JP6659766B2 - Optical measuring device and ultrasonic diagnostic device - Google Patents

Description

  Embodiments of the present invention relate to an optical measurement device and an ultrasonic diagnostic device.

  There are various techniques for noninvasively measuring the inside of a living body. Optical measurement, which is one of them, has an advantage that a compound to be measured can be selected by selecting a wavelength without a problem of exposure. A general biological light measurement device irradiates the inside of a living body through the skin by pressing the light irradiation unit against the surface of the living skin, and measures the transmitted or reflected light that has passed through the skin again and exited outside the living body. Various biological information is calculated based on the Underlying the determination of the presence of abnormal tissue inside a living body by optical measurement is based on the difference in light absorption coefficient from normal tissue. That is, since the absorption coefficient of the abnormal tissue differs inside the living body, a difference in the detected light amount occurs according to the difference in the absorption amount. That is, if the inverse problem is solved from the detected light amount, the absorption coefficient of the abnormal tissue can be obtained, and the properties of the abnormal tissue can be determined from the obtained absorption coefficient. In addition, the measurement position and depth are analyzed using the measured light. In this analysis method, the method of adjusting the distance between the light irradiation unit (hereinafter abbreviated as light source) and the detector (spatial resolution method), and the difference in time of light arrival using a light source whose intensity changes over time (Decomposition method) that obtains depth information from, and a method combining these methods. With these analysis methods, a biological optical measurement device that can acquire a high-quality signal is realized. However, imaging of information using light in a living body has a problem with low spatial resolution. Furthermore, in order to obtain correct position information from the detection result of the reflected light, it is necessary to calculate a large amount of data with a complicated algorithm, and it cannot be determined in real time.

  One application that is considered highly feasible in living body optical measurement is breast cancer testing. However, as described above, there is a problem in resolution and analysis time in optical measurement alone. Therefore, a method for improving inspection performance in combination with another modality is desirable. Therefore, we proposed a method to compensate for the low spatial resolution of light using the morphological information of ultrasonic echo. According to this method, it is expected that the morphological feature in the living tissue and the component distribution of the morphological feature portion can be determined in a shorter time than before, but there is still room for improvement in the immediate determination.

  By the way, breast cancer is one of the leading causes of death in women. Screening and early diagnosis of breast cancer has tremendous value in reducing mortality and controlling health care costs. Current methods involve palpation of breast tissue and x-rays to look for suspicious tissue deformation. If there is a suspicious spot on the radiograph, an ultrasound image is taken and a surgical histology is performed. These series of tests take a considerable amount of time to reach the final conclusion. In addition, there is also a problem in that the young people before menopause have many mammary glands and it is difficult to obtain sensitivity in X-ray photography. Therefore, screening by ultrasonic imaging is particularly significant for young people.

  In general, in ultrasonic imaging, a still image of an ultrasonic image is collected by a certified operator, and a judgment is made based on morphological information on the image by a specialized interpreter (there may be a plurality of images). Considering the risk of oversight due to operator fatigue and reduced concentration during screening, screening by one operator is limited to a maximum of 50 persons per day.

  In capturing an ultrasonic image, knowledge and experience of an operator are very important to capture a still image capturing morphological features. Accurate and rapid screening also requires proficiency. For example, the test time per subject is typically 5 to 10 minutes, but it may take longer depending on the skill of the operator. That is, in the current screening by ultrasonic imaging, the accuracy of image acquisition may vary depending on the skill level of the operator. Furthermore, when taking an image, it is necessary to watch the image at all times, and since it is left to the judgment of the operator alone, even a skilled operator has a large mental burden. There is also a method of collecting all image information in a moving image, but in this case, the burden on the image reader becomes large.

  In order to solve such problems in ultrasonic image diagnosis, a method has been proposed in which the measurement position of an ultrasonic probe is guided in a plane direction by metabolic information of a living body obtained by living body optical measurement, thereby reducing the burden on a technician. Proposed. With such a method, it is possible to relatively easily detect and determine an abnormal portion in a short time and in comparison with the related art in ultrasonic imaging.

JP 2004-073559 A JP 2009-247683 A JP 2000-237196 A JP 2005-331292 A JP-A-2007-020735 JP 2009-077931 A

  However, there is still room for improvement in ultrasonic probe position guidance for ultrasonic imaging using living body optical measurement.

The optical measurement device according to the present embodiment is used together with an ultrasonic probe, and includes a light irradiation unit, a plurality of pairs of light detection units, and an output unit. The light irradiating unit irradiates the subject with light from at least one position. The plurality of pairs of light detectors are a plurality of pairs of light detectors, each of which is disposed with the ultrasonic transmission / reception surface of the ultrasonic probe interposed therebetween, and the symmetry axis of each pair is located in the ultrasonic transmission / reception surface. In addition, each pair of symmetry axes is arranged so as to be aligned with one of the sides that define the ultrasonic transmitting / receiving surface, and detects the intensity of light reflected within the subject. The output unit outputs support information based on the degree of approach to a part having an abnormal light absorption coefficient in the subject.

FIG. 1 is a block diagram of an ultrasonic diagnostic apparatus 1 according to the first embodiment. FIG. 2 is a block diagram of the biological light measurement device 4 including the optical probe 40 and the light measurement processing unit 42. FIG. 3 is a diagram illustrating an arrangement example of the light irradiation unit 400 and the light detection units 401 a to 401 d with respect to the ultrasonic probe 12. FIGS. 4A, 4B, and 4C are diagrams for explaining a process of measuring the degree of adhesion using the arrangement example of FIG. FIGS. 5A, 5B, and 5C are diagrams for explaining the measurement processing of the three-dimensional azimuth and the distance of the abnormal part. FIG. 6 is a diagram illustrating an example of the arrangement of the light irradiation unit 400 and the light detection units 401a to 401d used in the measurement processing of the three-dimensional azimuth and the distance of the abnormal part. FIG. 7 is an example of the support information displayed on the monitor 14 when the degree of adhesion to the breast and the three-dimensional azimuth and the distance of the abnormal site in the breast cancer test are measured. FIG. 8 is a modified example of the support information displayed on the monitor 14. FIG. 9 is a diagram showing an example of support information for primary guidance for locating an abnormal part in the ultrasonic scanning area. FIG. 10 is a diagram illustrating an example of support information for secondary guidance for maximizing the signal amount of light from an abnormal part after moving the ultrasonic probe 12 according to the primary guidance. FIG. 11 shows an embodiment in which the absorption signal strength (or attenuation signal strength) of each light detection unit 401 calculated based on the signal strength of the detection light of each light detection unit 401 is displayed by a level meter as support information. is there. FIGS. 12A and 12B show an example of support information output as an audio signal. FIG. 13 is a modification of the arrangement shown in FIG. FIG. 14 shows another modification of the arrangement shown in FIG. FIG. 15 shows another modification of the arrangement shown in FIG. FIG. 16 shows another modification of the arrangement shown in FIG. FIG. 17 shows another modification of the arrangement shown in FIG. FIG. 18 shows another modification of the arrangement shown in FIG. FIG. 19 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 1 according to the second embodiment. FIG. 20 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 1 according to the third embodiment. FIG. 21 shows an example of a procedure for determining the degree of adhesion and determining the direction of the abnormal part using the biological light measurement device 4 shown in FIG. FIG. 22 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 1 according to the fourth embodiment. FIG. 23 is a diagram of the probe of the ultrasonic diagnostic apparatus 1 according to the fifth embodiment as viewed from the subject contact surface side. FIG. 24 is a diagram schematically illustrating the position and size of an abnormal site specified on the ultrasonic scanning cross section when the abnormal site is approximated as a sphere. FIG. 25 is a diagram showing an ultrasonic image corresponding to an ultrasonic scanning section. FIG. 26 is a diagram for explaining a display form of an abnormal part whose position and size are specified on the ultrasonic image. FIG. 27 is a diagram illustrating a first modification 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. FIG. 28 is a diagram illustrating a second modification 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. FIG. 29 is a diagram illustrating a 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. FIG. 30 is a diagram showing a form in which the approach state between the abnormal part and the probe identified by the biological light measurement is shown as the brightness (change) of a part (for example, an icon or the like) of the screen of the ultrasonic image. FIGS. 31A to 31D are diagrams illustrating an example in which the brightness of the icon changes as the probe approaches the specified abnormal part. FIGS. 32A to 32D are diagrams exemplifying a state in which the color and the like of the icon change as the probe approaches the specified abnormal part. FIGS. 33A to 33D are diagrams illustrating a state where the display area of the icon changes as the probe approaches the specified abnormal part. FIGS. 34A to 34D are diagrams illustrating a state where the display position of the icon changes as the probe approaches the specified abnormal part. FIGS. 35A to 35D are diagrams illustrating a manner in which the amplitude of the icon swing changes as the probe approaches the specified abnormal part. FIGS. 36A to 36D are diagrams illustrating a state in which the shape of the icon changes as the probe approaches the specified abnormal part.

  Hereinafter, each embodiment will be described with reference to the drawings. In the following description, components having substantially the same functions and configurations are denoted by the same reference numerals, and repeated description will be made only when necessary.

