JP2015188466A - Ultrasonic measurement apparatus and measurement method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonic measurement apparatus, a measuring method, etc. capable of measuring sieve-like board thickness information while suppressing a burden on a user.SOLUTION: An ultrasonic measurement apparatus 100 includes a sensor surface 220 that can contact the surface of an eyelid when the ultrasonic measurement apparatus 100 is mounted, an ultrasonic transducer device 210 for transmitting an ultrasonic beam to a discus nervi optici part of an eyeball through the sensor surface 220 and receiving an ultrasonic echo by the ultrasonic beam, and a control part 125 for measuring sieve-like board thickness information based on the received ultrasonic echo.

Description

  The present invention relates to an ultrasonic measurement apparatus, a measurement method, and the like.

  Recent studies have found that a reduction in phloem thickness at the fundus is one of the mechanisms for the development of glaucoma. Therefore, if the phloem plate thickness can be grasped more accurately, it becomes possible to improve the diagnostic accuracy of whether or not there is a suspicion of glaucoma, to perform more effective medication treatment, and the like.

  Conventionally, as a method for analyzing the structure of the fundus, there is an invention as described in Patent Document 1, for example. In the invention disclosed in Patent Document 1, the structure of the fundus including the phloem plate is optically analyzed through the cornea using an OCT (Optical Coherence Tomography) apparatus.

Special Table 2002-513310

  However, as in the prior art of Patent Document 1, in the method of measuring the sieve plate thickness using a stationary OCT apparatus, the user (measured person) faces the OCT apparatus and the head It was necessary to perform measurement with the part fixed. In addition, such an OCT apparatus is difficult to carry, and the measurement location is limited to hospitals and clinics. Therefore, the burden placed on the user before measuring the sieve plate thickness was large.

  According to some aspects of the present invention, it is possible to provide an ultrasonic measurement device, a measurement method, and the like that can measure sieve-like plate thickness information while suppressing a burden on the user.

  One aspect of the present invention is to transmit an ultrasonic beam to the optic papilla of an eyeball through the sensor surface that can contact the surface of the eyelid when the ultrasonic measurement device is mounted, and to use the ultrasonic beam. The present invention relates to an ultrasonic measurement device that includes an ultrasonic transducer device that receives an ultrasonic echo and a control unit that measures sieving plate thickness information based on the received ultrasonic echo.

  In one embodiment of the present invention, the user wears the ultrasonic measurement device so that the sensor surface is in contact with the heel surface. Then, an ultrasonic beam is transmitted to the optic papilla of the eyeball via the sensor surface (an eyelid surface), an ultrasonic echo for the transmitted ultrasonic beam is received, and sieving plate thickness information based on the received ultrasonic echo Measure.

  Therefore, it is possible to measure the sieve plate thickness information while suppressing the burden on the user.

  In one embodiment of the present invention, the control unit is based on a phase difference between the first ultrasonic echo from the surface of the sieve plate and the second ultrasonic echo from the back surface of the sieve plate. The sieve plate thickness information may be measured.

  As a result, it is possible to obtain sieving plate thickness information before the correction process.

  In one aspect of the present invention, the control unit identifies a first part and a second part in the eyeball, and calculates a correction parameter from a positional relationship between the first part and the second part. The sieve thickness information may be corrected using the correction parameter.

  This makes it possible to obtain correct sieve plate thickness information.

  In the aspect of the invention, the first part may be a central part of the eyeball, and the second part may be the optic papilla.

  Accordingly, it is possible to obtain a correction parameter used in the correction process for the phloem plate thickness information based on the positional relationship between the center of the eyeball and the optic papilla.

  In the aspect of the invention, the control unit may specify an incident angle of the ultrasonic beam on the sieve plate as the correction parameter.

  Thereby, it is possible to correct the sieve plate thickness information calculated by the ultrasonic echo based on the incident angle of the ultrasonic beam to the sieve plate.

  In one aspect of the present invention, the incident angle of the ultrasonic beam is an angle formed by a vector from the optic nerve head to the center of the eyeball and a vector from the sensor surface to the optic nerve head. It may be an angle.

  This makes it possible to calculate the incident angle of the ultrasonic beam with respect to the sieve plate or the optic papilla.

  In one aspect of the present invention, the control unit may stop measuring the sieving plate thickness information when the specified incident angle is equal to or greater than a given angle.

  As a result, it is possible to suppress an error that occurs in the correction process of the sieve-like plate thickness information.

  In one aspect of the present invention, the control unit acquires a cross-sectional image by scanning an area including the optic nerve head with the ultrasonic beam, and recognizes the shape of the optic nerve head in the acquired cross-sectional image. Then, the central part of the optic nerve head may be specified.

  Accordingly, it is possible to transmit an ultrasonic beam to the sieve plate based on the specified position of the optic nerve head.

  In one aspect of the present invention, the control unit detects a position of the optic nerve head based on the received ultrasonic echo, and identifies a first part and a second part in the eyeball. Based on the positional relationship between the first part and the second part, a correction parameter of the sieve plate thickness information is obtained, and the first ultrasonic echo from the surface of the sieve plate and the sieve shape The sieve plate thickness information may be measured based on a phase difference with the second ultrasonic echo from the back surface of the plate, and the sieve plate thickness information may be corrected by the correction parameter.

  Thereby, even when the ultrasonic beam is irradiated with being inclined with respect to the sieve plate, it is possible to measure correct sieve plate thickness information and the like.

  Moreover, in one aspect of the present invention, a storage unit that stores the measured sieve-like plate thickness information in time series order may be included.

  This makes it possible to compare the newly measured sieve plate thickness information with the past sieve plate thickness information.

  In addition, in one aspect of the present invention, a notification unit that notifies that the sieve plate thickness represented by the sieve plate thickness information is equal to or less than a given threshold value may be included.

  This makes it possible for the user to know that the sieve plate is thin and that glaucoma is suspected.

  In one embodiment of the present invention, a support unit that supports a sensor unit having the sensor surface and the ultrasonic transducer device is included, and the sensor surface is supported by the support unit so as to be in contact with the heel surface. May be.

  As a result, the user can simply put on the ultrasonic measurement device (glasses frame) so that the sensor surface comes into contact with the eyelid surface and the ultrasonic beam can be transmitted in the eyeball direction.

  In one aspect of the present invention, the control unit identifies the position of the optic papilla, and irradiates the ultrasonic beam on a measurement range set based on the identified position of the optic papilla. The blood flow information may be measured based on the Doppler shift amount of the ultrasonic echo.

  This makes it possible to measure blood flow information in a given measurement range centered on the optic nerve head, for example.

  In one embodiment of the present invention, the control unit may measure at least one of intraocular pressure and an eyeball diameter based on the ultrasonic echo.

  This makes it possible to perform ultrasonic irradiation processing based on at least one information of intraocular pressure and eyeball diameter.

  In the aspect of the invention, the control unit may irradiate the corner portion with the ultrasonic beam when the sieve plate thickness represented by the sieve plate thickness information is equal to or less than a given threshold value. Processing may be performed.

  This makes it possible to treat the eyeball with an ultrasonic beam when the sieve plate is thin and there is a suspicion of glaucoma.

  In one aspect of the present invention, the control unit measures an intraocular pressure based on the received ultrasonic echo, the sieve plate thickness is equal to or less than the given threshold value, and the intraocular pressure is determined. When the pressure is higher than a given pressure, the irradiation process of irradiating the corner with the ultrasonic beam may be performed.

  This makes it possible to determine the timing for treating an ocular disease with an ultrasonic beam based not only on the intraocular pressure but also on the sieve plate thickness.

  In another aspect of the present invention, when the ultrasonic measurement device is mounted, an ultrasonic transducer device is used to superimpose the optic nerve head of the eyeball through the sensor surface of the ultrasonic measurement device that can contact the surface of the eyelid. The present invention relates to a measurement method of transmitting a sound beam, receiving an ultrasonic echo by the ultrasonic beam, and measuring sieve-like plate thickness information by a control unit based on the received ultrasonic echo.

1 is a configuration example of an ultrasonic measurement apparatus according to the present embodiment. 1 is a detailed configuration example of an ultrasonic measurement apparatus according to the present embodiment. The example of a structure of a sensor part. Explanatory drawing about mounting | wearing of an ultrasonic measurement apparatus. The flowchart explaining the flow of a sieve-like plate thickness measurement process. Explanatory drawing around the eyeball. 7A and 7B are explanatory diagrams of ultrasonic transmission / reception processing with respect to the sieve plate. FIG. 8A to FIG. 8D are explanatory diagrams of the sieve plate thickness measurement process. The flowchart explaining the flow of a blood-flow information measurement process. 10A to 10C are explanatory diagrams of blood flow information measurement processing. Explanatory drawing about the glaucoma treatment using an ultrasonic wave. 12A and 12B are flowcharts for explaining the flow of eyeball information measurement processing. The flowchart explaining the flow of the glaucoma treatment using an ultrasonic wave. FIG. 14A and FIG. 14B are flowcharts illustrating details of glaucoma treatment. The figure explaining the measurement of the eyeball diameter by an ultrasonic measuring device. An example of the relationship between the intraocular pressure and the fluctuation of the eyeball diameter. The figure explaining estimation of the intraocular pressure by an ultrasonic measuring device. FIG. 18A to FIG. 18C are configuration examples of ultrasonic transducer elements. 1 is a first configuration example of an ultrasonic transducer device. FIG. 20A and FIG. 20B are diagrams for explaining beam scanning by the first configuration example of the ultrasonic transducer device. The figure explaining estimation of a true eyeball diameter. The 2nd structural example of an ultrasonic transducer device. The figure explaining the beam scan by the 2nd structural example of an ultrasonic transducer device. The flowchart explaining the estimation calculation process of an eyeball diameter. The flowchart explaining the process which specifies the relationship between eyeball diameter information and intraocular pressure. The flowchart explaining the estimation process of intraocular pressure.

  Hereinafter, this embodiment will be described. In addition, this embodiment demonstrated below does not unduly limit the content of this invention described in the claim. In addition, all the configurations described in the present embodiment are not necessarily essential configuration requirements of the present invention.

1. Ultrasonic Measuring Device FIG. 1 shows a configuration example of an ultrasonic measuring device 100 of the present embodiment. The ultrasonic measurement apparatus 100 according to this embodiment includes a sensor unit 200 and a control unit 125. The sensor unit 200 includes an ultrasonic transducer device 210, a sensor surface 220, a transmission unit 110, and a reception unit 120. Note that the ultrasonic measurement apparatus 100 (ultrasonic apparatus) of the present embodiment is not limited to the configuration in FIG. 1, and some of the components are omitted, replaced with other components, or other components are replaced. Various modifications such as addition are possible.

