectional screen of the living body, the diameter (φ), and the optical absorption coefficient (k), and at least four quantities of light are required The measurement results. In the case of spheroid approximation, at least 5 photometric results are required. Here, the paired detectors are symmetrical in terms of the optical model, and the light intensities should have equal values, so the detection data are not regarded as independent values.

The calculation circuits 426 a and 426 b compare the numerical values preliminarily recorded in the database with the intensity of light detected by each light detection unit 401 . As a means of comparison, there is, for example, a selection method under the method of least squares. In this case, since the light intensity at each detector position changes by number of digits, it is necessary to use normalized relative intensity changes after normalization using the light intensity of the case where there is no light-absorbing site, and so on. The comparison between the value of the database and the intensity of the detected light can be instantaneously calculated in seconds or less. Therefore, information on the position (x, y), diameter (φ), and optical absorption coefficient (k) of the abnormal absorption site can be grasped in real time.

That is, in this embodiment, instead of using the intensity of light detected by each light detection unit 401 to calculate the position and size of an abnormal site in the subject as an inverse problem (see the first embodiment, etc.), The database stored in the storage unit and the intensity of light actually detected by each light detection unit 401 are used as a positive problem to calculate the position and size of the abnormal site in the subject. Such a calculation method is particularly practical when, for example, real-time performance is important. However, it is not limited to this example, and it is of course possible to employ the algorithm as the inverse problem described in the first embodiment and the like. In addition, if necessary, it is also possible to prepare light of other wavelengths transmitted from the subject, sense the light as reference light, and standardize the measured light quantities of other wavelengths, thereby reducing measurement errors caused by various variations. error.

The calculated position and size of the abnormal site are displayed on the ultrasonic image in a predetermined form in real time. FIG. 25 is a diagram showing an ultrasound image corresponding to an ultrasound scan section, and FIG. 26 is a diagram for explaining a display form of an abnormal site whose position and size are specified on the ultrasound image. On the ultrasonic image shown in FIG. 25, if the position and size of the abnormal part are calculated, the determined position (center (x, y)) and size (diameter φ) of the circle. Accordingly, the observer can intuitively grasp the approximate position and size of the abnormal site in real time on the ultrasonic image. In addition, by recording an ultrasonic image showing an abnormal site, image diagnosis can be performed using the ultrasonic image in which the abnormal site is necessarily visualized.

(Modification 1)

FIG. 27 is a view of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment viewed from the subject contact surface side, and shows Modification 1 of the arrangement of the light irradiation unit 400 and the light detection unit 401 . The light irradiation units 400 are arranged on the central axis C in the longitudinal direction of the ultrasonic transmission/reception surface 120 , and emit light of a specific wavelength (not two wavelengths) of light. In addition, four pairs (four sets) of photodetectors 401 are provided with the central axis C in the longitudinal direction of the ultrasonic wave transmitting and receiving surface as a symmetrical axis. Thereby, it is possible to obtain information on the position and size of the abnormal site and the optical absorption coefficient (k) without using light of two wavelengths.

(Modification 2)

FIG. 28 is a view of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment viewed from the subject contact surface side, and shows Modification 2 of the arrangement of the light irradiation unit 400 and the light detection unit 401 . As shown in the figure, the two light irradiation units 400 are adjacently arranged at different positions on the central axis C in the longitudinal direction of the ultrasonic wave transmitting and receiving surface 120 . In addition, two pairs (two groups) of photodetectors 401 are provided with the central axis C in the longitudinal direction of the ultrasonic wave transmitting and receiving surface as a symmetry axis. Also in this modified example, it is possible to obtain information on the position and size of the abnormal site and the optical absorption coefficient (k) without using light of two wavelengths. In addition, compared with the examples shown in FIGS. 23 and 25 , there is an advantage that the number of photodetectors 401 can be further reduced.