(First embodiment)
FIG. 1 shows a block diagram of an ultrasonic diagnostic apparatus 1 according to the present embodiment. The ultrasonic diagnostic apparatus 1 shown in FIG. 1 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. Further, the ultrasonic diagnostic apparatus 1 according to the present embodiment transmits the optical probe 40 and the optical measurement processing unit 42 for realizing the biological optical measurement device 4 and the support information for supporting the arrangement operation of the ultrasonic probe 12. And a support information generating unit 44 for generating.

  In the present embodiment, as shown in FIG. 1, an ultrasonic diagnostic apparatus 1 having a built-in living body optical measurement device (integrated with the living body optical measuring device) will be described as an example. However, without being limited to this example, the biological optical measurement device and the ultrasonic diagnostic device may be formed as separate structures.

  The ultrasonic probe 12 is a device (probe) that transmits ultrasonic waves to a subject, typically a living body, and receives a reflected wave from the subject based on the transmitted ultrasonic waves. A plurality of piezoelectric vibrators, a matching layer, a backing material, and the like. The piezoelectric vibrator transmits an ultrasonic wave in a desired direction in a scan area based on a drive signal from the ultrasonic transmission unit 21 and converts a reflected wave from the subject into an electric signal. The matching layer is an intermediate layer provided on the piezoelectric vibrator and for efficiently transmitting ultrasonic energy. The backing material prevents ultrasonic waves from propagating backward from the piezoelectric vibrator. When an ultrasonic wave is transmitted from the ultrasonic probe 12 to the subject, the transmitted ultrasonic wave is successively reflected on the discontinuous surface of the acoustic impedance of the body tissue, and is received by the ultrasonic probe 12 as an echo signal. The amplitude of the echo signal depends on the difference in acoustic impedance at the discontinuous surface that has been reflected. Further, the echo when the transmitted ultrasonic pulse is reflected by the moving blood flow undergoes a frequency shift due to the Doppler effect depending on the velocity component of the moving object in the ultrasonic transmission / reception direction.

  In the present embodiment, it is assumed that the ultrasonic probe 12 is a one-dimensional array probe in which a plurality of ultrasonic transducers are arranged along a predetermined direction. However, without being limited to this example, the ultrasonic probe 12 may be a two-dimensional array probe (a probe in which a plurality of ultrasonic transducers are arranged in a two-dimensional matrix) or a mechanical 4D A probe (a probe capable of executing ultrasonic scanning while mechanically swaying the ultrasonic transducer array in a direction orthogonal to the arrangement direction) may be used.

  The input device 13 is connected to the device main body 11, and various switches, buttons, and tracks for inputting various instructions, conditions, instructions for setting a region of interest (ROI), various image quality condition setting instructions, and the like from the operator to the device main body 11. It has a ball, mouse, keyboard, etc. In addition, the input device 13 has a button or the like for instructing a timing at which puncture information including a needle tip position of a puncture needle is taken in a puncture assist function described later.

  The monitor 14 displays in-vivo morphological information and blood flow information as images 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 pulser circuit, and the like (not shown). In the trigger generation circuit, a trigger pulse for forming a transmission ultrasonic wave is repeatedly generated at a predetermined rate frequency fr Hz (period; 1 / fr second). Further, in the delay circuit, a delay time necessary for focusing the ultrasonic waves in a beam shape for each channel and determining transmission directivity is given to each trigger pulse. The pulser 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 (not shown). The amplifier circuit amplifies the echo signal captured via the probe 12 for each channel. The A / D converter converts the amplified analog echo signal into a digital echo signal. The delay circuit determines the reception directivity of the digitally converted echo signal, gives a delay time necessary for performing the reception dynamic focus, and then performs an addition process in an adder. By this addition, the reflected component of the echo signal from the direction corresponding to the reception directivity is emphasized, and the reception directivity and the transmission directivity form an overall beam for ultrasonic transmission and reception.

  The B-mode processing unit 23 receives the echo signal from the receiving unit 22, performs logarithmic amplification, envelope detection processing, and the like, and generates data whose signal intensity is represented by brightness.

  The Doppler processing unit 24 extracts a blood flow signal from the echo signal received from the receiving unit 22, and generates blood flow data. Extraction of blood flow is usually performed by CFM (Color Flow Mapping). In this case, the blood flow signal is analyzed, and blood flow information such as average velocity, variance, and power is obtained for multiple points as blood flow data.

  The RAW data memory 25 uses the plurality of B-mode data received from the B-mode processing unit 23 to generate B-mode RAW data that is B-mode data on a three-dimensional ultrasonic scanning line. The RAW data memory 25 uses the plurality of blood flow data received from the Doppler processing unit 24 to generate blood flow RAW data that is blood flow data on a three-dimensional ultrasonic scanning line. A three-dimensional filter may be inserted after the RAW data memory 25 to perform spatial smoothing for the purpose of reducing noise and improving image connection.

  The volume data generation unit 26 generates B-mode volume data and blood flow volume data by executing RAW-to-voxel conversion including interpolation processing that takes spatial position information into account.

  The image processing unit 28 performs a predetermined image such as volume rendering, multi-planar reconstruction display (MPR: multi planar reconstruction), maximum intensity projection display (MIP: maXimum intensity projection) on the volume data received from the volume data generation unit 26. Perform processing. Note that a two-dimensional filter may be inserted after the image processing unit 28 to perform spatial smoothing for the purpose of reducing noise and improving image connection.

  The display processing unit 30 executes various types of image data generated and processed in the image processing unit 28, such as dynamic range, brightness (brightness), contrast, γ curve correction, and RGB conversion.

  The control processor 31 has a function as an information processing device (computer) and controls the operation of each component. Further, the control processor 31 executes a process according to an ultrasonic probe operation support function described later.

  The storage unit 32 includes a dedicated program for realizing an ultrasonic probe operation support function described later, imaged volume data, diagnostic information (patient ID, doctor's findings, etc.), a diagnostic protocol, transmission / reception conditions, and other data groups. Have been kept. It is also used for storing images in an image memory (not shown) as necessary. The data in the storage unit 32 can be transferred to an external peripheral device via the interface unit 33.

  The interface unit 33 is an interface for the input device 13, a network, and a new external storage device (not shown). In addition, an external biological optical measurement device can be connected to the ultrasonic diagnostic apparatus main body 11 via the interface unit 33. Data such as ultrasonic images and analysis results obtained by the device can be transferred to another device via the network by the interface unit 33.

  FIG. 2 is a block diagram of the biological light measurement device 4 including the optical probe 40 and the light measurement processing unit 42.

  The optical probe 40 has at least one light irradiation unit 400 and a plurality of light detection units 401. The light irradiation unit 400 irradiates light (near infrared light) generated by the light source 420 toward the subject. The light detection unit 401 has a detection surface configured by, for example, an end of an optical fiber, and includes a plurality of detection elements that photoelectrically convert reflected light from inside the subject input from the detection surface via the optical waveguide unit. Become. As the detection element, for example, a CCD, an APD, a photomultiplier, or the like can be adopted in addition to a light receiving element such as a photodiode or a phototransistor. A light matching layer may be provided on the contact surfaces of the light irradiation section 400 and the light detection sections 401 with the subject.

  FIG. 3 is a diagram illustrating an arrangement example of the light irradiation unit 400 and the light detection units 401 a to 401 d with respect to the ultrasonic probe 12. In the figure, the light irradiating unit 400 is arranged near the center of the ultrasonic transmitting and receiving surface 120 of the ultrasonic probe 12, and the ultrasonic transmitting and receiving surface 120 (with respect to the subject) is arranged on the circumference around the light irradiating unit 400. An example is shown in which the photodetectors 401a to 401d are arranged at equal intervals so as to surround the (contact surface). The contact surface of the light irradiation unit 400 and each of the light detection units 401a to 401d with the subject is set to, for example, the same level as the ultrasonic transmission / reception surface 120, and directly or indirectly comes into contact with the subject surface during measurement. It is arranged in a state. 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 illustrated in FIG. Application examples of the arrangement will be described later in detail.

  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 emits light of a wavelength (for example, light in the range of 600 nm to 1800 nm in the vicinity of a wavelength band called a window of a living body) having a small absorption in a living body, or light of a specific wavelength (for example, living body Light-emitting elements such as semiconductor lasers, light-emitting diodes, solid-state lasers, and gas lasers that generate light in a wavelength range of 750 to 850 nm that is in a wavelength range called a window and is absorbed by hemoglobin in blood. The light generated in the light source 420 is supplied to the light irradiation unit 400 via an optical waveguide configured by an optical fiber or a thin-film optical waveguide (or via direct space propagation). Note that the light source 420 may be configured integrally with the light irradiation unit 400.

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

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

  The arithmetic circuit 426 determines the degree of adhesion between the light detection unit 401 and the surface of the subject based on the change in the intensity of the detected light between the light detection units 401, and an abnormal portion (for example, Depth from the surface of the subject at a specific wavelength (a part that absorbs more than normal tissue), and an abnormal part based on a predetermined position (for example, the light irradiation unit 400, the center of the ultrasonic transmitting / receiving surface 120, etc.). Calculate the three-dimensional position 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, an ultrasonic probe operation support function of the present ultrasonic diagnostic apparatus will be described. This function calculates at least one of the degree of adhesion between the ultrasonic probe 12 and the surface of the subject, and the three-dimensional azimuth and the distance (approach) of the abnormal site in the subject, and based on the result, calculates the In addition, it generates and outputs support information for more appropriately guiding the position, orientation, posture, degree of pressurization, and the like of the ultrasonic probe 12 with respect to the diagnosis target portion, thereby supporting the operation of the ultrasonic probe.