  The ultrasonic transducer device 210 transmits an ultrasonic beam. Specifically, an ultrasonic beam is transmitted (irradiated) toward the eyeball (corner corner, optic papilla etc.) through the surface of the eyelid (eye lid). The ultrasonic transducer device 210 may receive (transmit / receive) ultrasonic waves. For example, the ultrasonic transducer device 210 transmits an ultrasonic beam in the eyeball direction through the eyelid, and receives an ultrasonic echo in which the ultrasonic beam is reflected by an object.

  The ultrasonic transducer device 210 has an ultrasonic transducer element. The ultrasonic transducer element converts a transmission signal, which is an electric signal, into ultrasonic waves. The ultrasonic transducer element converts an ultrasonic echo from an object (subject) into an electrical signal. The ultrasonic transducer element may be, for example, a thin film piezoelectric ultrasonic transducer element or a bulk piezoelectric ultrasonic transducer element, or a capacitive micromachined ultrasonic transducer element (CMUT). It may be.

  The sensor surface 220 contacts the heel surface when the ultrasonic measurement device (sensor unit) is attached. The sensor surface 220 is, for example, a surface that contacts the heel surface at the time of mounting (measurement) of the outer surfaces of the sensor unit 200. The sensor surface 220 may be, for example, the surface of a protective film that covers the ultrasonic transducer device 210, or the surface of a member that propagates ultrasonic waves such as an acoustic lens. The sensor surface 220 may contact the heel surface via a gel applied to the heel surface.

  The transmission unit 110 performs ultrasonic beam transmission processing. Specifically, the transmission unit 110 generates and amplifies a pulse signal based on the control of the control unit 125 (transmission / reception control unit), and transmits a transmission signal (drive signal) that is an electrical signal to the ultrasonic transducer device 210. Is output. The ultrasonic transducer device 210 converts a transmission signal that is an electrical signal into an ultrasonic wave, and transmits the ultrasonic wave. The transmission unit 110 can be configured by, for example, a pulse generator, an amplifier, or the like. Note that at least a part of the transmission unit 110 may be provided outside the sensor unit 200 (for example, integrated with the control unit 125). The transmission signal may be, for example, a sine wave pulse, a rectangular wave pulse, or a triangular wave pulse. Moreover, it is not limited to the pulse for 1 period, For example, the pulse for 1/2 period, the pulse for 3/2 period, the pulse for 2 periods, etc. may be sufficient.

  The receiving unit 120 performs ultrasonic echo reception processing. Specifically, the ultrasonic transducer device 210 converts an ultrasonic echo from the subject (object) into an electric signal and outputs the electric signal to the receiving unit 120. The reception unit 120 performs reception processing such as amplification, detection, A / D conversion, and phase matching on an analog reception signal that is an electrical signal from the ultrasonic transducer device 210, and a digital reception signal after reception processing. (Digital data) is output to the control unit 125. The receiving unit 120 can be configured by, for example, a low noise amplifier, a voltage control attenuator, a programmable gain amplifier, a low pass filter, an A / D converter, and the like. Note that at least a part of the receiving unit 120 may be provided outside the sensor unit 200 (for example, integrated with the control unit 125).

  FIG. 2 shows a detailed configuration example of the ultrasonic measurement apparatus 100 of the present embodiment. In FIG. 2, the control unit 125 includes a transmission / reception control unit 130 and a processing unit 140. The ultrasonic measurement apparatus 100 further includes a storage unit 150 and a notification unit 160.

  The transmission / reception control unit 130 controls transmission / reception processing by the transmission unit 110 and the reception unit 120 based on the control processing of the processing unit 140. Specifically, for example, the switching control between the transmission period and the reception period, or the timing of the transmission signal output from the transmission unit 110 is controlled to perform the beam scan control of the ultrasonic beam or the gain control of the reception unit 120.

  The processing unit 140 performs control processing of the ultrasonic measurement apparatus 100 and various types of processing. For example, measurement processing of phleboform thickness information, blood flow information measurement processing, eyeball information measurement processing, ultrasonic irradiation processing, ultrasonic image recognition processing, or intraocular pressure estimation calculation processing is performed. The processing unit 140 can be realized by a processor such as a CPU (program executed by the processor), an ASIC logic circuit, or the like.

  The storage unit 150 is configured by a storage device such as a semiconductor memory (DRAM or SRAM), for example, and receives signals, sieve plate thickness information, blood flow information (blood flow velocity, etc.), eyeball information (eyeball diameter, intraocular pressure). Etc.). In addition, the storage unit 150 further includes a non-volatile storage device such as a flash memory, and stores previously measured screen-like plate thickness information, blood flow information, eyeball information, and the like in the order of its own sequence. Thereby, it is possible to compare the newly measured sieve plate thickness information and blood flow information with the past sieve plate thickness information and blood flow information.

  The notification unit 160 is a device that notifies information, and can be realized by, for example, a display (display device) or a speaker. The notification unit 160 notifies the user of the notification information from the processing unit 140. The display is, for example, a liquid crystal display, an organic EL display, or the like, and displays display image data including notification information from the processing unit 140. The notification unit 160 may be, for example, a beeper that generates a beep sound, an LED that emits light or blinks, or a vibrator that vibrates. The notification information may include information related to normal or abnormal intraocular pressure, information related to temporal changes in eyeball information (such as intraocular pressure), and information for instructing a user to perform a necessary operation.

  FIG. 3 shows a configuration example of the sensor unit 200. The sensor unit 200 includes an ultrasonic transducer device 210, a sensor surface 220, a protective film 230, a base substrate 240, a flexible substrate 250, a transmission unit 110, and a reception unit 120. Note that the sensor unit 200 of the present embodiment is not limited to the configuration of FIG. 3, and various modifications such as omitting some of the components, replacing them with other components, and adding other components. Implementation is possible. For example, at least one of the transmission unit 110 and the reception unit 120 may be provided outside the sensor unit 200. Alternatively, a part of the control unit 125 may be provided in the sensor unit 200.

  Since the ultrasonic transducer device 210 and the sensor surface 220 have already been described, detailed description thereof is omitted here.

  The ultrasonic transducer device 210, the transmission unit 110, and the reception unit 120 are provided on one surface of the base substrate 240. For example, each chip of the ultrasonic transducer device 210, the transmission unit 110, and the reception unit 120 is mounted on the substrate 240. The protective film 230 is a member (transparent member) that protects the ultrasonic transducer device 210, the transmission unit 110, and the reception unit 120. For example, the protective film 230 can be formed of a silicone resin or the like. In a state where the sensor surface 220 is in contact with the heel surface, the ultrasonic beam from the ultrasonic transducer device 210 and the ultrasonic echo reflected by the object are transmitted via the sensor surface 220 and the protective film 230.

  The ultrasonic transducer device 210 and the transmission unit 110 and the reception unit 120 are electrically connected by a flexible substrate 250. That is, the transmission signal of the ultrasonic transducer device 210 from the transmission unit 110 and the reception signal from the ultrasonic transducer device 210 to the reception unit 120 are transmitted by the wiring formed on the flexible substrate 250.

  The sensor unit 200 is supported by the support unit 170 in contact with the heel surface. The support portion 170 can be formed of an elastic material such as metal or resin. The sensor unit 200 is electrically connected to the control unit 125 (transmission / reception control unit 130) by the wiring 180.

  The ultrasonic measurement apparatus 100 of the present embodiment is an apparatus that can be worn by a user in a wearable manner. FIG. 4 is an explanatory diagram regarding the mounting of the ultrasonic measurement apparatus 100.

  The ultrasonic measurement apparatus 100 according to the present embodiment includes a support unit 170. The support unit 170 supports the sensor unit 200 including at least the sensor surface 220 and the ultrasonic transducer device 210. In FIG. 4, the support portion 170 is provided on a glasses-type frame. Specifically, the support portion 170 is fixed to a glasses-type frame. The support part 170 (and the sensor part 200) may be a member that can be attached to and detached from the frame.

  According to the configuration of FIG. 4, the sensor unit 200 can be reliably brought into contact with the lower arm by the support unit 170. Therefore, it is possible to perform ultrasonic measurement while reducing the physical burden on the subject. For example, the sensor unit 200 is supported by the support unit 170 so that the sensor surface 220 comes into contact with the user's eyelid when the user puts on a glasses-type frame. Then, the ultrasonic transducer device 210 of the sensor unit 200 is placed on a desired part (such as a sieve plate) of the eyeball while the sensor surface 220 is supported by the support unit 170 so as to come into contact with the heel surface in this way. Irradiate with ultrasonic waves. By doing so, a user who is a subject may always wear the ultrasonic measurement device 100 and measure phleboscopic thickness information and blood flow information at an appropriate timing, or may treat eye diseases. It becomes possible.

  Although the right eye part is shown in FIG. 4, the support part 170 can be similarly provided on the frame for the left eye part so that the sensor part 200 can be reliably brought into contact with the lower eyelid. Further, the frame is not limited to the eyeglass shape shown in FIG. 4, and may have another shape. Further, it is desirable that the support portion 170 is a member that is elastically deformed. In this way, the user can elastically deform the support portion 170 so that the sensor surface 220 properly contacts the heel surface at the time of wearing, thereby improving user convenience.

  The transmission / reception control unit 130 (control unit) is provided, for example, in a temple portion of a glasses-type frame. The sensor unit 200 and the transmission / reception control unit 130 are electrically connected by a wiring 180 provided along the frame. The transmission / reception control unit 130 is electrically connected to the ultrasonic measurement apparatus main body 101 (main apparatus) by a cable 190.

  The processing unit 140, the storage unit 150, and the notification unit 160 (display) in FIG. 2 are provided in the ultrasonic measurement device main body 101 (main device). The ultrasonic measurement apparatus main body 101 may be a dedicated portable terminal or a general-purpose portable terminal such as a smartphone.

  The transmission / reception control unit 130 and the ultrasonic measurement apparatus main body 101 (processing unit 140) may be connected by wireless communication such as short-range wireless communication instead of the cable 190.

  In FIG. 4, the transmission / reception control unit 130 is provided in the temple portion of the eyeglass-type frame and the processing unit 140 and the like are provided in the ultrasonic measurement apparatus main body 101. However, the present embodiment is not limited to this. That is, all the functions of the control unit 125 may be realized by a device attached to the temple portion of the eyeglass-type frame, or may be realized by the ultrasonic measurement device main body 101. A device that realizes part or all of the functions of the control unit 125 may be provided in the sensor unit 200.