(Modification 3)

29 is a view of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment viewed from the subject contact surface side, and is a view showing Modification 3 of the arrangement of the light irradiation unit 400 and the light detection unit 401 . As shown in the drawing, the two light irradiation units 400 are arranged on the central axis C in the longitudinal direction of the ultrasonic transmitting and receiving surface 120 so as to sandwich the ultrasonic transmitting and receiving surface 120 . In addition, two pairs (two groups) of photodetectors 401 are provided with the central axis C in the longitudinal direction of the ultrasonic wave transmitting and receiving surface as a symmetry axis. Also in this modified example, it is possible to obtain information on the position and size of the abnormal site and the optical absorption coefficient (k) without using light of two wavelengths. In addition, like Modification 2, there is an advantage that the number of photodetection units 401 can be further reduced compared to the examples shown in FIGS. 23 and 25 . Furthermore, by arranging the light irradiation units 400 at both ends of the ultrasonic probe 12 , there is an advantage that it is easy to guide the abnormal part to the vicinity of the center on the central axis C of the ultrasonic transceiving surface 120 .

According to the configuration as above, it is possible to guide (navigate) the probe above the suspicious tissue in the subject and obtain ultrasonic images and perform biophotometry while the suspicious tissue is included in the scanning section. Measurement. Therefore, using the detected light, the position and size of the suspicious tissue can be calculated simply and quickly as a direct problem of comparing the intensity of the light detected by each detection unit with the database generated in advance, which can be significantly improved. improve real-time performance. The operator can perform the placement of the probe directly above the suspicious tissue in the subject, the visual inspection of the cross-section of the ultrasonic image, and the blood metabolism information (hemoglobin content) clearly shown on the ultrasonic image in real time with high timing. Absorption position, size, absorption coefficient, etc.) Observation and judgment of benign and malignant. As a result, regardless of proficiency, anyone can perform breast cancer examination and judgment (detection of abnormal site, judgment of benignity and malignancy) etc. accurately, appropriately and quickly.

In addition, in biological optical measurement, the maximum distance from the light irradiation part to the light detection part is required to be twice or more the measurable depth of the abnormal part, so the overall probe tends to be larger. In the present embodiment, the light emitting unit and the light detecting unit are arranged near the ultrasonic probe as the central axis of the ultrasonic transmitting and receiving surface in the longitudinal direction, so that the ultrasonic probe and the photodetector can be integrated. The overall size of the detector becomes small and compact.

(sixth embodiment)

In each of the above-described embodiments, as the means of guiding the probe to the abnormal part or transmitting the good adhesion of the probe, for example, the display method shown in FIGS. 7 to 10 or the display method shown in FIG. The method of transmitting sound signals, etc. However, during actual imaging, the examiner moves the probe while observing the ultrasonic image, so it may be a heavy burden to also watch the probe operation support information as shown in FIG. 7 and the like. In addition, transmission based on sound signals has the advantage that the examiner can receive scanning guidance without looking at the screen, but also has the disadvantage that the examinee becomes disturbed by abnormal sounds.

Therefore, in the present embodiment, the ultrasonic diagnostic apparatus 1 is described in which the information indicating the proximity state of the probe to the abnormal site specified by the bioluminescence measurement is reduced as much as possible to the examiner's attention load, Immediately visualized display makes it easy to guide the detector to the anomaly.

In the present embodiment, the display form of the information showing the proximity state of the probe to the abnormal site and the support information for the probe operation has, for example, the following two features. First, information indicating the proximity state of the probe to the abnormal site is displayed as a part of the screen of the ultrasonic image that the examiner focuses on. Thereby, the examiner can obtain information without reciprocating the line of sight. Second, the information indicating the proximity state of the probe to the abnormal site is displayed in a form that can instantly grasp the contents without hindering the examiner's action of concentrating on the ultrasonic diagnostic image.