(Measurement of adhesion)
First, a process of measuring the degree of adhesion between the light detection unit 401 and the surface of the subject will be described. Here, the degree of adhesion is an amount related to the thickness of the air layer existing in the gap between the light detection unit 401 and the living body surface and the ratio of the cross-sectional area occupying the optical path. Ideally, it is desired that there is no air layer or that the thickness be less than the wavelength of the detection light and the coverage be 0.1% or less.

  FIGS. 4A, 4B, and 4C are diagrams for explaining a process of measuring the degree of adhesion using the arrangement example of FIG. In each of FIGS. 4A, 4B, and 4C, the upper part is a cross-sectional view taken along line AA of FIG. 3, and the lower part is an irradiation surface of the light irradiation unit 400 and each detection of the light detection unit 401. The projection of the surface onto the surface of the subject is shown respectively.

  As shown in FIG. 4A, first, near-infrared light is irradiated from the light irradiation unit 400 into the subject in a state where the probe P is arranged on the surface of the subject. At this time, the detection surfaces of the light detection units 401b to 401d (corresponding to ch2 to ch4, respectively) preferably come into contact with the surface of the subject, while the detection surfaces of the light detection units 401a (corresponding to ch1) and the surface of the subject are interposed. Is assumed to have a space (gap). In such a case, a part of the reflected light emitted from the subject is reflected on the detection surface due to the difference in the refractive index in the light detection unit 401a distant from the subject surface. As a result, the intensity of the light incident on the light detection unit 401a is weaker than the light incident on the light detection units 401b to 401d. 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 at the light detection unit 401a and the signal level of the light intensity set in advance, or the numerical value calculated from the signal level of the light intensity at the light detection units 401b to 401d using the specified risk factor. Compare. As a result, if the signal level of the light intensity at the light detection unit 401a is low, the arithmetic circuit 426 determines that the light detection unit 401a is separated from the subject surface (the state of reduced adhesion). When all the light detection units 401 are determined to have an appropriate degree of adhesion, the degree of adhesion of the ultrasonic probe 12 surrounded by the light detection units 401 is also determined to be within an appropriate range.

  The support information generation unit 44 instructs and guides the position, posture, orientation, and the like of the ultrasonic probe 12 based on the determination result and the calculation result of the arithmetic circuit 42 in order to bring the ultrasonic transmission / reception surface 120 into close contact with the subject. Generate support information. The generated support information is displayed on the monitor 14 in a predetermined form. A specific example of the support information will be described later in detail.

  The operator operates the ultrasonic probe 12 according to the guidance based on the displayed support information, and measures the degree of adhesion again. As a result, when it is determined that the degree of adhesion is within the appropriate range, the ultrasonic image capturing is started.

(Measurement processing of three-dimensional azimuth and distance of abnormal part)
Next, the measurement processing of the three-dimensional azimuth and the distance of the abnormal part will be described. FIGS. 5A, 5B, and 5C are diagrams for explaining the measurement processing of the three-dimensional azimuth and the distance of the abnormal part. FIG. 6 is a diagram illustrating an example of the arrangement of the light irradiation unit 400 and the light detection units 401a to 401d used in the measurement processing of the three-dimensional azimuth and the distance of the abnormal part. In each of FIGS. 5A, 5B, and 5C, the upper section is a cross-sectional view taken along the line AA of FIG. 6, and the lower section is a light receiving unit 400 and a light detecting unit 401. The projection on the sample surface is shown with the abnormal part as an absorber.

  First, in order to calculate the three-dimensional azimuth and the distance of the abnormal site, with the probe P placed on the surface of the object, the specific wavelength at which the absorption amount increases at the abnormal site from the light irradiation unit 400 toward the inside of the object. Light is irradiated. As shown in FIG. 5A, the reflected light of the irradiated light from the inside of the subject is divided into light detection units 401a ′ to 401d ′ located at positions near (close to) the light irradiation unit 400, and FIG. As shown in b), the light is detected by the light detection units 401a to 401d located at positions (outer peripheral positions) far from the light irradiation unit 400, respectively.

  Incident light passes through the living body while being scattered, but is absorbed more when passing through an abnormal site. Therefore, the detection light of the light detection unit (the detection unit 401a and the light detection unit 401a 'in the examples of FIGS. 5 and 6) placed at the specific distance includes the depth information of the abnormal part. The light analysis unit 424 analyzes the detection light from the light detection units 401a to 401d (each corresponding to ch1 to 4) and the light detection units 401a 'to 401d' (each corresponding to ch5 to 8) arranged in each direction. . As a result, for example, when ch2 <ch1 <ch3 and ch4 in FIG. 5A and ch5 and 6 <ch7 and 8 in FIG. 5B, between ch2 and ch1 (between ch5 and ch6) ) And near the ch2 (ch5) side, it can be seen that an abnormal site exists. Further, for example, since the signal intensities of ch5 and ch6 are weaker than the signal intensities of ch2 and ch1, it can be understood that the abnormal portion exists at a relatively shallow position.

  The arithmetic circuit 426 compares the analyzed signal intensity distribution at the near position with the signal intensity distribution at the outer peripheral position, and as shown in FIG. 5C, determines the reference position of the existing abnormal part (for example, the light irradiation unit 400). Calculate the three-dimensional direction and distance from. Specifically, a light intensity signal in a normal tissue obtained by a function of the distance between the light irradiation unit 400 and the light detection unit 401 is set as a reference value, and light detection at another position is further performed by the reference value in one light detection unit 401. The reference value of the unit 401 is normalized. The normalized reference value is used as a coefficient of light intensity at the position of each light detection unit 401, and the difference between the light intensity signal actually measured by each light detection unit 401 and the light intensity reference value is obtained. The ratio to the reference value is calculated and used as the change rate, and the direction and approach state of the abnormal part are calculated from the change rate and the position information. Further, the X coordinate of each light detection unit 401 is multiplied by the rate of change, and the result of the multiplication is obtained as a sum or an average value to obtain an X direction component. Similarly, the Y direction component and the Z direction component are obtained. The direction (azimuth information) of the abnormal part is generated by obtaining the direction angle of the direction vector obtained by combining the components obtained as a result. Further, an absolute value is obtained by multiplying the X coordinate of each light detection unit 401, a change rate, and a coefficient, and the absolute values are summed to obtain an X component. Similarly, the Y direction component and the Z direction component are obtained. Using the value obtained by summing the absolute values in each direction, the three-dimensional distance of the abnormal part with respect to the light irradiation unit 400 is calculated.

  The support information generation unit 44 provides support information for instructing and guiding the movement of the ultrasonic probe 12 based on the obtained three-dimensional azimuth and three-dimensional distance so as to arrange the abnormal part in the ultrasonic scanning area. Generate The generated support information is displayed on the monitor 14 in a predetermined form. A specific example of the support information will be described later in detail.

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

(Support information)
FIG. 7 is an example of the support information displayed on the monitor 14 when the degree of adhesion to the breast and the three-dimensional azimuth and the distance of the abnormal site in the breast cancer test are measured. In the example of the figure, the degree of adhesion of the ultrasonic transmitting / receiving surface 120 to the breast surface is displayed by shading of the image. For example, a dark portion at the lower right on the screen indicates a region where the signal intensity is relatively low. . In addition, the fact that the estimated depth display of the abnormal part on the right side of the figure is at the zero position indicates that the cause of the intensity decrease is on the surface. From both displays, it can be seen that it indicates that the probe is floating above the surface of the living body in a region where the signal intensity is low. The operator performs an operation of strongly pressing the lower right side of the probe according to the guidance of the displayed support information so that the dark portion has the same brightness as the other regions.

  FIG. 8 is a modified example of the support information displayed on the monitor 14, in which a detection failure portion is displayed with a cross mark based on the calculated probe adhesion. In the example shown in the figure, since the crosses are concentrated at the lower right of the screen, it can be understood that the degree of adhesion between the detection surface of the light detection unit 401 corresponding to the cross and the subject surface is low. The operator visually recognizes the displayed support information, and performs an operation of strongly pressing the lower right side of the probe in accordance with the guidance so as to improve the degree of adhesion of the detection failure portion.

  After the ultrasonic probe 12 is operated in accordance with the support information shown in FIG. 7 or FIG. 8 and the degree of adhesion of the probe 12 to the subject surface falls within an appropriate range, the azimuth information of the abnormal part and the abnormal part On the other hand, a moving direction and a moving amount for arranging the ultrasonic probe 12 more suitably are provided as support information.

  FIG. 9 is a diagram showing an example of support information for primary guidance for locating an abnormal part in the ultrasonic scanning area. By moving the ultrasonic probe 12 in the arrow direction 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 of the light from the abnormal part after moving the ultrasonic probe 12 according to the primary guidance (when the plurality of light detection units 401 detect the light from the abnormal part, the sum of the signal amounts). FIG. 7 is a diagram showing an example of support information for the purpose of secondary guidance for maximizing ()). By the secondary guidance, the ultrasonic probe 12 is moved so that the signal amount is maximized depending on the depth of the abnormal part. By performing such a stepwise guidance, it is possible to acquire more signals from an abnormal site than in the past.