  Various methods can be employed as a method of bringing the sensor surface 220 of the sensor unit 200 into contact with the heel surface. For example, in addition to the above-described spectacle frame type, an eye mask type or a method of directly attaching the sensor unit 200 to the eyelid may be employed. Further, the part that contacts the sensor surface 220 of the sensor unit 200 may be an upper eyelid or another part.

2. Screen-like plate thickness measurement process The ultrasonic measurement apparatus 100 of the present embodiment superimposes on the optic nerve head of the eyeball via the sensor surface 220 that can contact the eyelid surface when the ultrasonic measurement apparatus 100 is mounted, and the sensor surface 220. It includes an ultrasonic transducer device 210 that transmits an ultrasonic beam and receives an ultrasonic echo from the ultrasonic beam, and a control unit 125 that measures sieve plate thickness information based on the received ultrasonic echo.

  In the present embodiment, the user wears the ultrasonic measurement device 100 so that the sensor surface 220 contacts the heel surface. Then, an ultrasonic beam is transmitted to the optic papilla of the eyeball through the sensor surface 220 (an eyelid surface), and an ultrasonic echo for the transmitted ultrasonic beam is received, and the squeeze plate thickness is based on the received ultrasonic echo Measure information.

  Thus, in this embodiment, since a user's sieve plate | board thickness information is measured with an ultrasonic wave, a user does not feel dazzling at the time of a measurement. In addition, although the measurement is performed by bringing the sensor surface 220 into contact with the eyelid surface, it is not brought into contact with the eyeball, so that there is no pain during measurement and hygiene management is easy. Further, unlike the invention of Patent Document 1 described above, it is not necessary to fix the head directly to the OCT apparatus at the time of measurement, so that the user can perform measurement in an easy posture. .

  As a result, it is possible to measure the sieve plate thickness information without imposing a burden on the user. In addition, when the ultrasonic measurement apparatus 100 according to the present embodiment is small, the measurement location is not limited to a hospital or a clinic, and measurement can be performed anywhere.

  Furthermore, it is also possible to increase the number of times of measurement of sieve plate thickness information without imposing a burden on the user. As a result, it is possible to improve the measurement accuracy and the diagnosis accuracy of whether or not there is a suspicion of glaucoma.

  Next, details of the sieving plate thickness measurement process of the present embodiment will be described using the flowchart of FIG.

  As shown in FIG. 6, the sieve plate is located in the optic disc. Therefore, in the sieving plate thickness measurement process of the present embodiment, first, the control unit 125 performs a position detection process of the optic nerve head (S101).

  In the optic nerve head position detection process, as shown in FIG. 20A or FIG. 23 described later, the fundus is scanned widely, and the optic nerve head is detected by pattern recognition. That is, the control unit 125 scans an area including the optic papilla with an ultrasonic beam to acquire a cross-sectional image, recognizes the shape of the optic papilla in the acquired cross-sectional image, and specifies the central portion of the optic papilla. To do. Specifically, this is realized by generating a B-mode image (cross-sectional image) and performing known pattern matching, etc., using the generated B-mode image, as in the case of detecting the position of a corner portion described later. it can. As a result, for example, in the example of FIG. 7A, the position of the optic nerve head (the center thereof) is specified as the position N. Then, it is possible to transmit an ultrasonic beam to the sieve plate using the identified position of the optic nerve head as a mark.

  Here, FIG. 7 (A) and FIG. 7 (B) show the state at the time of transmission / reception of ultrasonic waves with respect to the sieve plate. FIG. 7A is an explanatory diagram of the ultrasonic beam UB transmitted to the sieve plate, and FIG. 7B is an explanatory diagram of the ultrasonic echoes (UE1 and UE2) from the sieve plate. . FIG. 7B is a simplified view of FIG. 7A in order to make it easier to distinguish between the ultrasonic echo UE1 from the surface of the sieve plate and the ultrasonic echo UE2 from the back surface. is there.

  In the sieve plate thickness measurement process in step S104 described later, as shown in FIG. 7A, the ultrasonic transducer device 210 of the sensor unit 200 transmits the ultrasonic beam UB from the sensor surface S to the position N of the optic papilla. Irradiate toward. Next, as shown in FIG. 7B, the ultrasonic transducer device 210 includes a first ultrasonic echo UE1 from the surface RS of the sieve plate and a second ultrasound from the back surface BS of the sieve plate. The sound wave echo UE2 is received. Then, the control unit 125 measures sieve plate thickness information based on the phase difference between the first ultrasonic echo UE1 and the second ultrasonic echo UE2. If it does in this way, the length of k1 can be calculated | required as a film thickness value of a sieve-like board.

  However, the length actually desired to be obtained as the film thickness value of the sieve plate is not the length of k1, but the length of k in FIG. 7B. Therefore, in the present embodiment, correction processing is performed on the length of k1 to obtain the length of k. In the first place, the reason why the length of k1 is obtained as a result of obtaining the sieving plate thickness by the above-described processing is that the ultrasonic beam is inclined and irradiated to the sieving plate. Therefore, if it is known how much the ultrasonic beam is irradiated with respect to the sieve plate, the true sieve plate thickness can be obtained by correcting the sieve plate thickness.

  Therefore, the control unit 125 specifies the first part and the second part in the eyeball, obtains a correction parameter from the positional relationship between the first part and the second part, and uses the correction parameter to obtain the sieving plate thickness information. Correct.

  This makes it possible to obtain correct sieve plate thickness information.

  In this example, the first part is the central part of the eyeball, and the second part is the optic papilla.

  This makes it possible to obtain a correction parameter from the positional relationship between the center of the eyeball and the optic papilla.

  And the control part 125 specifies the incident angle of the ultrasonic beam to a sieve plate as a correction parameter.

  Thereby, it is possible to correct the sieve plate thickness information calculated by the ultrasonic echo based on the incident angle of the ultrasonic beam to the sieve plate.

  In order to perform the processing as described above, the control unit 125 performs calculation processing of the incident angle of the ultrasonic beam with respect to the sieve plate (or optic papilla N) after step S101 (S102).

  Here, as shown in FIG. 8A, the incident angle of the ultrasonic beam is determined by the vector NC from the optic nerve head N to the center C of the eyeball, and the vector SN from the sensor surface S to the optic nerve head N. Is the angle θ formed by.

Specifically, as shown in FIG. 8B, first, ultrasonic waves are scanned so as to rotate on a circle LN centered on the optic nerve head N at a given angular interval. For example, 36 points (points r0 to r35) are set in increments of 10 ° on a circle LN centered on the optic papilla N. In FIG. 8B, a scanning line connecting the points r1 and r19 (vector r ₁ r _19, hereinafter, the vector connecting other points among the points r0 to r35 is also called). The state of irradiating an ultrasonic beam is shown. The point r19 is a point diagonal to the point r1 with respect to the center point N of the optic nerve head. Then, the ultrasonic transducer device 210 irradiates the ultrasonic beam while rotating the scanning line of the ultrasonic beam by 10 °. That is, the ultrasonic beam is irradiated to each of the vector r ₀ r ₁₈ to the vector r ₁₇ r ₃₅ . Then, every time the ultrasonic beam is irradiated, an angle φ _{i, j} formed by the vector NC and the vector SN is obtained by the equation (1). Note that i and j are integers of 0 ≦ i and j ≦ 35, and i ≠ j.

However, in this example, as shown in Expression (1), it is assumed that the center point of the eyeball is on each normal vector with respect to the vector r ₀ r ₁₈ to the vector r ₁₇ r ₃₅ , and each incident angle φ _{i. , J} is calculated.

For example, a specific example will be described with reference to FIG. FIG. 8C shows the incident angles _φ1 , ₁₉ when the ultrasonic beam is irradiated as shown in FIG. 8B. In this example, instead of directly obtaining the angle between the vector NC and the vector SN, first, the angle δ is obtained from the inner product of the vector r ₁ r ₁₉ and the vector SN. Then, assuming that the center point of the eyeball is on the normal vector of the vector r ₁ r ₁₉ , the incident angle φ _1,19 = π / 2−φ 2 of the ultrasonic beam is obtained. The same calculation is performed for other scan data.

Then, the above equation (1) is calculated for all scanning data, and the minimum value of the calculated angles φ _{i, j} is determined as the incident angle θ of the ultrasonic beam to the sieve plate.

  This makes it possible to calculate the incident angle of the ultrasonic beam with respect to the sieve plate (or optic nerve head N).

  Next, the control unit 125 determines whether or not the calculated incident angle θ is smaller than a given angle (S103). If the incident angle θ is equal to or greater than a given angle, even if correction of the sieve plate thickness is performed based on the calculated incident angle θ, the error with respect to the true sieve plate thickness will increase. is there. The given angle is, for example, 10 °.

  Therefore, if the specified incident angle θ is equal to or greater than the given angle, the control unit 125 stops measuring the sieve plate thickness information, returns to step S101, and the incident angle θ is greater than the given angle. Repeat the process until it becomes smaller.

  As a result, it is possible to suppress an error that occurs in the correction process of the sieve-like plate thickness information.

  On the other hand, when the control unit 125 determines that the incident angle θ is smaller than the given angle, the control unit 125 performs a sieve plate thickness measurement process (S104). Note that the sieving plate thickness measurement process is performed by the process described above with reference to FIGS. Specifically, a temporary sieve plate thickness k1 is obtained by the following equation (2). In Equation (2), t is the phase difference time between the first ultrasonic echo from the surface of the sieve plate and the second ultrasonic echo from the back surface of the sieve plate, and v is the speed of sound. It is. Since the phase difference time t is the time taken when the ultrasonic beam reciprocates through the sieve plate, the product of the phase difference time t and the sound velocity v is divided by 2 to obtain the temporary sieve plate thickness k1. Can be sought.

And the control part 125 performs a correction process with respect to the sieve-like board thickness obtained by performing a measurement process, and calculates | requires true sieve-like board thickness (S105). Specifically, in the correction process, as shown in FIG. 8D, the calculation of the following equation (3) is performed based on the sieve plate thickness k1 obtained in step S104 and the incident angle θ obtained in step S102. To obtain the true sieve thickness k.

Thereafter, the storage unit 150 stores (stores) the acquired ultrasonic echo waveform data, the acquisition date and time of various data, the sieve plate thickness (film thickness value), and the like (S106). The above is the flow of the sieve thickness measurement process of this embodiment.