FIG. 30 is a diagram showing a state in which the proximity state of the abnormal site specified by bio-optical measurement and the probe is displayed as a part of the ultrasound image screen (for example, an icon or the like). FIGS. 31( a ) to ( d ) are diagrams illustrating how the brightness of the icon changes as the detector approaches the identified abnormal site.

The brightness of the icon A displayed on the upper right of the ultrasonic image screen shown in FIG. 30 changes as the detector approaches the identified abnormal part as shown in FIGS. When it is close to the abnormal part (that is, when the ultrasonic transmitting and receiving surface 120 is arranged directly above the abnormal part), it is brightest as shown in FIG. 31( c ). In addition, when the ultrasonic transceiving surface 120 moves away from the abnormal part, the brightness of the icon A changes from the state of FIG. 31(c) to the state of FIG. 31(d). And gradually darkened.

(Modification 1)

FIGS. 32( a ) to ( d ) are diagrams illustrating how the color of the icon changes as the detector approaches the identified abnormal site.

For example, when the color of the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. displayed in a predetermined hue (for example, green) as shown. If the detector is scanned according to the supporting information, and the distance between the abnormal part and the detector becomes within a certain range, the color of the icon A will change to other hues (such as orange) as shown in Figure 33(b). In the case of an abnormal part, it is displayed in red, for example, as shown in FIG. 33( c ). In addition, when the ultrasonic transceiving surface 120 moves away from the abnormal part, the brightness of the icon A changes from red in FIG. 33(c) to other colors corresponding to the distance between the abnormal part and the detector. (Green in the example of Fig. 33(d)).

(Modification 2)

The proximity state of the abnormal site identified by the biophotometric measurement to the probe may be expressed as a change in the on-off period of a part (icon, etc.) of the screen of the ultrasonic image. For example, the icon A displayed on the upper right of the screen of the ultrasonic image is turned on and off at a long period of not less than a certain period when the distance between the abnormal site specified by the bioluminescence measurement and the probe is at least a certain level. Scan the detector according to the information indicating the proximity of the detector to the abnormal part. As the distance between the abnormal part and the detector becomes smaller, the on-off period of the icon A becomes shorter. When the detector is closest to the abnormal part, the icon A turns on and off with the shortest cycle. In addition, when the ultrasonic transmission/reception surface 120 is separated from directly above the abnormal part, the icon A is turned on and off while changing the period according to the distance between the abnormal part and the probe.

(Modification 3)

FIGS. 33( a ) to ( d ) are diagrams illustrating how the display area of the icon changes as the detector approaches the specified abnormality site.

For example, the area of the icon A displayed on the upper right of the ultrasound image screen shown in FIG. The distance of the sensor becomes smaller and larger, and becomes the largest as shown in Fig. 33(c) when it is closest to the abnormal part. In addition, when the ultrasonic transmitting and receiving surface 120 moves away from the abnormal part, the area of the icon A decreases as the probe moves away from the abnormal part, as shown in Fig. 33(c) and Fig. 33(d). .

(Modification 4)

FIGS. 34( a ) to ( d ) are diagrams illustrating how the display positions of the icons change as the detector approaches the identified abnormal site.

For example, the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. 30, as shown in FIG. 34(a) and FIG. When the separation is greater than a certain amount, it is displayed at the same position, and when it is closest to the abnormal part (when the distance between the abnormal part and the detector is within a certain range), it is displayed on the Prescribed position (in the example of the figure, the display position goes up). In addition, when the ultrasonic transmitting and receiving surface 120 is separated by a certain amount or more from directly above the abnormal part, the icon A is displayed at the same position as in FIG. 34( a ) and FIG. 34( b ), as shown in FIG. 34( d ). .

(Modification 5)

FIGS. 35( a ) to ( d ) are diagrams illustrating how the amplitude of the vibration of the icon changes as the probe approaches the identified abnormal site.