  FIG. 11 shows an embodiment in which the absorption signal strength (or attenuation signal strength) of each light detection unit 401 calculated based on the signal strength of the detection light of each light detection unit 401 is displayed by a level meter as support information. is there. From the figure, it can be seen from the balance of the signal intensities that an abnormal site exists near the light source.

  FIGS. 7 to 11 exemplify a case where the support information indicating the degree of adhesion of the probe, the moving direction and the moving amount of the ultrasonic probe, and the like is output as an image on the monitor 14. On the other hand, it is also possible to output support information by an acoustic signal.

  FIGS. 12A and 12B show an example of support information output as an audio signal. In the example of FIG. 12A, the operator is informed of the current degree of adhesion of the light detection unit 401 (or the ultrasonic transmission / reception surface) by the periodicity of sound. For example, when the all-light detection unit 401 is determined to be non-contact, the upper stage is in a silent state, when at least one of the light detection units 40 is determined to be non-contact, the middle stage is an intermittent sound, and when the all-light detection unit 401 is in close contact. If it is determined to be appropriate, the lower continuous sound is output. In the example of FIG. 12B, the approach information of the abnormal part is notified by the level of the sound (frequency). For example, as the probe approaches the abnormal part, the continuous sound output in the cycle shown in the upper part of FIG. 12B is reduced in frequency as shown in FIG. 12B. The support information based on such an acoustic signal has a feature that an operator can receive scanning guidance without looking at the monitor 14. Also, without being limited to the example, it is possible to output the support information as an acoustic signal by controlling, for example, volume, articulation, rhythm, melody, voice, and the like.

(Arrangement modification)
Next, a modification of the arrangement of the light irradiation unit 400 and the light detection unit 401 with respect to the ultrasonic probe 12 will be described.

  FIG. 13 is a modification of the arrangement shown in FIG. In the modification shown in the figure, the light irradiating unit 400 (light source) is disposed on the central axis (symmetric axis) in the longitudinal direction of the ultrasonic transmitting / receiving surface 120, and is radial to the light source and located on the central axis of the ultrasonic probe 120. The plurality of light detection units 401 are arranged on a double concentric circle so as to be line-symmetric with respect to the light detection units 401. As described above, the arrangement symmetry axis of the light detection unit 401 and the center axis of the ultrasonic lobe 12 are substantially matched (or the arrangement symmetry axis of the light detection unit 401 is set within the range of the device width of the ultrasonic probe). 6. Since the relative position error between the two types of detection systems is eliminated, the arrangement is more excellent than that of FIG. Note that the maximum distance from the light irradiating unit 400 to the light detecting unit 401 is required to be at least twice the measurable depth of the abnormal part, and therefore the entire probe P tends to be large. However, by arranging the light irradiation unit 400 at a position close to the center axis of the ultrasonic probe 12 as in the present modification, downsizing of the entire probe P can be realized as compared with the example of FIG. .

  FIG. 14 shows another modification of the arrangement shown in FIG. In the modified example shown in the drawing, the light detection units 401 are long and symmetrically arranged in the axial direction of the ultrasonic probe 12. With this arrangement, the entire width of the probe P can be suppressed, so that the ultrasonic probe 12 can be easily swung.

  FIG. 15 shows another modification of the arrangement shown in FIG. In the modification shown in the figure, a plurality of light irradiation units 400 are symmetrically arranged on both sides of the ultrasonic probe 12. Further, a plurality of light detection units 401 are arranged radially with respect to the centers of the plurality of light sources and symmetrically with respect to the center axis of the ultrasonic probe 12. As described above, since the axes of the optical measurement system and the ultrasonic probe 12 are made to coincide with each other, the relative position error between the two types of detection systems is eliminated. In addition, by using the selective detection of the plurality of light irradiation units 400 and the plurality of light detection units 401, the distance from the light source is substantially increased, and the location of the abnormal site can be detected in a wider range than the single light source. It has special features.

  FIG. 16 shows another modification of the arrangement shown in FIG. In the modification shown in the figure, a plurality of light irradiation units 400 are symmetrically arranged on both sides of the ultrasonic probe 12, and another light irradiation unit 400 is arranged on the center axis of the ultrasonic probe 12. Further, a plurality of light detection units 401 are arranged radially with respect to the centers of the plurality of light sources and symmetrically with respect to the center axis of the ultrasonic probe 12. Also in this modification, the axes of the optical measurement system and the ultrasonic probe 12 are made to coincide with each other, and the relative position error between the two types of detection systems is eliminated, so that the arrangement is superior to the embodiment of FIG. Another characteristic is that the use of a plurality of light sources makes it possible to detect the location of an abnormal site in a wider range. Further, by adopting a configuration in which the wavelength of the output light of the plural light sources on both sides of the probe and another light source on the center axis of the ultrasonic probe 12 is changed, more information can be obtained at the same time.

  FIG. 17 shows another modification of the arrangement shown in FIG. In the modification shown in the figure, a plurality of ultrasonic probes 12 (two are illustrated in FIG. 17) are arranged in series with their central axes aligned, and at least one light irradiation unit 400 is arranged at the center of the gap. ing. Also in this modification, the axes of the optical measurement system and the ultrasonic probe 12 are made to coincide with each other, and the relative position error between the two types of detection systems is eliminated, so that the arrangement is superior to the embodiment of FIG. In addition, by arranging the light irradiating unit 400 at the center of the arrangement of the plurality of ultrasonic probes 12, there is a feature in that the existence search area of the abnormal part can be detected in a wide range.

  FIG. 18 shows another modification of the arrangement shown in FIG. In the modification shown in the figure, the light detection units 401 are arranged so as to be dense near the final guidance position of the abnormal part. Also in this modification, the axes of the optical measurement system and the ultrasonic probe 12 are made to coincide with each other, and the relative position error between the two types of detection systems is eliminated, so that the arrangement is superior to the embodiment of FIG. In addition, by arranging the light detection unit 401 densely, light absorption information of an abnormal part can be detected with high spatial accuracy.

  In each of the examples described above, the case where the plurality of photodetectors 401 are arranged in two concentric circles is illustrated. However, without being limited to the respective examples, the light detection units 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, there is an effect relating to the degree of adhesion between the photodetector and the surface of the subject. That is, in the biological light measurement, when the light detection unit is not in close contact with the subject, there is a possibility that a reflection loss occurs on the detection surface (light incident portion) of the light detection unit and a loss of up to 10% is generated. is there. On the other hand, the difference due to the absorption of the abnormal portion is on the order of%, and the difference in the signal due to the above-described problem with the setting of the light detection unit is larger. Therefore, it is considered that whether or not the degree of adhesion between the light detection unit and the living body is appropriate is information to be confirmed before the detection of the abnormal site. According to this ultrasonic diagnostic apparatus, the degree of adhesion between the probe and the surface of the subject is calculated using the biological light measurement function, and based on the result, support information for guiding the probe to a more suitable position is generated. Output. The operator can grasp the current contact state of the probe on the surface of the subject and, if the contact is incomplete, easily determine the posture, orientation, pressing direction, moving direction, and the like of the probe according to the guidance based on the support information. And can be corrected quickly.

  Second, there is an effect related to effective use of the depth information of the abnormal part. The relative position of the abnormal part located near the skin surface and the abnormal part existing at a depth of several cm differs from the detector that obtains the maximum signal. In addition to the depth of the abnormal part in the azimuth calculation, the position guidance should be performed appropriately. According to the ultrasonic diagnostic apparatus according to the present embodiment, the three-dimensional azimuth and distance of the abnormal part in the subject are calculated using the biological light measurement function, and based on the calculation result, the abnormal part The support information for guiding the position of the ultrasonic probe is generated and output so as to be arranged at a suitable position. 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 abnormal part is scanned by the ultrasonic information according to the guidance by the support information. The position, posture, orientation, and the like of the ultrasonic probe can be easily and quickly corrected so as to be included in the region.

  Third, there is an effect relating to the alignment (alignment) between the ultrasonic probe and the optical detection system. In the present embodiment, the ultrasonic 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 in the ultrasonic transmission / reception plane. . As a result, it is possible to correct a delicate error occurring between the optimum position induced by the signal analysis of the optical system and the image position seen by the ultrasonic echo.

  As described above, regardless of the operator's experience, etc., it is possible to always acquire a suitable ultrasonic image of an abnormal part in a state in which the ultrasonic transmitting / receiving surface and the subject surface are in good contact with each other, and the ultrasonic image diagnosis Quality can be improved.

(Second embodiment)
FIG. 19 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 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 part, and calculates the degree of adhesion using the light, the three-dimensional orientation of the abnormal part, and the like. Perform the identification of. Further, the arithmetic circuit 426 fetches the ultrasonic image from the ultrasonic imaging system, and estimates the position of the abnormal part in the ultrasonic scanning area image based on, for example, a change in the luminance value on the ultrasonic image. Is used to improve the positional accuracy in the optical measurement of living body and to perform the closeness test of the abnormality of the part. By using the living body optical measurement system and the ultrasonic imaging system in this manner, it is possible to more accurately calculate the degree of adhesion and specify the three-dimensional azimuth of the abnormal site and the like.