  Summarizing the above processing flow, the control unit 125 detects the position of the optic nerve head based on the received ultrasonic echoes (S101). And the control part 125 specifies the 1st site | part and 2nd site | part in an eyeball, and calculates | requires the correction parameter of sieve-like plate | board thickness information based on the positional relationship of a 1st site | part and a 2nd site | part. (S102). Further, the control unit 125 measures the slab thickness information based on the phase difference between the first ultrasonic echo from the surface of the sieving plate and the second ultrasonic echo from the back surface of the sieving plate. (S104), and the sieve plate thickness information is corrected by the correction parameter (S105).

  By performing such processing, it is possible to measure correct sieve plate thickness information and the like even when the ultrasonic beam is irradiated with being inclined with respect to the sieve plate.

  Moreover, the alerting | reporting part 160 may alert | report that the sieve plate thickness which the sieve plate thickness information represents has become below a predetermined threshold value.

  This makes it possible for the user to know that the sieve plate is thin and that glaucoma is suspected.

  Further, the control unit 125 may perform an irradiation process of irradiating the corner portion with the ultrasonic beam when the sieve plate thickness represented by the sieve plate thickness information is equal to or less than a given threshold value.

  As a result, when the sieve plate is thin and there is a suspicion of glaucoma, it is possible to treat the eyeball with an ultrasonic beam as described later.

3. Blood Flow Information Measurement Processing Next, blood flow information measurement processing will be described. The control unit 125 of the present embodiment measures blood flow information in the fundus based on the received Doppler shift amount of the ultrasonic echo.

  In the present embodiment, the user wears the ultrasonic measurement device 100 so that the sensor surface 220 contacts the heel surface. Then, an ultrasonic beam is transmitted to the fundus via the sensor surface 220 (an eyelid surface), an ultrasonic echo for the transmitted ultrasonic beam is received, and blood flow information is obtained based on the Doppler shift amount of the received ultrasonic echo. taking measurement.

  Here, the Doppler shift amount can include information obtained by comparing information regarding the frequency of the transmitted ultrasonic beam and information regarding the frequency of the received ultrasonic echo.

  The blood flow information is information related to blood flow in the user's fundus. Specifically, the blood flow information is, for example, a blood flow amount or a blood flow velocity in the fundus. However, in the following, a case where blood flow velocity is mainly measured as blood flow information will be described as an example, but the present embodiment is not limited thereto.

  Thus, in this embodiment, since the measurement is performed by bringing the sensor surface 220 into contact with the eyelid surface without bringing a part of the ultrasonic measurement device 100 into contact with the eyeball, for example, there is no pain during measurement. The physical burden on the user is extremely small. It is safe because it does not damage the eyeball.

  Thereby, blood flow information can be measured without imposing a burden on the user. Therefore, it is possible to increase the number of times of blood flow information measurement. As a result, it is possible to improve the measurement accuracy and the diagnosis accuracy of whether or not there is a suspicion of glaucoma.

  Specifically, the control unit 125 specifies the position of the optic papilla, irradiates an ultrasonic beam to the measurement range set based on the specified position of the optic papilla, and performs a Doppler shift amount of the ultrasonic echo Based on the above, blood flow information is measured.

  This makes it possible to measure blood flow information in a given measurement range centered on the optic nerve head, for example.

  At this time, the control unit 125 scans an area including the optic nerve head with an ultrasonic beam to obtain a sectional image, recognizes the shape of the optic nerve head in the obtained sectional image, Specify the part.

  Thereby, it is possible to specify the measurement range of blood flow information based on the position of the central portion of the specified optic nerve head.

  In this embodiment, the blood flow velocity around the optic papilla (measurement range) is mainly obtained as blood flow information based on the Doppler shift amount, but the direction of blood flow (blood flow direction) in the measurement range is determined. The direction is not always parallel to the irradiation direction of the ultrasonic beam.

  Therefore, the control unit 125 identifies the incident angle of the ultrasonic beam to the optic nerve head or the retina, and identifies blood flow information based on the identified incident angle and the Doppler shift amount.

  Thereby, even when the blood flow direction in the measurement range intersects with the irradiation direction of the ultrasonic beam, it is possible to correctly specify the blood flow information.

  Here, details of the blood flow information measurement processing of the present embodiment will be described using the flowchart of FIG.

  First, similarly to step S101 in FIG. 5, the control unit 125 performs a position detection process of the optic nerve head (S201).

  Next, the control unit 125 calculates the incident angle of the ultrasonic beam on the optic nerve head or retina (S202).

Here, as shown in FIG. 10A, the incident angle of the ultrasonic beam includes a vector SN from the sensor surface S to the optic nerve head N, and a measurement point on the retina from the optic nerve head N (rk to be described later). An angle σ _k formed by the vector Nr _k to. FIG. 10A also shows an enlarged view of the periphery of the optic nerve head. In addition, it should be noted that the incident angle of the ultrasonic beam used for determining the blood flow velocity is an angle different from the incident angle used in the above-described sieve-like plate thickness measurement process.

Specifically, as shown in FIG. 10B, ultrasonic waves are scanned so as to rotate on a circle LN centered on the optic nerve head N at a given angular interval. For example, 18 measurement points (points r0 to r17) are set on a circle LN centered on the optic nerve head N in increments of 20 °. That is, in this case, k is an integer of 0 ≦ k ≦ 17. Then, the ultrasonic transducer device 210 irradiates the ultrasonic beam while rotating the scanning line of the ultrasonic beam by 20 °. That is, the ultrasonic beam is applied to each of the vector Nr ₀ to the vector Nr ₁₇ . As an example, FIG. 10B shows a state in which an ultrasonic beam is irradiated to a scanning line (vector Nr ₃ ) connecting the optic nerve head N and the measurement point r3, and FIG. The incident angle σ ₃ when the ultrasonic beam is irradiated as shown in FIG. 10 is as shown in FIG.

Then, the control unit 125, an angle sigma _k of angle vector Nr _k and vector SN, obtained by equation (4).

Thereby, it is possible to calculate the incident angle of the ultrasonic beam with respect to the optic papilla N or the retina.

Next, the control unit 125 performs blood flow velocity measurement processing based on the Doppler shift amount obtained by irradiating the vector Nr _k with the ultrasonic beam and the incident angle σ _k at that time ( S203). Specifically, the blood flow velocity v _k is calculated by the following equation (5). In equation (5), c is the speed of sound, f is the incident wave frequency, and _fd is the transition frequency. Also, in the processing of step S202 and step S203, the initial value of k is set to 0.

Next, the control unit 125 determines whether or not the incident angle σ _k obtained in step S202 is smaller than a given angle (S204). This is because, when the incident angle is equal to or greater than a given angle, as in the above-described step S103 in FIG.

  Therefore, the control unit 125 stops measuring blood flow information when the specified incident angle is equal to or greater than a given angle. Then, k is incremented (S205), and the process returns to step S201.

  This makes it possible to suppress errors that occur in the blood flow information measurement process.

  On the other hand, when the specified incident angle is smaller than the given angle, the storage unit 150 stores (stores) the acquired ultrasonic echo waveform data, the acquisition date and time of various data, the blood flow velocity, and the like ( S206).

  To summarize the above processing flow, the control unit 125 detects the position of the optic papilla based on the received ultrasonic echo (S201) and is set based on the specified position of the optic papilla. Is irradiated with an ultrasonic beam, the incident angle of the ultrasonic beam to the optic nerve head or retina is identified (S202), and blood flow information is identified based on the identified incident angle and the Doppler shift amount (S202). S203).

  By performing such processing, it is possible to correctly specify blood flow information even when the blood flow direction in the measurement range intersects with the irradiation direction of the ultrasonic beam.

  Further, the control unit 125 may obtain the maximum value of the Doppler shift amount in the measurement range as the blood flow information.

  Thereby, the maximum blood flow velocity in the measurement range can be obtained as blood flow information.

  Moreover, the alerting | reporting part 160 may alert | report that the blood flow velocity which blood-flow information represents became below a predetermined threshold value.

  As a result, the blood flow velocity is reduced, and the user can know that there is a suspicion of glaucoma.

  Moreover, the control part 125 may perform the irradiation process which irradiates an ultrasonic beam to a corner part, when the blood-flow velocity which blood-flow information represents becomes below a predetermined threshold value.

  As a result, when the blood flow velocity is low and there is a suspicion of glaucoma, the eyeball can be treated with an ultrasonic beam as described later.

4). Eyeball Information Measurement Processing As shown in FIG. 6, the ultrasonic transducer device 210 of the ultrasonic measurement apparatus 100 of the present embodiment is a corner of the eyeball (a target site for treatment in a broad sense) through the eyelid surface. Is irradiated (transmitted) with an ultrasonic beam UB. Specifically, for example, an ultrasonic beam UB is applied to the fiber column or Schlemm's tube shown in FIG.

  That is, in this embodiment, the sensor surface 220 of the sensor unit 200 contacts the heel surface at the time of wearing. For example, as described with reference to FIG. 4, the support unit 170 that supports the sensor unit 200 is provided, and the sensor surface 220 is supported by the support unit 170 so as to be in contact with the heel surface. Therefore, only by the user wearing the ultrasonic measurement device 100 (glasses frame), the sensor surface 220 comes into contact with the eyelid surface, and an ultrasonic beam can be transmitted in the eyeball direction. Then, for example, by transmitting an ultrasonic beam in a direction intersecting (orthogonal) with the sensor surface 220, it becomes possible to irradiate the corner of the eyeball (fiber column or Schlemm's canal) with the ultrasonic beam.

  For example, as shown in FIG. 11, aqueous humor, which is a liquid circulating in the eye, is made of ciliary body, passes around the iris, flows toward the fiber column, and is discharged from Schlemm's canal. . As the aqueous humor circulates in this way, the intraocular pressure of the eyeball can be kept substantially constant.

  When the intraocular pressure increases due to abnormal circulation of the aqueous humor, the optic nerve is likely to be damaged, and the risk of developing eyeball diseases such as glaucoma increases.

  Therefore, in this embodiment, as shown in FIG. 6, the ultrasonic transducer device 210 irradiates the corner portion with the ultrasonic beam UB. By doing so, it becomes possible to promote discharge of aqueous humor. For example, abnormalities in the circulation of the aqueous humor in the fiber column, Schlemm's canal, etc. are eliminated, and the intraocular pressure increased due to the abnormal circulation in the aqueous humor is reduced, so that eye diseases such as glaucoma can be treated.

  In this case, in the ultrasonic measurement apparatus 100 of the present embodiment, the sensor surface 220 has a structure that contacts the eyelid when worn, not the eyeball surface. Therefore, even during the daily life of the user, it is possible to treat glaucoma and the like by irradiating the corners with ultrasonic beams. That is, the user always wears the ultrasonic measurement device 100 and can treat an ocular disease with an ultrasonic beam.