For example, the vibration amplitude of the icon A displayed on the upper right of the ultrasound image screen shown in FIG. It changes as the distance from the detector gets closer, and when it is closest to the abnormal part, it is displayed as a swing with the largest amplitude as shown in Fig. 35(c). In addition, when the ultrasonic transmitting and receiving surface 120 moves away from directly above the abnormal part, the amplitude of the swing of the icon A decreases as the probe moves away from the abnormal part as shown in FIG. 35( d ).

(Modification 6)

FIGS. 36( a ) to ( d ) are diagrams illustrating how the shape of the icon changes as the probe approaches the identified abnormal site.

For example, the shape of the icon A displayed on the upper right of the ultrasound image screen shown in FIG. 30 is as shown in FIGS. 36( a ) and 36 ( b ). It changes as the distance of the device gets closer (in the example in the figure, the number of convex parts increases), and when it is closest to the abnormal part, it is displayed in a shape with the most convex parts as shown in Fig. 36(c). In addition, when the ultrasonic transmitting and receiving surface 120 moves away from the abnormal part, the shape of the icon A changes such that the number of convex parts decreases as the probe moves away from the abnormal part, as shown in FIG. 36( d ). .

Among them, various display examples for notifying the proximity state of the abnormal part and the detector are shown. Of course, these display methods can be combined arbitrarily. For example, in addition to the display method based on the color change of the icon shown in Modification 1, brightness changes may also be combined, and the on-off cycle, display area, shape, and swing size may be related to the approximate The state changes correspondingly at the same time. Thereby, the approach state of an abnormal part and a probe can be presented in the form with higher visibility.

According to the above-mentioned structure, the proximity state of the abnormal part in the subject and the probe on the surface of the subject can be displayed on the screen displaying the ultrasonic image through the brightness, color, on-off period, display area, and brightness of the icon. The shape, the amplitude of the oscillations, or a combination thereof, to provide visual cues. As a result, the examiner can visually recognize the ultrasound image and the probe operation support information without reciprocating the line of sight. In addition, the probe operation support information is presented as a change in the brightness of the icon or the like. Therefore, the examiner's attention to the ultrasonic diagnostic image is not hindered, and the probe operation support information that can be grasped quickly and easily is presented.

Several embodiments of the present invention have been described, and these embodiments are indicated as examples and are not intended to limit the scope of the invention. These new embodiments can be implemented in other various forms, and various omissions, substitutions, and changes can be made without departing from the gist of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and their equivalents.

Claims (19)

1. a diagnostic ultrasound equipment, wherein, possesses:

Ultrasonic detector, sends ultrasound wave from ultrasonic transmission/reception towards subject, is received in via described ultrasonic transmission/reception face the ultrasound wave being reflected in described subject;

Photo-detector, there is illumination part and multiple optical detection part, this illumination part is around described ultrasonic transmission/reception face, be arranged on the central shaft of long side direction of described ultrasonic transmission/reception face, from at least one position to described subject internal radiation light, the plurality of optical detection part, around described ultrasonic transmission/reception face, take the central shaft of the long side direction of described ultrasonic transmission/reception face as axis of symmetry is configured in diverse location, detects the light intensity being reflected in described subject;

Image generation unit, uses the ultrasound wave being received by described ultrasonic detector, generates ultrasonography;

Computing unit, the light intensity detecting based on described each optical detection part, calculating illustrates abnormal portion bit position and the size of the absorption coefficient of light of regulation in described subject; And

Display unit, shows the described ultrasonography that described abnormal portion bit position and size are expressed.

2. diagnostic ultrasound equipment as claimed in claim 1, wherein,

Also possess:

Memory element, by abnormal portion bit position and size in described subject, according to each combination of the light intensity of the position of described multiple optical detection parts, stores in advance;

Described computing unit, by the combination of light intensity and the combination of the light intensity of storing in described memory element that relatively detect in described each optical detection part, calculates abnormal portion bit position and the size of the absorption coefficient of light that regulation is shown in described subject.