(Third embodiment)
FIG. 20 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 1 according to the third embodiment. The living body light measuring device 4 shown in FIG. 2 includes a light source 420a that generates a wavelength light having a small absorption at an abnormal site and a high transmittance of a subject, and a light source 420b that generates a specific wavelength light absorbed at the abnormal site. The configuration includes a light source and an optical mixer 421 that mixes light from both light sources. In this configuration, the degree of adhesion of the light detection unit 401 and the effect of absorption due to an abnormal site are separated by relatively comparing a wavelength having high transmittance of the subject with a detected light amount at a specific wavelength. Further, by standardizing the detected light amount of the specific wavelength based on the detected light amount of the wavelength transmitted through the subject, it is possible to reduce a measurement error due to a variation in the degree of adhesion between the ultrasonic probe 12 and the subject.

  Further, the biological light measurement device 4 shown in FIG. 20 has arithmetic circuits 426a and 426b. For example, when the ultrasonic probe 12 is guided, the arithmetic circuit 426a executes a simple calculation of the degree of adhesion and the azimuth identification of the abnormal part. On the other hand, at the time of the abnormality test, the arithmetic circuit 426b executes precise calculation for specifying the degree of adhesion and the direction of the abnormal part. However, when the arithmetic circuit 426a or the arithmetic circuit 426b has a sufficient calculation speed and arithmetic ability, it is possible to guide the ultrasonic probe 12 by using one of the arithmetic circuits.

  FIG. 21 shows an example of a procedure for determining the degree of adhesion and determining the direction of the abnormal part using the biological light measurement device 4 shown in FIG. As shown in the figure, the light irradiating section 400 alternately emits a wavelength having a high transmittance of the subject and a specific wavelength absorbed at the abnormal site into the living body. As described above, in the light detection unit 401 distant from the subject surface, a part of the signal light emitted from the subject is reflected on the surface due to the difference in the refractive index, and weakens the intensity of the light incident on the detector. .

  Therefore, as shown in FIG. 21A, first, when a wavelength having a high transmittance of the subject is used and the measured signal intensity is smaller than a preset light intensity signal level, the light detector 401 at that position is used. Is determined to be separated from the subject surface. By generating and displaying the support information based on the result of the determination of the degree of adhesion, an instruction and guidance for applying pressure in a direction in which the entire probe is brought into close contact with the subject are performed. As a result, as shown in FIG. 21B, the pressure of the photodetector 401 on the surface of the subject is adjusted.

  Next, as shown in FIG. 21C, the specific wavelength absorbed by the abnormal site is incident on the living body, and the emitted light is detected by each light detection unit 401. The rate of change of the amount of detected light due to the degree of adhesion is the same at a wavelength at which the transmittance of a living body is high and at a specific wavelength absorbed at an abnormal site, and the difference between the two is small. The significant difference between the detected light amounts of the two wavelengths depends on the presence or absence of an abnormal site. Then, after normalizing the amount of light of a specific wavelength absorbed by the abnormal site with light having a wavelength that is high in the transmittance of the living body, the three-dimensional orientation of the abnormal site in the subject is determined in the same manner as in the first embodiment. And distance are obtained, and azimuth information and distance information are generated. By generating and displaying support information based on the azimuth information and the distance information, the moving direction and the pressing direction of the entire ultrasonic probe 12 are instructed and guided. As a result, when it is determined that the probe measurement position is within the appropriate range, the ultrasonic image capturing is started.

(Fourth embodiment)
FIG. 22 is a block diagram of the biological light measurement device 4 included in the ultrasonic diagnostic apparatus 1 according to the fourth embodiment. In addition to the example shown in FIG. 20, the biological light measurement device 4 shown in FIG. 20 takes in an ultrasonic image acquired by ultrasonic imaging as data in optical calculation, thereby improving positional accuracy and estimating abnormalities of a part. Testing is possible. In the present embodiment, guidance of a probe relating to the degree of adhesion, guidance of the ultrasonic probe 12 to an abnormal site, imaging of an ultrasonic image, precision optical measurement, linking and recalculation of an ultrasonic image and optical data, and correction image formation Measurement is completed in order. In the example shown in FIG. 22, the operation circuit 426a as a simple calculation circuit is usually used for guiding the ultrasonic probe 12, but when the signal strength is high, the operation circuit 426b as a calculation circuit for precision calculation is used. You may choose.

  In each of the embodiments described above, the biological light measurement by manual operation has been described. On the other hand, the biological light measurement may be performed by an automatic operation.

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

  FIG. 23 is a diagram of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment as viewed from the object contact surface side, and is a diagram illustrating 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 on the center axis C in the longitudinal direction of the ultrasonic transmitting / receiving surface 120 around the ultrasonic transmitting / receiving surface 120. In the present embodiment, the light irradiator 400 irradiates the subject with light of two wavelengths simultaneously or selectively. The plurality of light detection units 401 are also arranged in a pair around the ultrasonic transmission / reception surface 120 with the center axis C in the longitudinal direction of the ultrasonic transmission / reception surface as a symmetry axis, and are radially arranged around the light irradiation unit 400. ing. Note that, in the example of FIG. 5, the plurality of light detection units 401 are arranged on concentric circles of radii r1, r2, and r3 (for example, r1 = 15 mm, r2 = 25 mm, r3 = 35 mm, etc.) around the light irradiation unit 400. In addition, three pairs (three sets) of light detection units 401 are arranged so as to be axially symmetric with respect to the center axis C. The light irradiating section 400 and each light detecting section 401 are covered with a light shielding plate 403.

  Note that the arrangement of the light irradiation unit 400 and the plurality of light detection units 401 is not limited to the example of FIG. 23, and various modes can be adopted. That is, the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment has a configuration in which the ultrasonic scanning surface substantially coincides with the axis of symmetry (the plane of symmetry) in which the plurality of light detection units 401 are arranged, or optical detection. Any configuration may be used as long as the configuration symmetry axis of the vessel falls within the range of the device width of the ultrasonic echo probe (or the width of the ultrasonic transmitting / receiving surface 120 in the short direction).

  In addition, the biological light measurement device 4 according to the present embodiment further includes a storage unit that stores a database for specifying the position and size of the abnormal site in the ultrasonic scanning cross section. This storage unit may be an internal memory or an external memory, but an embodiment in which the storage unit is stored in a semiconductor memory in the apparatus is preferable in view of a request for quick processing and a required memory capacity. Other configurations are substantially the same as those shown in FIGS. The database pre-corresponds the position and size of the abnormal part in the ultrasonic scanning plane of the ultrasonic probe 12 for each optical absorption coefficient (k) for each combination of the light intensity detected by each light detection unit 401. It is attached. The arithmetic circuits 426a and 426b perform calculations for comparing the intensity of light actually detected by each light detection unit 401 with a numerical value stored in a database in advance, and determine the position and size of the abnormal part in the ultrasonic scanning plane. Identify

  From the light irradiation unit 400 arranged as shown in FIG. 23, light of two specific wavelengths (for example, absorption wavelength of oxygenated hemoglobin (around 770 nm)) and deoxygenated hemoglobin of which the amount of absorption is increased at an abnormal site with high biological transmittance. Light having two absorption wavelengths (around 900 nm) is irradiated into the specimen. The irradiated light propagates while being scattered in the subject, and is absorbed more when passing through an abnormal site. The plurality of light detectors 401 arranged as shown in FIG. 23 detect light emitted from the subject at each position. The light detected by each light detection unit 401 includes the depth information of the abnormal part. The light analysis unit 424 analyzes the light detected by each light detection unit 401. The arithmetic circuits 426a and 426b determine the degree of adhesion between the photodetector 401 and the surface of the subject based on the intensity change of the detection light between the photodetectors 401, Calculate the position and size (size).

  The arithmetic circuits 426a and 426b determine the degree of adhesion between the photodetector 401 and the surface of the subject based on the intensity change of the detection light between the photodetectors 401 and the predetermined light absorption in the subject according to the algorithm described above. The three-dimensional position and distance of the abnormal part based on the depth of the abnormal part indicating the target coefficient from the surface of the subject and a predetermined position are calculated. 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 / guidance (navigation) of the position, posture, orientation, and the like of the ultrasonic probe 12 according to the method described above. The generated support information is displayed on the monitor 14 in a predetermined form, for example. The operator moves the ultrasonic probe 120 according to the displayed support information so that the ultrasonic transmission / reception surface 120 is located directly above the abnormal part having the predetermined light absorption coefficient. There are various variations in the display form of the support information for moving the ultrasonic transmitting / receiving surface 120 right above the abnormal part. This will be described later in detail in a sixth embodiment.

  On the surface of the subject, the ultrasonic transmission / reception surface 120 is positioned directly above the abnormal part exhibiting a predetermined light absorption coefficient (or the abnormal part is positioned on a symmetric plane below the longitudinal symmetry axis of the ultrasonic probe 12). (2) The ultrasonic probe 120 is disposed. As a result, when the position of the ultrasonic probe 12 is determined to be within an appropriate range, the calculation of the position and size of the abnormal part is executed by the following method.