  In addition, the ultrasonic measurement apparatus 100 of the present embodiment includes a control unit 125 that controls the ultrasonic transducer device 210. The control unit 125 performs control on transmission / reception of ultrasonic waves by the ultrasonic transducer device 210, for example.

  Specifically, the control unit 125 (processing unit) performs eyeball information measurement processing by transmitting and receiving ultrasonic waves. The eyeball information is information about the eyeball that can be measured by ultrasound, and is, for example, intraocular pressure information, eyeball diameter information, or ultrasound image information about the eyeball. The measurement process based on transmission / reception of ultrasonic waves is, for example, a measurement process performed based on the received ultrasonic echoes by transmitting an ultrasonic beam, receiving an ultrasonic echo.

  And the control part 125 (processing part) performs the irradiation process which irradiates an ultrasonic beam to a corner part based on the result of a measurement process. For example, the control unit 125 determines the irradiation timing, irradiation direction, irradiation energy, or the like of the ultrasonic beam based on the result of the measurement process. And it controls so that an ultrasonic beam is irradiated with the irradiation timing, irradiation direction, or irradiation energy. By doing so, it is possible to irradiate an ultrasonic beam with irradiation timing, irradiation direction or irradiation energy suitable for the treatment of an ocular disease. For example, it is possible to determine an appropriate irradiation timing and specify the location of a corner portion, and to irradiate an ultrasonic beam having an appropriate irradiation energy in the direction of the specified corner portion at the irradiation timing. This makes it possible to efficiently treat glaucoma and the like.

  For example, in the eyeball information measurement process, the control unit 125 measures intraocular pressure information, and performs an ultrasound beam irradiation process based on the intraocular pressure information. For example, the irradiation timing is determined based on the intraocular pressure information, and an ultrasonic beam is irradiated to the corner portion at the determined irradiation timing. For example, the ultrasound beam is irradiated at the timing when it is determined that the intraocular pressure is suspected of abnormal circulation of the aqueous humor. Alternatively, the irradiation energy is determined based on the intraocular pressure information, and an ultrasonic beam is transmitted with the determined irradiation energy.

  Note that the intraocular pressure information measured by the measurement process is not necessarily the intraocular pressure itself, and may be information that can be associated with at least the intraocular pressure. Here, the association means association by estimation processing (calculation by an estimation formula) or numerical correspondence processing by a correspondence table (table). For example, when the information obtained by the measurement process is an eyeball diameter, the eyeball diameter and the intraocular pressure can be associated by an estimation process or the like as described later. Accordingly, in this case, the intraocular pressure information is the eyeball diameter, and the intraocular pressure associated with the intraocular pressure information is the intraocular pressure obtained by an estimation process using the eyeball diameter, a numerical value correspondence process, or the like.

  For example, when the intraocular pressure associated with the intraocular pressure information is higher than a predetermined value, the control unit 125 performs an ultrasonic beam irradiation process. This predetermined value (threshold value) is stored in, for example, the storage unit 150 in FIG. Then, for example, at a timing when the measured intraocular pressure is determined to be higher than a predetermined value, an ultrasonic beam is applied to the corner portion. For example, the intraocular pressure varies with time (time and season), and there are individual differences in the intraocular pressure variation pattern. Intraocular pressure varies depending on gender, age, body position (standing position, sitting position, etc.) and race. Therefore, it is desirable to set the predetermined value to a different value depending on the user who is the subject. In addition, when the ultrasonic measurement apparatus 100 can acquire time information (date and time information), it is desirable to set the predetermined value based on the acquired time information. By doing so, it is possible to irradiate the ultrasonic beam at an appropriate irradiation timing in consideration of time and individual differences. In particular, since the ultrasonic measurement apparatus 100 of this embodiment can be always worn, the intraocular pressure information that changes with time can be stored in the storage unit 150 in time series. Therefore, the predetermined value may be set based on the intraocular pressure information stored in time series as described above.

  The control unit 125 controls the irradiation energy of the ultrasonic beam according to the intraocular pressure associated with the intraocular pressure information. For example, when the intraocular pressure is lower than a threshold (predetermined value) for setting the irradiation energy, the irradiation energy of the ultrasonic beam is set to the first irradiation energy, and when the intraocular pressure is higher than the threshold (predetermined value). The second irradiation energy is set higher than the first irradiation energy. In other words, the irradiation energy is set to be higher as the intraocular pressure is higher. In this way, by irradiating an ultrasonic beam with high irradiation energy when the intraocular pressure is high, circulation of aqueous humor or the like is promoted, and the degree of reduction of intraocular pressure can be further increased. The irradiation energy can be set by, for example, the irradiation time, the voltage of the ultrasonic transmission signal, the wave number, or the like. For example, when the irradiation energy is increased, the irradiation time may be increased, the voltage of the ultrasonic transmission signal may be increased, or the wave number may be increased.

  Further, the control unit 125 measures the intraocular pressure based on the received ultrasonic echo, and the ultrasonic beam is measured when the phloem plate thickness is equal to or less than a given threshold value and the intraocular pressure is equal to or greater than the given pressure. Irradiation treatment for irradiating the corner portion may be performed.

  This makes it possible to determine the timing for treating an ocular disease with an ultrasonic beam based not only on the intraocular pressure but also on the sieve plate thickness.

  Further, the control unit 125 may perform an irradiation process of irradiating the corner with an ultrasonic beam when the blood flow velocity is equal to or lower than a given threshold and the intraocular pressure is equal to or higher than a given pressure.

  This makes it possible to determine the timing for treating an ocular disease with an ultrasonic beam based not only on intraocular pressure but also on the blood flow velocity around the optic nerve head.

  In addition, in the eyeball information measurement process, the control unit 125 may perform an image recognition process of a corner portion based on an ultrasound image, and perform an ultrasound beam irradiation process based on the result of the image recognition process. For example, an ultrasonic image (biological cross-sectional image or the like) such as a B-mode image is generated based on an ultrasonic reception signal (ultrasonic echo). Then, by performing image recognition processing on the generated ultrasonic image, the location of the corner (fiber column, Schlemm's tube, etc.) is specified. This image recognition processing can be realized by known pattern matching or the like. For example, a reference image in which a reference pattern of a corner portion is reflected is prepared, and the location (position) of the corner portion is specified by performing pattern matching between the generated ultrasonic image and the reference image. It is expected that the corner reference pattern will be different for each user. Therefore, the reference image showing the reference pattern at the corner may be stored and registered in the storage unit 150 of FIG. 2 in association with each user. In the image recognition process, a reference image associated with the user is read out from the storage unit 150, and pattern matching with the ultrasonic image obtained for the user is performed to specify the location of the corner portion. . Then, by transmitting an ultrasonic beam toward the specified corner portion, irradiation of the ultrasonic beam to the corner portion is realized. Details of the control of the ultrasonic beam direction (beam scanning) will be described later.

  In this way, the location of the corner portion can be specified by image recognition processing of the ultrasound image by effectively utilizing the ultrasound image generation function of the ultrasound measurement device 100. Then, by transmitting the ultrasonic beam to the specified location, it is possible to appropriately irradiate the corner portion with the ultrasonic beam, promote drainage of the aqueous humor, etc., and appropriately treat glaucoma and the like. For example, the location of the corner varies depending on the user who is the subject and there are individual differences. Therefore, in the method of irradiating the ultrasonic beam toward the fixed direction, the ultrasonic beam is appropriately irradiated to the corner. It may not be possible. In this regard, if the location of the corner portion is specified by the ultrasonic image, even if the location of the corner portion varies due to individual differences, the ultrasound beam can be appropriately irradiated to the corner portion.

  The control unit 125 performs a process of transmitting an ultrasonic beam in the first direction in the measurement process, and a process of transmitting the ultrasonic beam in a second direction different from the first direction in the irradiation process. I do. For example, when measuring eyeball information such as intraocular pressure information in the measurement process, for example, an ultrasonic beam is irradiated toward the center (substantially center) of the eyeball. That is, the first direction is a direction from the ultrasonic transducer device 210 toward the center of the eyeball. As a result, the intraocular pressure diameter information can be measured as described later, and the intraocular pressure information can be estimated from the intraocular pressure diameter.

  On the other hand, in the irradiation process, for example, an ultrasonic beam is irradiated toward a corner portion (target portion). That is, the second direction is a direction from the ultrasonic transducer device 210 toward the corner, which is generally a direction different from the first direction.

  Accordingly, by transmitting the ultrasonic beam in the first direction in the measurement process, while appropriately measuring the intraocular pressure information and the like, transmitting the ultrasonic beam in the second direction in the irradiation process, the corner portion The ultrasonic beam can be appropriately irradiated toward In this case, the switching between the first and second directions can be realized by a beam scan described later.

  The ultrasonic transducer device 210 transmits an ultrasonic beam in the eyeball direction via the eyelid surface and receives an ultrasonic echo of the ultrasonic beam.

  And the control part 125 (processing part) performs the process which acquires the eyeball diameter information which is the information about the eyeball diameter in several different timing (time) based on the received signal of an ultrasonic echo. The eyeball diameter information is obtained from the time difference between the first reception signal of the ultrasonic echo and the second reception signal received after the first reception signal with respect to one transmission signal of the ultrasonic beam. That is, the control unit 125 estimates and calculates intraocular pressure based on the eyeball diameter information.

  Specifically, the eyeball diameter information includes a first received signal corresponding to an ultrasonic echo from the sclera near the eyelid that the sensor surface 220 contacts and a second corresponding to an ultrasonic echo from the sclera far from the eyelid. It is the information regarding the eyeball diameter (eyeball diameter) obtained from the time difference with the received signal. The eyeball diameter information does not have to be the eyeball diameter value (length) itself. For example, the ultrasound echo from the sclera close to the eyelid (first received signal) and the ultrasound echo from the sclera far from the eyelid ( It may be a time difference from the second received signal), or may be an amplitude waveform (A mode waveform) of the received signal of the ultrasonic echo.

  The time intervals of the plurality of different timings are longer than the time difference between the first received signal and the second received signal.

  In addition, the control unit 125 performs an eyeball diameter estimation calculation process based on the eyeball diameter information acquired by ultrasonic measurement. Specifically, the control unit 125 performs an ultrasonic beam beam scan process, and performs an eyeball diameter estimation calculation process based on the eyeball diameter information for a plurality of beam directions. By doing so, the eyeball diameter can be estimated with high accuracy. Details of the eyeball diameter estimation calculation process will be described later.