3. diagnostic ultrasound equipment as claimed in claim 1 or 2, wherein,

Described multiple optical detection part is provided with at least four pairs take the central shaft of the long side direction of described ultrasonic transmission/reception face as axis of symmetry.

4. diagnostic ultrasound equipment as claimed in claim 1 or 2, wherein,

Described illumination part is from more than two position light irradiations,

Described multiple optical detection part is provided with at least two pairs take the central shaft of the long side direction of described ultrasonic transmission/reception face as axis of symmetry.

5. diagnostic ultrasound equipment as claimed in claim 1 or 2, wherein,

Described illumination part irradiates the light that comprises at least two kinds of frequencies,

Described multiple optical detection part is provided with at least three pairs take the central shaft of the long side direction of described ultrasonic transmission/reception face as axis of symmetry.

6. the diagnostic ultrasound equipment as described in any one in claim 1 to 5, wherein,

Also possess:

Approach information generating unit, based on described abnormal portion bit position and the size calculating, generate for representing the approach information of described ultrasonic transmission/reception towards the situation that approaches at described abnormal position.

7. diagnostic ultrasound equipment as claimed in claim 6, wherein,

Described display unit shows the described information that approaches together with described ultrasonography.

8. diagnostic ultrasound equipment as claimed in claim 7, wherein,

The described information that approaches is, the lightness of the part by making picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position changes, and represents the approach situation of described ultrasonic transmission/reception towards described abnormal position.

9. diagnostic ultrasound equipment as claimed in claim 7, wherein,

The described information that approaches is, by make the area change of a part for picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

10. diagnostic ultrasound equipment as claimed in claim 7, wherein,

The described information that approaches is, by make the light on and off frequency change of a part for picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

11. diagnostic ultrasound equipments as claimed in claim 7, wherein,

The described information that approaches is, by the amplitude variations that makes the part vibration of picture show corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

12. diagnostic ultrasound equipments as claimed in claim 7, wherein,

The described information that approaches is, by make the foxy of a part for picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

13. diagnostic ultrasound equipments as claimed in claim 7, wherein,

The described information that approaches is, by make the change in location of the icon on picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

14. diagnostic ultrasound equipments as claimed in claim 7, wherein,

The described information that approaches is, by make the change of shape of a part for picture corresponding to the distance between described ultrasonic transmission/reception face and described abnormal position, to represent the approach situation of described ultrasonic transmission/reception towards described abnormal position.

15. diagnostic ultrasound equipments as described in any one in claim 1 to 14, wherein,

The light intensity of described computing unit based on detecting in described each optical detection part, calculates the degree of being close on described each optical detection part and described subject surface,

This diagnostic ultrasound equipment also possesses:

Support information generating unit, based on the described degree of being close to calculating, generate the support information of the operation for supporting described ultrasonic detector; And

Support information output unit, export described support information.

16. diagnostic ultrasound equipments as claimed in claim 15, wherein,

Described support packets of information is containing the position of described ultrasonic detector, at least one in, posture, pressurization degree.

17. diagnostic ultrasound equipments as claimed in claim 15, wherein,

Described support packets of information is containing for so that the mode of the signal intensity sum maximum from described abnormal position that described multiple optical detection part detects configures the information of described photo-detector and described ultrasonic detector.

18. diagnostic ultrasound equipments as claimed in claim 1, wherein,

The variation of the light intensity of described computing unit based on described ultrasonography and described multiple optical detection part detections, calculates described abnormal portion bit position and size.

19. diagnostic ultrasound equipments as claimed in claim 1, wherein,

Described illumination part irradiation comprises the light as the first wave long component of the absorbing wavelength band at described abnormal position and the second wave length composition except the absorbing wavelength band at described abnormal position,

The detection light intensity that described computing unit comparison is caused by described first wave long component and the detection light intensity being caused by described second wave length composition, calculate described abnormal portion bit position and size.

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