  FIG. 24 is a diagram schematically illustrating the position and size of an abnormal site specified on the ultrasonic scanning cross section when the abnormal site is approximated as a sphere. Using the center position (x, y), size (diameter φ), and level of optical absorption coefficient (k) of the sphere as parameters, solve the light diffusion equation as a forward problem as the light intensity at the position of each photodetector, and solve the solution. Is stored in the storage unit of the biological light measurement device 4 in advance as a database in which is associated with light absorption information. When the light absorption region is approximated by the simplest spherical shape, it can be solved analytically by an approximate solution of the modified Bessel function, but it is difficult to solve analytically by a more complicated shape. Therefore, an approximate value is obtained by using a light diffusion equation simulation with scattering using the finite element method. The database can select and calculate the parameter level appropriately, and create a table based on the calculation. Here, the simulation is illustrated as a method of creating the light intensity table.However, a method of creating a phantom that matches the level of each parameter and determining a numerical value by actual measurement, a part of the actual measurement data and the simulation result are combined. There is also a method to create them together. Therefore, in the case of the spherical approximation, the unknowns to be obtained are the position (x, y), diameter (φ), and optical absorption coefficient (k) of the living body on the tomographic screen. Results are needed. In the case of spheroid approximation, at least five light quantity measurement results are required. Here, the paired detectors are symmetrical in terms of an optical model, and the light intensity should have the same value. Therefore, the detection data is not treated as an independent value.

  The arithmetic circuits 426a and 426b compare the numerical values recorded in the database in advance with the light intensities detected by the respective light detection units 401. As means for comparison, for example, there is a selection method by the least square method. In this case, since the light intensity at each detector position changes by an order of magnitude, appropriate measures such as using a normalized relative intensity change standardized by the light intensity when there is no light absorbing portion are required. The comparison between the database value and the detected light intensity can be calculated instantaneously in less than a second. Therefore, information on the position (x, y), diameter (φ), and optical absorption coefficient (k) of the abnormal absorption part can be known in real time.

  That is, in the present embodiment, the position and the size of the abnormal part in the subject are not calculated as an inverse problem (see the first embodiment and the like) using the intensity of the light detected by each light detection unit 401. Instead, the position and size of the abnormal site in the subject are calculated as a forward problem using the database stored in advance in the storage unit and the light intensity actually detected by each light detection unit 401. . Such a calculation method is particularly useful, for example, when real-time processing is important. However, the present invention 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. Also, if necessary, light of another wavelength that transmits through the subject is prepared, this is detected as reference light, and the measurement light amount of another wavelength is standardized, thereby reducing measurement errors due to various variations. You may do so.

  The calculated position and size of the abnormal part are displayed in real time in a predetermined form on the ultrasonic image. FIG. 25 is a diagram showing an ultrasonic image corresponding to an ultrasonic scanning section, and FIG. 26 is a diagram for explaining a display form of an abnormal part whose position and size are specified on the ultrasonic image. is there. When the position and the size of the abnormal part are calculated on the ultrasonic image shown in FIG. 25, for example, as shown in FIG. 26, the position specified by the color assigned to the optical absorption coefficient (k) ( A circle having a center (x, y)) and a size (diameter φ) is displayed. This allows the observer to intuitively grasp the approximate position and size of the abnormal part on the ultrasonic image in real time. Further, by recording an ultrasonic image in which an abnormal part is displayed, it is possible to perform image diagnosis using an ultrasonic image in which the abnormal part is always visualized.

(Modification 1)
FIG. 27 is a diagram of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment as viewed from the subject contact surface side, and is a diagram illustrating a first modification of the arrangement of the light irradiation unit 400 and the light detection unit 401. . The light irradiating unit 400 is arranged on the central axis C in the longitudinal direction of the ultrasonic transmitting / receiving surface 120, and irradiates light of a specific one wavelength (not two wavelengths). In addition, four pairs (four sets) of the photodetectors 401 are provided with the central axis C in the longitudinal direction of the ultrasonic transmission / reception surface as a symmetric axis. This makes it 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 diagram of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment as viewed from the object contact surface side, and is a diagram illustrating a second modification of the arrangement of the light irradiation unit 400 and the light detection unit 401. . As shown in the figure, two light irradiation units 400 are arranged adjacent to different positions on the center axis C in the longitudinal direction of the ultrasonic transmitting / receiving surface 120. Further, two pairs (two sets) of the light detection units 401 are provided with the central axis C in the longitudinal direction of the ultrasonic transmission / reception surface as a symmetric axis. According to this modification as well, it is possible to obtain information on the position and size of the abnormal part and the optical absorption coefficient (k) without using light of two wavelengths. Further, as compared with the examples shown in FIGS. 23 and 25, there is an advantage that the number of the light detection units 401 can be reduced.

(Modification 3)
FIG. 29 is a diagram of the probe of the ultrasonic diagnostic apparatus 1 according to the present embodiment as viewed from the subject contact surface side, and is a diagram illustrating a third modification of the arrangement of the light irradiation unit 400 and the light detection unit 401. . As shown in the figure, two light irradiation units 400 are arranged on the center axis C in the longitudinal direction of the ultrasonic transmitting / receiving surface 120 with the ultrasonic transmitting / receiving surface 120 interposed therebetween. Further, two pairs (two sets) of the light detection units 401 are provided with the central axis C in the longitudinal direction of the ultrasonic transmission / reception surface as a symmetric axis. According to this modification as well, it is possible to obtain information on the position and size of the abnormal portion and the optical absorption coefficient (k) without using two wavelengths of light. Further, similarly to the second modification, there is an advantage that the number of the light detection units 401 can be reduced as compared with the examples shown in FIGS. Further, by arranging the light irradiation units 400 at both ends of the ultrasonic probe 12, there is an advantage that an abnormal site can be easily guided to the vicinity of the center on the central axis C of the ultrasonic transmitting / receiving surface 120.

  According to the configuration described above, the probe is guided (navigation) over the suspicious tissue inside the subject, and the acquisition of the ultrasonic image and the measurement of the biological light are performed with the suspicious tissue included in the scanning section. Can be. For this reason, the position and size of the suspicious tissue using the detected light can be easily and quickly calculated as a forward problem comparing the intensity of the light detected by each detection unit with a previously generated database. In this way, real-time performance can be dramatically improved. The surgeon arranges the probe directly above the suspect tissue in the subject, visually inspects the tomogram using an ultrasonic image, and expresses blood metabolism information (information such as hemoglobin absorption position, size, absorption coefficient, etc.) specified on the ultrasonic image. ), Etc., and benign / malignant judgments can be sequentially executed with high real-time performance. As a result, regardless of the level of skill, anyone can accurately, appropriately and promptly perform breast cancer inspection / determination (detection of abnormal site and determination of benign / malignant).

  In biological light measurement, the maximum distance from the light irradiation unit to the light detection unit is required to be at least twice as large as the measurable depth of the abnormal site, and therefore the entire probe tends to be large. In the present embodiment, the light irradiation unit and the light detection unit are arranged in the vicinity of the ultrasonic probe as the central axis in the longitudinal direction of the ultrasonic transmission and reception surface, so that the ultrasonic probe and the optical probe are integrated. The overall size of the probe can be reduced.

(Sixth embodiment)
In each of the above-described embodiments, as a means for guiding the probe to an abnormal site or for transmitting a suitable degree of adhesion of the probe, for example, the display method shown in FIGS. 7 to 10 or the acoustic signal shown in FIG. The transmission method and the like have been exemplified. However, at the time of actual imaging, the inspector moves the probe while observing the ultrasonic image, so that it is a heavy burden to simultaneously watch the probe operation support information shown in FIG. 7 and the like. It may be. In addition, transmission by an acoustic signal has a merit that an inspector can receive scanning guidance without looking at a screen, but has a demerit that a subject becomes anxious due to an abnormal sound.

  Therefore, in the present embodiment, information indicating the approach state of the probe to the abnormal site specified by the biological light measurement is displayed so as to be promptly observable in a form in which the examiner's gaze load is reduced as much as possible, and the abnormal site of the probe is displayed. The ultrasonic diagnostic apparatus 1 for facilitating guidance to the patient will be described.

  The display form of the information indicating the approach state of the probe to the abnormal part and the support information of the probe operation in the present embodiment have, for example, the following two features. First, information indicating the approach state of the probe to the abnormal site is displayed as a part of the screen of the ultrasonic image watched by the examiner. Thus, the inspector can obtain information without reciprocating the line of sight. Second, the information indicating the approach state of the probe to the abnormal site is displayed in a form that allows the examiner to instantaneously grasp the contents of the ultrasonic diagnostic image so as not to hinder the act of concentrating attention on the ultrasonic diagnostic image. .

  FIG. 30 is a diagram illustrating a form in which the approach state between the probe and the abnormal part specified by the biological light measurement is shown as a part (for example, an icon or the like) of the screen of the ultrasonic image. FIGS. 31A to 31D are diagrams illustrating an example in which the brightness of the icon changes as the probe approaches the specified abnormal part.