  The control unit 125 performs intraocular pressure estimation processing based on the estimated eyeball diameter information. Specifically, the control unit 125 sets the first eyeball diameter information and the first measured intraocular pressure value obtained when the subject is in the sitting position (first state in a broad sense), and the subject is in the standing position ( In a broad sense, the relationship between the eyeball diameter information and the intraocular pressure obtained based on the second eyeball diameter information and the second measured intraocular pressure obtained in the second state) (relational expression) From this, the intraocular pressure is estimated. If the relationship between the eyeball diameter information and the intraocular pressure is specified, the control unit 125 can estimate the intraocular pressure from the eyeball diameter information acquired by ultrasonic measurement. Details of the intraocular pressure estimation process will be described later.

  The processing for obtaining the relationship between the eyeball diameter information and the intraocular pressure may be performed by the control unit 125, or may be performed by an apparatus (for example, a tonometer) that actually measures the intraocular pressure measurement value. Alternatively, a personal computer (PC) may be used.

  Next, the operation of the ultrasonic measurement apparatus 100 of this embodiment will be described. FIG. 12A is a flowchart for explaining the basic operation of this embodiment.

  As shown in FIG. 12A, in the present embodiment, first, eyeball information measurement processing is performed by transmitting and receiving ultrasonic waves (step S1). Based on the measurement result, an irradiation process of the ultrasonic beam to the corner is performed (step S2).

  FIG. 12B is a flowchart for explaining the operation when the measurement process in step S1 of FIG. 12A is measurement of intraocular pressure.

  First, the intraocular pressure is measured by transmitting and receiving ultrasonic waves (step S11). Then, it is determined whether the intraocular pressure is higher than a predetermined threshold (predetermined value) (step S12). If the intraocular pressure is higher than a predetermined threshold value, the corner portion is irradiated with an ultrasonic beam having irradiation energy corresponding to the intraocular pressure (step S13).

  FIG. 13 is a flowchart for explaining the operation in the case where the measurement process in step S1 of FIG. 12A is a process for specifying the location of a corner based on an ultrasonic image.

  First, an ultrasonic image is generated by transmitting and receiving ultrasonic waves (step S21). Then, based on the generated ultrasonic image, corner corner image recognition processing is performed (step S22), and the corner portion (fiber column body, Schlemm's canal) is identified by the image recognition processing (step S23). . Then, by transmitting the ultrasonic beam to the specified place, the corner is irradiated with the ultrasonic beam (step S24).

  FIG. 14A and FIG. 14B are flowcharts for explaining a detailed operation example of this embodiment. First, as shown in FIG. 14A, a measurement process of intraocular pressure P is performed (step S31). Next, it is determined whether or not the measured intraocular pressure P is greater than or equal to a threshold value (predetermined value) Pmin (step S32). The threshold value Pmin is a threshold value on the low intraocular pressure side. If the intraocular pressure P is lower than the threshold value Pmin, the process L is executed (step S33). The process L is a process prepared for a case where the intraocular pressure is low, but can be a null process (a process in which nothing is performed).

  If the intraocular pressure P is greater than or equal to the threshold Pmin, it is determined whether or not the intraocular pressure P is less than or equal to the threshold Pmax (step S34). The threshold value Pmax is a threshold value on the high intraocular pressure side. If the intraocular pressure P is higher than the threshold value Pmax, the process H is executed (step S35). The process H is a process prepared for a case where the intraocular pressure is high. On the other hand, when the intraocular pressure P is less than or equal to the threshold value Pmax, the process returns to step S31. That is, when Pmin ≦ P ≦ Pmax, it is assumed that the intraocular pressure P is in the normal range, and the process of measuring the intraocular pressure P is continued without executing the processes L and H.

  FIG. 14B is a flowchart illustrating an example of processing H. First, a corner portion is detected (step S41). For example, the location of the corner is detected by image recognition processing of an ultrasonic image. Then, an intraocular pressure difference ΔP = P−Pmax between the intraocular pressure P measured in step S31 of FIG. 14A and the threshold Pmax used in step S34 is obtained (step S42).

  Next, it is determined whether or not ΔP is larger than, for example, 5 mHg (threshold for determining irradiation energy) (step S43). If larger, the irradiation time of the ultrasonic beam is set to T = 10 seconds, for example (step S43). S44). On the other hand, when ΔP is 5 mHg or less, the irradiation time of the ultrasonic beam is set to T = 3 seconds, for example (step S45). And the irradiation process of the ultrasonic beam to a corner part is performed by the set irradiation time T (step S46). By doing so, it is possible to control the irradiation energy of the ultrasonic beam according to the intraocular pressure.

5. Eyeball Diameter Estimation Calculation Processing and Intraocular Pressure Estimation Processing FIG. 15 is a diagram for explaining measurement of eyeball diameter (eyeball diameter information in a broad sense) by the ultrasonic measurement apparatus 100 of the present embodiment. As shown in FIG. 15, the sensor unit 200 (sensor surface) is in contact with the heel surface (lower heel surface). An ultrasonic beam UB is transmitted in the eyeball direction from the ultrasonic transducer device 210 included in the sensor unit 200, and an ultrasonic echo UE1 from the sclera near the heel (lower eyelid) and an ultrasonic echo UE2 from the sclera far from the heel Is received by the ultrasonic transducer device 210.

  The time difference between the first received signal corresponding to the ultrasonic echo UE1 and the second received signal corresponding to the ultrasonic echo UE2 is proportional to the distance between the sclera close to the heel and the sclera far from the heel. By measuring the time difference between the first received signal and the second received signal, information on the eyeball diameter can be obtained. For example, when the sound velocity of the ultrasonic wave in the eyeball is v and the time difference between the first received signal and the second received signal is td, the eyeball diameter D is given by the following equation (6).

FIG. 16 shows an example of the relationship between intraocular pressure and eyeball diameter variation obtained from an experiment with pig eyes. As can be seen from FIG. 16, the variation of the eyeball diameter is expressed by a linear function of intraocular pressure. Therefore, if the eyeball diameter is known, the intraocular pressure can be estimated.

  FIG. 17 is a diagram for describing estimation of intraocular pressure by the ultrasonic measurement apparatus 100 of the present embodiment. Since the eyeball diameter D is expressed by a linear function of intraocular pressure P, the following equation (7) is established.

Here, a and b are parameters that specify the relationship between the eyeball diameter D and the intraocular pressure P. Since the relationship between the eyeball diameter D and the intraocular pressure P varies depending on the subject, it is necessary to determine the parameters a and b for each subject. According to the ultrasonic measurement apparatus 100 of the present embodiment, the parameters a and b can be determined as follows.

  It is known that the intraocular pressure in a sitting state (sitting position) is different from the intraocular pressure in a standing state (standing position). Accordingly, when the subject is in the sitting position (first state), the first eyeball diameter D1 is acquired by ultrasonic measurement, and the first intraocular pressure measurement value P1 is acquired by intraocular pressure examination. Further, when the subject is in a standing position (second state), the second eyeball diameter D2 is acquired by ultrasonic measurement, and the second intraocular pressure measured value P2 is acquired by intraocular pressure examination.

  From the equation (7), the following equation is established.

Accordingly, the parameters a and b can be obtained from the equations (8) and (9).

  Thus, according to the ultrasonic measurement apparatus 100 of the present embodiment, the eyeball diameter is measured by measuring the eyeball diameter while the subject is in the sitting position and in the standing position, and further inputting the actually measured intraocular pressure value by the tonometry. And the intraocular pressure (specifically, parameter values a and b) can be specified for each subject. The intraocular pressure can be estimated from the eyeball diameter acquired by ultrasonic measurement using the specified parameter values a and b.

  The process for obtaining the relationship (parameter value) between the eyeball diameter information and the intraocular pressure may be performed by the control unit 125 as described above, or a device (for example, a tonometer) that actually measures the intraocular pressure measurement value, Alternatively, a personal computer (PC) may be used.

6). Ultrasonic Transducer Element FIGS. 18A to 18C show a configuration example of the ultrasonic transducer element 10 used in the ultrasonic measurement apparatus 100 of the present embodiment. The ultrasonic transducer element 10 includes a vibration film (membrane, support member) 50 and a piezoelectric element part. The piezoelectric element section includes a first electrode layer (lower electrode) 21, a piezoelectric layer (piezoelectric film) 30, and a second electrode layer (upper electrode) 22. In addition, the ultrasonic transducer element 10 of this embodiment is not limited to the structure of FIG. 18 (A)-FIG. 18 (C), a part of the component is abbreviate | omitted or replaced with another component, Various modifications such as adding other components are possible.

  FIG. 18A is a plan view of the ultrasonic transducer element 10 formed on the substrate (silicon substrate) 60 as seen from a direction perpendicular to the substrate 60 on the element formation surface side. FIG. 18B is a cross-sectional view showing a cross section along A-A ′ of FIG. FIG. 18C is a cross-sectional view showing a cross section along B-B ′ of FIG.

  The first electrode layer 21 is formed on the vibration film 50 as a metal thin film, for example. The first electrode layer 21 may be a wiring that extends to the outside of the element formation region and is connected to the adjacent ultrasonic transducer element 10 as shown in FIG.

The piezoelectric layer 30 is formed of, for example, a PZT (lead zirconate titanate) thin film, and is provided so as to cover at least a part of the first electrode layer 21. The material of the piezoelectric layer 30 is not limited to PZT. For example, lead titanate (PbTiO ₃ ), lead zirconate (PbZrO ₃ ), lead lanthanum titanate ((Pb, La) TiO ₃ ), etc. May be used.

  The second electrode layer 22 is formed of a metal thin film, for example, and is provided so as to cover at least a part of the piezoelectric layer 30. The second electrode layer 22 may be a wiring that extends to the outside of the element formation region and is connected to the adjacent ultrasonic transducer element 10 as shown in FIG.

The vibration film (membrane) 50 is provided so as to close the cavity region 40 by a two-layer structure of, for example, a SiO ₂ thin film and a ZrO ₂ thin film. The vibration film 50 supports the piezoelectric layer 30 and the first and second electrode layers 21 and 22 and can vibrate according to the expansion and contraction of the piezoelectric layer 30 to generate ultrasonic waves.

  The cavity region 40 is formed by etching by reactive ion etching (RIE) or the like from the back surface (surface on which no element is formed) side of the substrate 60 (silicon substrate). The resonance frequency of the ultrasonic wave is determined by the size of the vibration film 50 that can be vibrated by the formation of the cavity region 40, and the ultrasonic wave is directed to the piezoelectric film 30 side (from the back to the front in FIG. 18A). Radiated.