  The brightness of the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. 30 changes as the probe approaches the specified abnormal part, as shown in FIGS. 31 (a) and (b). Is closest to the abnormal part (that is, when the ultrasonic transmission / reception surface 120 is disposed right above the abnormal part), the light becomes the brightest as shown in FIG. Also, when the ultrasonic transmitting / receiving surface 120 is separated from right above 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 the probe moves from the abnormal part. It gradually darkens as you move away.

(Modification 1)
FIGS. 32A to 32D are diagrams exemplifying a state in which the color and the like of the icon change as the probe approaches the specified abnormal part.

  For example, the color of the icon A displayed at the upper right of the screen of the ultrasonic image shown in FIG. 32 indicates that the distance between the abnormal site and the probe specified by the biological light measurement is longer than a certain value. ) Is displayed in a predetermined hue (for example, green). When the probe is scanned according to the support information and the distance between the abnormal part and the probe is within a certain range, the color of the icon A changes to another hue (for example, orange) as shown in FIG. When the user has approached the abnormal part, it is displayed in red, for example, as shown in FIG. When the ultrasonic transmission / reception surface 120 is separated from immediately above the abnormal part, the brightness of the icon A changes from red in FIG. 33C to another color according to the distance between the abnormal part and the probe. (Green in the example of FIG. 33D).

(Modification 2)
The approaching state between the probe and the abnormal site specified by the biological light measurement may be indicated as a change in the blinking cycle of a part (such as an icon) of the screen of the ultrasonic image. For example, the icon A displayed on the upper right of the screen of the ultrasonic image blinks at a constant or longer cycle when the distance between the probe and the abnormal site specified by the biological light measurement is greater than a certain value. The probe is scanned according to the information indicating the approach state of the probe to the abnormal part, and the blinking cycle of the icon A becomes shorter as the distance between the abnormal part and the probe is reduced. When the probe comes closest to the abnormal part, the icon A becomes , Flickers in the shortest cycle. When the ultrasonic transmission / reception surface 120 is separated from right above the abnormal part, the icon A blinks while changing the period according to the distance between the abnormal part and the probe.

(Modification 3)
FIGS. 33A to 33D are diagrams illustrating a state where the display area of the icon changes as the probe approaches the specified abnormal part.

  For example, as shown in FIGS. 33A and 33B, the area of the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. 33, the distance increases with the distance, and reaches the maximum when approaching the abnormal part as shown in FIG. 33 (c). In addition, when the ultrasonic transmission / reception surface 120 is separated from right above the abnormal part, the area of the icon A becomes smaller as the probe moves away from the abnormal part, as shown in FIGS. 33 (c) and 33 (d). Become.

(Modification 4)
FIGS. 34A to 34D are diagrams illustrating a state where the display position of the icon changes as the probe approaches the specified abnormal part.

  For example, the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. 30 is, as shown in, for example, FIGS. 34 (a) and 34 (b), the abnormal site and the probe identified by the biological light measurement. Is displayed at the same position when the distance is longer than a certain distance, and when the probe is closest to the abnormal part (when the distance between the abnormal part and the probe is within a certain range), FIG. It is displayed at a predetermined position as shown (in the example of the figure, the display position is raised). When the ultrasonic transmitting / receiving surface 120 is separated from the position just above the abnormal part by a certain amount or more, the icon A is positioned at the same position as in FIGS. 34 (a) and 34 (b) as shown in FIG. 34 (d). Will be displayed.

(Modification 5)
FIGS. 35A to 35D are diagrams illustrating a manner in which the amplitude of the icon swing changes as the probe approaches the specified abnormal part.

  For example, the amplitude of the fluctuation of the icon A displayed on the upper right of the screen of the ultrasonic image shown in FIG. 30 is, for example, as shown in FIGS. 35 (a) and 35 (b). It changes as the distance between the part and the probe becomes shorter, and when the part comes closest to the abnormal part, it is displayed with a swing of the maximum amplitude as shown in FIG. When the ultrasonic transmitting / receiving surface 120 is separated from right 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.

(Modification 6)
FIGS. 36A to 36D are diagrams illustrating a state in which the shape of the icon changes as the probe approaches the specified abnormal part.

  For example, the shape of the icon A displayed at the upper right of the screen of the ultrasonic image shown in FIG. 30 is, for example, as shown in FIGS. It changes as the distance from the probe becomes shorter (in the example of the figure, the number of convex portions increases). When the abnormal portion comes closest, the convex portion is displayed in the shape having the largest number of convex portions as shown in FIG. You. When the ultrasonic transmission / reception surface 120 is separated from right above the abnormal part, the shape of the icon A is such that the number of convex portions decreases as the probe moves away from the abnormal part, as shown in FIG. Change.

  In addition, various display examples for notifying the approaching state between the abnormal part and the probe are shown. Of course, these notations can be arbitrarily combined. For example, in addition to the display method based on the color change of the icons shown in the first modification, a change in lightness may be combined, and a blinking cycle, a display area, a shape, a magnitude of shaking, and the like may be simultaneously determined according to an approaching state. It may be changed. Thereby, the approaching state between the abnormal part and the probe can be presented in a form with higher visibility.

  According to the configuration described above, the approach state between the abnormal site in the subject and the probe on the subject surface is displayed on the screen on which the ultrasonic image is displayed, by the brightness, the color, the blink period, the display area, and the shape of the icon. , The amplitude of the sway, or a combination thereof. Thereby, the inspector can visually recognize the ultrasonic image and the probe operation support information without reciprocating the line of sight. Further, the probe operation support information is presented as a change in the brightness of the icon or the like. For this reason, it is possible to present the lobe operation support information that can be quickly and easily grasped without disturbing the examiner's attention to the ultrasonic diagnostic image.

  Further, an optical measurement device according to another embodiment 1 is an optical measurement device used together with an ultrasonic probe, and a light irradiation unit that irradiates light from at least one position in a subject; A plurality of light detection units disposed at least on both sides of the ultrasonic transmission / reception surface with the center axis of the ultrasonic transmission / reception surface as a symmetric axis, and detecting the intensity of light reflected in the subject; A calculation for calculating at least an approach degree between a position of a portion exhibiting an abnormal light absorption coefficient in the subject and a predetermined position based on the position of the light irradiation unit based on the intensity of light detected by the detection unit. And an output unit that outputs support information based on the proximity.

  As another embodiment 2, in the optical measurement device according to the other embodiment 1, at least two pairs of the plurality of light detection units may be provided with a straight line passing through the light irradiation unit as a symmetric axis.

  As another embodiment 3, in the optical measurement device according to the first or second embodiment, the light irradiation unit may emit light from two or more positions.

  As another embodiment 4, in the optical measurement device according to the first or second embodiment, the light irradiation unit may emit light including at least two types of frequencies.

  As another embodiment 5, in the optical measurement device according to any of the other embodiments 1 to 4, the support information may include an acoustic signal reflecting the proximity.

  As another embodiment 6, in the optical measurement device according to any of the first to fifth embodiments, the support information may include information that visually indicates the degree of approach.

  As another embodiment 7, in the optical measurement device according to any one of the other embodiments 1 to 6, the calculation unit is configured to perform the abnormal light absorption based on the intensity of light detected by each of the light detection units. The position of the part indicating the coefficient may be further calculated, and the support information may include information indicating the position of the part indicating the abnormal light absorption coefficient.

  As another embodiment 8, in the optical measurement device according to any one of the other embodiments 1 to 7, the light irradiation unit has a plurality of light sources corresponding to a plurality of wavelengths, and the calculation unit includes the light source. It may be provided every time.

  As a ninth embodiment, in the optical measurement device according to any one of the first to eighth embodiments, the light irradiation unit includes a first wavelength component that is an absorption wavelength band of a portion exhibiting the abnormal light absorption coefficient. And, irradiating light including a second wavelength component excluding the absorption wavelength band of the portion showing the abnormal light absorption coefficient, the calculation unit, the intensity of the detection light caused by the first wavelength component and the second The position of the part exhibiting the abnormal light absorption coefficient may be calculated by comparing the intensity of the detection light caused by the two wavelength components.

  As another embodiment 10, in the optical measurement device according to any one of the other embodiments 1 to 9, the calculation unit includes an ultrasonic image acquired using an ultrasonic probe provided with the optical measurement device; At least the proximity may be calculated based on a change in light intensity detected by the plurality of light detection units.

  As another embodiment 11, in the optical measurement device according to any one of the other embodiments 1 to 10, the light irradiation unit includes the light irradiation unit around the ultrasonic transmission / reception surface of an ultrasonic probe provided with the light measurement device. The plurality of photodetectors are arranged on the central axis in the longitudinal direction of the ultrasonic transmitting and receiving surface, and are arranged at different positions around the ultrasonic transmitting and receiving surface with the central axis in the longitudinal direction of the ultrasonic transmitting and receiving surface as the symmetry axis. May be performed.

  Another embodiment 12 is an optical measurement device used together with an ultrasonic probe, wherein the light irradiator irradiates light from at least one position into a subject, and a central axis of an ultrasonic transmitting / receiving surface of the ultrasonic probe. A plurality of light detection units disposed at least on both sides of the ultrasonic transmission / reception surface with the symmetric axis as the symmetry axis and detecting the intensity of light reflected within the subject, and an abnormal light absorption coefficient within the subject And an output unit that outputs, as an acoustic signal, information on the approach to the part indicating the above.