  The lower electrode (first electrode) of the ultrasonic transducer element 10 is formed by the first electrode layer 21, and the upper electrode (second electrode) is formed by the second electrode layer 22. Specifically, a portion of the first electrode layer 21 covered with the piezoelectric layer 30 forms a lower electrode, and a portion of the second electrode layer 22 covering the piezoelectric layer 30 forms an upper electrode. . That is, the piezoelectric layer 30 is provided between the lower electrode and the upper electrode.

  The piezoelectric film 30 expands and contracts in the in-plane direction when a voltage is applied between the lower electrode and the upper electrode, that is, between the first electrode layer 21 and the second electrode layer 22. The ultrasonic transducer element 10 uses a monomorph (unimorph) structure in which a thin piezoelectric element portion and a vibration film 50 are bonded together. When the piezoelectric element portion expands and contracts in a plane, the dimensions of the bonded vibration film 50 are as follows. As it is, warping occurs. Therefore, by applying an AC voltage to the piezoelectric film 30, the vibration film 50 vibrates in the film thickness direction, and ultrasonic waves are emitted by the vibration of the vibration film 50. The voltage applied to the piezoelectric film 30 is, for example, 10 to 30 V, and the frequency is, for example, 1 to 10 MHz.

  The drive voltage of the bulk ultrasonic transducer element is about 100 V from peak to peak, whereas in the thin film piezoelectric ultrasonic transducer element as shown in FIGS. The voltage can be reduced from the peak to about 10 to 30 V from the peak.

7). Ultrasonic Transducer Device In the ultrasonic measurement apparatus 100 of the present embodiment, as described with reference to FIG. 15, from the first received signal corresponding to the ultrasonic echo UE1 from the sclera close to the eyelid (lower eyelid) and the eyelid The eyeball diameter (eyeball information in a broad sense) is measured by measuring the time difference from the second received signal corresponding to the ultrasonic echo UE2 from the far sclera. When the ultrasonic beam UB transmitted from the ultrasonic transducer device 210 passes through the center of the eyeball, the eyeball diameter can be accurately measured. However, in practice, it is difficult to always keep the position and direction of the sensor unit 200 constant. Therefore, it is difficult to always transmit the ultrasonic beam UB toward the center of the eyeball.

  Therefore, in the ultrasonic measurement apparatus 100 of the present embodiment, the control unit 125 performs a beam scan of the ultrasonic beam UB, and performs an eyeball diameter estimation calculation process based on the eyeball diameter information for a plurality of beam directions. Specifically, the control unit 125 scans the ultrasonic beam UB in the X direction and the Y direction by sector scan (phase scan) or linear scan, and acquires eyeball diameter values for a plurality of beam directions. The maximum value among the plurality of eyeball diameter values is estimated as the true eyeball diameter value.

  Further, for example, when the location of the corner portion is specified by the image recognition process or the like as described above, if the ultrasonic beam UB can be scanned in the X direction and the Y direction, the ultrasonic beam is applied to the specified location. By performing scanning so that UB is irradiated, it becomes possible to irradiate the corner portion with an ultrasonic beam.

  FIG. 19 shows a first configuration example of the ultrasonic transducer device 210 of the present embodiment. The ultrasonic transducer device 210 of this configuration example includes a plurality of ultrasonic transducer elements 10 arranged in an 8 × 8 matrix, signal terminals SG1 to SG64, and a plurality of common voltage terminals COM.

  As shown in FIG. 19, 16 signal terminals SG <b> 1 to SG <b> 64 are arranged on each side of the ultrasonic transducer device 210. A plurality of common voltage terminals COM are arranged at each corner portion. The arrangement of the signal terminals SG1 to SG64 and the common voltage terminal COM is not limited to that shown in FIG.

  One electrode of each of the 64 ultrasonic transducer elements 10 is connected to a corresponding one of the signal terminals SG1 to SG64. The other electrode of each element is connected to one of the plurality of common voltage terminals COM by a wiring not shown. In the transmission period, a transmission signal from the transmission unit 110 is input to the signal terminals SG1 to SG64, and in the reception period, reception signals from the 64 ultrasonic transducer elements 10 are received via the signal terminals SG1 to SG64. Is output to the unit 120. In this way, since transmission signals having different phases can be input to the 64 ultrasonic transducer elements 10, beam scanning by sector scanning is performed in both the X direction and the Y direction. It can be carried out.

  FIGS. 20A and 20B are diagrams for explaining beam scanning by the first configuration example of the ultrasonic transducer device 210. FIG. As shown in A1 and A2 of FIG. 20A, the ultrasonic transducer device 210 provided in the sensor unit 200 can scan the emission direction of the ultrasonic beam in the Y direction by approximately ± 45 ° by sector scanning. it can. In actual measurement, the change in the beam direction may be about ± 5 to 10 °, for example. For example, as shown in FIG. 20A, the ultrasonic beam is scanned from UB1 to UB2 and then to UB3. Although not shown, the beam direction can be similarly scanned in the X direction. Thereby, positions, such as a sieve plate, an optic disc part, and a corner part, can be specified.

  FIG. 20B shows a scan of the ultrasonic beam when viewed virtually from the position of the PS in FIG. According to the ultrasonic measurement apparatus 100 of the present embodiment, as shown in FIG. 20B, it is possible to scan in the X direction by changing the angle in the Y direction by 1 °, for example. That is, the eyeball diameter can be acquired over a predetermined range of the sclera by performing from the first beam scan SC1 to the n-th (n is an integer of 2 or more) beam scan SCn.

  In addition, when a place such as a sieve plate, optic papilla and corner is specified, the ultrasonic beam is scanned in the X and Y directions so that the specified position is irradiated with the ultrasonic beam. This makes it possible to irradiate the sieve plate, the optic papilla, and the corners with an ultrasonic beam.

  FIG. 21 is a diagram for explaining the estimation of the true eyeball diameter by the beam scans SC1 to SCn shown in FIG. FIG. 21 plots the measured values of the eyeball diameter with respect to the angle in the X direction for each of the beam scans SC1 to SCn. As can be seen from FIG. 21, the maximum value of the measured eyeball diameter values is the true eyeball diameter value to be obtained. Therefore, the control unit 125 performs the beam scans SC1 to SCn, acquires a measured value of the eyeball diameter for each scan, and estimates that the maximum value among the measured eyeball diameter values is a true eyeball diameter value. be able to.

  When the angle that gives the maximum value of the measured eyeball diameter is the upper or lower angle of the scan range in the X or Y direction, there is a possibility that the beam that passes through the center of the eyeball is not included in the scan range There is. In this case, the control unit 125 can shift the scan range in an appropriate direction.

  FIG. 22 shows a second configuration example of the ultrasonic transducer device 210 of the present embodiment. The ultrasonic transducer device 210 of this configuration example includes a device UDX that performs linear scanning in the X direction and a device UDY that performs linear scanning in the Y direction. The device UDX includes a plurality of ultrasonic transducer elements 10 arranged in a matrix of 8 rows and 16 columns, signal terminals SGX1 to SGX16, and a plurality of common voltage terminals COM. Similarly, the device UDY includes a plurality of ultrasonic transducer elements 10 arranged in a matrix of 16 rows and 8 columns, signal terminals SGY1 to SGY16, and a plurality of common voltage terminals COM.

  One electrode of the eight ultrasonic transducer elements 10 in the i-th row (i is an integer satisfying 1 ≦ i ≦ 16) of the device UDX is common to the i-th signal terminal SGXi among the signal terminals SGX1 to SGX16. Connected. The other electrode of each ultrasonic transducer element 10 is commonly connected to the common voltage terminal COM. In the transmission period, transmission signals from the transmission unit 110 are input to the signal terminals SGX1 to SGX16, and in the reception period, reception signals from the ultrasonic transducer elements 10 in each column are received via the signal terminals SGX1 to SGX16. Is output to the unit 120.

  The eight ultrasonic transducer elements 10 in the j-th row (j is an integer satisfying 1 ≦ j ≦ 16) of the device UDY are commonly connected to the j-th signal terminal SGYj among the signal terminals SGY1 to SGY16. The other electrode of each ultrasonic transducer element 10 is commonly connected to the common voltage terminal COM. In the transmission period, transmission signals from the transmission unit 110 are input to the signal terminals SGY1 to SGY16, and in the reception period, reception signals from the ultrasonic transducer elements 10 in each row are received via the signal terminals SGY1 to SGY16. 120 is output.

  By sequentially inputting transmission signals from the signal terminals SGX1 to SGX16 of the device UDX, the ultrasonic beam can be linearly scanned in the X direction. Similarly, by sequentially inputting transmission signals from the signal terminals SGY1 to SGY16 of the device UDY, the ultrasonic beam can be linearly scanned in the Y direction.

  FIG. 23 is a diagram for explaining beam scanning according to the second configuration example of the ultrasonic transducer device 210. In FIG. 23, similarly to FIG. 20B, scanning of the ultrasonic beam when viewed virtually from the position of the PS in FIG. 20A is shown.

  As shown in FIG. 23, by using the device UDX to scan in the X direction, it is possible to obtain a measured value of the eyeball diameter for the scan range SAX in the X direction. Further, by performing scanning in the Y direction using the device UDY, it is possible to acquire a measured value of the eyeball diameter for the scan range SAY in the Y direction. The maximum value among the eyeball diameter values measured in the two scan ranges SAX and SAY can be estimated as the true eyeball diameter value.

  As described above, according to the ultrasonic measurement apparatus 100 of the present embodiment, an ultrasonic beam is scanned in the X direction and the Y direction, eyeball diameter values are acquired in a plurality of beam directions, and a plurality of acquired eyeball diameter values are acquired. Can be estimated as a true eyeball diameter value. By doing so, the eyeball diameter can be accurately estimated even when the beam direction is deviated from the center of the eyeball or when the position and direction of the sensor unit 200 are changed.

  Further, by scanning the ultrasonic beam, it is possible to accurately irradiate the specified location such as the sieve plate, the optic nerve head and the corner portion with the ultrasonic beam. For example, there are individual differences in the location of the phloem plate, optic papilla and corners, etc. By scanning and irradiating the ultrasonic beam in this way, the phloem plate, optic papilla and corners, etc. Even if the location of the subject varies from subject to subject, it becomes possible to respond appropriately.

8). Details of Eyeball Diameter Estimation Calculation Processing and Intraocular Pressure Estimation Processing FIG. 24 is an example of a flowchart of eyeball diameter estimation calculation processing by the ultrasonic measurement apparatus 100 of the present embodiment. The process illustrated in FIG. 24 is executed by the control unit 125. In the flow of FIG. 24, the case where the beam scans SC1 to SCn shown in FIG. 20B are performed using the first configuration example (FIG. 19) of the ultrasonic transducer device 210 will be described as an example.

  First, the control unit 125 sets the beam scan number (index) i to an initial value 1 (step S51). Next, a beam scan SCi is performed to acquire eyeball diameter information DAi (step S52), and the acquired eyeball diameter information DAi is written in the storage unit 150 (step S53).

  Next, the controller 125 increments the beam scan number i (step S54), and determines whether or not the beam scan number i is greater than a predetermined integer value n (step S55). Here, the predetermined integer value n is the number of beam scans in the X direction. When the beam scan number i is equal to or smaller than the predetermined integer value n, the process returns to step S52, and the control unit 125 performs the beam scan SCi and repeats the process of acquiring the eyeball diameter information DAi.

  When the beam scan number i is larger than the predetermined integer value n, the control unit 125 performs an eyeball diameter estimation calculation process based on the acquired eyeball diameter information DA1 to DAn (step S56). Specifically, the control unit 125 estimates that the maximum value among the eyeball diameters acquired by the beam scans SC1 to SCn is the true eyeball diameter D. Then, the estimated true eyeball diameter D is written in the storage unit 150 (step S57).

  FIG. 25 is an example of a flowchart of processing for specifying the relationship between eyeball diameter information and intraocular pressure by the ultrasonic measurement apparatus 100 of the present embodiment. The process illustrated in FIG. 25 is executed by the control unit 125.

  First, the control unit 125 performs ultrasonic measurement in the sitting position, and acquires the first eyeball diameter D1 (first eyeball diameter information in a broad sense) (step S61). Next, the control unit 125 generates notification information that prompts the user to input the actual intraocular pressure value P1 (first actual intraocular pressure value) in the sitting position, and outputs the notification information to the notification unit 160 (step S62). Then, the control unit 125 writes the input first intraocular pressure actual measurement value P1 in the storage unit 150 (step S63).

  Next, the control unit 125 performs ultrasonic measurement in a standing position to acquire a second eyeball diameter D2 (second eyeball diameter information in a broad sense) (step S64). Next, the control unit 125 generates notification information that prompts the user to input the measured intraocular pressure value P2 (second measured intraocular pressure value) in the standing position, and outputs the notification information to the notification unit 160 (step S65). . Then, the control unit 125 writes the input second intraocular pressure actual measurement value P2 in the storage unit 150 (step S66).

  Next, the control unit 125 determines parameters a and b from the first eyeball diameter D1, the first intraocular pressure actual measurement value P1, the second eyeball diameter D2 and the second intraocular pressure actual measurement value P2 (step S67). ). Specifically, parameters a and b are obtained from the equations (8) and (9) already described. Then, the control unit 125 writes the determined parameters a and b in the storage unit 150 (step S68).

  FIG. 26 is an example of a flowchart of intraocular pressure estimation processing by the ultrasonic measurement apparatus 100 of the present embodiment. The process illustrated in FIG. 26 is executed by the control unit 125.

  First, the control unit 125 performs ultrasonic measurement to acquire the eyeball diameter D (step S71). Specifically, for example, the eyeball diameter D is acquired by the flow shown in FIG. Next, the control unit 125 reads parameters a and b that specify the relationship between the eyeball diameter and the intraocular pressure from the storage unit 150 (step S72), and performs an intraocular pressure P estimation process (step S73). Specifically, the intraocular pressure P can be obtained from the equation (7) already described.

  Then, the control unit 125 generates notification information regarding whether the intraocular pressure is normal or abnormal based on the estimated intraocular pressure P, and outputs the generated notification information to the notification unit 160 (step S74). . Since the normal intraocular pressure range varies among individuals, a normal value range (Pmin to Pmax) that differs for each subject can be stored in the storage unit 150 in advance.

  Next, the control unit 125 reads the eyeball diameters D (t1), D (t2),..., D (tk) from the storage unit 150 at k (k is an integer of 2 or more) timings (time) ( Step S75). Here, the eyeball diameter D (t1) is the eyeball diameter acquired at time t1, and D (t2) to D (tk) are the eyeball diameters acquired at time t2 to tk.

  Next, the control unit 125 performs time series intraocular pressures P (t1), P (t2) based on the time series eyeball diameters D (t1), D (t2),..., D (tk),. · P (tk) is estimated (step S76). Specifically, the intraocular pressure at each time can be obtained from Equation (7) already described.

  Next, the control unit 125 generates notification information regarding temporal changes in intraocular pressure based on the time-series intraocular pressures P (t1), P (t2),..., P (tk), and the generated notifications. Information is output to the notification unit 160 (step S77). By doing so, it is possible to accurately grasp temporal changes in intraocular pressure.

  As described above, according to the ultrasonic measurement apparatus 100 of the present embodiment, it is possible to accurately acquire the eyeball diameter information at a plurality of different timings while reducing the physical burden on the subject, and the acquired eyeball. The diameter information can be stored in the storage unit. Information on temporal changes in intraocular pressure can be easily acquired based on the stored eyeball diameter information. As a result, for example, in the treatment of glaucoma, it is possible to grasp changes in intraocular pressure over several days of intraocular pressure after medication or treatment and for each activity state (wake-up, daily activity, sleeping, etc.) of the subject within the day. Improvement of therapeutic effect can be expected.

  Although the present embodiment has been described in detail as described above, it will be easily understood by those skilled in the art that many modifications can be made without departing from the novel matters and effects of the present invention. Accordingly, all such modifications are intended to be included in the scope of the present invention. For example, a term described at least once together with a different term having a broader meaning or the same meaning in the specification or the drawings can be replaced with the different term in any part of the specification or the drawings. Further, the configuration and operation of the ultrasonic measurement apparatus are not limited to those described in the present embodiment, and various modifications can be made.

10 ultrasonic transducer elements, 21 first electrode layer (lower electrode),
22 second electrode layer (upper electrode), 30 piezoelectric film (piezoelectric layer), 40 cavity region,
45 openings, 50 vibrating membranes, 60 substrates, 100 ultrasonic measuring devices,
101 ultrasonic measurement apparatus main body, 110 transmission unit, 120 reception unit, 125 control unit,
130 transmission / reception control unit, 140 processing unit, 150 storage unit, 160 notification unit,
170 support part, 180 wiring, 190 cable, 200 sensor part,
210 ultrasonic transducer device, 220 sensor surface, 230 protective film,
240 base substrate, 250 flexible substrate

Claims (17)

A sensor surface that can contact the surface of the heel when the ultrasonic measurement device is mounted;
An ultrasonic transducer device that transmits an ultrasonic beam to the optic papilla of the eyeball through the sensor surface and receives an ultrasonic echo from the ultrasonic beam;
A control unit for measuring sieve thickness information based on the received ultrasonic echo;
An ultrasonic measurement apparatus comprising: In claim 1,
The controller is
Measuring the sieving plate thickness information based on the phase difference between the first ultrasonic echo from the surface of the sieving plate and the second ultrasonic echo from the back surface of the sieving plate, Ultrasonic measuring device. In claim 1 or 2,
The controller is
The first part and the second part in the eyeball are specified, a correction parameter is obtained from the positional relationship between the first part and the second part, and the sieve plate thickness information is corrected by the correction parameter. An ultrasonic measurement apparatus characterized by: In claim 3,
The first part is:
The center of the eyeball;
The second part is
An ultrasonic measurement apparatus, which is the optic nerve head. In claim 3 or 4,
The controller is
An ultrasonic measurement apparatus characterized by specifying an incident angle of the ultrasonic beam on the sieve plate as the correction parameter. In claim 5,
The incident angle of the ultrasonic beam is
An ultrasonic measurement apparatus characterized in that the angle is an angle formed by a vector from the optic nerve head to the center of the eyeball and a vector from the sensor surface to the optic nerve head. In claim 5 or 6,
The controller is
The ultrasonic measurement apparatus, wherein when the specified incident angle is equal to or larger than a given angle, the measurement of the sieve plate thickness information is stopped. In any one of Claims 1 thru | or 7,
The controller is
Scanning an area including the optic papilla with the ultrasonic beam to obtain a cross-sectional image, recognizing a shape of the optic papilla in the acquired cross-sectional image, and specifying a central portion of the optic papilla Ultrasonic measuring device characterized by. In claim 1,
The controller is
Based on the received ultrasonic echo, the position of the optic nerve head is detected, the first part and the second part in the eyeball are specified, and the first part and the second part Based on the positional relationship, a correction parameter of the sieving plate thickness information is obtained, and the position of the first ultrasonic echo from the front surface of the sieving plate and the second ultrasonic echo from the back surface of the sieving plate is determined. An ultrasonic measurement apparatus characterized by measuring the sieve plate thickness information based on a phase difference and correcting the sieve plate thickness information with the correction parameter. In any one of Claims 1 thru | or 9,
An ultrasonic measurement apparatus comprising: a storage unit that stores the measured sieve-like plate thickness information in time series. In any one of Claims 1 thru | or 10.
An ultrasonic measurement apparatus comprising: an informing unit for informing that the sieving plate thickness represented by the sieving plate thickness information is equal to or less than a given threshold value. In any one of Claims 1 thru | or 11,
A support portion for supporting a sensor portion having the sensor surface and the ultrasonic transducer device;
Including
The sensor surface is
The ultrasonic measurement apparatus is supported by the support portion so as to be in contact with the surface of the heel. In any one of Claims 1 to 12,
The controller is
The position of the optic papilla is specified, the ultrasonic beam is irradiated to a measurement range set based on the specified position of the optic papilla, and blood is measured based on the Doppler shift amount of the ultrasonic echo. An ultrasonic measurement apparatus characterized by measuring flow information. In any one of Claims 1 thru | or 13.
The controller is
An ultrasonic measurement apparatus that measures at least one of intraocular pressure and eyeball diameter based on the ultrasonic echo. In any one of Claims 1 thru | or 14.
The controller is
An ultrasonic measurement apparatus that performs an irradiation process of irradiating a corner portion with the ultrasonic beam when the sieve plate thickness represented by the sieve plate thickness information is equal to or less than a given threshold value. In claim 15,
The controller is
Measuring intraocular pressure based on the received ultrasonic echoes,
When the sieve plate thickness is equal to or less than the given threshold value and the intraocular pressure is equal to or greater than the given pressure, the irradiation process of irradiating the corner with the ultrasonic beam is performed. Ultrasonic measuring device. An ultrasonic beam is transmitted to the optic papilla of the eyeball by an ultrasonic transducer device through the sensor surface of the ultrasonic measurement device that can contact the heel surface when the ultrasonic measurement device is mounted,
Receiving an ultrasonic echo from the ultrasonic beam;
A measurement method characterized in that, based on the received ultrasonic echoes, sieve thickness information is measured by a control unit.