  As a thirteenth embodiment, in the ultrasonic diagnostic apparatus according to the thirteenth embodiment, the acoustic signal may be output at a high or low frequency.

  Although several embodiments of the present invention have been described, these embodiments are provided by way of example and are not intended to limit the scope of the invention. These new embodiments can be implemented in other various forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and equivalents thereof.

DESCRIPTION OF SYMBOLS 1 ... Ultrasonic diagnostic apparatus, 11 ... Device main body, 12 ... Ultrasonic probe, 13 ... Input device, 14 ... Monitor, 21 ... Ultrasonic transmission unit, 22 ... Ultrasonic receiving unit, 23 ... B-mode 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 light Probe, 42: Optical measurement processing unit, 44: Support information generation unit, 400: Light irradiation unit, 401: Light detection unit, 420: Light source 420, 422: Optical signal control unit, 424: Optical analysis unit, 426: Operation circuit

Claims (24)

An optical measurement device used with an ultrasonic probe,
A light irradiation unit that irradiates light from at least one position in the subject,
A plurality of pairs of photodetectors each disposed with an ultrasonic transmission / reception surface of the ultrasonic probe interposed therebetween, wherein a symmetry axis of each pair is located in the ultrasonic transmission / reception surface and a symmetry of each pair is provided. axis coincides with the line parallel to the long side defining said ultrasonic wave transmission and reception surface, and a light detecting portion of the plurality of pairs for detecting the intensity of said reflected in the object light,
An output unit that outputs support information based on the degree of approach to a part showing an abnormal light absorption coefficient in the subject,
Equipped with,
The optical measurement device , wherein the plurality of pairs of light detection units are arranged on concentric circles having different radii around the light irradiation unit . The light detecting portion of the plurality of pairs, the are arranged in a region sandwiched extension of the two short sides of the ultrasonic transmitting and receiving surface, the optical measuring device according to claim 1. An optical measurement device used with an ultrasonic probe,
A light irradiation unit that irradiates light from at least one position in the subject,
A plurality of pairs of photodetectors each disposed with an ultrasonic transmission / reception surface of the ultrasonic probe interposed therebetween, wherein a symmetric axis of each pair is located in the ultrasonic transmission / reception surface and a symmetry of each pair is provided. axis coincides with the line parallel to the long side defining said ultrasonic wave transmission and reception surface, and a light detecting portion of the plurality of pairs for detecting the intensity of said reflected in the object light,
An output unit that outputs support information based on the degree of approach to a part showing an abnormal light absorption coefficient in the subject,
Equipped with,
The optical measurement device , wherein the plurality of pairs of light detection units are arranged in a region between two extended lines of the short side on the ultrasonic transmission / reception surface . Based on the intensity of light detected in each of the light detection units, at least the proximity between a position of a part showing an abnormal light absorption coefficient in the subject and a predetermined position based on the position of the light irradiation unit is determined. The optical measurement device according to any one of claims 1 to 3, further comprising a calculation unit that performs calculation. It said plurality of optical detecting unit, before Kijika line at least two pairs provided in which the optical measuring device as claimed in any one of claims 1 to 4 as a symmetrical axis. The light irradiating unit is at least a pair of light irradiating units that irradiate light from two or more positions, and each pair of the light irradiating units is disposed with an ultrasonic transmitting and receiving surface of the ultrasonic probe interposed therebetween, and any one of claims 1 to 5 axis of symmetry of pairs the axis of symmetry of the position to and each pair ultrasonic transmitting and receiving plane are arranged side by side with one of the sides defining the ultrasonic transmitting and receiving flush The optical measurement device according to the item. Optical measuring device as claimed in any one of claims 1 to 6 wherein the light irradiation unit irradiates light including at least two kinds of frequencies. The support information, the optical measuring device as claimed in any one of claims 1 to 7 including an acoustic signal. The support information, the optical measuring device as claimed in any one of claims 1 to 8 includes information indicating the closeness visually. The light irradiation unit is an optical measuring device as claimed in any one of claims 1 to 9 having a plurality of light sources corresponding to a plurality of wavelengths. Based on the intensity of light detected in each of the light detection units, at least the proximity between a position of a part showing an abnormal light absorption coefficient in the subject and a predetermined position based on the position of the light irradiation unit is determined. Further comprising a calculation unit for calculating,
The light irradiation unit includes a first wavelength component that is an absorption wavelength band of a portion exhibiting the abnormal light absorption coefficient, and a second wavelength component excluding an absorption wavelength band of the portion exhibiting the abnormal light absorption coefficient. Irradiate light,
The calculator compares a strength of the detected light due to the intensity and the second wavelength component of the detection light caused by the first wavelength component according to claim 1 to 10 at least calculate the proximity The optical measurement device according to claim 1. 12. The plurality of pairs of photodetectors are arranged outside a region between two extended sides of the ultrasonic transmitting and receiving surface, which are interposed between the two extended lines. 13. Optical measuring device. An ultrasonic probe,
A light irradiation unit that irradiates light from at least one position in the subject,
A plurality of pairs of photodetectors each disposed with an ultrasonic transmission / reception surface of the ultrasonic probe interposed therebetween, wherein a symmetric axis of each pair is located in the ultrasonic transmission / reception surface and a symmetry of each pair is provided. axis coincides with the line parallel to the long side defining said ultrasonic wave transmission and reception surface, and a light detecting portion of the plurality of pairs for detecting the intensity of said reflected in the object light,
An output unit that outputs support information based on the degree of approach to a part showing an abnormal light absorption coefficient in the subject,
Equipped with,
The ultrasonic diagnostic apparatus , wherein the plurality of pairs of light detection units are arranged on concentric circles having different radii around the light irradiation unit . 14. The ultrasonic diagnostic apparatus according to claim 13 , wherein the plurality of pairs of photodetectors are arranged in a region between two extended short lines on the ultrasonic transmitting and receiving surface. An ultrasonic probe,
A light irradiation unit that irradiates light from at least one position in the subject,
A plurality of pairs of photodetectors each disposed with an ultrasonic transmission / reception surface of the ultrasonic probe interposed therebetween, wherein a symmetric axis of each pair is located in the ultrasonic transmission / reception surface and a symmetry of each pair is provided. axis coincides with the line parallel to the long side defining said ultrasonic wave transmission and reception surface, and a light detecting portion of the plurality of pairs for detecting the intensity of said reflected in the object light,
An output unit that outputs support information based on the degree of approach to a part showing an abnormal light absorption coefficient in the subject,
Equipped with,
An ultrasonic diagnostic apparatus , wherein the plurality of pairs of light detection units are arranged in a region between two extended short lines on the ultrasonic transmission / reception surface . Based on the intensity of light detected in each of the light detection units, at least the proximity between a position of a part showing an abnormal light absorption coefficient in the subject and a predetermined position based on the position of the light irradiation unit is determined. The ultrasonic diagnostic apparatus according to any one of claims 13 to 15, further comprising a calculating unit for calculating. It said plurality of optical detecting unit, prior ultrasonic diagnostic apparatus as claimed in any one of at least two pairs provided by which claims 13 to 16 Kijika line as a symmetrical axis. The light irradiating unit is at least a pair of light irradiating units that irradiate light from two or more positions, and each pair of the light irradiating units is disposed with an ultrasonic transmitting and receiving surface of the ultrasonic probe interposed therebetween, and any one of claims 13 to 17 axis of symmetry of pairs the axis of symmetry of the position to and each pair ultrasonic transmitting and receiving plane are arranged side by side with one of the sides defining the ultrasonic transmitting and receiving flush An ultrasonic diagnostic apparatus according to any one of the preceding claims. The ultrasonic diagnostic apparatus according to any one of claims 13 to 18 , wherein the light irradiator irradiates light including at least two types of frequencies. The support information, the ultrasonic diagnostic apparatus as claimed in any one of claims 13 to 19 including an acoustic signal. The support information, the ultrasonic diagnostic apparatus as claimed in any one of claims 13 to 20 including the information indicating the closeness visually. 22. The ultrasonic diagnostic apparatus according to claim 13, wherein the light irradiation unit has a plurality of light sources corresponding to a plurality of wavelengths. Based on the intensity of light detected in each of the light detection units, at least the proximity between a position of a part showing an abnormal light absorption coefficient in the subject and a predetermined position based on the position of the light irradiation unit is determined. Further comprising a calculation unit for calculating,
The light irradiating unit includes a first wavelength component that is an absorption wavelength band of a portion exhibiting the abnormal light absorption coefficient, and a second wavelength component excluding an absorption wavelength band of the portion exhibiting the abnormal light absorption coefficient. Irradiate light,
The calculator compares a strength of the detected light due to the intensity and the second wavelength component of the detection light caused by the first wavelength component according to claim 13 to 22, at least calculate the proximity The ultrasonic diagnostic apparatus according to claim 1. Light detecting portion of the plurality of pairs, wherein is arranged outside the region sandwiched extension of the two long sides of the ultrasonic wave transmission and reception surface, any one of claims 13 to claim 23 Ultrasonic diagnostic equipment.